JP3153316B2 - Ultrasound diagnostic equipment - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a medical ultrasonic diagnostic apparatus which irradiates an ultrasonic wave to a subject and visualizes the inside of the subject by a reflected signal, and more particularly to a medical ultrasonic diagnostic apparatus utilizing the Doppler effect. The present invention relates to an ultrasonic diagnostic apparatus with a Doppler function that visualizes internal movements (blood flow dynamics and the like).

[0002] Ultrasound diagnostic apparatuses have a B-mode function for imaging the internal structure of a subject and a Doppler function for imaging information relating to movement such as blood flow. The B-mode function is
The object is scanned with a narrowly focused ultrasonic beam, the reflected signal is subjected to luminance modulation, and a B-mode tomographic image is obtained. The B-mode tomographic image is usually displayed on a monitor as a monochrome image having gradation.

On the other hand, the Doppler function utilizes the principle that a reflected signal from a moving reflecting / scattering body such as a blood flow shifts in frequency by the Doppler effect, and analyzes the shift amount to visualize the dynamics.

The Doppler function includes a pulse Doppler (PW).
D) and a function called color flow mapping (CFM). The pulse Doppler (PWD)
Attention is paid to the dynamics of an arbitrary point (sample volume) in the B-mode tomographic image, and its frequency shift is obtained as a spectrum by a frequency analysis method such as fast Fourier transform (FFT). Become

[0005] Therefore, the flow velocity of the region of interest (region of interest),
While it is easy to recognize the time change, for example, when grasping the blood flow dynamics of the whole heart chamber, the sample volume is sequentially moved and observed thoroughly, which requires a great deal of diagnostic time.

The color flow map (CFM) improves this point, and obtains a wide range of motion (average flow velocity) in the B-mode tomographic image by a method called an autocorrelation method.
Superimpose on the mode image. At this time, it can be distinguished from a monochrome B-mode tomographic image by performing color display or the like.

[0007] Therefore, it is possible to grasp the whole picture of the movement, and to easily find an abnormal part such as a valve regurgitation or stenosis in the heart chamber. On the other hand, since the flow velocity value is expressed by the hue and brightness of the color, it is difficult to accurately grasp the flow velocity value only by looking at the image.

In general, when diagnosing abnormal tissue of abdominal tissue (for example, hepatocellular carcinoma), it is important to determine what characteristics of blood flow exist around the abnormal tissue. For example,
If an artery with a pulsating wave enters the abnormal tissue, canceration of the abnormal tissue is suspected.

In such a case, if the position of the pulsation wave is to be known from the pulse Doppler (PWD) image, it is necessary to examine the presence or absence of the pulsation wave in a plurality of regions of interest around the abnormal tissue. There is not realistic.

Therefore, on the B-mode image, an area where a pulsating wave (artery) exists, an area where a standing wave (vein) exists, and the like are displayed in one B-mode image. Necessary for improving the diagnosis speed.

[0011]

2. Description of the Related Art FIG. 8 is a view for explaining a conventional ultrasonic diagnostic apparatus. In the figure, reference numeral 1 denotes an ultrasonic transducer for transmitting and receiving ultrasonic waves, and a beam former 2
The transmission signal from the object is converted into an ultrasonic wave, and the reflected wave from the subject is converted into an electric signal.

Reference numeral 2 denotes a beam former for converging an ultrasonic beam in a scanning direction designated by the controller 11. Reference numerals 3 and 4 each digitize a signal received from each scanning direction and store the digitized signal in a display memory. Mode B-mode digital scan converter (B-mode DSC)
Department. Digital Scan Converter (DSC)
In the part, the subject, with a beam-like ultrasonic signal, for example,
When the scanning is performed in a fan shape, the echo signals of the ultrasonic waves that enter the time series are converted into digital signals, and the digital signals are stored in a bit map memory in the scanned fan shape.

