JP2019017655A - Ultrasound diagnostic apparatus, image processing apparatus, and image processing program - Google Patents

Abstract

To provide an ultrasound diagnostic apparatus with which the resolution of a zoomed-up image is increased.SOLUTION: The ultrasound diagnostic apparatus includes an image generation unit 120, a display control unit 141, and a reception unit 142. The image generation unit generates display image data from ultrasound image data. The display control unit causes a display unit to display the display image data. The reception unit receives operation performed on the display image data displayed on the display unit from an operator. The image generation unit, when the reception unit receives a zoom-up operation for zooming up the display image data, zooms up the ultrasound image data according to the zoom-up operation and regenerates new, zoomed-up display image data.SELECTED DRAWING: Figure 1

Description

  Embodiments described herein relate generally to an ultrasonic diagnostic apparatus, an image processing apparatus, and an image processing program.

  2. Description of the Related Art Conventionally, an ultrasonic diagnostic apparatus that performs ultrasonic scanning on a three-dimensional region in a subject to generate and display an MPR (Multi Planar Reconstruction) image or a VR (Volume Rendering) image has been put into practical use. In order to display the MPR image or the VR image, the image data generated by the reconstruction process or the rendering process is temporarily stored in the frame buffer and displayed according to the display size of the display. Further, if necessary, a zoom function, that is, a display image enlargement / reduction function is used. For example, when it is desired to observe the image data in the region of interest in detail, the image data is enlarged, and when it is desired to observe a wider region, the image data is reduced.

JP2013-414A Special table 2015-500083 gazette JP 2014-239841 A

  The problem to be solved by the present invention is to provide an ultrasonic diagnostic apparatus, an image processing apparatus, and an image processing program capable of improving the resolution of an enlarged image.

  The ultrasonic diagnostic apparatus according to the embodiment includes an image generation unit, a display control unit, and a reception unit. The image generation unit generates display image data from the ultrasonic image data. The display control unit displays the display image data on the display unit. The accepting unit accepts an operation on the display image data displayed on the display unit from an operator. When the reception unit receives an enlargement operation for enlarging the display image data, the image generation unit enlarges the ultrasonic image data according to the enlargement operation, and creates a new display image after enlargement Regenerate the data.

FIG. 1 is a block diagram illustrating a configuration example of the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 2 is a diagram for explaining a case where enlargement is performed using image data stored in the frame buffer. FIG. 3 is a diagram for explaining an enlargement function by the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 4 is a diagram for explaining an enlargement function by the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 5 is a flowchart showing a processing procedure of the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 6 is a diagram for explaining processing of the ultrasonic diagnostic apparatus according to the modification of the first embodiment. FIG. 7 is a diagram for explaining processing of the ultrasonic diagnostic apparatus according to the modification of the first embodiment. FIG. 8 is a diagram for explaining an enlargement function by the ultrasonic diagnostic apparatus according to the second embodiment.

  Hereinafter, an ultrasonic diagnostic apparatus, an image processing apparatus, and an image processing program according to embodiments will be described with reference to the drawings. Hereinafter, as an example, a case where the embodiment described below is applied to an ultrasonic diagnostic apparatus will be described, but the embodiment is not limited thereto. For example, the embodiment can be applied to an image processing apparatus that can process ultrasonic image data collected by an ultrasonic diagnostic apparatus.

(First embodiment)
FIG. 1 is a block diagram illustrating a configuration example of an ultrasonic diagnostic apparatus 1 according to the first embodiment. As shown in FIG. 1, the ultrasonic diagnostic apparatus 1 according to the first embodiment includes an apparatus main body 100, an ultrasonic probe 101, an input device 102, and a display 103. The ultrasonic probe 101, the input device 102, and the display 103 are connected to the apparatus main body 100.

  The ultrasonic probe 101 includes a plurality of vibrators (for example, piezoelectric vibrators), and the plurality of vibrators generate ultrasonic waves based on a drive signal supplied from a transmission / reception circuit 110 included in the apparatus main body 100 described later. To do. The plurality of transducers included in the ultrasonic probe 101 receives reflected waves from the subject P and converts them into electrical signals. In addition, the ultrasonic probe 101 includes a matching layer provided on the vibrator, a backing material that prevents propagation of ultrasonic waves from the vibrator to the rear, and the like.

