JPH09322897A - Doppler ultrasonograph - Google Patents

Abstract

PROBLEM TO BE SOLVED: To obtain the results of measurement with a simple operation by minimizing the effect of errors of a bloodstream waveform per heart beat of a subject. SOLUTION: A Doppler ultrasonograph displays a bloodstream waveform of a subject on a screen and is provided with a hemodromometer 4 in which an ultrasonic wave is received from or to the subject at a fixed repeated cycle and at least a Dopper shift component contained in an echo data thereof is detected in phase to determine a power spectrum distribution of a bloodstream velocity by an analysis of frequency, a Doppler frame memory 6 and a monitoring device 9. This apparatus is provided with a synchronizing means 5A to make each of bloodstream waveforms by heart beats synchronize the same time phase of the heart beat and a synthesizing means 5B to synthesize a plurality of bloodstream waveforms synchronized by the synchronizing means 5A.

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 equipped with a Doppler mode for displaying a blood flow velocity in an ultrasonic diagnostic apparatus for medical use, and particularly to accurately measuring a blood flow velocity. The present invention relates to an ultrasonic Doppler diagnostic device that enables

[0002]

2. Description of the Related Art FIG. 4 is a block circuit diagram of an ultrasonic Doppler diagnostic apparatus according to the prior art, FIG. 5 is an example of a monitor display of a blood flow waveform according to the prior art, and FIG. 6 is an ultrasonic Doppler used in the prior art and the present invention. FIG. 7 is a block diagram of the Doppler frame memory of the diagnostic device, and FIG.

Ultrasonic diagnostic equipment used for medical purposes includes
There is a mode called Doppler mode that displays the blood flow velocity in the body on the screen. In this Doppler mode, ultrasonic waves reflected from moving objects such as blood cells shift to a frequency slightly higher or lower than the frequency of the original transmitted ultrasonic waves in proportion to the speed of movement of these blood cells due to the Doppler effect. This is used to detect the velocity of blood flow.

A display of the blood flow waveform in the Doppler mode is shown in FIG. In FIG. 5, the vertical axis represents the Doppler frequency shift amount, which represents the blood flow velocity. Normally, the center of the display screen has a velocity of 0, and positive and negative blood flow velocities are shown above and below. Here, the positive blood flow velocity means a velocity component coming toward the ultrasonic probe, and the negative velocity means a velocity component moving away from the ultrasonic probe. The horizontal axis is the time axis, and the blood flow waveform is drawn while scrolling horizontally. The brightness of the blood flow waveform represents the power of the signal of the velocity component.

Next, a configuration example of an ultrasonic diagnostic apparatus according to the prior art will be described with reference to FIG. In FIG. 4, the ultrasonic Doppler diagnostic apparatus detects a transmission / reception circuit 2 that transmits an ultrasonic wave to the ultrasonic probe 1 and receives an echo from a subject, and an echo signal 21 from the transmission / reception circuit 2 with a reference wave 31. Detection circuit 33 and filter 34, and detection circuit 36 and filter 37 for detecting echo signal 21 from transmitter / receiver circuit 2 with reference wave 32.
A Doppler signal extraction circuit 3 for extracting the Doppler shift frequency, A / D converters 35 and 38, and a frequency analysis unit 41 for calculating and analyzing the power spectrum of the Doppler shift component,
Blood flow rate analyzing means 4 and a Doppler frame memory 6
A scroll control circuit 7, a display memory 8 and a monitor 9.

In such a configuration, ultrasonic waves are transmitted to the ultrasonic probe 1, and echoes from the subject are received by the transmission / reception circuit 2. This echo signal 21 is quadrature-detected by the detection circuits 33 and 36 using two reference waves 31 and 32 that are equal in frequency to the transmission frequency and are 90 degrees out of phase with each other. By taking it out, a Doppler shift signal can be obtained. This Doppler shift signal is 90 degrees out of phase, and one is considered as one complex number with the real part and the other as the imaginary part, and after being digitized by the A / D converters 35 and 38, for example, the fast Fourier transform (hereinafter , The fast Fourier transform is abbreviated as FFT), and the like, by performing frequency analysis processing such as a method, a velocity spectrum including positive and negative can be obtained.

The frequency analysis processing by the FFT for one time corresponds to one line in the vertical direction of the display screen of the monitor 9. That is, assuming that the display screen is composed of, for example, 512 × 512 pixels, data of 1 horizontal pixel × 512 vertical pixels can be obtained by one FFT frequency analysis. Depending on the resolution of the FFT frequency analysis processing, data for 512 pixels in the vertical direction may not be obtained, but in that case, data for 512 pixels is created by linearly interpolating the data in the middle portion.