A color flow map (6) for demodulating a received signal from the beam former unit 2 into a Doppler signal by a mixer and detecting an average flow velocity, dispersion, flow direction and the like by an autocorrelation method. (CFM)
Is to write the output of the color flow map (CFM) analysis unit 6 to the display memory in the same manner as the B-mode digital scan converter (B-mode DSC) units 3 and 4. Color Flow Map (CFM)
Digital Scan Converter (DS for CFM)
C) part.

A demodulator 14 demodulates the received signal from the beam former 2 using a mixer, analyzes the frequency of the Doppler signal at the sample volume position (region of interest) specified by the controller 11, and outputs a pulse for obtaining a spectrum. Doppler (PWD) analysis unit, 15 is the pulse Doppler (P
WD) A scroll memory unit that displays the spectrum obtained by the analysis unit 14 as a temporal change.

Reference numeral 16 denotes a display color of the color flow map (CFM) when the output of the color flow map (CFM) analysis section 6 is superimposed on the B-mode tomographic image and the display color of the color flow map (CFM). It is a color flow map (CFM) scale display means showing the relationship with the kinetic speed of the specimen.

Reference numeral 5a denotes the B-mode digital scan converter (B-mode DSC) units 3 and 4 and the color flow map (CFM) digital scan converter (CFM DSC) unit 7 A video processing unit that processes the memory output of the scroll memory unit 15 and creates a display signal on the display monitor 5b,
It is a display monitor that displays modal tomographic images, color flow map (CFM) images, and pulsed Doppler (PWD) images.

Reference numeral 11 denotes a control unit for controlling the entire apparatus such as scanning and display by a user operation; 12, a keyboard for performing a user operation; and 13, a sample volume setting or the like on the B-mode tomographic image. This is a setting method used to specify a region (region of interest).

In the above-mentioned conventional ultrasonic diagnostic apparatus, the B-mode tomographic image, the color flow map (CFM) image, the pulse Doppler
(PWD) The image was displayed selectively. For example, color
The flow map (CFM) image is displayed on the display monitor 5b alone.
Display monitor for B-mode tomographic image and pulsed Doppler (PWD) image
5b Split display on top.

As described above, the color flow map (CFM) image is obtained by demodulating the received signal from the beam former 2 into a Doppler signal by a mixer, and averaging the flow velocity, variance, and flow by an autocorrelation method. Is detected, the detected speed information is converted into color information, and is displayed by being superimposed on the B-mode tomographic image.

[0020]

Conventionally, a mechanism for displaying a blood flow velocity superimposed on the B-mode tomographic image has been provided.
In the ultrasonic diagnostic apparatus as described above, the flow approaching the probe and the flow moving away are only displayed in different colors,
It does not indicate flow characteristics, for example, pulsating waves, standing waves, and the like.

However, it is very important to distinguish whether the flow being observed is a pulsating flow or a steady flow. For example, as described above, in diagnosing abnormal tissue of abdominal tissue (for example, hepatocellular carcinoma), what characteristics of blood flow exist around the abnormal tissue is important. If there is an artery nearby, a pulsating flow is observed, and if there is a vein, a steady flow is observed.

However, in the conventional apparatus (see FIG. 8), for example, a change in blood flow in a B-mode image is captured by a color flow map (CFM) image.
Alternatively, the pulsed Doppler (PWD) image was used to observe the temporal flow velocity distribution at one point (region of interest) in the B-mode tomographic image to identify the blood flow dynamics around the abnormal tissue. Therefore, as described above, there is a problem that it takes a long time to make a diagnosis and is not realistic.

In view of the above-mentioned conventional disadvantages, the present invention provides a mechanism for displaying a blood flow velocity in a B-mode tomographic image, for example, a color image.
Ultrasound diagnostic equipment with a mechanism to display flow map (CFM) images and pulsed Doppler (PWD) images. Ultrasound diagnostic equipment that displays pulsation and stationary blood vessel information in one image The purpose is to provide.

[0024]

FIG. 1 to FIG. 5 are explanatory diagrams of the principle of the present invention. FIG. 1 shows an example of the configuration, and FIG. 2 shows a pulsating wave (A) and a standing wave (B). 3 and 4 show the principle of the autocorrelation function, FIG. 3 shows a function formula of the autocorrelation, and FIG. 4 shows the relationship between the blood flow velocity and the autocorrelation value or the spectrum power value. FIG. 5 shows an example of a temporal change of the display image (peak hold value of the blood flow velocity) in the process. The above problem is solved by an ultrasonic diagnostic apparatus configured as described below.

