JP2001269341A - Ultrasonic imaging method, ultrasonic imaging device, and ultrasonograph - Google Patents

Ultrasonic imaging method, ultrasonic imaging device, and ultrasonograph

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Publication number
JP2001269341A
JP2001269341A JP2000083395A JP2000083395A JP2001269341A JP 2001269341 A JP2001269341 A JP 2001269341A JP 2000083395 A JP2000083395 A JP 2000083395A JP 2000083395 A JP2000083395 A JP 2000083395A JP 2001269341 A JP2001269341 A JP 2001269341A
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ultrasonic image
ultrasonic
pixel
generating
value
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JP2000083395A
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Japanese (ja)
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JP4511679B2 (en
Inventor
Hiroshi Hashimoto
浩 橋本
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Ge Yokogawa Medical Systems Ltd
ジーイー横河メディカルシステム株式会社
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Abstract

PROBLEM TO BE SOLVED: To observe a flow-in or flow-out state of a contrast medium in the entire image without setting of a concerned region by an operator. SOLUTION: The ultrasonograph 100 comprises an ultrasonic probe 1, a transmitting/receiving part 2 for transmitting ultrasonic wave into a subject and outputting a receiving signal corresponding to the wave, a B-mode processor 3 for generating B-mode data from the receiving signal, a DSC 4 for generating an ultrasonic image from the B-mode data, a frame memory 5 for storing and outputting a directly previous ultrasonic image, a difference arithmetic part 6 for outputting a difference between the latest ultrasonic image and the directly previous ultrasonic image, and a variation speed ultrasonic image generating part 7 for generating a variation speed ultrasonic image G1 with luminance and displayed color determined according to the difference, and a CRT 8.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

The present invention relates to an ultrasonic image generating method, an ultrasonic image generating apparatus, and an ultrasonic diagnostic apparatus.
More specifically, the present invention relates to an ultrasonic image generating method, an ultrasonic image generating apparatus, and an ultrasonic diagnostic apparatus for generating an ultrasonic image capable of observing a state of inflow and outflow of a contrast agent in an entire image.

[0002]

2. Description of the Related Art A TIC (Time Intensity Curve) is known as a conventional technique for observing the state of inflow and outflow of a contrast agent. Diagnosis by TIC is performed as follows. (1) The subject is scanned by the ultrasonic diagnostic apparatus, and a B-mode image is displayed. As shown in FIG. 19, the regions of interest ROI1, ROI2,
Set ROI3. (2) Inject the contrast agent into the subject. (3) The ultrasonic diagnostic apparatus sequentially generates B-mode images one after another in time series, and graphs the temporal changes in the average luminance of the regions of interest ROI1, ROI2, and ROI3 as shown in FIG. indicate. (4) The doctor or technician recognizes the difference between the inflow and outflow of the contrast agent for each of the regions of interest ROI1, ROI2, and ROI3 from the TIC graph, and identifies a tumor.

[0003]

In the above-mentioned TIC, for example, it is necessary to properly set a region of interest such that one region of interest is set at a healthy site and another region of interest is set at a lesion site. There is a problem that the burden on the user is large. Therefore, an object of the present invention is to generate an ultrasonic image capable of observing a state of inflow and outflow of a contrast agent in an entire image so that an image diagnosis can be appropriately performed without an operator setting a region of interest. An object of the present invention is to provide an image generating method, an ultrasonic image generating device, and an ultrasonic diagnostic device.

[0004]

According to a first aspect of the present invention, there is provided an image processing apparatus comprising: a plurality of ultrasonic images generated in a time series; An ultrasonic image generation method is provided, which generates an ultrasonic image. In the ultrasonic image generation method according to the first aspect, by comparing the color and the brightness of each pixel of the changing speed ultrasonic image, the difference between each pixel of the inflow speed and the outflow speed of the contrast agent at the same time is determined. Because it can be recognized, it is possible to identify a tumor. Since it is not necessary to set the region of interest, the burden on the operator can be reduced.

