JP2714329B2 - 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 method for transmitting an ultrasonic wave to a subject, scanning the transmitting direction in a plane, and, based on the reflected waves, a tomographic image and a blood flow distribution in the plane. The present invention relates to an ultrasonic diagnostic apparatus for creating an image.

[0002]

2. Description of the Related Art A conventional ultrasonic diagnostic apparatus of this type uses a single ultrasonic probe to combine a blood flow distribution image and a tomographic image (B-mode image) by using an ultrasonic Doppler method and a pulse reflection method. There is a device that displays a blood flow distribution image in real time by superimposing a color blood flow distribution image on a monochrome tomographic image. This apparatus is known as an ultrasonic blood flow imaging apparatus. However, since the ultrasonic beam transmitted from the ultrasonic probe is scanned in one plane, a blood flow distribution image and a tomographic image are not obtained. It is an image about a scanning surface. Therefore, when the blood vessel is bent three-dimensionally,
There is a problem that only an ultrasonic image of the scanning plane appears on the display screen, and imaging of a blood vessel portion other than the ultrasonic scanning plane cannot be performed. In addition, if the scanning plane is changed by changing the direction of the ultrasonic probe or moving the position, imaging of other parts is possible,
On each imaging screen, only a fragmentary image of a part of the blood flow for each scanning plane is displayed, and it is difficult to grasp the state of the entire blood flow.

[0003] Conventionally, when it is desired to grasp the state of the entire blood flow, an angiographic image of the subject is taken by X-ray fluoroscopy using an X-ray diagnostic apparatus, and a blood vessel including all three-dimensional data is obtained. Displaying images has become mainstream.

[0004] However, the X-ray diagnostic apparatus has a large system configuration compared to the ultrasonic diagnostic apparatus, and uses X-rays. Therefore, there are various restrictions in handling, so that the X-ray diagnostic apparatus is simple. It has been required to perform imaging equivalent to X-ray fluoroscopy with a usable ultrasonic diagnostic apparatus.

From such a viewpoint, the applicant of the present application has filed Japanese Patent Application No.
In -401139, a plurality of cross sections of an ultrasonic wave are stored in a frame memory, weighted according to the position of the cross section at the time of reading, and all the cross sections are added, so that the luminance is changed according to the position and the distance is changed. We proposed to express the feeling and thereby enable three-dimensional observation of blood vessels.

[0006]

However, in the case of the ultrasonic diagnostic apparatus having the configuration proposed by the applicant of the present invention,
After storing each data of multiple cross sections of ultrasonic waves, in order to combine three-dimensional angiogram images when reading them out,
The memory capacity must be increased, which is disadvantageous from the viewpoint of further reducing the circuit scale.

SUMMARY OF THE INVENTION The present invention has been made in view of the above circumstances. It is an object of the present invention to perform imaging equivalent to X-ray fluoroscopy by using ultrasonic waves, and to realize operability and reliability with a simple circuit configuration. It is to provide an ultrasonic diagnostic apparatus with high performance.

[0008]

According to the present invention, there is provided an ultrasonic probe having an ultrasonic scanning surface movable in a three-dimensional space, and a receiving probe obtained by driving the ultrasonic probe. Image generating means for generating one frame of tomographic image information and blood flow distribution information for each ultrasonic scanning plane from a wave signal, and storing the blood flow distribution information and the positional information of the ultrasonic scanning plane in association with each pixel A frame memory, and past information stored in the frame memory and blood flow information in the latest frame, and determine whether blood flow information exists for each pixel in the latest frame. And outputs the latest blood flow information and the corresponding position information to the pixels where there is, and outputs the past blood flow information and the corresponding position information to the pixels where there is no blood flow information. The above A calculation means for forming three-dimensional blood flow distribution information on a memory, and a display means for superimposing and displaying the three-dimensional blood flow distribution information stored in the frame memory on the tomographic image information. Is an ultrasonic diagnostic apparatus.

