JP2007044354A - Ultrasonic diagnostic equipment and ultrasonic diagnostic equipment control program - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an ultrasonic diagnostic equipment and an ultrasonic diagnostic equipment control program which can form a suitable three-dimensional image by optimizing a luminance value to each two-dimensional tomographic image constituting the three-dimensional image. <P>SOLUTION: In the case of displaying the three-dimensional image, a concerned area is set to each two-dimensional tomographic image constituting the three-dimensional image, and optimization of the luminance value to each two-dimensional tomographic image such as gain control of each two-dimensional tomographic image is carried out based on a difference value between luminance of each area and optimal luminance set in advance. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

  The present invention relates to an ultrasound diagnostic apparatus that provides information useful for medical diagnosis and a control program thereof, and in particular, improves examination operability and diagnostic performance by optimizing image conditions when constructing a three-dimensional image. It is something to be made.

  An ultrasonic diagnostic apparatus is a medical imaging device that non-invasively obtains a tomographic image of soft tissue in a living body from a body surface by an ultrasonic pulse reflection method. Compared to other medical imaging equipment, this ultrasound diagnostic device is small and inexpensive, has no exposure to X-rays, etc., is highly safe, can be easily moved to the vicinity of patients, and blood flow imaging is possible. It is widely used in the heart, abdomen, urology, and obstetrics and gynecology.

  When generating a three-dimensional image in such an ultrasonic diagnostic apparatus, a plurality of two-dimensional tomographic images are acquired, spatially arranged, and subjected to interpolation processing as necessary to generate a three-dimensional image. Is done. Thereby, various diagnostic objects can be imaged three-dimensionally.

  In general, it is important to optimize the luminance value in imaging using an ultrasonic diagnostic apparatus. In a conventional ultrasonic diagnostic apparatus, optimization of luminance relating to an entire three-dimensional image is realized by feeding back a smoothing condition of luminance values relating to a specific region of a specified two-dimensional tomographic image (for example, Patent Documents). 1).

In addition, as a well-known document relevant to this application, there exist the following, for example.
JP 2002-209889 A

  However, the conventional ultrasonic diagnostic apparatus has the following problems, for example.

  That is, since the brightness optimization condition determined by the conventional brightness value optimization method is related to the tomographic image, it is not always the optimum condition for all the two-dimensional tomographic images constituting the three-dimensional image. Absent. For example, when an ultrasonic wave is transmitted to a partially spherical structure such as a fetal head, the intensity of the reflected wave varies depending on the relationship between the ultrasonic wave transmission direction and the surface shape of the structure (for example, in FIG. As shown, the closer the surface of the structure and the ultrasonic transmission direction are to a right angle, the greater the intensity of the reflected wave). Therefore, depending on the relationship between the ultrasonic transmission direction and the surface shape of the structure, the brightness of each two-dimensional tomographic image for constructing a three-dimensional image may differ as shown in FIGS. 10 (a) and 10 (b). In such a case, even when the same structure is scanned, a three-dimensional image with a constant luminance is generated as shown in FIG.

  The present invention has been made in view of the above circumstances, and an ultrasonic diagnosis capable of generating a suitable three-dimensional image by optimizing image conditions for each two-dimensional tomographic image constituting the three-dimensional image. It is an object of the present invention to provide an apparatus and an ultrasonic diagnostic apparatus control program.

  In order to achieve the above object, the present invention takes the following measures.

  According to a first aspect of the present invention, an ultrasonic transmission / reception unit that ultrasonically scans a three-dimensional region in a subject and generates volume data of an echo signal corresponding to the three-dimensional region, and the volume data, An image generation unit that generates at least two two-dimensional tomographic images included in the three-dimensional region, a display unit that displays the generated ultrasonic image, and a physical quantity based on an echo signal for each two-dimensional tomographic image is acquired. An acquisition unit; a calculation unit that calculates an image condition for each of the two-dimensional tomographic images based on the acquired physical quantity; and the ultrasonic transmission / reception unit and the calculation unit based on the image condition of each of the two-dimensional tomographic images. An ultrasonic diagnostic apparatus comprising: control means for controlling at least one of the image generation means.