[0005] In a second aspect, the present invention provides a method for determining the maximum value of the change rate of pixel values of a plurality of ultrasonic images generated in time series, which is reflected in the pixel value of a corresponding pixel. An ultrasonic image generation method is provided, which generates an ultrasonic image. In the ultrasonic image generation method according to the second aspect, by comparing the color and luminance of each pixel of the maximum change speed ultrasonic image, the difference between the pixels of the maximum value of the inflow velocity of the contrast agent in a certain period is determined. , It is possible to identify a tumor. Since it is not necessary to set the region of interest, the burden on the operator can be reduced.

[0006] In a third aspect, the present invention provides a method for calculating the minimum change speed of pixel values of a plurality of ultrasonic images generated in time series, the change speed being higher than the minimum change speed reflecting the pixel value of a corresponding pixel. An ultrasonic image generation method is provided, which generates an ultrasonic image. In the ultrasonic image generation method according to the third aspect, by comparing the color and luminance of each pixel of the minimum change speed ultrasonic image, the difference between the pixels of the maximum value of the outflow velocity of the contrast agent in a certain period is determined. , It is possible to identify a tumor. Since it is not necessary to set the region of interest, the burden on the operator can be reduced.

[0007] In a fourth aspect, the present invention relates to a change-rate dispersion ultrasonic wave in which the variance of the change speed of the pixel values of a plurality of ultrasonic images generated in time series is reflected on the pixel values of the corresponding pixels. An ultrasonic image generating method, which generates an image. In the ultrasonic image generation method according to the fourth aspect, by comparing the color and luminance of each pixel of the change-rate-dispersed ultrasonic image, the variation in the inflow speed and the outflow speed of the contrast agent during a certain period between each pixel is reduced. , It is possible to identify a tumor. Since it is not necessary to set the region of interest, the burden on the operator can be reduced.

In a fifth aspect, the present invention provides a method for generating a maximum-value ultrasonic image in which the maximum value of pixel values of a plurality of ultrasonic images generated in time series is reflected on the pixel value of a corresponding pixel. To provide an ultrasonic image generation method. In the ultrasonic image generation method according to the fifth aspect, by comparing the color and luminance of each pixel of the maximum-value ultrasonic image, it is possible to recognize the difference between the pixels in the inflow amount of the contrast agent in a certain period. , And can identify tumors. Since it is not necessary to set the region of interest, the burden on the operator can be reduced.

[0009] In the sixth aspect, the present invention is directed to an arrival time ultrasonic image reflecting the time until the pixel value of each pixel of a plurality of ultrasonic images generated in time series reaches a maximum value. And generating an ultrasonic image. In the ultrasonic image generation method according to the sixth aspect, by comparing the color and brightness of each pixel of the arrival time ultrasonic image, the difference between the pixels in the time until the inflow amount of the contrast agent reaches the maximum is obtained. , It is possible to identify a tumor. Since it is not necessary to set the region of interest, the burden on the operator can be reduced.

In a seventh aspect, the present invention provides an ultrasonic image storing means for storing a plurality of ultrasonic images generated in time series, and an arithmetic means for calculating a changing speed of a pixel value of the ultrasonic image. And a changing speed ultrasonic image generating means for generating a changing speed ultrasonic image in which the changing speed is reflected on a pixel value. The ultrasonic image generation device according to the seventh aspect can suitably implement the ultrasonic image generation method according to the first aspect.

According to an eighth aspect, the present invention provides an ultrasonic image storing means for storing a plurality of ultrasonic images generated in time series, and obtaining a maximum value of a change rate of a pixel value of the ultrasonic image. An ultrasonic image generating apparatus comprising: an arithmetic unit; and a maximum changing speed ultrasonic image generating unit configured to generate a maximum changing speed ultrasonic image in which a maximum value of the changing speed is reflected in a pixel value. I do. The ultrasonic image generation device according to the eighth aspect can suitably implement the ultrasonic image generation method according to the second aspect.

According to a ninth aspect, the present invention provides an ultrasonic image storing means for storing a plurality of ultrasonic images generated in time series, and obtaining a minimum value of a changing speed of a pixel value of the ultrasonic image. An ultrasonic image generating apparatus comprising: an arithmetic unit; and a minimum changing speed ultrasonic image generating unit configured to generate a minimum changing speed ultrasonic image in which a minimum value of the changing speed is reflected in a pixel value. I do. The ultrasonic image generating device according to the ninth aspect can suitably implement the ultrasonic image generating method according to the third aspect.