The display means superimposes and displays blood flow distribution information on tomographic image information generated for each ultrasonic scanning plane, and displays the three-dimensional blood stored in the frame memory on the tomographic image information. An image on which flow distribution information is superimposed can be displayed.

[0010] The calculating means can calculate by correcting the pixel position according to the position information.

[0011]

According to the present invention, for example, as shown in FIG. 1, a three-dimensional angio image 400 is displayed on the left screen 300A of the color monitor 300, and a color blood flow image 45 is displayed on the right screen 300B.
0 is to be displayed in real time.

Therefore, in the first and second embodiments of the present invention, for example, as shown in FIG.
And a single frame memory 200 to create a three-dimensional angiogram image by the following algorithm.
However, C _n; data indicating the current blood flow velocity, V _n; current fluoroscopic image data, V _{n-1; 1} frame before fluoroscopic image data, W _n; Current Depth (depth) data, W _{n- 1} ;
Depth data one frame before, C _th : a parameter for determining whether or not the blood flow is truly based on the blood flow velocity. Note that the initial value is V ₀ = W ₀ = 0.

[0013] First, ROM 100, when receiving the C _n for each frame, and determines the presence or absence of data in the blood flow in the frame.

This is the case when abs (C _n ) <V _th or when there is no blood flow data.

At this time, old data is written to the frame memory 200, and the depth is increased by one.

If there is blood flow data, that is, abs
When (C _n ) ≧ C _th , the latest data is written to the frame memory 200 and the depth is set to 1.

By performing the above operation cyclically for each pixel, a three-dimensional angiogram image can be created when data is written to one frame memory 200. Therefore, by adding the data read from the frame memory 200 for display to a monitor (not shown), a three-dimensional angiogram image by ultrasonic waves can be displayed on the monitor. As a result, it is not necessary to increase the memory capacity of the frame memory.

In particular, according to the configuration of the second aspect of the invention, it is possible to correct a blood vessel position error in a three-dimensional angiogram image generated when the ultrasonic probe is rotated in a direction intersecting the scanning plane. .

[0019]

FIG. 3 is a block diagram showing a circuit configuration of an ultrasonic diagnostic apparatus according to a first embodiment to which the present invention is applied.

In the ultrasonic diagnostic apparatus according to the first embodiment, an ultrasonic probe 2, a transmission system 3, a reception system 4, a B-mode processing system 5, a CFM (color flow) Mapping) a processing system 6, a display system 7, an operation switch 8, and the like.

The ultrasonic probe 2 is of a sector-type electronic scanning type, is composed of a number of ultrasonic transducers arranged in a line, and changes the timing of the voltage applied to each transducer to generate an ultrasonic beam. It can be scanned in a fan shape and focused. Further, the ultrasonic scanning surface can be controlled so as to change in a three-dimensional space.

The transmission system 3 includes a pulse generator 3A, a transmission delay circuit 3B, and a pulser 3C. In the transmission system 3, a pulse generator 3A generates a rate pulse and sends the rate pulse to a transmission delay circuit 3B. The transmission delay circuit 3B gives a predetermined delay time to each of the transducers so as to focus the ultrasonic beam in a predetermined direction with respect to the rate pulse received from the pulse generator 3A, and sends this delay rate pulse to the pulser 3C. . The pulser 3C repeatedly drives each transducer of the ultrasonic probe 2 a predetermined number of times based on the delay rate pulse received from the transmission delay circuit 3B.

When the transmission of the ultrasonic probe 2 by the transmission system 3 is performed, the ultrasonic pulse transmitted from the ultrasonic probe 2 to the subject (not shown) is generated by the Doppler due to the blood flow flowing in the subject. It becomes a received signal with a shift,
Waves are received by the same transducer of the ultrasonic probe 2.