  When ultrasonic waves are transmitted from the ultrasonic probe 101 to the subject P, the transmitted ultrasonic waves are successively reflected by the discontinuous surface of the acoustic impedance in the body tissue of the subject P, and reflected wave signals (echo signals) Are received by a plurality of transducers included in the ultrasonic probe 101. The amplitude of the received reflected wave signal depends on the difference in acoustic impedance at the discontinuous surface where the ultrasonic wave is reflected. Note that the reflected wave signal when the transmitted ultrasonic pulse is reflected by the moving blood flow or the surface of the heart wall depends on the velocity component of the moving object in the ultrasonic transmission / reception direction due to the Doppler effect. And undergoes a frequency shift.

  In the first embodiment, the ultrasonic probe 101 shown in FIG. 1 is a one-dimensional ultrasonic probe in which a plurality of piezoelectric vibrators are arranged in a line, or a plurality of piezoelectric vibrators arranged in a line. Is a mechanically oscillated mechanical 4D (Dimension) ultrasonic probe, and is applicable to any of two-dimensional ultrasonic probes in which a plurality of piezoelectric vibrators are arranged two-dimensionally in a lattice shape Is possible.

  The input device 102 includes a mouse, a keyboard, a button, a panel switch, a touch command screen, a foot switch, a trackball, a joystick, and the like, receives various setting requests from an operator of the ultrasonic diagnostic apparatus 1, and The various setting requests received are transferred.

  The display 103 displays a GUI (Graphical User Interface) for the operator of the ultrasound diagnostic apparatus 1 to input various setting requests using the input device 102, display image data generated in the apparatus main body 100, and the like. Is displayed.

  The apparatus main body 100 is an apparatus that generates display image data based on a reflected wave signal received by the ultrasonic probe 101. For example, as shown in FIG. 1, the apparatus main body 100 includes a transmission / reception circuit 110, a signal processing circuit 120, an image processing circuit 130, a processing circuit 140, an internal storage circuit 150, an image memory 160, and a frame buffer 170. And have. The transmission / reception circuit 110, the signal processing circuit 120, the image processing circuit 130, the processing circuit 140, the internal storage circuit 150, the image memory 160, and the frame buffer 170 are connected to be communicable with each other.

  The transmission / reception circuit 110 includes a pulse generator, a transmission delay unit, a pulser, and the like, and supplies a drive signal to the ultrasonic probe 101. The pulse generator repeatedly generates rate pulses for forming transmission ultrasonic waves at a predetermined rate frequency. The transmission delay unit generates a delay time for each piezoelectric vibrator necessary for focusing the ultrasonic wave generated from the ultrasonic probe 101 into a beam and determining transmission directivity. Give for each rate pulse. The pulser applies a drive signal (drive pulse) to the ultrasonic probe 101 at a timing based on the rate pulse. That is, the transmission delay unit arbitrarily adjusts the transmission direction of the ultrasonic wave transmitted from the piezoelectric vibrator surface by changing the delay time given to each rate pulse.

  The transmission / reception circuit 110 has a function capable of instantaneously changing the transmission frequency, the transmission drive voltage, and the like in order to execute a predetermined scan sequence based on an instruction from the processing circuit 140 described later. In particular, the change of the transmission drive voltage is realized by a linear amplifier type transmission circuit capable of instantaneously switching the value or a mechanism for electrically switching a plurality of power supply units.

  The transmission / reception circuit 110 includes a preamplifier, an A / D (Analog / Digital) converter, a reception delay unit, an adder, and the like. The transmission / reception circuit 110 performs various processing on the reflected wave signal received by the ultrasonic probe 11 and reflects it. Generate wave data. The preamplifier amplifies the reflected wave signal for each channel. The A / D converter A / D converts the amplified reflected wave signal. The reception delay unit gives a delay time necessary for determining the reception directivity. The adder performs an addition process of the reflected wave signal processed by the reception delay unit to generate reflected wave data. By the addition processing of the adder, the reflection component from the direction corresponding to the reception directivity of the reflected wave signal is emphasized, and a comprehensive beam for ultrasonic transmission / reception is formed by the reception directivity and the transmission directivity.

  The transmission / reception circuit 110 transmits an ultrasonic beam in a two-dimensional direction from the ultrasonic probe 101 when scanning a two-dimensional region of the subject P. Then, the transmission / reception circuit 110 generates two-dimensional reflected wave data from the reflected wave signal received by the ultrasonic probe 101. Further, when scanning the three-dimensional region of the subject P, the transmission / reception circuit 110 transmits an ultrasonic beam from the ultrasonic probe 101 in a three-dimensional direction. Then, the transmission / reception circuit 110 generates three-dimensional reflected wave data from the reflected wave signal received by the ultrasonic probe 101.