[0013] In a tenth aspect, the present invention provides an ultrasonic image storing means for storing a plurality of ultrasonic images generated in time series, and an operation for obtaining a variance of a change speed of a pixel value of the ultrasonic image. Means, and a change-speed-dispersion ultrasonic image generating means for generating a change-speed-dispersion ultrasonic image in which the variance of the change speed is reflected in a pixel value. The ultrasonic image generation device according to the tenth aspect can suitably implement the ultrasonic image generation method according to the fourth aspect.

According to an eleventh aspect, the present invention provides a maximum value holding means for holding a maximum value of a pixel value of each pixel of a plurality of ultrasonic images generated in time series, and converting the maximum value into a pixel value. There is provided an ultrasonic image generating apparatus comprising: a maximum value ultrasonic image generating means for generating a reflected maximum value ultrasonic image. The ultrasonic image generation device according to the eleventh aspect can suitably implement the ultrasonic image generation method according to the fifth aspect.

According to a twelfth aspect, the present invention provides an arrival time obtaining means for obtaining a time until a pixel value of each pixel of a plurality of ultrasonic images generated in time series reaches a maximum value; There is provided an ultrasonic image generating apparatus comprising: a time-of-arrival ultrasonic image generating means for generating a reflected time-of-arrival ultrasonic image. The ultrasonic image generation device according to the twelfth aspect can suitably execute the ultrasonic image generation method according to the sixth aspect.

According to a thirteenth aspect, the present invention provides an ultrasonic probe, transmitting / receiving means for transmitting an ultrasonic wave from the ultrasonic probe and obtaining a received signal corresponding thereto, and an ultrasonic probe based on the received signal. An ultrasonic diagnostic apparatus comprising: an ultrasonic image generating unit configured to generate an ultrasonic image; and at least one ultrasonic image generating apparatus according to the seventh to twelfth aspects. In the ultrasonic diagnostic apparatus according to the thirteenth aspect, at least one of the ultrasonic image generating method according to the sixth aspect and the ultrasonic image generating method according to the sixth aspect can be suitably implemented.

The changing speed ultrasonic image, the highest changing speed ultrasonic image, the lowest changing speed ultrasonic image, the changing speed dispersive ultrasonic image, the highest value ultrasonic image, or the arrival time ultrasonic image can be used. One of the pixels may correspond to one of the pixels of the ultrasonic image generated in time series (one-to-one correspondence). Alternatively, one of the pixels of the changing speed ultrasonic image, the highest changing speed ultrasonic image, the lowest changing speed ultrasonic image, the changing speed dispersed ultrasonic image, the highest value ultrasonic image, or the arrival time ultrasonic image. One may correspond to a plurality of pixels (for example, a point corresponding one-to-one and eight points around it) of the ultrasonic image generated in time series (one-to-many correspondence). Alternatively, a plurality of pixels of the changing speed ultrasonic image, the highest changing speed ultrasonic image, the lowest changing speed ultrasonic image, the changing speed dispersed ultrasonic image, the highest value ultrasonic image or the arrival time ultrasonic image. May correspond to a plurality of pixels of the ultrasonic image generated in time series (a plurality-to-plural correspondence. In this case, a group of pixels in a plurality of blocks partitioned so as to cover the entire image) It becomes correspondence of each other).
Alternatively, a plurality of pixels of the changing speed ultrasonic image, the highest changing speed ultrasonic image, the lowest changing speed ultrasonic image, the changing speed dispersed ultrasonic image, the highest value ultrasonic image or the arrival time ultrasonic image. May correspond to one of the pixels of the ultrasonic image generated in time series (a plural-to-one correspondence. In this case, a plurality of pixels in a plurality of blocks partitioned so as to cover the entire image). Pixel and representative pixel).

Further, the plurality of ultrasonic images generated in time series are not limited to display images having pixel values and coordinates which can be displayed on a screen, but are easily included in the display images. The data may be convertible. For example, the data may be data relating to reception signals of a large number of sound rays forming one frame.

[0019]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS Hereinafter, the present invention will be described in more detail with reference to the embodiments shown in the drawings. Note that the present invention is not limited by this.