The receiving system 4 to which a received signal obtained by transmitting and receiving the ultrasonic wave is added includes a preamplifier 4A, a receiving delay circuit 4B, and an adder 4C. In the receiving system 4, the preamplifier 4A amplifies the received signal to a predetermined level,
The amplified reception signal is sent to the reception delay circuit 4B. The reception delay circuit 4B gives, for each transducer, a delay time for returning the amplified reception signal received from the preamplifier 4A based on the delay time given by the transmission delay circuit 3B. Adder 4C
Adds and synthesizes the received signals from the respective vibrators passed through the reception delay circuit 4B, and sends out the added and synthesized output to the B-mode processing system 5 and the CFM processing system 6, respectively.

The B-mode processing system 5 includes a logarithmic amplifier 5A, an envelope detection circuit 5B, and an A / D converter 5C, and performs the following processing under the control of the system controller 1. That is, in the B-mode processing system 5, the logarithmic amplifier 5A
A logarithmically amplifies the combined reception signal received from the adder 4C and sends it to the envelope detection circuit 5B. Envelope detection circuit 5
B detects the envelope of the combined reception signal received from the logarithmic amplifier 5A, and sends out the detection output to the A / D converter 5C. Therefore, the A / D converter 5C converts the detection output from the envelope detection circuit 5B into a digital signal, and outputs the digital signal to the display system 7 as a tomographic image echo (monochrome B mode image).

On the other hand, the CFM processing system 6 includes a phase detection circuit 6
An A / A / D converter 6B, an MTI processing system 6C, an autocorrelator 6D, and a calculation unit 6E are provided, and perform the following processing under the control of the system controller 1. That is, in the CFM processing system 6, the phase detection circuit 6A receives the received signal from the adder 4C, performs quadrature phase detection on the received signal, removes high-frequency components by a low-pass filter (not shown), and performs Doppler polarization. A Doppler detection output for a shift signal, that is, a blood flow image is obtained. The Doppler detection output also includes unnecessary reflected signals (clutter components) from slow-moving objects such as the heart wall in addition to blood flow information. Therefore, the Doppler detection outputs are mutually converted into digital signals by the A / D converter 6B, and are passed through the MTI filter 6C. Where M
TI is a technology used in radar, which is called Moving-Tra.
Abbreviation of get-Indicator, a method of detecting only moving targets using the Doppler effect. Therefore, the MTI filter 6C detects the movement of the blood flow based on the phase change between the same pixels in the rate pulse repeatedly transmitted a predetermined number of times, and removes clutter.

To analyze the frequency of the signal from which the clutter has been removed, an autocorrelator 6D is provided next to the MTI filter 6C.
The autocorrelator 6D has a functional configuration for performing two-dimensional multipoint analysis in real time, and requires less operation than the FFT method.

The operation unit 6E at the next stage of the autocorrelator 6D
Has a functional configuration having an average speed calculation unit, a dispersion calculation unit, and a power calculation unit. Then, in this autocorrelator 6D, the average speed calculation unit obtains the average Doppler shift frequency fd, the variance calculation unit obtains the variance σ ² , and the power calculation unit obtains the total power TP. The total power TP is proportional to the intensity of the scattered echo from the blood flow, but M
The echo from the moving object corresponding to the cut-off frequency of the TI filter 6C or lower is removed. The blood flow information thus obtained is output to the display system 7. As described above, the display system 7 to which the outputs of the B-mode processing system 5 and the CFM processing system 6 are added is a B-mode DSC (digital
(Scan converter) 7A, DSC 7B for CFM, color processing circuit 7C, D / A converter 7D, color monitor 7
E is provided. In this display system 7, DS for CFM
C7B is a coordinate conversion control circuit 10, a plurality of input buffers 11, an interpolation operation circuit 12, a frame memory (A) 13, an angiogram operation circuit 1 as shown in FIG.
4. A frame memory (B) 15 is provided, and data flows as shown by a solid line, and a control signal flows as shown by a dotted line.
That is, in the circuit configuration of FIG. 2, the speed data (6 bits) input from the CFM
1 is switched and input for each raster. The coordinate conversion control circuit 10 performs conversion control from polar coordinates to rectangular coordinates, and gives a read address from each input buffer 11, an interpolation coefficient, and a write address to the frame memory.
Under the above control, the interpolation calculation circuit 12 performs an interpolation calculation on the data from each input buffer, and writes the data after the calculation in the frame memory (A) 13. At the same time, the data is also sent to the angiogram operation circuit 14. The angiogram operation circuit 14 is provided in the ROM 10 of FIG.
The processing operation is performed as described with reference to FIG.