  According to a second aspect of the present invention, an ultrasonic transmission / reception function for causing a computer to ultrasonically scan a three-dimensional area in a subject and generate volume data of an echo signal corresponding to the three-dimensional area, and the volume data An image generation function for generating at least two two-dimensional tomographic images included in the three-dimensional region, a display function for displaying the generated ultrasonic image, and a physical quantity based on an echo signal for each of the two-dimensional tomographic images Based on the acquired physical quantity, a calculation function for calculating an image condition for each two-dimensional tomographic image, and the ultrasonic transmission / reception based on the image condition for each two-dimensional tomographic image And a control function for controlling at least one of the image generating means and the image generating means.

  As described above, according to the present invention, an ultrasonic diagnostic apparatus and an ultrasonic diagnostic apparatus that can generate a suitable three-dimensional image by optimizing image conditions for each two-dimensional tomographic image constituting the three-dimensional image. A control program can be realized.

  Hereinafter, embodiments of the present invention will be described with reference to the drawings. In the following description, components having substantially the same function and configuration are denoted by the same reference numerals, and redundant description will be given only when necessary.

  FIG. 1 is a diagram showing a block configuration of an ultrasonic diagnostic apparatus 10 according to the present embodiment. As shown in the figure, the ultrasonic diagnostic apparatus 10 includes an ultrasonic probe 12, an input device 13, a monitor 14, a transmission / reception unit 21, a B-mode processing unit 22, a Doppler processing unit 23, a data analysis unit 24, and an image generation circuit. 25, an image memory 26, a control processor 27, a software storage unit 28, an internal storage device 29, and an interface unit 30. Hereinafter, the function of each component will be described.

  The ultrasonic probe 12 generates ultrasonic waves based on a drive signal from the ultrasonic transmission / reception unit 21, converts a reflected wave from the subject into an electric signal, and a matching layer provided in the piezoelectric vibrator. And a backing material for preventing the propagation of ultrasonic waves from the piezoelectric vibrator to the rear. When ultrasonic waves are transmitted from the ultrasonic probe 12 to the subject P, the transmitted ultrasonic waves are successively reflected by the discontinuous surface of the acoustic impedance of the body tissue and received by the ultrasonic probe 12 as an echo signal. . The amplitude of this echo signal depends on the difference in acoustic impedance at the discontinuous surface that is supposed to be reflected. In addition, the echo when the transmitted ultrasonic pulse is reflected by the moving blood flow or the surface of the heart wall depends on the velocity component in the ultrasonic transmission direction of the moving body due to the Doppler effect, and the frequency Receive a shift.

  The ultrasonic probe 12 may be either a two-dimensional probe in which piezoelectric vibrators are arranged in a two-dimensional matrix, or a one-dimensional probe in which piezoelectric vibrators are arranged in a one-dimensional array. When performing a three-dimensional volume scan with the ultrasonic probe 12 as a one-dimensional probe, the ultrasonic probe 12 or the piezoelectric vibrator array is oscillated by mechanical control or manually.

  The input device 13 is connected to the device main body 11, and includes a trackball 13a and various switches / buttons 13b for inputting various parameter condition setting and changing instructions, a region of interest (ROI) setting instruction, etc. from the operator to the device main body 11. A mouse 13c, a keyboard 13d, and the like.

  The monitor 14 displays in vivo morphological information and blood flow information as an image based on the video signal from the image generation circuit 25.

  The transmission / reception unit 21 includes a trigger generation circuit, a delay circuit, a pulsar circuit, and the like (not shown). In the pulsar circuit, a rate pulse for forming a transmission ultrasonic wave is repeatedly generated at a predetermined rate frequency fr Hz (period: 1 / fr second). Further, in the delay circuit, a delay time necessary for focusing the ultrasonic wave into a beam shape for each channel and determining the transmission directivity is given to each rate pulse. The trigger generation circuit applies a drive pulse to the probe 12 at a timing based on this rate pulse.

  Further, the transmission / reception unit 21 includes an amplifier circuit, an A / D converter, an adder, and the like which are not shown. The amplifier circuit amplifies the echo signal captured via the probe 12 with a predetermined gain for each channel. In the A / D converter, a delay time necessary for determining the reception directivity is given to the amplified echo signal, and thereafter, an addition process is performed in the adder. By this addition, the reflection component from the direction corresponding to the reception directivity of the echo signal is emphasized, and a comprehensive beam for ultrasonic transmission / reception is formed by the reception directivity and the transmission directivity.