First Embodiment FIG. 1 is a configuration diagram showing an ultrasonic diagnostic apparatus according to a first embodiment of the present invention. This ultrasonic diagnostic apparatus 100
An ultrasonic probe 1 and a transmitting / receiving unit 2 that transmits an ultrasonic wave into a subject, receives an echo corresponding thereto, and outputs a reception signal.
A B-mode processing unit 3 for generating B-mode data from the received signal, a DSC (Digital Scan Converter) 4 for generating the latest ultrasonic image from the B-mode data,
A frame memory 5 for outputting an ultrasonic image one frame before the latest ultrasonic image (an immediately preceding ultrasonic image);
A difference calculator 6 for calculating a difference V i (x, y) between the luminance S i (x, y) of the latest ultrasonic image and the luminance S i−1 (x, y) of the immediately preceding ultrasonic image; A changing speed ultrasonic image generating unit 7 for generating a changing speed ultrasonic image G1 composed of pixels whose luminance and display color are determined according to the difference V i (x, y), and the latest ultrasonic image and the changing speed CRT 8 displaying ultrasonic image G1
Are provided. Note that (x, y) represents the coordinates of the pixel.

FIG. 2 is a flowchart showing the changing speed ultrasonic image generation processing by the ultrasonic diagnostic apparatus 100 of FIG.
Note that a contrast agent is injected into the subject between immediately before and immediately after the start of this processing. In step ST1, a frame number counter i is initialized to "1".

In step ST2, the ultrasonic probes 1 to D
The subject is scanned by SC4, and the latest ultrasonic image is generated. In step ST3, the frame number counter i =
If 1, the process proceeds to step ST4, and if the frame number counter i ≧ 2, the process proceeds to step ST6.

In step ST4, the latest ultrasonic image is stored in the frame memory 5. If the previous ultrasonic image is already stored, it is overwritten. In step ST5, the frame number counter i is incremented by "1". Then, the process returns to step ST2.

In step ST6, the difference calculator 6 calculates a difference V i (x) between the luminance S i (x, y) of the latest ultrasonic image and the luminance S i−1 (x, y) of the immediately preceding ultrasonic image. the y), V i (x, y) = S i (x, y) -S i-1 (x, a y), is calculated. The absolute value of the difference V i (x, y) indicates the speed of change in luminance, that is, the inflow speed or outflow speed of the contrast agent. As for the sign of the difference V i (x, y), a positive value indicates an increase in luminance, that is, an inflow of a contrast agent, and a negative value indicates a decrease in luminance, that is, an outflow of a contrast agent.

[0025] At step ST7, the change rate of the ultrasonic image generating unit 7 generates the difference value V i (x, y) change speed ultrasonic image G1 decided luminance and display colors of the pixels in accordance with the. For example, the larger the absolute value of the difference V i (x, y), the higher the brightness. If the sign is positive, the display color is red, and if the sign is negative, the display color is blue. In step ST8, when the operator instructs the end, the process ends, and if not, the process returns to step ST4.

Next, a display example of the changing speed ultrasonic image G1 will be described with reference to FIGS. For convenience of description, it is assumed that there are first to fourth regions A to D having different blood inflow / outflow characteristics as shown in FIG. Also,
The first area A to the fourth area D have TIC characteristics a to d as shown in FIG.

FIG. 5 is a schematic diagram showing the correspondence between the differences based on the TIC characteristics a to d of FIG. 4 and the pixel values (luminance, display color).

FIG. 6 is a schematic diagram of the changing speed ultrasonic image G1 (t1) at time t1 in FIG. The first area A looks dark red, the second area B looks slightly bright red, the third area C looks bright red, and the fourth area D looks black. Therefore, it can be seen that the gas flows into the first region A to the third region C and the flow speed into the third region C is the highest.

FIG. 7 is a schematic diagram of the changing speed ultrasonic image G1 (t2) at time t2 in FIG. The first area A looks dark blue, the second area B looks slightly light blue, the third area C looks light blue, and the fourth area D looks black. Accordingly, it can be seen that the gas flows out of the first area A to the third area C, and the outflow speed from the third area C is the highest.

FIG. 8 is a schematic diagram of the changing speed ultrasonic image G1 (t3) at time t3 in FIG. The first area A and the second area B appear dark red, the third area C appears dark blue, and the fourth area D appears black. Therefore, it can be seen that the gas flows again into the first area A and the second area B and still flows out from the third area C.