For example, the interpolation data is _expressed as C _n (6 bits, −
32 to +31), the data to be written into the frame memory (B) by the operation is V _n (6 bits, −32 to +31), W _n
(6 bits, 0 to +63), data read from the same address as the write address of the frame memory (B) before writing is written as V _n-1 (6 bits, −32 to +31), W
_n-1 (6-bit, 0; +63) and when, firstly, the angiogram arithmetic circuit 14, when receiving the C _n for each frame, and determines the presence or absence of blood flow data at that frame. The determination is made by comparison with abs (C _n) and C _th.

C _th is a parameter for removing noise, which is about four.

When there is no blood flow data, that is, when abs (C _n ) <C _th , V _n = V _{n -1} W _n = W _{n -1} +1 if W _n > 63 then V _n = 0 W _n = 0 endif and old data is written to the frame memory (B). This is done individually for each pixel.

When there is blood flow data, that is, abs
When (C _n ) ≧ C _th , the processing of V _n = C _n W _n = 1 is performed, and the latest data is written to the frame memory (B). This is also done individually for each pixel.

Such processing can be realized by a 256K × 16 bit ROM.

As shown in FIG. 5, the angiogram operation circuit 14 comprises an absolute value circuit 140, first and second mixers 142A and 142B, a comparator 144, and first and second AND gate units 146A and 146B. , +1
A logic circuit including the adder 148 can be used. In the configuration of the logic circuit, the current 6-bit data C _n indicating the blood flow rate input to the absolute value circuit 140, a 1-frame fluoroscopic image data V _n-1 of the previous 6-bit first AND gate unit 146A, and directly adds the 6-bit depth data W _n−1 of the previous frame to the +1 adder 148.
To enter. Further, in the comparator 144 which gives the parameter C _th for determining whether the blood flow is truly blood flow from the blood flow velocity as 5-bit data, the comparator 144 receives the absolute value of C _n of the 5-bit data from the absolute value circuit 140, C _th and the first and second mixers 1 according to the comparison result.
42A and 142B are controlled. More first mixer 142A, provides data C _n of 6 bits indicating the current blood flow rate and the second mixer 142B provides control data 6 bits from the system controller 1. At this time, the first and second AND gate units 146A, 146A, 1
At 46B, when the overflow bit OVF from the +1 adder 148 is received and W _n-1 +1 exceeds 63, the current depth data W _n and the data C indicating the current blood flow velocity
Since the gate processing for the _n 0 is made, from the first mixer 142A current fluoroscopic image data V _n, also from the second mixer 142B current Depth data W _n of blood flow data, respectively It is changed as described with reference to FIG. 2 depending on the presence or absence, and is written into the frame memory (B) 15 at the next stage.

As described above, the angiogram operation circuit 1
4, when writing V _n and W _n to the frame memory (B) 15, the writing is performed for one address at 1
It is assumed that only one ultrasonic scan is performed.
In other words, the frame memory (B) 15 functions as a one-frame delay element.

Thereafter, the TV from the frame memory (A) 13
The display V data read in the TV scanning direction and the angio data read from the frame memory (B) 15 in the TV scanning direction are the same as the display B data read in the TV scanning direction from the B-mode DSC 7A. Color processing circuit 7
C and is subjected to color processing for displaying the color monitor 7E.

The display V data, angio data,
When each of the display B data is displayed on the color monitor 7E, it is assumed that it is displayed in an area as shown in FIG.

For example, as the display B data, exactly the same image is displayed as a real-time image on the right half and the left half of the screen as shown in FIG.

The display data V is displayed on the left half of the screen as shown in FIG.

The angio data is displayed on the right half of the screen as shown in FIG.