(1) In an ultrasonic diagnostic apparatus having mechanisms 6, 7, and 5 for superimposing and displaying blood flow velocity information on a B-mode image, based on information on temporal changes in blood flow velocity, Area identification means 6 and 10 for identifying the characteristics of the blood flow velocity information on the B-mode image into areas of at least three characteristics of a pulsating wave, a standing wave, and no flow, and instructing means for instructing the start and end of the identification 9 and 11, and the indicating means 9,
Within the identification time to end instruction from the start instruction identification from 11, the characteristic value ,, for each identified by the area identifying means 6, 10 area, by switching a blood flow velocity display on the B-mode image display It is constituted so that. In this case,
The area identifying means may determine that the blood flow velocity is once within the identification period.
The blood flow area where the blood flow exists even though the area exceeds the predetermined threshold
Pulsating wave from the extracted blood flow area
Is configured to extract the region of.

[0026] (2) The ultrasonic diagnostic apparatus, the
Area identification hand stage 6 and 10, near to extract the region of the pulsation wave
Alternatively, a periodicity is found using an autocorrelation function of the blood flow velocity in the blood flow region, and the blood flow is recognized as a pulsating wave.

[0027] (3) The ultrasonic diagnostic apparatus, the
Identification hand stage 6,10 a region, to extract the region of the pulsation wave
In this case , the periodicity is found by frequency analysis of the blood flow velocity in the blood flow region, and the pulse flow is recognized.

[0028] (4) In the ultrasonic diagnostic apparatus, in between the <br/> identification phase, the repetition period of the same scanning line direction, and, or the number of transmissions is configured to change to other dates .

[0029]

FIG. 1 shows the principle and operation for solving the above problems.
This will be described with reference to FIG. First, in FIG. 2D, a region A is a region where a pulsating wave exists, and a region B is a region where a steady flow exists. In region A, a pulsating wave as shown in FIG. 2 (b) is observed. The vertical axis is the blood flow velocity, and the horizontal axis is time. or,
In region B, a standing wave having no change in flow velocity as shown in FIG. 2 (c) is observed.

The distinction between the pulsating wave and the standing wave is determined in two steps. First, within the identification period shown in FIG.
If the blood flow velocity exceeds a certain level (threshold) even once, that region is defined as a blood flow region. Next, in the blood flow area, as described later, the place where the pulse wave component was observed is referred to as a pulse wave area (A),
The other blood flow region is defined as a standing wave region (B).

FIG. 4 shows a method of calculating the pulse wave component. The pulse wave component is simply a variation of the blood flow velocity, for example, by observing the variance of the blood flow velocity, if the variance value is a certain level or more, it may be a pulsating wave, and if it is less than a certain level, it may be a steady flow FIGS. 3 and 4 show an example in which, for example, an autocorrelation function is calculated to further increase the accuracy.

Hereinafter, a method of identifying a pulsating wave using the autocorrelation function will be described. First, the autocorrelation function is defined by equation (E) shown in FIG. Generally, equation (E) is calculated as 1 / (T + 1)
The autocorrelation function is defined by multiplication, but since it is not an essential problem, the 1 / (T + 1) is omitted.

However, if the sampling interval of data (here, blood flow velocity) is Δt, the Δt is the frame interval of the ultrasonic image. {See FIG. 4 (a)} kΔt = τ _k : lag of correlation function iΔt = t _i : time when data is obtained T + 1: (period from i−T to i); when calculating correlation function The analysis data length is usually longer than the period of the pulsation wave to be analyzed.

## EQU1 ## In the above equation (E), i = i +
The recurrence formula when it is set to 1 is the formula (E1) shown in FIG.

Here, for example, when T = 4 and k = 0, 1,
Considering the example of 2 (indicated by k max), assuming that V (0) is the first data, it is necessary to satisfy i−T−k ≧ 0 when V (jk) = V (iTk).