  For example, the signal processing circuit 120 performs logarithmic amplification, envelope detection processing, and the like on the reflected wave data received from the transmission / reception circuit 110, and data (B-mode data) in which the signal intensity at each sample point is expressed by luminance. ) Is generated. Specifically, the signal processing circuit 120 generates data (B mode data) representing a tomographic image of a tissue and a contrast agent echo component. The B mode data generated by the signal processing circuit 120 is output to the image processing circuit 130.

  For example, the signal processing circuit 120 generates motion information based on the Doppler effect of the moving body from the reflected wave data received from the transmission / reception circuit 110 as data (Doppler data) extracted at each sample point in the scanning region. . Specifically, the signal processing circuit 120 extracts blood flow components (color Doppler components) and tissue components (tissue Doppler components) from the reflected wave data based on the Doppler effect, and moves the moving body such as average velocity, dispersion, and power. Data (Doppler data) obtained by extracting information from multiple points is generated. Here, the moving body is, for example, a blood flow, a tissue such as a heart wall, or a contrast agent. The motion information obtained by the signal processing circuit 120 is sent to the image processing circuit 130 and displayed on the display 103 as an average velocity image, a dispersion image, a power image, or a combination image thereof.

  Here, the B-mode data and Doppler data generated in the signal processing circuit 120 are data represented by a scanning line signal string of ultrasonic scanning, and are referred to as “raw data (low data)”. That is, the Raw data is data in which a space having a shape corresponding to the type of ultrasonic probe (linear probe, convex probe, sector probe, etc.) is represented by a scanning line signal string. In the present embodiment, raw data collected by ultrasonic scanning on a three-dimensional space is referred to as “three-dimensional raw data”.

  The image processing circuit 130 generates display image data from the data generated by the signal processing circuit 120. In the case of two-dimensional scanning, the image processing circuit 130 generates B-mode image data for display in which the intensity of the reflected wave is represented by luminance from the B-mode data generated by the signal processing circuit 120. Further, the image processing circuit 130 generates display Doppler image data representing moving body information from the Doppler data generated by the signal processing circuit 120. The Doppler image data is velocity image data, distributed image data, power image data, or image data obtained by combining these.

  Here, the image processing circuit 130 generally converts (scan converts) a scanning line signal sequence (raw data) of ultrasonic scanning into a scanning line signal sequence of a video format typified by a television or the like, and displays it. Image data is generated. Specifically, the image processing circuit 130 generates display image data by performing coordinate conversion in accordance with the ultrasonic scanning mode by the ultrasonic probe 101.

  That is, B-mode data and Doppler data are ultrasonic data (Raw data) before the scan conversion process, and data generated by the image processing circuit 130 is display image data after the scan conversion process. Here, the Raw data is also referred to as ultrasonic image data in order to facilitate the following description. In addition, when the signal processing circuit 120 generates 3D Raw data (3D B mode data and 3D Doppler data), the image processing circuit 130 performs voxel data and interpolation processing on the 3D Raw data. In some cases, three-dimensional image data to be called is generated. Here, in order to facilitate the following description, the three-dimensional raw data and the voxel data are referred to as ultrasonic image data. Then, the image processing circuit 130 performs coordinate transformation and various rendering processes on the three-dimensional ultrasonic image data according to the ultrasonic scanning mode by the ultrasonic probe 101 to obtain two-dimensional image data, that is, display. Image data is generated.

  Here, “voxel data” represents, for example, data in which three-dimensional raw data is incorporated into a predetermined three-dimensional data space. In other words, for example, the image processing circuit 130 generates the three-dimensional B-mode image data as voxel data by incorporating the three-dimensional B-mode data by coordinate transformation (interpolation) into a predetermined three-dimensional data space. To do. Further, the image processing circuit 130 generates the three-dimensional Doppler image data as voxel data by incorporating the three-dimensional Doppler data by converting the coordinates into a predetermined three-dimensional data space. In other words, data in a state before being assigned to the data space as voxel data (a state in which no interpolation processing is performed) is referred to as “raw data”. In the following embodiments, “Raw data” and “voxel data” are collectively referred to as “ultrasound image data”.

  The processing circuit 140 controls the entire processing of the ultrasonic diagnostic apparatus 1. Specifically, the processing circuit 140 is based on various setting requests input from the operator via the input device 102, various control programs and various data read from the internal storage circuit 150, and the transmission / reception circuit 110, signal processing, and the like. The processing of the circuit 120 and the image processing circuit 130 is controlled. In addition, the processing circuit 140 controls the display 103 to display the display image data stored in the frame buffer 170.