In this relationship, the image processing circuit 7C superimposes three types of data to display B data and angio data on the right half of the screen as shown in FIG. In the left half of, B data and V data are displayed.

Next, the display is colored by a color processing circuit 7C.
The following describes how to do this.

FIG. 7 is a block diagram of the color processing circuit 7C. As shown in FIG. 7, a group of coloring ROMs 16 for coloring the display B data and coloring for coloring the display V data are shown. A ROM 17 group, a ROM 18 for non-linear gradation conversion of the Angio data W, a coloring ROM 19 group for coloring display of the Angio data W and V, and mixers 20 and 21 are provided.
The color monitor 7 converts the signals into analog red (R), green (G), and blue (R) color signals by a group of converters 7D.
E.

In the color processing circuit 7C, the coloring ROM 16 group performs processing for expressing the display B data in black and white. However, if there is V data or angio data at the same pixel location, display of V and angio data is prioritized.

The coloring ROM 17 group performs coloring as shown in FIGS. 8A and 8B corresponding to the V data.

The group of coloring ROMs 19 performs processing for simultaneously displaying the three-dimensional position information W and the speed information V in Table 1 or displaying only the three-dimensional position information W for the angio data.

First, when displaying W and V simultaneously, coloring is performed as shown in FIG.

That is, the direction and speed of the blood flow are shown in FIG.
Coloring as shown in (a) is performed, and green is added as three-dimensional information.

When information on the flow velocity is unnecessary and only the three-dimensional structure of the blood vessel is to be viewed, the display of only W is sufficient. Therefore, in the case of this coloring, display is made as shown in FIG. 10 using only the value of W and the sign of V.

If information on the direction of the blood flow is not required, the arrangement may be as shown in FIG.

From the above, according to the first embodiment of the present invention, imaging equivalent to X-ray fluoroscopy can be performed by ultrasonic waves with a simple circuit configuration. And in real time,
While viewing the conventional color Doppler image and tomographic image, you can see the ultrasonic angiogram image that superimposes the blood flow from a certain point in time to the present, so that scanning fails or the ultrasonic angio When a gram image is not obtained, it can be understood immediately and can be redone. As a result, the operability and reliability when constructing the angiogram are improved.

Further, based on the configuration of the first embodiment of the present invention shown in FIG. 3, it may be modified as shown in FIGS. 12, 13, and 14, respectively. That is, in the first embodiment of the present invention, the data input to the B-mode DSC 7A and the CFM DSC 7B are described as data obtained by scanning at present, but as in the first modification shown in FIG. The B-mode image memory 500 is provided before the mode DSC 7A, and the CFM is provided before the CFM DSC 7B.
Image memories 600 are provided, and the data before being input to the DSC in each of the image memories 500 and 600 is stored in a large-capacity memory so that tens to hundreds of frames can be fetched.
A similar angiogram display can also be performed from 00 and 600.

Further, in the first embodiment of the present invention, the B-mode for superimposed display on the angiogram is always the image of the latest frame, but the B-mode for superimposed display is also as follows. Image may be used.

For example, as shown in a second modified example shown in FIG. 13, the system controller 1 is provided before the B-mode DSC 7A.
A switch 30 is provided which can be opened and closed by the switch. And
The switch 30 is used to display the B-mode image of the time phase designated by the operator using the operation switch 8 for the subsequent B-mode D
It is released by the system controller 1 so that writing to the SC 7A can be stopped. With this, DSC for B mode
In 7A, the B-mode image at that time is always stored, and the angiogram is to be synthesized with this B-mode image.

In the third modification shown in FIG.
As shown in FIG. 6, (n + 1) frame memories 74-1 to 74- (n
+1), and stores the B-mode data input from the B-mode processing system 5 to the first mixer 70 in the frame memories 74-1 to 74-1.
A B-mode DSC 7F, which is switched at 74- (n + 1) and is output from the second mixer 72 to the color processing circuit 7C, is used, so that it can always be synthesized with the B-mode image n frames before. I have.

