JPH0433648A - Ultrasonic diagnostic device - Google Patents

Abstract

PURPOSE:To shorten the inspection time and to improve the accuracy of a BDF image by setting, for instance, the number of frames and the low flow velocity detecting function to the highest and the maximum, respectively by a BDF and detecting whether blood exists or not, detecting the quality of a blood flow by an FFT, and setting optimumly each condition of the BDF from the Doppler pattern concerned. CONSTITUTION:Ultrasonic reception of an ultrasonic raster and ultrasonic reception of a one-point Doppler are executed alternately in a rate, and a simultaneous display of BDF/FFT is executed. Accordingly, the scan is executed as B1DB1DB1D...without changing the ultrasonic raster, the device becomes a BDF/FFT simultaneous mode, and comparing with a single BDF detection range + or -PRF/2 of a conventional BDF mode, a period of the ultrasonic raster becomes half, therefore, the BDF detection range becomes + or -PRF/4 in the same way as an FFT detection range. As a result, a low flow velocity detecting function can be improved, and also, while observing the position and the direction of a blood vessel in a real time by a BDF image, a range gate of an FFT can be set quickly to the inside of the blood vessel, therefore, the operation time is shortened and an operation burden of a surgical operator can be reduced, and also, a satisfactory blood pattern can be observed.

Description

[Detailed Description of the Invention] [Object of the Invention] (Industrial Application Field) The present invention transmits and receives ultrasonic waves from an ultrasound probe to a subject using a wave transmitting/receiving circuit, and transmits and receives signals obtained thereby. The present invention relates to an ultrasonic diagnostic apparatus that detects a Doppler shift signal from a phase detector using a phase detection circuit, analyzes the frequency of the signal using a frequency analysis circuit, and displays ultrasonic information.

(Prior Art) The ultrasonic Doppler method is a method of obtaining and visualizing functional information accompanying the movement of a moving object within a living body. That is, the ultrasonic Doppler method utilizes the ultrasonic Doppler effect in which when an ultrasonic wave is reflected by a moving object, the frequency of the reflected wave shifts in proportion to the moving speed of the object. Specifically, by transmitting ultrasonic rate pulses to a living body and obtaining the frequency deviation due to the Doppler effect from the phase change of the reflected wave echo, we can obtain motion information of a moving object at the depth position where the echo was obtained. I can do it.

According to this ultrasonic Doppler method, it is possible to know the direction of the flow of blood at a position in the living body and the state of the flow, whether it is turbulent or regular.

In order to obtain blood flow information from ultrasonic echoes, the ultrasonic probe and transceiver circuit are driven to send ultrasonic pulses in a certain direction a predetermined number of times, and the received ultrasonic pulses are The acoustic wave echo is detected by a phase detection circuit to obtain phase information, that is, a signal consisting of a Doppler signal and a clutter component. This signal is converted into a digital signal by an A/D converter, clutter components are removed by a filter, and the Doppler shift signal due to blood flow is frequency analyzed by a high-speed frequency analyzer such as an autocorrelation method, and the average value of the Doppler shift is , the variance value of the Doppler shift, the average intensity of the Doppler shift, etc. Here, by performing the above-described series of processes while scanning the ultrasound beam from one side to the other in correspondence with the sector scan screen, information on two-dimensionally distributed blood flow can be detected. Then, blood flow information such as a two-dimensional blood flow velocity image showing the direction and velocity of blood flow described above, and B-mode images and M-mode images obtained by another system are processed using a DSC (digital scan converter). The images are superimposed and combined and displayed on a TV monitor, etc.

(Problems to be Solved by the Invention) By the way, in the conventional ultrasonic diagnostic apparatus described above, ultrasonic waves can be obtained by transmitting multiple rate ultrasonic waves to the same ultrasonic raster. For example, B D F (B mode) such as CFM image (two-dimensional color flow mapping image)
dopplcr rlow) image, for example, in a certain ultrasound raster B, the ultrasound is transmitted only 8 times, and then in the next ultrasound raster B2, the ultrasound is transmitted only 8 times, and this scanning is performed sequentially. Detectability V l
There is a relationship Va+In-C-PRF/(2f-n) between l1in and the ultrasound transmission pulse repetition frequency PRF. Note that n is the number of data, C is the speed of sound, and f is the ultrasonic frequency.