  Further, the processing circuit 140 executes a display control function 141 and a reception function 142 as shown in FIG. Here, for example, each processing function executed by the display control function 141 and the reception function 142 which are components of the processing circuit 140 shown in FIG. 1 is a storage device of the ultrasonic diagnostic apparatus 1 in the form of a program executable by a computer. (For example, the internal storage circuit 150). The processing circuit 140 is a processor that realizes a function corresponding to each program by reading each program from the storage device and executing the program. In other words, the processing circuit 140 in a state where each program is read has each function shown in the processing circuit 140 of FIG. Each processing function executed by the display control function 141 and the reception function 142 will be described later.

  The internal storage circuit 150 stores a control program for performing ultrasonic transmission / reception, image processing, and display processing, diagnostic information (for example, patient ID, doctor's findings, etc.), various data such as a diagnostic protocol and various body marks. To do. The internal storage circuit 150 is also used for storing image data stored in the image memory 160 as necessary. The data stored in the internal storage circuit 150 can be transferred to an external device via an interface (not shown).

  The image memory 160 is a memory that stores ultrasonic image data generated by the signal processing circuit 120 to the image processing circuit 130. For example, the image memory 160 stores three-dimensional raw data corresponding to a plurality of scanning planes as ultrasonic image data. For example, the image memory 160 can also store voxel data in which three-dimensional raw data is incorporated in a predetermined data space.

  The B mode data and Doppler data stored in the image memory 160, that is, Raw data can be called by an operator after diagnosis, for example, and become display image data via the image processing circuit 130.

  The frame buffer 170 is a storage area for storing display image data (frame buffer data) to be displayed on the display 103. For example, the display image data stored in the frame buffer 170 is converted into a display image of the display size (number of pixels) of the display 103 by interpolation processing such as linear interpolation. Then, the converted display image is displayed on the display 103. For example, the frame buffer 170 stores MPR (Multi Planar Reconstruction) image data and VR (Volume Rendering) image data generated by the image processing circuit 130 as display image data.

  In the ultrasonic diagnostic apparatus 1 according to the first embodiment, the three-dimensional raw data can be collected by various collection methods. For example, the following four methods are representative as methods for collecting three-dimensional raw data.

  The first method is a method called Sensor 3D method. The Sensor 3D method acquires the positional information of the ultrasonic probe 101 that scans the two-dimensional scanning plane, and moves the ultrasonic probe 101 in a direction substantially perpendicular to the scanning plane, so that two-dimensional two-dimensional frames of different positions can be obtained. This is a method of collecting raw data as three-dimensional raw data. In the Sensor3D method, since each frame is not necessarily equally spaced, voxel data in which sample positions are evenly spaced is generated based on position information when two-dimensional raw data of each frame is collected. .

  The second method is a method called Smart3D method. The Smart3D method collects a plurality of frames of two-dimensional raw data by moving the ultrasonic probe 101 in a direction substantially perpendicular to the scanning plane, and each frame (sample position) in the two-dimensional raw data of a plurality of frames is equal. This is a method of collecting three-dimensional raw data on the assumption that they are arranged at intervals. In this case, since it is assumed that the frames are arranged at equal intervals, the voxel data does not necessarily have to be generated.

  The third method is a method called Mecha4D method. The Mecha4D method uses a mechanical 4D probe that mechanically swings a one-dimensional array (a transducer group) that scans a two-dimensional scanning plane in a direction substantially perpendicular to the scanning plane, and generates three-dimensional two-dimensional raw data. It is a method of collecting as dimension Raw data. In the Mecha4D method, the positional relationship of the two-dimensional raw data of each frame is known (equal intervals) due to mechanical swinging, and therefore, three-dimensional raw data is generated based on this positional relationship. In this case, since the frames are arranged at equal intervals, the voxel data does not necessarily have to be generated.

  The fourth method is a method called a two-dimensional array method. The two-dimensional array method is a method of collecting three-dimensional raw data by performing three-dimensional ultrasonic scanning using a two-dimensional array type ultrasonic probe having a plurality of transducers arranged in a grid. The sample positions of the three-dimensional raw data collected by the two-dimensional array method are equally spaced. In this case, since the sample positions are equally spaced, voxel data does not necessarily have to be generated.