According to the ultrasonic diagnostic apparatus 100 according to the first embodiment, the overall state of inflow and outflow of the contrast agent can be grasped at a glance from the brightness and display color of each pixel of the changing speed ultrasonic image G1. . Further, the operator does not need to set the region of interest.

Second Embodiment FIG. 9 is a block diagram showing an ultrasonic diagnostic apparatus according to a second embodiment of the present invention. The same components as those of the ultrasonic diagnostic apparatus 100 according to the first embodiment are denoted by the same reference numerals. The ultrasonic diagnostic apparatus 200 includes an ultrasonic probe 1, a transmitting / receiving unit 2, a B-mode processing unit 3,
And SC4, and the frame memory 5, a difference calculator 6, the difference V i (x, y) maximum value max_V i (x, y) of the difference maximum value hold unit 26 to hold the difference maximum value max_V i ( x, y)
And a CRT 8 that generates a maximum change speed ultrasonic image G2 that generates a maximum change speed ultrasonic image G2 composed of pixels whose brightness and display color are determined according to.

FIG. 10 is a flow chart showing the maximum changing speed ultrasonic image generation processing by the ultrasonic diagnostic apparatus 200 of FIG. Note that a contrast agent is injected into the subject between immediately before and immediately after the start of this processing. Steps ST1 to ST5 and ST8 are as described in the flowchart of FIG.
In step ST26, the difference maximum value holding unit 26
The highest value max_V i (x, y) of the difference V i (x, y) to hold.
In step ST27, the maximum change speed ultrasonic image generator 27, the difference maximum value max_V i (x, y) maximum change rate ultrasound image G2 decided luminance and display colors of the pixels in accordance with the
Generate

According to the ultrasonic diagnostic apparatus 200 according to the second embodiment, the changing speed ultrasonic image G shown in FIG.
1 (t1) continues to be displayed as the maximum change speed ultrasonic image G2 even after time t1. From the brightness and display color of each pixel of the maximum change speed ultrasonic image G2, the overall situation of the maximum inflow speed of the contrast agent can be grasped at a glance. Further, the operator does not need to set the region of interest.

Third Embodiment FIG. 11 is a configuration diagram showing an ultrasonic diagnostic apparatus according to a third embodiment of the present invention. The same components as those of the ultrasonic diagnostic apparatus 100 according to the first embodiment are denoted by the same reference numerals. The ultrasonic diagnostic apparatus 300 includes an ultrasonic probe 1, a transmitting / receiving unit 2, a B-mode processing unit 3,
And DSC 4, a frame memory 5, a difference calculator 6, the difference V i (x, y) minimum min_V i (x, y) of the difference minimum value hold unit 36 to hold the difference minimum value min_v i ( x,
It is configured to include a CRT 8 and a minimum-change-rate ultrasonic image generation unit 37 that generates a minimum-change-rate ultrasonic image G3 composed of pixels whose brightness and display color are determined according to y).

FIG. 12 shows the ultrasonic diagnostic apparatus 300 of FIG.
FIG. 7 is a flowchart showing a minimum change speed ultrasonic image generation process by the. In addition, between immediately before and immediately after the start of this processing,
A contrast agent is injected into the subject. Steps ST1 to ST5
And ST8 are as described in the flowchart of FIG. In step ST36, the lowest difference holding unit 36
It is, to hold the difference V i (x, y) the minimum value min_V i (x, y) of the. In step ST37, a minimum change rate ultrasound image generating unit 37 generates the minimum change rate ultrasound image G3 decided luminance and display colors of the pixels in accordance with the difference minimum value min_V i (x, y).

According to the ultrasonic diagnostic apparatus 300 according to the third embodiment, the changing speed ultrasonic image G shown in FIG.
1 (t2) is continuously displayed as the minimum change speed ultrasonic image G3 even after the time t2. From the brightness and display color of each pixel of the minimum change speed ultrasonic image G3, the overall situation of the maximum outflow speed of the contrast agent can be grasped at a glance. Further, the operator does not need to set the region of interest.