As a method for improving this low flow rate detection ability V 1n, an alternating skin tone method has been known. This alternating scan method (known) can be used, for example, for ultrasonic rasters.
2. B, B2... Alternate scan, for example 8
Repeat Bq B4. B IB4...
The alternating scans of . In addition, the ultrasound raster scans include Bl, B2.
B3. B4... According to this, the pulse repetition frequency PRF'' in any ultrasonic raster is equal to the previous pulse repetition frequency PRF by the number of alternate scan stages N.
It becomes 1/N of That is, PRF' -PRF/N As a result, the value of the low flow rate detection ability V sin becomes 1/N, so the low flow rate detection ability can be improved by N times.

On the other hand, in ultrasonic Doppler that transmits FFT images, when a range gate is applied to an observation point P of a certain ultrasonic raster and ultrasonic waves are transmitted a predetermined number of times, the time of the blood velocity distribution (spectrum) is determined by the frequency analysis. You can get the desired change.

However, in the past, the BDF image mode and the FFT mode were each performed independently;
After observing the position and direction of blood vessels using a BDF image in the DF mode, after a while, the mode was switched to the FFT mode, a range gate was set at the observation point, and the blood flow pattern was observed. As a result, operations took time, and images lacked real-time performance. Furthermore, it takes a considerable amount of time to search for blood vessels with low flow velocity using FFT.

SUMMARY OF THE INVENTION Therefore, an object of the present invention is to provide an ultrasonic diagnostic apparatus that can shorten operating time and reduce the operating burden on the operator through simple operations, improve the resolution of BDF images, and improve the accuracy of blood flow. It's about doing.

[Structure of the Invention] (Means for Solving the Problems) In order to solve the above problems and achieve the objects, the present invention takes the following measures. The present invention provides a BDF means for obtaining a BDF image that superimposes a blood flow image on a B-mode image based on a received signal obtained by transmitting and receiving ultrasonic waves from an ultrasound probe to a subject; FF7 means for obtaining an FFT image based on the
a first control means that controls at least a wave transmitting/receiving circuit to perform multiple ultrasound receptions for each rate to perform multiple ultrasound receptions to obtain one ultrasound raster of the BDF image and multiple ultrasound receptions to obtain the FFT image; Based on the presence or absence of blood flow detected by the BDF means, the blood flow velocity at the blood flow location set by the FF7 means is used to obtain the average flow velocity, power, and dispersion, and a Doppler pattern is extracted and adapted to this. The image forming apparatus is characterized by comprising a second control means for setting various conditions for the BDF image and supplying these to at least the BDF means and the first control means.

The second control means sets the rate frequency based on the maximum average flow velocity, sets the low flow velocity detection ability based on the minimum average flow velocity, and determines the pulsatility of the blood flow based on the difference between the maximum and minimum average flow velocity. a setting means for setting the number of frames based on the rate frequency and the low flow velocity detection ability; a means for determining that it is white noise when the dispersion exceeds a predetermined value; The lfI characteristic is that the method includes means for setting each condition for the means.

(Effects) By taking such measures, the following effects are achieved. BDF/FFT is performed by alternating the rate of ultrasound reception of ultrasound raster and reception of 1-point Doppler ultrasound.
It is a device that simultaneously displays BDF images and FFT images, and detects the presence or absence of blood flow by setting the BDF to the maximum number of frames and maximum low flow rate detection ability, by utilizing the respective characteristics of BDF images and FFT images,
The quality of the blood flow (maximum velocity, minimum velocity 1 pulsatility) is detected by FFT by adjusting the FFT range gate to the location of blood flow, and each condition for BDF is optimally set using this Doppler pattern. Clinically necessary information such as the location of the flow, the direction of the blood vessel, and the pulsatility can be obtained without having to worry about device settings. As a result, the optimal setting of BDF conditions can be speeded up, thereby shortening the inspection time, reducing the operational burden on the operator, and improving the accuracy of the BDF image.