In the fourth modification shown in FIG. 15, (n + 1) image frame memories 76-1 one frame extra than n frames are provided before the B-mode DSC 7A as shown in FIG. And the B-mode data input from the B-mode processing system 5 to the first mixer 78 are stored in the frame memories 76-1 to 76- (n
+1) to switch from the second mixer 80 to the B-mode DSC
A B-mode image memory unit 7000 for outputting to the 7A is used, so that it can always be synthesized with the B-mode image n frames before.

Next, an ultrasonic diagnostic apparatus according to a second embodiment of the present invention will be described with reference to FIG.

The second embodiment is different from the first embodiment in that an ultrasonic probe can be controlled so that an ultrasonic scanning plane changes in a three-dimensional space.
In addition, a position detection circuit 9 detects position information on the ultrasonic scanning surface, and a CFM DSC 7H that performs a processing operation with reference to the position information is provided.

In this case, the CFM DSC 7H inputs the position information obtained by the position detection circuit 9 to the coordinate transformation control circuit 10 and the angiogram operation circuit 14 as shown in FIG. Processing is performed in the circuit 14 as follows. However, it is assumed that the position information is given as 6 bits of ₁ to 63 as Zn.

First, the algorithm will be described here.

If abs (C _n ) ≧ C _th and Z _n ≧ W _n-1 then V _n = C _n W _n = Z _n else V _n = V _n-1 W _n = W _n-1 endif (initial value V ₀ = W ₀ = 0) Such processing is performed by the absolute value circuit 14 as shown in FIG.
0, the first and second mixers 142A and 142B, and the first and second comparators 144 and 149 can be used for a logic circuit. That is, in FIG. 20 receives the 6-bit data C _n indicating the current blood flow rate in the absolute value circuit 140, C _n of 5-bit data from the absolute value circuit 140
Absolute value while performing blood flow velocity truly comparison with 5-bit data of the parameter C _th for determining whether the blood flow in the first comparator 144, and the 6-bit data Z _n indicating the position information of 1 The comparison with the 6-bit depth data W _{n- 1} before the frame is performed by the second comparator 149, and the first and second mixers are controlled according to whether or not the output of each comparator is satisfied. Further, the first mixer 1
42A has 6-bit data C indicating the current blood flow velocity.
_n and frame type before the 6-bit and a fluoroscopic image data V _n-1, also in the second mixer 142B, 6-bit data indicating the position information Z _n and the preceding frame Depth data W _n- because Type ₁ and, from the first mixer 142A current fluoroscopic image data and from the second mixer 142B according to FIG 2 in accordance with the presence or absence of current Depth data W _n are each blood flow data The data is changed as described and written into the next frame memory (B) 15.

On the other hand, the coordinate conversion control circuit 10 corrects an error generated as shown in FIG. 22 when the ultrasonic probe 2 crosses the operation surfaces A, B and C shown in FIG. 21 based on the phase information. A control signal can be output.

Thus, in the second embodiment of the present invention, the processing can be performed similarly to the first embodiment of the present invention, and at the same time, the displacement of the blood vessel on the ultrasonic image can be eliminated.

Also, based on the configuration of the second embodiment of the present invention shown in FIG. 18, FIGS.
6, and may be modified as shown in FIG.

That is, in the first modification of the second embodiment of the present invention, as shown in FIG. 23, the position detecting circuit 9 and the position data corresponding to each image of the image memory are stored in the configuration of FIG. Having the position information storage memory 700 allows the B-mode image memories 500 and C
Angiogram display can be performed with each data from the FM image memory 600.

In a second modification of the second embodiment of the present invention, as shown in FIG. 24, a position detecting circuit 9 is provided in the configuration of FIG. Further, in a third modification of the second embodiment of the present invention, as shown in FIG.
The position detection circuit 9 is provided. In a fourth modification of the second embodiment of the present invention, as shown in FIG. 26, a position detection circuit 9 is provided in a configuration equivalent to that of FIG. 15 using a B-mode DSC 7G including an image frame memory. It is. In each of the second to fourth modifications, B-mode synthesis can be performed in the same manner as the corresponding modification of the first embodiment of the present invention.