  The B-mode processing unit 22 receives the echo signal from the transmission / reception unit 21, performs logarithmic amplification, envelope detection processing, and the like, and generates B-mode information in which the signal intensity is expressed by brightness. The B-mode information is transmitted to the image generation circuit 25 and displayed on the monitor 14 as a B-mode image in which the intensity of the reflected wave is expressed by luminance.

  The Doppler processing unit 23 performs frequency analysis on velocity information from the echo signal received from the transmission / reception unit 21, extracts blood flow, tissue, and contrast agent echo components due to the Doppler effect, and obtains blood flow information such as average velocity, dispersion, and power. Ask for multiple points. The obtained blood flow information is sent to the image generation circuit 25 as Doppler information, and is displayed in color on the monitor 14 as an average velocity image, a dispersion image, a power image, and a combination image thereof.

  The data analysis unit 24 executes an image condition optimization process, which will be described later, under the control of the control processor 27. Here, the image condition is an echo signal value (for example, a B-mode detection data signal value, for example) at each position of the two-dimensional tomographic image before the scan conversion so that the luminance value of the finally displayed image is suitable. B-mode raster data signal value, RF data signal value, IQ data signal value, B-mode orthogonal transform data signal value, etc.) and conditions for determining the luminance value in each pixel of the two-dimensional tomographic image after scan conversion .

  The image generation circuit 25 includes a signal processing circuit, a scan converter, and an image formatter (each not shown). First, the signal processing circuit performs filtering so as to determine the image quality at the level of the scanning line signal string of the ultrasonic scan. The output of the signal processing circuit is sent to the scan converter and simultaneously stored in the image memory 26. The scan converter converts a scanning line signal string of ultrasonic scanning into a scanning line signal string of a general video format represented by a television or the like. This output is sent to an image formatter. Here, brightness and contrast adjustment, image processing such as a spatial filter, character information of various setting parameters, scales, a first reference line or a second reference line described later, etc. Are combined and output to the monitor 14 as a video signal. The image formatter controls the position of the baseline displayed on the monitor 14, the display scale of the Doppler waveform, and the like in response to a predetermined operation from the input device 13.

  The image memory 26 includes a storage memory that stores image data received from the image generation circuit 25. This image data can be called by an operator after diagnosis, for example, and can be reproduced as a still image or as a moving image using a plurality of images.

  The control processor 27 has a function as an information processing apparatus (computer), and statically or dynamically controls the operation of the main body of the ultrasonic diagnostic apparatus. In particular, the control processor 27 controls the transmission / reception unit 21, the image generation circuit 25, and the like according to image conditions obtained in an image condition optimization process described later.

  The software storage unit 28 stores a program for realizing various scan sequences and workflows, a dedicated program for realizing an image condition optimization function described later, and the like.

  The internal storage device 29 stores image data acquired by the ultrasonic diagnostic apparatus, image data acquired by the interface unit 30 via a network, various data groups such as various diagnostic protocols and ultrasonic transmission / reception conditions.

  The interface unit 30 is an interface related to the input device 13, the network, and a new external storage device (not shown). Data such as ultrasonic images and analysis results obtained by the apparatus can be transferred to another apparatus via the network by the interface unit 30.

(Image condition optimization function)
Next, details of the image condition optimization function of the ultrasonic diagnostic apparatus 1 will be described. This image condition optimization function optimizes the image condition for each two-dimensional tomographic image constituting the three-dimensional image so that the luminance of the finally displayed three-dimensional image is suitable. In the following, for the sake of specific explanation, a case where optimization of luminance values is executed as image condition optimization is taken as an example. However, the configuration may be such that, for example, the raw data (RF data or the like) signal value before scan conversion is optimized without being bound by this.

  FIG. 2 is a flowchart showing a flow of processing (image condition optimization processing) executed in accordance with the image condition optimization function. As shown in the figure, first, the data analysis unit 24 calculates the average luminance value of the region at the same position of the two-dimensional tomographic image with respect to the vertical direction (thickness direction) of the two-dimensional tomographic image constituting the three-dimensional image. Is acquired (step A). This area is manually set to a desired position by the operator or automatically set to a predetermined position in the apparatus. Moreover, although it can set in any position on a two-dimensional tomogram, it is preferable to set so that it may overlap with the region of interest in a diagnosis.

  FIG. 3 is a conceptual diagram showing acquisition of an average luminance value for each two-dimensional tomographic image in step A. In the figure, an example in which an average luminance value is obtained for each circular small region set on each two-dimensional tomographic image is shown.