(Embodiment) FIG. 1 is a schematic block diagram showing a sector electronic scanning type ultrasound diagnostic device as an embodiment of the ultrasound diagnostic device according to the present invention, FIG. 2 is a schematic diagram showing a BDF/FFT simultaneous mode, and FIG. FIG. 3 is a schematic diagram showing the BDF detection range and FFT detection range in the BDF and BDF/FFT simultaneous modes, and FIG. 4 is a schematic diagram showing the BDF image and FFT image.

This example will be explained below. The ultrasonic diagnostic device includes an ultrasonic probe 1. Transmission/reception circuit 2. B-mode processing section 3, phase detection circuit 4. FFT unit5. CFM unit 6, DSC
7, has a TV monitor 8.

The device also includes a rate generating section 9 that generates rate pulses. a raster control unit 15 as a first control means for obtaining ultrasonic rasters in different directions for each rate pulse;
H.

That is, the raster control unit 15 controls one ultrasonic raster (for example, Bl) in sector scanning as shown in FIG.
Transmission and reception of ultrasound is performed multiple times to obtain an FFT image using 1-point Doppler D, and transmission and reception of ultrasound is performed multiple times at alternate rates without changing the ultrasound raster B1. Controls circuit 2. Then, the raster control unit 15 performs scanning alternately, for example, BIDBID, etc., to create a simultaneous mode of a BDF image (an image in which a blood flow image is superimposed on a B-mode image) and an FFT image. The raster control section 15 also controls the B mode processing section 3. It controls the CFM unit 6 and DSC 7.

The ultrasonic probe 1 includes a plurality of transducers,
Each transducer transmits ultrasonic waves in a predetermined direction. The wave transmitting/receiving circuit 2 drives the ultrasound probe 1 to transmit data. Therefore, the ultrasonic probe 1 is
The ultrasonic waves generated are transmitted to the subject, and the reflected ultrasonic waves from the subject are received by the same transducer of the ultrasonic probe 1.

The B-mode processing section 3 performs envelope detection on the received signal input from the wave transmitting/receiving circuit 2 to obtain tomographic image data (B-mode image data), and outputs this tomographic image data to the DSC 7.

The phase detection circuit 4 phase-detects the received signal inputted from the wave transmitting/receiving circuit 2 to obtain a Doppler shift signal consisting of a Doppler signal due to blood flow and a clutter component.

The FFT 5 performs frequency analysis on the Doppler shift signal manually input from the phase detection circuit 4, and outputs FFT image data to the DSC 7 for obtaining temporal changes in blood flow velocity. This FF
T5 is a range gate section 5A and a BPF5B (band pass filter).

ADC5C (Analog to Digital Converter).

It consists of FFT5D. The range gate unit 5A applies a range gate to a certain arbitrary observation point on the ultrasonic scanning line on the TV monitor 8, and takes in the Doppler shift signal at this observation point from the phase detection circuit 4. B
PF5B extracts a specific frequency component of the Doppler shift signal. Further, the ADC 5C converts the extracted Doppler shift signal into a digital signal. The FFT 5D performs frequency analysis on the digital signal to obtain FFT image data, and outputs the FFT image data to the DSC 7.

The FFT image obtained by the FFT unit 5 has its low flow velocity detection ability and aliasing speed determined by setting conditions such as the number of calculation data and the number of sampling frequencies.

On the other hand, the CFM unit 6 (color flow mapping) obtains a phase change from the multi-rate Doppler shift signal inputted from the phase detection circuit 4, and performs frequency analysis to obtain the average velocity, flow velocity, etc. Note that the BDF image obtained by the CFM unit 6 and the B-mode processing section 3 has the same number of sample data.

By setting each condition of the number of samplings (rate frequency of ultrasonic transmission/reception/number of alternate scan steps), the number of frames, low flow velocity detection ability, and return speed are determined.