The vertical 5 obtained as a result of the FFT frequency analysis processing.
Data for 12 pixels is arranged on the rightmost vertical line of the display screen. When the next FFT frequency analysis is performed, the entire display screen scrolls one pixel to the left, the data displayed in the leftmost vertical line disappears, and the latest data becomes the rightmost vertical line. be painted. Actually, the data for 512 pixels in the vertical direction obtained by one FFT frequency analysis is written in the Doppler frame memory 6. In FIG. 6, the column address j of the Doppler frame memory 6 corresponds to the time axis of the display screen, and one column address j corresponds to one F
This is the result of FT frequency analysis. Doppler frame memory 6
The row address i of corresponds to each blood flow velocity component. At each address (i, j) of the Doppler frame memory 6, the brightness data of the display screen corresponding to the power spectrum x (i, j) of a certain blood flow velocity component at a certain time is written.

The data written in the Doppler frame memory 6 is further sent to the display memory 8. At this time, the scroll processing is performed by the scroll control circuit 7. The display memory 8 stores the results obtained by synthesizing (for example, taking a logical OR) data such as the Doppler image showing the above-mentioned blood flow waveform, the tomographic image of the examination part of the subject whose description is omitted, and further the character data. The data is written and finally becomes the data to be displayed on the CRT monitor device 9. As the Doppler frame memory 6 and the display memory 8, a dual port RAM for images is usually used.

Next, a method of using the Doppler mode using the ultrasonic Doppler diagnostic apparatus will be described. This method of using the Doppler mode has been used in the past to determine the presence or absence of blood regurgitation and the degree of regurgitation. In recent years, however, the color Doppler mode that two-dimensionally displays the average blood flow velocity has been developed. , The use of this Doppler mode blood flow waveform has decreased.
However, the spectrum display method as shown in FIG. 5 is used for measuring the peak value of the blood flow waveform and obtaining a numerical index based on the measured value to evaluate the function of the heart. Is the mainstream.

As such a numerical index, for example,
According to the simple Bernoulli's theorem, if the pressure difference is ΔP (mmHg) and the blood flow velocity is V (m / s),

[0012]

[Equation 1] Therefore, the intracardiac pressure can be estimated by measuring the blood flow waveform in the Doppler mode. The left ventricular inflow waveform of the heart has a waveform as shown in FIG. 7, but the ratio of the peak velocities of the portion called E wave and the portion called A wave, that is, A / E Can be evaluated for left ventricular diastolic function. In addition to the above description, there are methods for evaluating cardiac function based on the measured values of several Doppler spectrum waveforms.

[0013]

The measurement of the blood flow waveform in the Doppler mode is performed by temporarily stopping the scroll of the spectrum display and moving the measurement marker by moving the trackball, the cursor key or the like. Since it takes a lot of time and effort, the cardiac function is usually evaluated by the measurement result of one representative blood flow waveform among a plurality of blood flow waveforms. However, the blood flow waveform is due to the movement of the subject's heart, and since the blood flow waveform is slightly different for each heartbeat, there is an error in the measurement results depending on which heartbeat waveform was measured. It will be included.

By using the waveforms of the heartbeats of a plurality of times and measuring the averages a plurality of times, the fluctuations of the heartbeats can be averaged, but one index is obtained by performing such a plurality of measurements. This is a factor that increases labor and time,
It is not a realistic solution in the actual medical field.
Further, depending on the diagnosis content, the waveform formed by each peak value in the data measured multiple times may have an important meaning instead of the average data measured multiple times.

The present invention has been made in view of the above points, and an object thereof is to solve the above-mentioned problems and to simplify the measurement result for reducing the influence of the error of the blood flow waveform for each heartbeat of the subject. An object is to provide an ultrasonic Doppler diagnostic device that can be obtained by operation.

[0016]

In order to achieve the above object, in the present invention, ultrasonic waves are transmitted / received to / from an object, at least the Doppler shift component included in the echo data is phase-detected, and the frequency is analyzed. In an ultrasonic Doppler diagnostic apparatus that includes a blood flow velocity analysis unit for obtaining a power spectrum distribution of blood flow velocity, a Doppler frame memory, and a monitor device, and displays the blood flow waveform of a subject on a screen, The synchronizing means for synchronizing the blood flow waveform of 1) with the same time phase of the heartbeat, and the synthesizing means for synthesizing the blood flow waveforms of a plurality of times synchronized by the synchronizing means.