By substituting the above T = 4, k = 2 into the above equation, i-4-2 ≧ 0 i ≧ 6 That is, at the time when i = 6, all correlation values can be calculated. Become. Therefore, from the above equation (E), the autocorrelation value R (k, i) is given by: R (0,6) = V (2) ² + V (3) ² + V (4) ² + V (5) ² + V (6) ) ² R (1,6) = V (2) V (1) + V (3) V (2) + V (4) V (3) + V (5) V (4) + V (6) V (5) R (2, 6) = V (2) V (0) + V (3) V (1) + V (4) V (2) + V (5) V (3) + V (6) V (4) Calculation of correlation function , The above calculation is executed by i = 6. Thereafter, the calculation is performed using the recurrence formula of the above formula (E1). That is, R (0,7) = R (0,6) -V (2) ² + V (7) ² = V (3) ² + V (4) ² + V (5) ² + V (6) ² + V (7 ) ² R (1,7) = R (1,6) -V (2) V (1) + V (7) V (6) = V (3) V (2) + V (4) V (3) + V (5) V (4) + V (6) V (5) + V (7) V (6) R (2,7) = R (2,6) -V (2) V (0) + V (7) V (5) = V (3) V (1) + V (4) V (2) + V (5) V (3) + V (6) V (4) + V (7) V (5) Hereinafter, the same calculation is performed. can do.

In the above equation (E1), the time (i + 1)
Therefore, since the data from the time (i + 1) to the time (i-T-kmax) is required, the frame memory storing the ultrasonic image is (i + 1)-(i-T-kmax) + 1 = i + 1 -I + T + kmax + 1 = T + kmax + 2 Therefore, (T + kmax + 2) frame memories are required.

The method of obtaining the autocorrelation by the equation (E1) is a method of calculating the autocorrelation for each of a plurality of analysis sections of the autocorrelation in the diagram shown in FIG.
In this case, it is indicated that the above (T + kmax + 2) frame memories are required.

To calculate the autocorrelation for a sufficiently long analysis data length (T + 1), the above equation (E1) is set as follows. That is, R (k, i + 1) = R (k, i) + V (i + 1) V (i + 1-k) · (E3) That is, all data are added together with the start signal, and as shown in the above equation (E2). , Do not perform the operation of subtracting old data.

The calculation in this case can be performed in the same manner as described above, and therefore the details are omitted. In this case, however, the time (i + 1)
From time (i + 1) to time (i + 1−kmax) (where
Since kmax requires data up to the maximum number of lags, calculating the required number of frame memories in the same manner as described above gives: (i + 1)-(i + 1-kmax) + 1 = kmax + 1, that is, (kmax It suffices to have +1) frame memories, and the number of frame memories is smaller than in the case of the above equation (E2). Therefore, the autocorrelation calculation by the above equation (E3) is practical. is there.

FIG. 4A shows the blood flow velocity at a certain pixel (x, y) in a certain region of the B-mode tomographic image. Here, FIGS. 4B and 4C show the calculation of the autocorrelation function using the blood flow velocity data in the time section from the start to the end.
In the case of a pulsating wave, as shown in FIG. 4B, a peak value is detected within a detection range (several hundred msec to about 1 sec). The amount of this peak value B, or the value at the time of the correlation lag 0,
That is, when the ratio of the value R (0) to the value A and B / A are larger than the designated amount, the pulsating wave is determined. FIG. 4C shows an example of a steady flow, and no clear peak appears.

The correlation values from R (0), R (1) to R (k max) are obtained, and the respective values are plotted {FIG.
Within the detection range of reference｝, for example, if a curve fits a quadratic function and its curve curvature exceeds a predetermined threshold,
The pulsating wave may be identified, and if the curvature of the curve of the quadratic function is small, the pulsating wave may be identified as a standing wave.

The above-described method of discriminating a pulsating wave is based on an autocorrelation function. However, a frequency analysis using a known fast Fourier transform technique is performed to obtain a frequency spectrum as shown in FIGS. Needless to say, the presence or absence of the pulsation of the blood flow velocity may be detected.