  Next, the data analysis unit 24 uses the average luminance value for each small region to create a fitting curve indicating the relationship between the position in the thickness direction and the (average) luminance value as shown in FIG. 4 (step SB). . The reason why such a fitting curve is created is to make it easy to understand the luminance change in the thickness direction in the finally displayed three-dimensional image.

  Next, as shown in FIG. 5, a difference value between the target luminance value and the luminance value at each position in the thickness direction of the fitting curve is calculated (step SC). Here, the target luminance value is set in advance by manual input or automatic calculation based on examination items, patient information, and the like.

  Next, the data analysis unit 24 determines an image condition in each small region for each two-dimensional tomographic image based on each difference value calculated in step SC (step SD). For example, based on the calculated difference values, image conditions such as increasing / decreasing the gain in echo signal reception for each tomography or increasing / decreasing the luminance value for each tomography in the post process are calculated.

  In step SA, an average luminance value was obtained for one small region set on each two-dimensional tomographic image. However, without being bound by this, two or more small regions are set on each two-dimensional tomographic image, or a plurality of small regions (divided regions) that divide each two-dimensional tomographic image as shown in FIG. May be set, and the processing from step SA to step SD may be executed for each of them. Therefore, in such a case, an image condition is generated for each small area on one two-dimensional tomographic image, and transmission / reception control or the like according to the image condition is executed for each small area. The number of small areas set on one two-dimensional tomographic image is preferably selectable arbitrarily.

  FIG. 7 is a diagram illustrating a difference in a three-dimensional image depending on the presence / absence of the brightness value optimization process. As shown in the figure, when there is no luminance value optimization processing, the luminance differs for each two-dimensional tomographic image, whereas when there is luminance value optimization processing, the luminance of all the two-dimensional tomographic images. Are unified according to the target luminance value.

(Operation)
Next, the operation | movement in the three-dimensional image acquisition of this ultrasonic diagnostic apparatus 1 is demonstrated. In this embodiment, in order to make the description more specific, an example is given in which three-dimensional image data is acquired by moving two-dimensional scanning in the thickness direction.

  FIG. 7 is a flowchart showing the flow of each process executed in the three-dimensional image acquisition of the ultrasonic diagnostic apparatus 1. As shown in the figure, first, an ultrasonic wave is transmitted to a predetermined slice of the subject, and a reflected wave from the slice is received (step S1). The received reflected wave is converted into an echo signal, subjected to predetermined signal processing, and stored in the internal storage device 29 as ultrasonic image data for each frame (step S2).

  Next, the ultrasonic transmission / reception position (that is, the tomographic position to be scanned) is changed (step S3), and the necessary tomographic image data (that is, all the two-dimensional tomographic image data constituting the three-dimensional image). Is determined (step S4). If all the necessary tomographic image data has not been acquired, the processes of steps S1 to S4 are repeatedly executed.

  Next, image data analysis according to FIG. 2 is executed to determine image conditions (for example, transmission / reception conditions for adjusting the gain) (step S5). After changing the transmission / reception conditions so as to optimize the luminance value (step S6), the control processor 27 transmits the ultrasonic wave again to the predetermined tomography of the subject and receives the reflected wave from the tomography (step S7). ). The received reflected wave is converted into an echo signal according to the converted transmission / reception conditions, is subjected to predetermined signal processing, and is stored in the internal storage device 29 as ultrasonic image data for each frame (step S8).

  Next, the ultrasonic transmission / reception position is changed (step S9), it is determined whether or not the necessary tomographic image data has been acquired (step S10), and all necessary tomographic image data is acquired. If not, the processes in steps S7 to S10 are repeatedly executed. On the other hand, when the image data of all necessary tomographic images has been acquired, a three-dimensional image is constructed with the two-dimensional tomographic image subjected to the brightness value optimization processing (step S11) and displayed on the monitor 14. (Step S12).

  According to the configuration described above, the following effects can be obtained.

  According to this ultrasonic diagnostic apparatus, when generating a three-dimensional image, the image conditions are optimized for each two-dimensional tomographic image so that the brightness of each two-dimensional tomographic image constituting the three-dimensional image becomes a target value. To do. Therefore, the brightness of the entire three-dimensional image can be unified, and a three-dimensional image suitable for diagnosis can be provided. Moreover, according to this ultrasonic diagnostic apparatus, the brightness of the entire three-dimensional image can be automatically unified. As a result, the work burden on the operator can be reduced.