With the above configuration, the time phases of the blood flow waveforms of a plurality of heart beats are synchronized, the average or peak of the brightness is taken and synthesized, and an image is displayed so that one blood flow waveform is obtained without scrolling. Can be displayed. Therefore, it is possible to measure a blood flow waveform obtained by combining blood flow waveforms of a plurality of heartbeats with one measurement, and it is possible to cancel data having different blood flow velocities for each heartbeat. Further, when the average luminance is used as the synthesizing means, random noise is reduced, so that the boundary between the blood flow and the noise can be easily distinguished, and the marker alignment at the time of measurement can be easily performed.

Further, the synchronizing means detects the data having a magnitude equal to or larger than the predetermined power spectrum in the region equal to or higher than the predetermined Doppler shift frequency from the power spectrum data of the blood flow velocity by the blood flow velocity analyzing means. Synchronization can be performed by. With the above configuration, the blood flow waveform itself can be used as the simplest means for synchronizing the blood flow waveform.

The ultrasonic Doppler diagnostic apparatus further comprises means for detecting an electrocardiographic waveform, and the synchronizing means can perform synchronization by detecting a change in the electrocardiographic waveform. Further, the ultrasonic Doppler diagnostic apparatus includes means for detecting a heart sound waveform, and the synchronization means can perform synchronization by detecting a change in the heart sound waveform. With the above-described configuration, an ECG (electrocardiogram) waveform or P that is captured as data in the same ultrasonic diagnostic apparatus as a means for synchronizing blood flow waveforms.
Synchronization can be performed by using a CG (cardiogram) waveform as a trigger.

Further, the synthesizing means can synchronize the blood flow waveform data a plurality of times by the synchronizing means, and can take an arithmetic mean of the data for each corresponding same time phase and Doppler shift frequency. Further, the synthesizing means can synchronize the blood flow waveform data a plurality of times by the synchronizing means, and can take the maximum value of the data for each corresponding same time phase and Doppler shift frequency.

With the above configuration, the same time phase for each heartbeat
The average value of the brightness data at the same blood flow velocity can be taken, or the peak value of the brightness data can be taken.

[0022]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS FIG. 1 is a block circuit diagram of an ultrasonic Doppler diagnostic apparatus according to one embodiment of the present invention, FIG. 2 is a block circuit diagram of an ultrasonic Doppler diagnostic apparatus according to another embodiment, and FIG. FIG. 8 is an example diagram of a monitor display screen of a blood flow waveform according to one embodiment, and the same members corresponding to FIGS. 4 to 7 are denoted by the same reference numerals.

The basic configuration of the ultrasonic Doppler diagnostic apparatus shown in FIGS. 1 and 2 is the same as that of the prior art ultrasonic Doppler diagnostic apparatus shown in FIG. Other than the addition of a synchronizing means for synchronizing the heartbeat in the same time phase and a synthesizing means for synthesizing N blood flow waveforms a plurality of times, and the point that the scroll control circuit is omitted in the illustrated example The configuration is the same. FIG.
Since the configuration of the Doppler frame memory described in 1. is the same, detailed description thereof will be omitted, and the basic configuration of the ultrasonic Doppler diagnostic apparatus of one embodiment will be briefly described.

In FIG. 1, the ultrasonic Doppler diagnostic apparatus is
A transmission / reception circuit 2 that transmits an ultrasonic wave to the ultrasonic probe 1 and receives an echo from a subject, a detection circuit 33 that detects an echo signal 21 from the transmission / reception circuit 2 with a reference wave 31, a filter 34, and a transmission / reception circuit A detection circuit 36 that detects the echo signal 21 from 2 with a reference wave 32, a filter 37, and a Doppler signal extraction circuit 3 that extracts the Doppler shift frequency, A / D converters 35 and 38, and this A / D conversion The blood flow velocity analyzing means 4 for frequency-analyzing the converted data of the instruments 35 and 38 and for obtaining the power spectrum distribution of the blood flow velocity together with the frequency analysis unit 41, and the synchronization buffer for temporarily storing the power spectrum data of the frequency analysis unit 41 A memory 51 and a synchronization timing control circuit for synchronizing the blood flow waveform of each heartbeat with the same time phase of the heartbeat.
A synchronization means 5A composed of 52, an adder 54, a Doppler frame memory 6 and a divider 55. A control signal from the synchronization timing control circuit 52 causes a synchronization buffer memory 51 The data and the corresponding data from the Doppler frame memory 6 are added by the adder 54, the addition result is stored in the corresponding address position of the Doppler frame memory 6, and the addition processing is performed N times predetermined addition processing. Then, the divider 55 is provided with a synthesizing means 5B for synthesizing N times the blood flow waveform by dividing it by N, a display monitor 8 and a CRT monitor device 9.