The CFM unit 6 includes an ADC 6A and an AD converting the Doppler shift signal manually inputted from the phase detection circuit 4 into digital form.
A digital filter 6B that extracts only the Doppler signal from the digital Doppler shift signal obtained by the digital filter 6A, a correlator 6C that performs frequency analysis on the Doppler signal obtained by the digital filter 6B, and a correlator 6.
Based on the frequency analysis output obtained by C, the average velocity of blood flow,
It consists of an arithmetic unit 6D that calculates power and dispersion.

The DSC 7 includes the B mode processing section 3; r"r;"r
Unit 5. Data input from the CFM unit 6 is written, and these data are converted into TV scans and output to the TV monitor 8.

Next, the operation of the embodiment configured as described above will be explained. When a rate pulse is manually input from the rate generator 9 to the raster control unit 15, the raster control unit 15 transmits and receives ultrasonic waves a plurality of times to obtain one ultrasonic raster (for example, B1) as shown in FIG. FF by 1 point Doppler D
receiving ultrasound at least multiple times to obtain a T image;
A raster signal for each rate is output without changing the ultrasonic raster B1.

Then, when the ultrasonic probe 1 is driven to transmit by the transmitter/receiver circuit 2 inputting this raster signal, the ultrasonic pulses from the ultrasonic probe 1 are transmitted in the ultrasonic raster B, DB, D, etc.
waves are transmitted in the direction of The ultrasonic pulse becomes a received signal accompanied by a Doppler shift due to blood flow flowing in the living body, and is received by the ultrasonic probe 1 and the wave transmitting/receiving circuit 2. Further, the B mode processing unit 3 detects the B mode, and this detection signal is output to the DSC 7. Detected by the phase detection circuit 4, a signal consisting of a Doppler shift signal due to blood flow and a clutter component is obtained. Clutter components are removed from the output of the phase detection circuit 4 to obtain a Doppler shift signal.

Furthermore, this signal is frequency-analyzed by FFT5 to obtain blood flow velocity data consisting of the direction of blood flow (forward flow or reverse flow) and spectrum.

Further, the signal from the phase detection circuit 4 is subjected to color flow mapping processing by the CFM unit 6 which manually inputs the raster signal from the raster control section 15. These data are then written to the DS07, subjected to TV scan conversion, and displayed as an FFT image and a BD image on the TV monitor 8 as shown in FIG.
The F image is displayed simultaneously.

Therefore, as shown in FIG. 3, B, DB without changing the ultrasound raster (ie, the number of alternating stages is 1).

DB, D, etc. are scanned and the BDF/FFT simultaneous mode is entered. In other words, B due to the conventional BDF mode alone
Compared to the DF detection range ±PRF/2, the period of the ultrasonic raster is halved, so the BDF detection range becomes ±PRF/4 similarly to the FFT detection range. As a result, the low flow velocity detection ability can be improved, and the FFT range gate can be quickly set inside the blood vessel while observing the position and direction of the blood vessel in real time using a BDF image. As a result, the operation time can be shortened, the operational burden on the operator can be reduced, and a good blood flow pattern can be observed. As a modification of the above embodiment, for example, B, DB2DB, D
The ultrasonic rasters may be scanned alternately as shown in the following, and the ultrasonic rasters B, ci゛i and
Since it is 1/4 cycle compared to DF mode alone, BD
The F detection range can be improved to ±PRF/8.

As a result, the BDF image detects blood flow signals up to the vicinity of the blood vessel wall, which improves the embedding in the blood flow.

In other words, small blood vessels can be easily detected. Furthermore, once the location of blood flow is known from the BDF image, the FFT range gate can be set at that location, identifying arteries and veins, and determining the blood flow velocity (
E. Diagnostic information such as the degree of stenosis can be quickly obtained from the blood flow pattern, and the operating burden on the operator can be reduced.