That is, as shown in FIG. 4 (d), the time section from the start to the end is divided into appropriate analysis sections, and each is subjected to frequency analysis by a known fast Fourier transform to obtain a power spectrum of the obtained power spectrum. The average value is shown in FIGS. 4 (d) and 4 (e). In the case of a pulsating wave, as shown in FIG. 4D, a peak value is detected within a detection range (around 1 Hz). If the amount of the peak value B or the ratio to the DC component A, B / A, is larger than the specified amount, it is regarded as a pulsating wave. FIG.
(e) is an example of a steady flow, and a clear peak does not appear.

FIG. 5 shows how the peak value of the blood flow velocity changes over time in the above process. Immediately after the start of the process, the region where the blood flow exists is small, but it can be seen that the region with the blood flow becomes clear with the passage of time. FIG. 5 (c) indicates that there is an area with blood flow in the area A and the area B during the time interval from the start to the end. As described above, if the calculation as shown in FIG. 4 is performed on the area where the blood flow exists, the flow characteristics of each area can be displayed.

According to the present invention, vascular information discriminating pulsatility and steadiness can be obtained on one screen, so that useful information for diagnosis can be obtained.

[0047]

BRIEF DESCRIPTION OF THE DRAWINGS FIG. FIGS. 1 to 5 described above are explanatory diagrams of the principle of the present invention.
6 and 7 show an embodiment of the present invention. FIG. 6 schematically shows an autocorrelation function calculating section. FIG. 7 shows an ultrasonic diagnostic apparatus of the present invention. 1 shows an example of the entire configuration of a portion related to the present invention.

In the present invention, in the B-mode tomographic image,
A blood flow velocity information is superimposed and displayed, for example, an ultrasonic diagnostic apparatus having a mechanism for displaying a color flow map (CFM) image. Means for distinguishing at least three regions of flow velocity characteristics: pulsating wave, standing wave, and no flow 6,1
0, for example, a means using an autocorrelation function or a frequency analysis means and means 9 and 11 for instructing the start and end of the identification are provided, and the identification is performed within a period from the start to the end of the identification. Means for switching and displaying the region of each characteristic with blood flow velocity information (CFM image) on the B-mode tomography
10, 7, and 5 are the means necessary to carry out the present invention.
Note that the same reference numerals indicate the same object throughout the drawings.

Hereinafter, referring to FIGS. 1 to 4, FIG.
Referring to FIG. 6, an ultrasonic diagnostic apparatus according to the present invention will be described. First, in the principle configuration diagram of FIG. 1, 1 is a transducer for transmitting and receiving an ultrasonic wave, 2 is a beam generating unit (beam former) for generating an ultrasonic beam for transmission and reception,
3 is a detection unit for obtaining a detection signal, 4 is a scan converter for converting into a television signal, 6 is a Doppler analysis unit for calculating a blood flow velocity, specifically,
The flow map (CFM) analysis unit 7 is a scan converter for flow velocity data, specifically, a color flow map.
Digital Scanner Converter for Map (CFM) (DS
C) and 8 are transmission condition generation units for generating the transmission pulse repetition period and the number of transmissions. In the above, 1 to 8
Is the same as the conventional ultrasonic diagnostic apparatus shown in FIG.

9 and 10 are characteristic features of the present invention. Reference numerals 9 and 11 denote identification start / end designation means for instructing the start and end of identification of the standing wave / pulsating wave, and reference numeral 10 denotes a signal (blood flow velocity) from the CFM analysis unit 6 to use the characteristic of the blood flow. For example, it is a standing wave / pulsating wave discriminating means for discriminating between the above-mentioned pulsating wave and standing wave.

When the identification is started by the instruction of the identification start / end designation means 9, the scan converter 7 displays the output of the standing wave / pulsation wave identification means 10, that is, the signal whose characteristic is identified, as an input. Works like

In addition, the end signal from the identification start / end designation means 9, 11 displays the identification result in the time section (from the start to the end). In addition, it is configured to return to the conventional operation by means not shown.