  Note that the present invention is not limited to the above-described embodiment as it is, and can be embodied by modifying the components without departing from the scope of the invention in the implementation stage.

  (1) The image condition optimization function according to the present embodiment can also be realized by installing a program for executing the processing in a computer such as a workstation and developing the program on a memory. At this time, a program capable of causing the computer to execute the technique is stored in a recording medium such as a magnetic disk (floppy (registered trademark) disk, hard disk, etc.), an optical disk (CD-ROM, DVD, etc.), or a semiconductor memory. It can also be distributed.

  (2) In the above-described embodiment, all of the two-dimensional tomographic images constituting the three-dimensional image are targeted for image optimization processing. However, without being bound by this, the above-described image condition optimization processing can also be executed by using at least two two-dimensional tomographic images included in the three-dimensional image. For example, from the viewpoint of processing efficiency, when targeting a part of a two-dimensional tomographic image constituting a three-dimensional image, a plurality of two-dimensional tomographic images including the center of volume data, the center of volume data A two-dimensional tomographic image within a certain range including a plurality of two-dimensional tomographic images generated so as to include the center of the volume data and by thinning out the volume data at certain intervals can be used. Moreover, it is preferable that any two-dimensional tomographic image to be subjected to image optimization processing can be arbitrarily set.

  In addition, various inventions can be formed by appropriately combining a plurality of constituent elements disclosed in the embodiment. For example, some components may be deleted from all the components shown in the embodiment. Furthermore, constituent elements over different embodiments may be appropriately combined.

  As described above, according to the present invention, an ultrasonic diagnostic apparatus and an ultrasonic diagnostic apparatus that can generate a suitable three-dimensional image by optimizing image conditions for each two-dimensional tomographic image constituting the three-dimensional image. A control program can be realized.

FIG. 1 is a diagram showing a block configuration of an ultrasonic diagnostic apparatus 10 according to the present embodiment. FIG. 2 is a flowchart showing the flow of processing executed in the image condition optimization function. FIG. 3 is a conceptual diagram showing acquisition of an average luminance value for each two-dimensional tomographic image in step A of FIG. FIG. 4 is a diagram showing an example of a fitting curve related to the luminance value in the thickness direction created in step SB of FIG. FIG. 5 is a diagram showing a difference value between the target luminance value and the luminance value at each position of the fitting curve generated in step SB. FIG. 6 is a conceptual diagram for explaining another example of obtaining an average luminance value for each two-dimensional tomographic image in step A of FIG. FIG. 7 is a diagram illustrating a difference in a three-dimensional image depending on the presence / absence of the brightness value optimization process. FIG. 8 is a flowchart showing the flow of each process executed in the three-dimensional image acquisition of the ultrasonic diagnostic apparatus 1. FIG. 9 is a diagram for explaining a photographing mechanism of a three-dimensional ultrasonic image. FIG. 10 is a diagram for explaining a conventional luminance optimization method. FIG. 11 is a diagram for explaining a conventional luminance optimization method.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 ... Ultrasonic diagnostic apparatus, 12 ... Ultrasonic probe, 13 ... Input device, 14 ... Monitor, 21 ... Transmission / reception unit, 22 ... B mode processing unit, 23 ... Doppler processing unit, 24 ... Data analysis part, 25 ... Image generation Circuit, 26 ... Image memory, 27 ... Control processor, 28 ... Storage unit, 30 ... Interface unit

Claims (12)