Next, a second embodiment will be explained. The second embodiment is based on the first embodiment.
This is an improvement on the problem caused by the embodiment. That is,
In a BDF image obtained by a BDF scan, the location of blood flow and the direction of blood vessels can be easily seen, but the blood flow pattern is not known, so the blood flow velocity Va+In.

It is difficult to optimally set VlaX and frame rate. Further, in the FFT image, Vsln, Vmax, and pulsatile flow/steady flow can be easily detected, but it is difficult to determine the location of the blood vessel and the direction of the blood vessel without searching by moving the range gate. For this reason, simultaneous BDF/FFT scanning is performed to improve the low flow rate detection ability of BDF and investigate the location of blood flow, while observing the waveform of the blood flow situation (dynamics) using FFT.

However, in simultaneous BDF/FFT scanning, each must be set accurately together, e.g.
When the RF is changed, the sampling rates of both the BDF and FFT change, so operations to accurately match them are complicated.

Also, when determining the position of the FFT range gate, BD
Although it is based on the colored locations in the F image, blood flow cannot be detected in the BDF image unless the number of frames and low flow velocity detection ability are appropriate. Furthermore, signals other than blood flow (clutter, noise, etc.) may cause coloration, which is not appropriate.

Therefore, a method for optimizing BDF image conditions based on FFT signals is provided. FIG. 5 is a schematic block diagram showing the second embodiment, and FIG. 6 is a detailed block diagram of a CFM condition setting circuit inside the device. The second embodiment will be described in detail below with reference to the drawings.

In the second embodiment, the average flow velocity, power,
A CF that calculates the dispersion, extracts a Doppler pattern, and optimally sets each scan condition for the BDF image that matches the Doppler pattern.
From the M condition setting circuit 10 and this CFM condition setting circuit 10, frame number data, low flow rate detection ability data, and optimum PRF are obtained.
a system controller 12 that inputs data and provides optimum PRF data to the rate generation section 9, provides optimum PRF data, frame number data, and low flow velocity detection data to the raster control section 15, and provides frame number data to the CFM unit 6; We are prepared.

PRF here refers to ultrasonic pulse rate frequency, and is also simply referred to as rate frequency.

The CFM condition setting circuit 10 includes 1 as shown in FIG.
and the balance calculation section 210 and the distribution calculation section 22. MAX detection circuit 23
．． MIN detection circuit 24. Optimal PRF setting circuit 251 Pulsatility detection circuit 26. Low flow rate detection ability setting circuit 27. It consists of a frame number setting circuit 28.

The apparatus also includes a panel 5W40 having a plurality of switches corresponding to a plurality of conditions to be clinically set by the operator. The panel 5W40 has a FRAME switch for setting the frame rate, a V sin switch for setting the low flow rate detection capability, a V sin switch for setting the high flow rate detection capability, and a V IIax switch for setting the maximum depth of field. It has a DepLh switch for

Next, the operation of the second embodiment configured as described above will be explained.

(1) First, as an initial value, set the low flow rate detection ability to the minimum using the V min switch on panel 5W40, and
When the number of frames is set to the maximum using the ME switch, the system controller 12 sends a certain PRF, low flow rate detection ability, and number of frames to the rask control unit 15. Then, the three conditions and the rask signal are transmitted from the rask control unit 15 to the wave transmitting/receiving circuit 2. B mode processing section 3. This condition is given to CFM UniSoto 5 and DSC 7, and diagnostic information is displayed based on this condition. Note that when the number of frames is set to the maximum and the detectable low flow velocity is set to MIN, the blood flow signal is scanned so that it is displayed once on the TV monitor under the condition that loopback is allowed.

(2) Next, as shown in Figure 8, an arbitrary blood flow position on a certain ultrasound rask using 1-point Doppler (CI in the figure)
Adjust the FFT range gate (Pi in the figure) to one point manually or automatically using an operation console (not shown). Conditions for FFT at this time include, for example, ■range, zero shift.

Adjust the pixel shape etc. manually or automatically.