In such a structure, the ultrasonic probe 1 is applied to the examination site of the subject, and ultrasonic waves are transmitted to this site,
The echo signal 21 from the subject is received, the Doppler signal extraction circuit 3 extracts the Doppler shift frequency, and the frequency analysis unit 41 frequency-analyzes this Doppler shift frequency to obtain the power spectrum distribution of the blood flow velocity. The power spectrum data of the frequency analysis unit 41 is temporarily stored in the synchronization buffer memory 51. Data is written in the synchronization buffer memory 51 in the same configuration as the Doppler frame memory 6 described in the prior art shown in FIG.

[0026]

【Example】

(Embodiment 1) Next, a synchronization means 5A for synchronizing the blood flow waveform for each time according to the present invention with the same time phase of the heartbeat.
Will be described with reference to FIGS. 1 and 3. On the display screen shown in FIG. 3, the time points indicated by the vertical arrows ↑ are the timing points for synchronizing the heartbeats. This timing point is
In one embodiment illustrated by the solid line in FIG. 1, the frequency analysis unit 41
The frequency-analyzed data itself is used. That is, the synchronizing means 5A examines the luminance data of the portion corresponding to the predetermined Doppler shift frequency f0 or more from the power spectrum data of the blood flow velocity by the blood flow velocity analyzing means 4, and determines the luminance data in advance in this luminance data. Examine whether there is a power spectrum larger than x0. If there is no brightness data above the predetermined power spectrum x0,
The analysis result of the frequency analysis unit 41 at this time is written in one row of the synchronization buffer memory 51 and waits for the next frequency analysis result. When there is brightness data with a power spectrum of x0 or more, which is set in advance, the time of this frequency analysis
Let t0 be the reference time point for synchronization.

That is, the data of the frequency analysis result corresponding to the shaded portion in FIG. 3 is examined from the time of the left column, and in this column, the preset power spectrum set value x0 is used. The frequency analysis result in which one or more pieces of large luminance data exist is set as the reference time point t0 of the timing for synchronizing the heartbeats. The position on the display screen where the reference time point t0 is to be arranged is determined in advance. Now, if this reference time point is taken as the left end of the display screen, the first part of the rising edge of the blood flow waveform will not be displayed. To prevent this drawback,
The synchronization buffer memory 51 also stores the data before the reference time point so that the data before the reference time point t0 of the synchronization timing can be displayed. Conversely, if the synchronization reference time t0 may be displayed at the left end, or if the screen after a certain time has elapsed from the synchronization may be displayed at the left end, the synchronization buffer memory 51 is not always necessary. Absent.

By taking such synchronization timing,
Which column address (j0) in the synchronization buffer memory 51 corresponds to the left end of the screen is determined. Therefore, the frequency analysis result data is sent to the Doppler frame memory 6 in order from the leftmost column on the display screen of the synchronization buffer memory 51. At this time, the luminance data x (i, j) for each address (i, j) in the synchronization buffer memory 51 and the data for each corresponding address (i, j) in the Doppler frame memory 6 are added by the adder 54. The addition result becomes the data newly written in the Doppler frame memory 6. At the first time point when synchronization is started, all data in the Doppler frame memory 6 are cleared to 0. In this way, the Doppler frame memory 6 stores the addition result of data by N heartbeats multiple times at each address (i, j).
Is written to. When transferring the written data to the display memory 8, the number of times of addition of the data by the heartbeat is N
In the case of the number of times, the divider 55 divides the number by N and synthesizes the blood flow waveform of N times a plurality of times, thereby performing the averaging process.
In the display memory 8, an average value of N heartbeats can be written for each address.