Fourth Embodiment FIG. 13 is a configuration diagram showing an ultrasonic diagnostic apparatus according to a fourth embodiment of the present invention. The same components as those of the ultrasonic diagnostic apparatus 100 according to the first embodiment are denoted by the same reference numerals. The ultrasonic diagnostic apparatus 400 includes an ultrasonic probe 1, a transmitting / receiving unit 2, a B-mode processing unit 3,
A DSC 4, a frame memory 5, a difference calculating unit 6, a changing speed ultrasonic image generating unit 7, a changing speed ultrasonic image memory 45 for storing the generated series of changing speed ultrasonic images G1, and a series of changes. A variance calculator 46 for calculating the variance σ (x, y) of the luminance of the corresponding pixel of the velocity ultrasonic image G1, and a change made up of pixels whose luminance and display color are determined according to the variance σ (x, y). It is configured to include a change-velocity-dispersion ultrasonic image generation unit 47 that generates a velocity-dispersion ultrasonic image G4 and a CRT 8.

FIG. 14 shows the ultrasonic diagnostic apparatus 400 of FIG.
FIG. 7 is an exemplary diagram of a changing speed dispersion ultrasonic image G4 generated by the above. If the first area A to the fourth area D have a difference characteristic as shown in FIG. 5 and the luminance is increased and the display color is green as the variance is large, the first area A looks dark green, The second region B looks slightly bright green, the third region C looks bright green, and the fourth region D looks black.

According to the ultrasonic diagnostic apparatus 400 according to the above-described fourth embodiment, the overall state of the fluctuation of the inflow velocity and the outflow velocity of the contrast agent can be seen at a glance from the luminance of each pixel of the change velocity dispersion ultrasonic image G4. I can understand. Further, the operator does not need to set the region of interest.

Fifth Embodiment FIG. 15 is a block diagram showing an ultrasonic diagnostic apparatus according to a fifth embodiment of the present invention. The same components as those of the ultrasonic diagnostic apparatus 100 according to the first embodiment are denoted by the same reference numerals. The ultrasonic diagnostic apparatus 500 includes an ultrasonic probe 1, a transmitting / receiving unit 2, a B-mode processing unit 3,
DSC4, a maximum brightness hold unit 56 for holding the maximum brightness of the corresponding pixel of the series of generated ultrasound images, and a maximum value for generating a maximum value ultrasound image G5 including pixels having the maximum brightness as the brightness. Ultrasound image generation unit 57 and C
RT8.

FIG. 16 shows the ultrasonic diagnostic apparatus 500 of FIG.
FIG. 7 is an exemplary diagram of a maximum value ultrasonic image G5 generated by the above. The first area A to the fourth area D are TICs as shown in FIG.
If the display region has characteristics and the display color is orange, the first region A looks orange at the maximum luminance Ia, the second region B looks orange at the maximum luminance Ib, and the third region C looks orange at the maximum luminance Ic. , The fourth region D looks black.

According to the ultrasonic diagnostic apparatus 500 according to the fifth embodiment described above, the overall situation of the maximum value of the inflow amount of the contrast agent can be grasped at a glance from the luminance of each pixel of the maximum value ultrasonic image G5. Further, the operator does not need to set the region of interest.

Sixth Embodiment FIG. 17 is a block diagram showing an ultrasonic diagnostic apparatus according to a sixth embodiment of the present invention. The same components as those of the ultrasonic diagnostic apparatus 500 according to the fifth embodiment are denoted by the same reference numerals. The ultrasonic diagnostic apparatus 600 includes an ultrasonic probe 1, a transmitting / receiving unit 2, a B-mode processing unit 3,
DSC4, maximum brightness hold unit 56, maximum value ultrasonic image generation unit 57, and time from the time when the operator instructs the start of time measurement to the time when the maximum brightness hold unit 56 holds the latest maximum brightness , A arrival time ultrasonic image generation unit 67 that generates an arrival time ultrasonic image G6 composed of pixels having luminance according to the measured time, and a CRT 8. It is configured.

FIG. 18 shows the ultrasonic diagnostic apparatus 600 shown in FIG.
FIG. 6 is an exemplary diagram of a time-of-arrival ultrasonic image G6 generated by the above method. The first area A to the fourth area D are TICs as shown in FIG.
If the display area has characteristics and the display color is yellow, the first area A looks yellow with a luminance corresponding to the arrival time Ta, the second area B looks yellow with a luminance according to the arrival time Tb, and the third area C Looks yellow with a luminance corresponding to the arrival time Tc, and the fourth region D looks black.