(3) Thereafter, the FFT unit 5 performs FFT calculation on the signal at one point, and the CFM condition setting circuit 10 determines the average flow velocity, power, and dispersion, and extracts a Doppler pattern. That is, based on the FFT image data from the FFT unit 5, the average flow velocity of the blood flow is determined by the average calculation section 21, and the power and dispersion are determined by the dispersion calculation section 22 based on the FFT image data.

Here, if the variance data output from the variance calculation unit 22 is a predetermined value, for example, PRF/2 or more as shown in FIG. 9, the noise determination circuit 29 recognizes it as white noise. Then, the MAX detection circuit 23 detects the maximum of the average flow velocity, and the MIN detection circuit 24 detects the minimum of the average flow velocity.

Next, the pulsatility detection circuit 26 extracts a Doppler pattern. FIG. 7 is a diagram showing the Doppler pattern of the pulsatile flow and the Doppler pattern of the steady flow. The Doppler pattern includes, for example, a pulsatile flow as shown in FIG. 7(a), a pulsatile flow (bidirectional pattern) as shown in FIG. 7(b), and a steady flow as shown in FIG. 7(c). There are various patterns such as flow.

The steady flow is applied to veins or arteries near the periphery, and the pulsatile flow is applied to arteries, cardiac cavities, etc. according to the characteristics of each. Here, as shown in FIG. 7, pulsatility is evaluated by PI=(ab)/a. a is the maximum value and b is the minimum value.

If the difference (change width) between the maximum and minimum average flow velocity changes to more than the heartbeat cycle, for example, PRF/4, the pulsatility detection circuit 26 recognizes that the flow is pulsatile, and if the difference is less than or equal to the above value or If it is a smaller value, for example, PRF/6 or less, it is recognized as a steady flow. A Doppler pattern is extracted.

(4) Next, optimize the conditions for the BDF image. That is, when it is determined by the noise determination circuit 29 that the noise is not white noise, the optimum PRF setting circuit 25 sets the optimum rate frequency based on the maximum average flow velocity, and the low flow velocity detection capability setting circuit 27 sets the optimum rate frequency based on the maximum average flow velocity. The low flow rate detection ability is set based on the minimum, and the frame number setting circuit 28
The number of frames is set based on the pulsatility of the blood flow, the rate frequency, and low flow velocity detection ability. Here, for example, if the flow is pulsating as shown in Fig. 7(a), the high waterfall velocity detection ability is automatically set preferentially, and if the flow is pulsating as shown in Fig. 7(b), the flow velocity detection ability and A high frame rate is preferentially automatically set, and in the case of a steady flow shown in FIG. 7(c), a low flow rate detectability is preferentially automatically set. Note that even for other Doppler patterns, conditions corresponding to the Doppler pattern are preferentially automatically set in the same manner as described above.

and zero shift and frame rate by the system controller 12 in steady flow or pulsatile flow.

Low flow rate detection ability and maximum flow rate detection ability are set optimally.

On the other hand, if it is determined that it is white noise, the system controller 12 erases the color display and moves the range gate to another point.

As described above, according to the present embodiment, there is provided an apparatus that simultaneously displays BDF/FFT by performing ultrasonic reception of an ultrasonic raster and one-point Doppler ultrasonic reception at alternating rates.
By utilizing the respective characteristics of DF image and FFT image, BDF
For example, set the number of frames to the maximum and the low flow velocity detection capability to the maximum to detect the presence or absence of blood flow, set the FFT range gate to the position where the blood flow exists, and use FFT to determine the quality of the blood flow (maximum velocity, minimum velocity).

pulsatility) and optimally set each condition for BDF from this Doppler pattern, so clinically necessary information such as location of blood flow, direction of blood vessel, pulsatility, etc. can be used in device settings. You get it without the hassle. As a result, the optimal setting of BDF conditions can be speeded up, and the conventional problem of coloring only a portion of blood vessels, which occurs when the number of frames is insufficient, can be resolved.

This can shorten the inspection time, reduce the operational burden on the operator, and improve the accuracy of the BDF image.