In order to improve the accuracy of the standing wave / pulsating wave discrimination, the discrimination signal of the discrimination start / termination designation means 9 controls the control unit 11 so that the optimum transmission repetition cycle and the number of transmissions are performed within the discrimination period. Via the transmission condition generator 8
The pulsating wave, the standing wave, and the like are operated with higher accuracy by the identification signal of the identification start / end specifying means 9.

Next, the operation of the autocorrelation function calculation will be described more specifically with reference to FIGS. Here, for convenience of explanation, a case where the autocorrelation function is calculated by the method shown in the above equation (E3) is taken as an example.

As described above, in this method, the velocity information V (i + 1-k) corresponding to each pixel (x, y) of the B-mode tomographic image from the color flow map (CMF) analysis unit 6 is used. max), ~ V
(i) and V (i + 1) are sequentially stored in the (kmax + 1) frame memory 101 for speed storage shown in the figure, and the identification start / end designation means 9 shown in FIG. Based on the calculation start instruction signal via the terminal 11, the calculation of the autocorrelation function shown in the above equation (E3) is performed by the autocorrelation function calculation unit 1
The calculation results are stored in (kmax + 1) autocorrelation storage memories R (0), R (1),..., R (kmax) 102.

On the other hand, in the blood flow velocity peak hold unit 104 shown in FIG. 7, the blood flow corresponding to each pixel (x, y) of the B-mode tomographic image from the color flow map (CMF) analysis unit 6 is obtained. Information on the presence / absence of the peak hold of the flow velocity is generated, and is input to the pulsation / steady / no flow image generation unit 105.

When an end signal is output from the identification start / end specifying means 9, if there is peak hold information of the blood flow velocity corresponding to each pixel (x, y) on the B-mode tomographic image, the blood flow Therefore, the autocorrelation value from the autocorrelation storage memory 102 corresponding to the pixel (x, y) is referred to, and is compared with a predetermined threshold value. As shown in FIG. 4B, when an autocorrelation value larger than the threshold is detected, a predetermined color information (for example,
If the autocorrelation value does not exceed the threshold value as shown in FIG. 4 (c), it is recognized as a standing wave and predetermined color information (for example,
For a pixel that stores blue information) and has no information from the blood flow velocity peak hold unit 104, it recognizes that there is no blood flow, and performs a process of storing predetermined color information (for example, black information). This is performed for pixels.

In this process, the information from the blood flow velocity peak hold section 104 is converted into predetermined color information, for example, white, and the digital scan for the color flow map (CFM) is performed in real time.・ Converter (DS for CFM)
C) by sending it to the unit 7, for example, as shown in FIG. 5 (a), (b),
An area where a pixel with blood flow exists as shown in (c) is displayed.

When the identification end signal is output from the identification start / end designation means 9, the pulsation, steady state,
Flow-free image generation unit The information that identifies the pulsating wave, standing wave, and no flow stored in the bitmap memory in 105 is converted to a digital scan converter (CMF DSC) unit for color flow map (CMF). Send to 7,
Until then, the color flow map (CM
F) The image or the blood flow velocity peak hold image is replaced with the pulsating wave, the standing wave, and the image of no flow and displayed.

The display example at this time is shown in FIG. 2 (d) described above, and as is clear from this figure, the region showing the pulsating wave, the standing wave, and no flow on the B-mode tomographic image. , For example, can be displayed as a still image on one screen.

As described above, according to the present invention, an ultrasonic diagnostic apparatus having a mechanism for superimposing and displaying blood flow velocity information on a B-mode tomographic image based on a temporal change in the blood flow velocity is provided. Means for identifying at least three regions of blood flow velocity characteristics, pulsating wave, standing wave, and no flow 6,1
0, for example, a means using an autocorrelation function or a frequency analysis means, and a means 9 for instructing the start and end of the identification are provided. , Each region is switched and displayed with the blood flow velocity information on the B-mode tomography (or its peak hold information).