According to the ultrasonic diagnostic apparatus 600 according to the sixth embodiment described above, the overall state of the time from the luminance of each pixel of the arrival time ultrasonic image G6 to the amount of inflow of the contrast agent reaches the maximum value. You can grasp at a glance. Further, the operator does not need to set the region of interest.

-Other Embodiments- In the first to sixth embodiments, the difference, the maximum value, and the arrival time of the pixel value of each pixel of each ultrasonic image are obtained, but not the pixel value of each pixel. Alternatively, the difference, the maximum value, and the arrival time may be obtained by regarding the average value of the target pixel and eight pixels around the target pixel as the pixel value of the target pixel. In this case, the resolution is reduced,
Noise resistance can be improved.

In the first to sixth embodiments, D
Although the difference, the maximum value, and the arrival time are obtained based on the ultrasonic image generated in SC4, the difference, the maximum value, and the arrival time may be obtained based on the B-mode data output by the B-mode processing unit 3.

[0049]

According to the ultrasonic image generating method, the ultrasonic image generating apparatus, and the ultrasonic diagnostic apparatus of the present invention, the inflow and outflow state of the contrast agent can be observed in the whole image. Further, the operator does not need to set the region of interest one by one.

[Brief description of the drawings]

FIG. 1 is a configuration diagram illustrating an ultrasonic diagnostic apparatus according to a first embodiment.

FIG. 2 is a flowchart showing a changing speed ultrasonic image generation process according to the first embodiment.

FIG. 3 is a model diagram of regions having different inflow / outflow characteristics of blood.

FIG. 4 is a TIC characteristic diagram of each region in FIG. 3;

FIG. 5 is a differential characteristic diagram based on the TIC characteristics of FIG.

FIG. 6 is a view showing an example of a changing speed ultrasonic image at time t1.

FIG. 7 is an exemplary diagram of a changing speed ultrasonic image at time t2.

FIG. 8 is a view showing an example of a changing speed ultrasonic image at time t3.

FIG. 9 is a configuration diagram illustrating an ultrasonic diagnostic apparatus according to a second embodiment.

FIG. 10 is a flowchart showing a maximum changing speed ultrasonic image generation process according to the second embodiment.

FIG. 11 is a configuration diagram illustrating an ultrasonic diagnostic apparatus according to a third embodiment.

FIG. 12 is a flowchart illustrating a minimum change speed ultrasonic image generation process according to the third embodiment.

FIG. 13 is a configuration diagram showing an ultrasonic diagnostic apparatus according to a fourth embodiment.

FIG. 14 is a view showing an example of a changing speed dispersion ultrasonic image.

FIG. 15 is a configuration diagram illustrating an ultrasonic diagnostic apparatus according to a fifth embodiment.

FIG. 16 is a view showing an example of a maximum value ultrasonic image.

FIG. 17 is a configuration diagram illustrating an ultrasonic diagnostic apparatus according to a sixth embodiment.

FIG. 18 is an illustration of an arrival time ultrasonic image.

FIG. 19 is an explanatory diagram showing a region of interest set by an operator in a conventional ultrasonic diagnostic apparatus.

FIG. 20 is a TIC characteristic diagram of each region of interest in FIG. 19;

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Ultrasonic probe 2 Transmission / reception part 3 Mode processing part 4 DSC 5 Frame memory 6 Difference calculation part 7 Change speed ultrasonic image generation part 8 CRT 26 Difference maximum value hold part 27 Maximum change velocity ultrasonic image generation part 36 Difference minimum Value hold unit 37 Minimum change speed ultrasonic image generation unit 45 Change speed ultrasonic image memory 46 Dispersion calculation unit 47 Change speed dispersion ultrasonic image generation unit 56 Maximum luminance hold unit 57 Maximum value ultrasonic image generation unit 66 Maximum luminance arrival time Measuring section 67 Arrival time ultrasonic image generating section 100 Ultrasonic diagnostic apparatus 200 Ultrasonic diagnostic apparatus 300 Ultrasonic diagnostic apparatus 400 Ultrasonic diagnostic apparatus 500 Ultrasonic diagnostic apparatus 600 Ultrasonic diagnostic apparatus