Note that the present invention is not limited to the embodiments described above. For example, as a modification of the second embodiment, in step (3) the blood flow around the range gate is distinguished as to whether it is a pulsating flow or a steady flow, so this may be color-coded. Pulsating flow is shown in red, and steady flow is shown in fruits and vegetables. It goes without saying that various other modifications can be made without departing from the gist of the present invention.

[Effects of the Invention] According to the present invention, ultrasonic raster ultrasonic reception and one-point Doppler ultrasonic reception are performed at alternate rates, and BDF
/FFT simultaneous display device, BDF image and FF image
Utilizing the respective characteristics with the T image, detect the presence or absence of blood flow by setting the BDF to the maximum number of frames and maximum low flow rate detection ability, and then adjust the FFT range gate to the position where blood flow exists and use FFT to detect the blood flow. The quality of the blood flow (maximum velocity, minimum velocity 1 pulsatility) is detected, and each condition for BDF is optimally set from this Doppler pattern, so clinically Necessary information can be obtained without having to worry about device settings. As a result, it is possible to speed up the optimal setting of BDF conditions, thereby shortening the examination time, reducing the operational burden on the operator, and providing an ultrasonic diagnostic apparatus that can improve the accuracy of BDF images.

[Brief explanation of the drawing]

Fig. 1 is a schematic block diagram showing an embodiment of the ultrasonic diagnostic apparatus according to the present invention, Fig. 2 is a schematic diagram showing BDF/FFT simultaneous mode, and Fig. 3 is a BDF detection range in BDF and BDF/FFT modes. 4 is a schematic diagram showing a BDF image and an FFT image, FIG. 5 is a schematic block diagram showing a second embodiment of the present invention, and FIG. 6 is a schematic diagram showing a CFM condition setting circuit. 7 is a diagram showing the Doppler pattern of the receiver, FIG. 8 is a schematic diagram showing the BDF image and FFT image of the second embodiment, and FIG. 9 is a diagram showing the second embodiment.
FIG. 3 is a diagram showing the power and dispersion obtained from the FFT unit of the example. 1... Ultrasonic probe, 2... Wave transmitting/receiving circuit, 3...
B mode processing section, 4... phase detection circuit, 5... CF
M unit, 5...FFT unit, 6...CFM
Unit, 7...DSC, 8...TV monitor, 9.
...Rate generation section, 10...CFM condition setting circuit, 1
2...System controller, 15...Raster control unit, 40...Panel SW0 Applicant's agent Patent attorney Takehiko Suzue No. 2 Strategy 3 Figure 4 Figure 8 Figure 9

Claims (2)

[Claims] (1) A BDF means for obtaining a BDF image that superimposes a blood flow image on a B-mode image based on a received signal obtained by transmitting and receiving ultrasonic waves from an ultrasound probe to a subject; FFT means for obtaining an FFT image; receiving ultrasound a plurality of times and performing the FFT to obtain one ultrasound raster of the BDF image;
a first control means for controlling at least a wave transmitting/receiving circuit to receive ultrasound a plurality of times at each rate in order to obtain an image; and a first control means for controlling at least a wave transmitting/receiving circuit in order to receive ultrasound a plurality of times at each rate, and setting by the FFT means based on the presence or absence of blood flow detected by the BDF means. Using the blood flow velocity at the position where the blood flow exists, the average flow velocity, power, and dispersion are determined to extract a Doppler pattern, and each condition for the BDF image that matches this is set, and these are set at least in the BDF means, the first An ultrasonic diagnostic apparatus comprising: second control means for supplying power to the control means. (2) The second control means sets the rate frequency based on the maximum average flow velocity, sets the low flow velocity detection ability based on the minimum average flow velocity, and determines the pulsatility of the blood flow based on the difference between the maximum and minimum average flow velocity. a setting means for setting the number of frames based on the rate frequency and the low flow velocity detection ability; a means for determining that it is white noise when the dispersion exceeds a predetermined value; The ultrasonic diagnostic apparatus according to claim 1, further comprising means for setting each condition for the means.