[0062]

As described in detail above, the ultrasonic diagnostic apparatus of the present invention includes an ultrasonic diagnostic apparatus having a mechanism for superimposing and displaying blood flow velocity information in a B-mode tomographic image. Means for discriminating at least three regions of the blood flow velocity based on the temporal change of the blood flow velocity, such as a pulsating wave, a standing wave, and no flow 6,10, for example, means using an autocorrelation function Or frequency analysis means and means 9 for instructing the start and end of the identification, and providing the identified characteristics in the period from the start to the end of the identification.
, Each region is defined as blood flow velocity information on the B-mode tomogram,
Alternatively, since the display is switched and displayed with the peak hold information of the blood flow velocity, the pulsation wave and the blood flow information identifying the standing wave can be obtained in one image, which is useful for diagnosis. The effect can be obtained when sufficient information can be obtained.

[Brief description of the drawings]

FIG. 1 illustrates the principle of the present invention (part 1).

FIG. 2 is a diagram illustrating the principle of the present invention (part 2).

FIG. 3 is a diagram illustrating the principle of the present invention (part 3).

FIG. 4 is a view for explaining the principle of the present invention (part 4);

FIG. 5 is a diagram illustrating the principle of the present invention (part 5).

FIG. 6 shows an embodiment of the present invention (part 1).

FIG. 7 shows an embodiment of the present invention (part 2).

FIG. 8 is a diagram illustrating a conventional ultrasonic diagnostic apparatus.

[Explanation of symbols]

1 Ultrasonic transducer 2 Beam generation unit (beam former) 3,4 B-mode DSC unit 5 Display 5a Video processing unit 5b Display monitor 6 Color flow map (CFM) analysis unit (CFM)
Analysis unit) 7 Digital scan converter for CFM (DSC unit for CFM) 8 Transmission condition generation unit 9 Identification start / end designation unit 10 Pulsating wave / stationary wave identification unit 101 Speed storage frame memory 102 Autocorrelation storage memory 103 Autocorrelation Function calculation unit 104 Blood flow velocity peak and hold unit 105 Image generation unit for pulsating wave, standing wave, and no flow 11 Control unit 12 Operation keyboard 13 Setting means 14 Pulse
Doppler (PWD) analyzer 15 Scroll memory 16 CFM scale generator Pulsation wave Standing wave No flow Blood flow velocity identification signal

Claims (4)

(57) [Claims] 1. A ultrasonic diagnostic apparatus having a machine structure to display superimposed blood flow rate information on the B-mode image, based on the temporal change information of the blood flow velocity, the B-mode image on of the characteristics of the blood flow velocity information, pulsating, constant wave, to Mu flow
Of area identification hand identifies the region of the at least three characteristics
Provided with the step, the indication means to indicate the end and identification of the start, and identification to the end instruction from the start instruction of the identification of the instruction manual stages or al
Within another period, the characteristic value for each region identified in the area identification hand stage, by switching the blood flow velocity display on the B-mode image to a table Shimesuru ultrasonic diagnostic apparatus, the area identifying means, Blood flow velocity is 1 degree within the above identification period
The blood flow area where the blood flow exists even though the area exceeds the predetermined threshold
Pulsating wave from the extracted blood flow area
An ultrasonic diagnostic apparatus for extracting an area of a subject . 2. A the ultrasonic diagnostic apparatus, the region
Upon identification Hand stage extracts the region of the pulsating wave, the blood
2. The method according to claim 1, wherein a periodicity is found by using an autocorrelation function of a flow velocity value in a flow region, and is recognized as a pulsating wave.
An ultrasonic diagnostic apparatus according to item 1. 3. A the ultrasonic diagnostic apparatus, the region
When extracting the pulsation wave region, the identification means
The ultrasonic diagnostic apparatus according to claim 1, wherein periodicity is found by frequency analysis of a flow velocity value in a flow region, and the periodicity is recognized as a pulsating wave. 4. A the ultrasonic diagnostic apparatus, the identification
In the period, repetition period of the same scanning line direction, and, or the number of transmissions, the ultrasonic diagnostic apparatus according to claim 1, characterized in that changing to other dates.