Continued on front page F-term (reference) 4C301 CC02 DD01 DD06 EE13 JC12 JC13 KK02 5B057 AA07 BA05 CA02 CA08 CA12 CA16 CB01 CB08 CB12 CB16 CC01 CE14 CH08 CH11 CH20 DA16 DB02 DB05 DB09 DC22 DC32

Claims (13)

[Claims]
1. An ultrasonic image generation method comprising: generating a change speed ultrasonic image in which a change speed of pixel values of a plurality of ultrasonic images generated in a time series is reflected on corresponding pixel values. Method.
2. A maximum change speed ultrasonic image in which the maximum value of the change speed of the pixel value of a plurality of ultrasonic images generated in time series is reflected on the pixel value of a corresponding pixel. Ultrasound image generation method.
3. A method of generating a minimum change speed ultrasonic image in which a minimum value of a change speed of a pixel value of a plurality of ultrasonic images generated in time series is reflected on a pixel value of a corresponding pixel. Ultrasound image generation method.
4. The method according to claim 1, wherein a variance of the change speed of the pixel values of the plurality of ultrasonic images generated in time series is reflected on a pixel value of a corresponding pixel to generate a change speed dispersion ultrasonic image. Ultrasound image generation method.
5. An ultrasonic wave, wherein a maximum value ultrasonic image is generated by reflecting the maximum value of pixel values of a plurality of ultrasonic images generated in time series to the pixel value of a corresponding pixel. Image generation method.
6. An ultrasound system, wherein a time-of-arrival ultrasound image reflecting a time until pixel values of respective pixels of a plurality of ultrasound images generated in time series reach a maximum value is generated. Sound wave image generation method.
7. An ultrasonic image storing means for storing a plurality of ultrasonic images generated in time series, an arithmetic means for calculating a changing speed of a pixel value of the ultrasonic image, and converting the changing speed into a pixel value. An ultrasonic image generating apparatus comprising: a changing speed ultrasonic image generating means for generating a reflected changing speed ultrasonic image.
8. An ultrasonic image storage means for storing a plurality of ultrasonic images generated in time series, an arithmetic means for obtaining a maximum value of a change speed of a pixel value of the ultrasonic image, An ultrasonic image generating apparatus comprising: a maximum changing speed ultrasonic image generating means for generating a maximum changing speed ultrasonic image in which a maximum value is reflected on a pixel value.
9. An ultrasonic image storing means for storing a plurality of ultrasonic images generated in time series, an arithmetic means for obtaining a minimum value of a change speed of a pixel value of the ultrasonic image, An ultrasonic image generating apparatus comprising: a minimum changing speed ultrasonic image generating means for generating a minimum changing speed ultrasonic image in which a minimum value is reflected on a pixel value.
10. An ultrasonic image storage unit for storing a plurality of ultrasonic images generated in time series, an arithmetic unit for calculating a variance of a change speed of a pixel value of the ultrasonic image, and a variance of the change speed. An ultrasonic image generating apparatus comprising: a variable velocity dispersed ultrasonic image generating unit that generates a variable velocity dispersed ultrasonic image in which is reflected in a pixel value.
11. A maximum value holding means for holding a maximum value of a pixel value of each pixel of a plurality of ultrasonic images generated in time series, and a maximum value ultrasonic image reflecting the maximum value in a pixel value And a maximum value ultrasonic image generating means for generating the ultrasonic image.
12. An arrival time obtaining means for obtaining a time until a pixel value of each pixel of a plurality of ultrasonic images generated in time series reaches a maximum value, and an arrival time ultrasonic image reflecting the time difference. And an arrival time ultrasonic image generating means for generating an ultrasonic image.
13. An ultrasonic probe, transmitting and receiving means for transmitting an ultrasonic wave from the ultrasonic probe and obtaining a corresponding reception signal, and an ultrasonic image for generating an ultrasonic image based on the reception signal An ultrasonic diagnostic apparatus comprising: a generating unit; and at least one ultrasonic image generating apparatus according to any one of claims 7 to 12.
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