When the data is transferred from the Doppler frame memory 6 to the display memory 8, unlike the prior art,
Here, the scroll control 7 is not performed. When the synchronization timing is detected by a new heartbeat, a new average result is displayed, but the horizontal axis of the display screen always represents the same time phase of the heartbeat. As described above, the average result of a plurality of heartbeats can be displayed on the display screen. However, when looking for a sample point for Doppler detection while looking at the blood flow waveform, it is necessary to look at an image by a method of the related art that does not take average result data. Therefore, the actual ultrasonic diagnostic apparatus includes not only the constituent elements of the present invention shown in FIG. 1 but also the constituent elements of the conventional ultrasonic diagnostic apparatus shown in FIG. In the present embodiment, the blood flow waveform is individually scroll-displayed by the same operation procedure as that performed by the conventional ultrasonic diagnostic apparatus, and the person operating the ultrasonic diagnostic apparatus operates / instructs with a switch or the like. The display mode can be changed to display the average result as described.

Although one embodiment of the present invention has been described above, the basic structure and method can be realized in several different embodiments with almost the same structure. (Embodiment 2) First, regarding the timing of the synchronization means 5A, as described above, the frequency analysis data of the frequency analysis section 41 is taken into the synchronization timing control circuit 52, and the synchronization timing is controlled by this synchronization timing control circuit 52. Judging from the above, the frequency-analyzed data has a certain width and includes noise components, so the time axis cannot be perfectly adjusted for each heartbeat, and the peak position of the heartbeat will shift. Often.

Therefore, the ECG is used as the synchronization timing.
It is possible to use (electrocardiogram). Many ultrasonic diagnostic devices also have the ECG function,
It is performed to synchronize a tomographic image with an ECG and display only a tomographic image of a time phase having a heart beat. Using the trigger signal used at this time, the time when the trigger signal is input may be set as the synchronization reference time t0. Also, like the ECG, the PCG
There are many ultrasonic diagnostic devices with the function of (cardiogram), PCG
It is also possible to use this signal as the trigger signal and set the time when this trigger signal is input as the synchronization reference time t0. In addition, E
In order to use CG and PCG for synchronization, it is necessary to attach not only an ultrasonic probe to the subject but also an ECG and PCG probe.

The above structure has a biosensor 57 shown by a dotted line in FIG. 1, which is an electrocardiographic sensor or a heart sound sensor, and a sensor amplifier 58 for amplifying an output signal of the biosensor 57.
In place of the synchronization means using the frequency analysis data of the frequency analysis unit 41 shown by the solid line, the electrocardiographic waveform or the electroacoustic waveform from the biosensor 57 is input to the synchronization timing control circuit 52, It is possible to synchronize the blood flow waveform of N times with the same time phase. Further, for example, when an ECG (electrocardiogram) is used, the ECG device has a built-in trigger signal generation unit for synchronizing the tomographic images, and therefore the trigger signal may be used as the timing for synchronization. .

(Embodiment 3) Next, a synthesizing means 5C for synthesizing N blood flow waveforms a plurality of times will be described with reference to FIG. In the description of the above (Example 2), the synthesis of the blood flow waveform is performed by averaging the luminance data of each heartbeat. By averaging the brightness data of the blood flow waveform, the random noise included in the blood flow waveform is reduced, but the peaks of the individual waveforms are also averaged. When it is desired to detect the peak velocity of the blood flow, it may be desired to measure the maximum of the peaks of multiple heartbeats. In such a case, it is preferable to display the one having the maximum brightness among a plurality of heartbeats rather than taking the average of the brightness.

FIG. 2 is a block circuit diagram of an ultrasonic Doppler diagnostic apparatus according to another embodiment for detecting the peak velocity of the blood flow. The difference between the ultrasonic Doppler diagnostic apparatus shown in FIG. 2 and the block circuit diagram of the ultrasonic Doppler diagnostic apparatus in FIG. 1 is that the synthesizing means 5C in FIG. It is a point. In FIG. 2, the synthesizing means 5C includes a maximum value selection circuit 56 and a Doppler frame memory 6.

In such a configuration, the maximum value selection circuit 56
Compares the luminance data x (i, j) for each address (i, j) in the synchronization buffer memory 51 with the data for each corresponding address (i, j) in the Doppler frame memory 6 and finds a larger value. The other data is newly written in the corresponding address (i, j) area of the Doppler frame memory 6. At the beginning of synchronization, the data in the Doppler frame memory 6 is all 0
Clear it. In this way, the data of N heartbeats are compared a plurality of times in the Doppler frame memory 6, and the largest data, that is, the maximum value, can be written in each address (i, j).

However, when the luminance peak value is obtained in this way, unlike the case where the synthesizing means performs the averaging process, the noise once generated remains without being reduced, so that the noise on the screen increases. I will end up.