[0067] In the fifth modification of the second embodiment of the present invention, advance decide to display the B-mode image at advance which position, when the scanning of the position is carried out, the configuration of FIG. 27 Then, writing to the B-mode DSC 7A is performed. This enables B-mode synthesis with a predetermined position. The position at which the B-mode image is displayed can be determined by the operation switch 8 or the center position.

Although various basic configurations and modifications have been described with respect to the embodiments of the present invention, the present invention is not limited thereto.

For example, before the three-dimensional position information W is displayed, the non-linear gradation conversion is performed by the ROM 18 in FIG. 7 so that the range of the angio component can be changed between the present and the 32 frames as shown in FIG. As shown in FIG. 29, it is possible to reduce the size to half of 64 frames, or to change the coloring of W so as to enhance the ability to express three-dimensional information of a new frame as shown in FIG. At this time, if there are many blood vessels, if angio display is performed from many images, the screen will be filled with blood vessels and the B-mode image will be hidden. As a result, the relationship between the blood vessel and the tissue image from the B-mode image may not be clearly seen. In such a case, R
By reducing the number of frames to be three-dimensionally synthesized by the OM 18, it is possible to display only blood vessels in the vicinity of the B mode. However, by the ROM 18,
When the point where the output W ′ = 0 is combined with the B data by MU × 21, the B data is displayed. Note that W '≠
When the value is 0, angio data is displayed. In each process, the position of the ultrasonic probe 2 is not detected. The angiogram is 64 from the current frame to 63 frames before.
It is composed of frames. This display is a sector scan in which a new frame is superimposed on top.

[0070]

As described above, according to the present invention, when the ultrasonic probe is moved so that its scanning plane changes in a three-dimensional space, the tomographic image and the blood flow distribution image of the latest scanning frame are obtained. At the same time as displaying in real time, the blood flow distribution from the ultrasonic scan frame to the previous ultrasonic scan frame is superimposed so that the blood flow distribution of the new ultrasonic scan frame is on top, and the blood flow information and this The information of the ultrasonic scanning frame from which the blood flow information was collected is stored, and the blood flow information and the ultrasonic scanning frame information are displayed or stored so as to be displayed in real time on the tomographic image of the latest ultrasonic scanning frame. Control can be performed, whereby imaging similar to X-ray fluoroscopy can be performed. When imaging the ultrasonic three-dimensional angiographic image in this manner, since it is not necessary to store all the data of a plurality of cross sections of the ultrasonic wave, a small-capacity memory can be used, and the circuit scale can be further reduced. It is convenient to do it.

[Brief description of the drawings]

FIG. 1 is a diagram showing a state in which a three-dimensional angio image and a color blood flow image are simultaneously displayed.

FIG. 2 is a diagram showing a principle configuration of an ultrasonic diagnostic apparatus of the present invention.

FIG. 3 is a block diagram showing a circuit configuration of the ultrasonic diagnostic apparatus according to the first embodiment to which the present invention is applied.

FIG. 4 is a block diagram illustrating details of a CFM DSC of a display system according to the first embodiment of the present invention.

FIG. 5 is a circuit diagram showing an example in which the angiogram operation circuit according to the first embodiment of the present invention is configured by a logic circuit.

FIG. 6 is a diagram illustrating a form of image data displayed on a color monitor.

FIG. 7 is a block diagram illustrating details of a color processing circuit of a display system.

FIG. 8 is a diagram used to explain coloring of V data displayed on a color monitor.

FIG. 9 is a diagram used to explain an example of coloring of angio data displayed on a color monitor.

FIG. 10 is a diagram used to explain another example of coloring angio data displayed on a color monitor.

FIG. 11 is a diagram used to explain still another example of coloring of angio data displayed on a color monitor.

FIG. 12 is a block diagram showing a circuit configuration of a first modified example based on the ultrasonic diagnostic apparatus of the first embodiment to which the present invention is applied.