Ultrasonic transmission / reception means for ultrasonically scanning a three-dimensional region in a subject and generating volume data of an echo signal corresponding to the three-dimensional region;
Image generating means for generating at least two two-dimensional tomographic images included in the three-dimensional region based on the volume data;
Display means for displaying the generated ultrasound image;
Acquisition means for acquiring a physical quantity based on an echo signal for each of the two-dimensional tomographic images;
Calculation means for calculating an image condition for each two-dimensional tomographic image based on the acquired physical quantity;
Control means for controlling at least one of the ultrasonic transmission / reception means and the image generation means based on the image condition for each two-dimensional tomographic image;
An ultrasonic diagnostic apparatus comprising: The acquisition means acquires the physical quantity for each at least one region that exists for each of the two-dimensional tomographic images and corresponds to a position between the two-dimensional tomographic images,
The calculation means calculates a fitting curve indicating a relationship between a position in the thickness direction of the two-dimensional tomographic image and the physical quantity based on the physical quantity acquired for each region of the two-dimensional tomographic image, and the fitting Calculating the image condition based on a difference value between a curve and a preset target value;
The ultrasonic diagnostic apparatus according to claim 1. The acquisition means acquires the physical quantity for each of a plurality of divided regions constituting each of the two-dimensional tomographic images,
The calculation means calculates a fitting curve indicating a relationship between a position in the thickness direction of the two-dimensional tomographic image and the physical quantity based on the plurality of acquired physical quantities, and the fitting curve and a preset target value And calculating the image condition for each of the divided regions of each two-dimensional tomographic image based on the difference value between
The control means controls at least one of the ultrasonic transmission / reception means and the image generation means based on the image condition for each of the divided regions of the two-dimensional tomographic images;
The ultrasonic diagnostic apparatus according to claim 1.   The physical quantity includes a B-mode detection data signal value, a B-mode raster data signal value, an RF data signal value, an IQ data signal value, a B-mode orthogonal transformation data signal value relating to a region located at a corresponding position between the two-dimensional tomographic images. The ultrasonic diagnostic apparatus according to any one of claims 1 to 3, wherein the average value is any one of luminance values.   The ultrasonic diagnostic apparatus according to claim 1, wherein the control unit controls the ultrasonic transmission / reception unit so as to adjust a gain according to the image condition.   The said control means controls the said image generation means so that the luminance value in a post process may be adjusted according to the said image conditions for every said two-dimensional tomographic image, The one of the Claims 1 thru | or 4 characterized by the above-mentioned. The ultrasonic diagnostic apparatus as described. On the computer,
An ultrasonic transmission / reception function that ultrasonically scans a three-dimensional region in the subject and generates volume data of an echo signal corresponding to the three-dimensional region;
An image generating function for generating at least two two-dimensional tomographic images constituting the three-dimensional region based on the volume data;
A display function for displaying the generated ultrasound image;
Acquisition means for acquiring a physical quantity based on an echo signal for each of the two-dimensional tomographic images;
A calculation function for calculating an image condition for each of the two-dimensional tomographic images based on the acquired physical quantity;
A control function for controlling at least one of the ultrasonic transmission / reception means and the image generation means based on the image condition for each of the two-dimensional tomographic images;
An ultrasonic diagnostic apparatus control program characterized by realizing the above. In the acquisition function, the physical quantity is acquired for each of at least one region that exists for each two-dimensional tomographic image and corresponds to the position between the two-dimensional tomographic images,
In the calculation function, based on the physical quantity acquired for each region of the two-dimensional tomographic image, a fitting curve indicating a relationship between a position in the thickness direction of the two-dimensional tomographic image and the physical quantity is calculated. Calculating the image condition based on a difference value between a fitting curve and a preset target value;
The ultrasound diagnostic apparatus control program according to claim 7. In the acquisition function, the physical quantity is acquired for each of a plurality of divided regions constituting each of the two-dimensional tomographic images,
In the calculation function, a fitting curve indicating a relationship between a position in the thickness direction of the two-dimensional tomographic image and the physical quantity is calculated based on the plurality of acquired physical quantities, and the fitting curve and a preset target are calculated. Calculating the image condition for each of the divided regions of the two-dimensional tomographic image based on a difference value from the value;
In the control function, controlling at least one of the ultrasonic transmission / reception means and the image generation means based on the image condition for each of the divided regions of the two-dimensional tomographic images;
The ultrasound diagnostic apparatus control program according to claim 7.   The physical quantity includes a B-mode detection data signal value, a B-mode raster data signal value, an RF data signal value, an IQ data signal value, a B-mode orthogonal transformation data signal value relating to a region located at a corresponding position between the two-dimensional tomographic images. The ultrasound diagnostic apparatus control program according to any one of claims 7 to 9, wherein the average value is any one of luminance values.   The ultrasound diagnostic apparatus control program according to any one of claims 7 to 10, wherein, in the control function, the ultrasound transmission / reception unit is controlled to adjust a gain according to the image condition.   11. The control function according to claim 7, wherein the image generation unit is controlled to adjust a luminance value in a post process according to the image condition for each of the two-dimensional tomographic images. The ultrasound diagnostic apparatus control program according to Item.

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