[0037]

As described above, according to the configuration of the present invention, the Doppler waveform generated by each heartbeat is temporally synchronized, and the Doppler waveform of a plurality of synchronized heartbeats is averaged or peaked in luminance. By combining and displaying with 1
By performing the measurement once, it is possible to obtain a measurement value that does not include a variation error for each heartbeat.

The synthesis of waveforms by a plurality of heartbeats can be easily performed by holding the ultrasonic probe applied to the subject for a few seconds to a dozen seconds after the synthesis is started. In addition, when the average of luminance is used as a means of waveform synthesis, randomizing noise is reduced by the averaging process. Therefore, when Doppler gain is increased, for example, when examining minute blood flow, noise also increases and noise is increased. There is also an effect of improving the problem that it becomes difficult to distinguish the boundary between the blood flow waveform and.

[Brief description of drawings]

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

FIG. 2 is a block circuit diagram of an ultrasonic Doppler diagnostic apparatus according to another embodiment.

FIG. 3 is an example of a monitor display screen of a blood flow waveform according to an embodiment of the present invention.

FIG. 4 is a block circuit diagram of an ultrasonic Doppler diagnostic apparatus according to the related art.

FIG. 5 is a diagram showing an example of a monitor display of a blood flow waveform according to a conventional technique.

FIG. 6 is a configuration diagram of a Doppler frame memory of an ultrasonic Doppler diagnostic apparatus used in the related art and the present invention.

FIG. 7 is an example diagram of a left ventricular inflow waveform

[Explanation of symbols]

 1 Ultrasonic probe 2 Transmission / reception circuit 3 Doppler signal extraction circuit 31,32 Reference wave 33,36 Detection circuit 34,37 Filter 35,38 A / D converter 33,43 Buffer memory 4 Blood flow rate analysis means 41 Frequency analysis section 5A Synchronizing means 5B, 5c Synthesizing means 51 Synchronous buffer memory 52 Synchronous timing control circuit 53 Synchronous buffer memory output data 54 Adder 55 Divider 56 Maximum value selection circuit 57 Biosensor 58 Amplifier 6 Doppler frame memory 7 Scroll control Circuit 8 Display memory 9 CRT monitor device t0 Sync timing i, j Matrix address of memory x Luminance data

Claims (6)

[Claims] 1. A blood flow velocity analyzing means for transmitting and receiving ultrasonic waves to and from a subject, phase-detecting at least a Doppler shift component included in the echo data, and performing frequency analysis to obtain a power spectrum distribution of blood flow velocity. In an ultrasonic Doppler diagnostic apparatus that includes a Doppler frame memory and a monitor device and displays the blood flow waveform of a subject on a screen, a synchronization unit that synchronizes the blood flow waveform of each heartbeat with the same time phase of the heartbeat. An ultrasonic Doppler diagnostic apparatus comprising: a synthesizing unit configured to synthesize a plurality of blood flow waveforms synchronized by the synchronizing unit. 2. The ultrasonic Doppler diagnostic apparatus according to claim 1, wherein the synchronizing means has a predetermined value in a region above a predetermined Doppler shift frequency from the power spectrum data of the blood flow velocity by the blood flow velocity analyzing means. The ultrasonic Doppler diagnostic apparatus is characterized in that synchronization is performed by detecting data having a power spectrum larger than a predetermined power spectrum. 3. The ultrasonic Doppler diagnostic apparatus according to claim 1, wherein the ultrasonic Doppler diagnostic apparatus includes means for detecting an electrocardiographic waveform, and the synchronizing means detects the change in the electrocardiographic waveform. An ultrasonic Doppler diagnostic apparatus characterized by performing synchronization. 4. The ultrasonic Doppler diagnostic apparatus according to claim 1, wherein the ultrasonic Doppler diagnostic apparatus includes means for detecting a heart sound waveform, and the synchronizing means synchronizes by detecting a change in the heart sound waveform. An ultrasonic Doppler diagnostic apparatus characterized by: 5. The ultrasonic Doppler diagnostic apparatus according to any one of claims 1 to 4, wherein the synthesizing means synchronizes the blood flow waveform data of a plurality of times by the synchronizing means, and responds to each other. An ultrasonic Doppler diagnostic apparatus characterized by taking an arithmetic mean of data for each temporary phase and Doppler shift frequency. 6. The ultrasonic Doppler diagnostic apparatus according to any one of claims 1 to 4, wherein the synthesizing means synchronizes the blood flow waveform data of a plurality of times by the synchronizing means, and responds to each other. An ultrasonic Doppler diagnostic apparatus, wherein the maximum value of data is taken for each temporary phase and Doppler shift frequency.