FIG. 13 is a block diagram showing a circuit configuration of a second modified example based on the ultrasonic diagnostic apparatus of the first embodiment to which the present invention is applied.

FIG. 14 is a block diagram showing a circuit configuration of a third modified example based on the ultrasonic diagnostic apparatus of the first embodiment to which the present invention is applied.

FIG. 15 is a block diagram showing a circuit configuration of a fourth modified example based on the ultrasonic diagnostic apparatus of the first embodiment to which the present invention is applied.

FIG. 16 shows B used in a third modification of the first embodiment of the present invention.
FIG. 3 is a block diagram illustrating details of a mode DSC.

FIG. 17 shows B used in a fourth modification of the first embodiment of the present invention.
FIG. 3 is a block diagram showing details of a mode image memory unit.

FIG. 18 is a block diagram illustrating a circuit configuration of an ultrasonic diagnostic apparatus according to a second embodiment to which the present invention has been applied.

FIG. 19 is a CFM of a display system according to a second embodiment of the present invention.
FIG. 4 is a block diagram showing details of a DSC for use in the present invention.

FIG. 20 is a block diagram illustrating an example in which the angiogram operation circuit according to the second embodiment of the present invention is configured by a logic circuit;

FIG. 21 is a diagram showing the relationship between the tilt of the ultrasonic probe and the scanning plane during imaging.

FIG. 22 is a diagram used to explain a case where a blood vessel position in an ultrasonic image is corrected.

FIG. 23 is a block diagram showing a circuit configuration of a first modified example based on the ultrasonic diagnostic apparatus of the second embodiment to which the present invention is applied.

FIG. 24 is a block diagram showing a circuit configuration of a second modified example based on the ultrasonic diagnostic apparatus of the second embodiment to which the present invention is applied.

FIG. 25 is a block diagram showing a circuit configuration of a third modified example based on the ultrasonic diagnostic apparatus of the second embodiment to which the present invention is applied.

FIG. 26 is a block diagram showing a circuit configuration of a fourth modified example based on the ultrasonic diagnostic apparatus of the second embodiment to which the present invention is applied.

FIG. 27 is a block diagram showing a circuit configuration of a fifth modified example based on the ultrasonic diagnostic apparatus of the third embodiment to which the present invention is applied.

FIG. 28 is a diagram illustrating an example of processing characteristics of nonlinear gradation conversion performed before displaying three-dimensional position information of angio data.

FIG. 29 is a diagram illustrating another example of processing characteristics of non-linear gradation conversion performed before displaying three-dimensional position information of angio data.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 System controller 2 Ultrasonic probe 3 Transmission system 4 Receiving system 5 B-mode processing system 6 CFM processing system 7 Display system 8 Operation switch 9 Position detection circuit 100 ROM 200 Frame memory

Claims (3)

(57) [Claims] 1. An ultrasonic probe having an ultrasonic scanning surface movable in a three-dimensional space, and one frame of tomographic image information for each ultrasonic scanning surface from a received signal obtained by driving the ultrasonic probe. Image generating means for generating blood flow distribution information; a frame memory for storing the blood flow distribution information and the position information of the ultrasonic scanning surface in association with each pixel; and past information stored in the frame memory. Input the blood flow information in the latest frame and determine whether there is blood flow information for each pixel in the latest frame. 3D blood flow distribution information is formed on the frame memory by outputting past blood flow information and corresponding position information to pixels having no blood flow information. Operator An ultrasonic diagnostic apparatus comprising: a stage; and display means for displaying the three-dimensional blood flow distribution information stored in the frame memory so as to be superimposed on the tomographic image information. 2. The display means superimposes and displays blood flow distribution information on tomographic image information generated for each ultrasonic scanning plane, and displays the three-dimensional blood stored in the frame memory on the tomographic image information. The ultrasonic diagnostic apparatus according to claim 1, wherein an image on which the flow distribution information is superimposed is displayed. 3. The arithmetic unit according to claim 1, wherein the calculation unit corrects the pixel position according to the position information and performs the calculation.
An ultrasonic diagnostic apparatus as described in the above.