  In the first embodiment, a case where three-dimensional raw data is collected by the Sensor3D method will be described. However, the embodiment is not limited to this, and the case where the data is collected by an arbitrary collection method other than the Sensor3D method. It is also applicable to.

  Incidentally, in general, the zoom function (enlargement function and reduction function) interpolates and displays the display image data stored in the frame buffer 170 in accordance with the display size of the display 103. For this reason, the display resolution of the display image displayed on the display 103 is defined by the resolution of the frame buffer 170. That is, even if the display image is enlarged, a resolution higher than the resolution of the frame buffer 170 cannot be obtained. Further, since the resolution of the frame buffer 170 is usually inferior to the resolution of the image data (ultrasonic image data) that is the basis of the display image data, it is possible to obtain the resolution of the original image data even if the display image is enlarged. I can't do it as well.

  The case of enlarging using image data stored in the frame buffer 170 will be described with reference to FIG. FIG. 2 is a diagram for explaining a case where enlargement is performed using image data stored in the frame buffer 170. FIG. 2 illustrates a series of processing until the three-dimensional raw data is displayed on the display 103 and the resolution of the image data at each stage in association with each other. The meaning of the resolution of the image data in each stage exemplified by the numerical value is, for example, when image data of 1024 * 512 pixels is converted to 820 * 410 pixels of three-dimensional raw data, and image data of the same region is converted to 3 The dimension RAW data is stored in 1024 * 512 pixels, and the voxel data is stored in 820 * 410 pixels. Therefore, the resolution of the three-dimensional RAW data is better. Note that FIG. 2 illustrates an example in which the linear probe is moved in the elevation direction (perpendicular to the transducer array) and three-dimensional raw data is collected by the Sensor3D method.

  As shown in FIG. 2, in S10, for example, three-dimensional raw data is collected by the Sensor3D method. For example, the signal processing circuit 120 generates data in which two-dimensional B-mode data of a plurality of frames are arranged in the elevation direction as three-dimensional raw data. The generated three-dimensional raw data is stored in a storage area (three-dimensional raw data memory) in the image memory 160. In the following description, a case where B-mode data is used as the three-dimensional raw data will be described. May be. Further, the number of samples of the image data exemplified below is merely an example, and can be changed to an arbitrary number of samples.

  In the three-dimensional raw data, the X-axis direction corresponds to the depth direction (range direction), the Y-axis direction corresponds to the scanning direction (azimuth direction), and the Z-axis direction corresponds to the moving direction (elevation direction) of the ultrasonic probe 101. The number of samples in the X-axis direction, Y-axis direction, and Z-axis direction of the three-dimensional raw data is, for example, 1024 * 512 * 400. That is, the three-dimensional raw data illustrated in FIG. 2 is an image in which 400 samples of B-mode data in which the number of samples in each scanning line is 1024 samples and the number of scanning lines is 512 are arranged along the elevation direction. Corresponds to data.

  In the Sensor 3D method, the ultrasonic probe 101 is moved manually. For this reason, the B-mode data of a plurality of frames are not necessarily arranged in one direction and at equal intervals due to the influence of camera shake or the like. Therefore, position information at the time of collecting B-mode data for each frame is acquired by a position sensor (such as a magnetic sensor or a gyro sensor) and stored in the image memory 160 in association with the B-mode data for each frame.

  Subsequently, in S11, voxel data is generated from the three-dimensional raw data. For example, the image processing circuit 130 reads out three-dimensional raw data and position information from the image memory 160. Then, the image processing circuit 130 performs interpolation processing using position information on the three-dimensional raw data whose sample positions are not necessarily equally spaced, and generates voxel data in which the sample positions are evenly spaced. Specifically, the image memory 160 has a data space (voxel data memory) for voxel data in which the number of samples is defined in advance. Then, the image processing circuit 130 generates data corresponding to the voxel data memory by interpolation processing of the three-dimensional raw data, and incorporates the generated data in the voxel data memory.

  In the voxel data memory, the X′-axis direction corresponds to the X-axis direction, the Y′-axis direction corresponds to the Y-axis direction, and the Z′-axis direction corresponds to the Z-axis direction. The number of samples in the X′-axis direction, the Y′-axis direction, and the Z′-axis direction of the voxel data memory is, for example, 1024 * 512 * 512. In the voxel data stored in the voxel data memory, data in the X′-axis direction, the Y′-axis direction, and the Z′-axis direction are arranged at equal intervals by interpolation processing.

  Subsequently, in S <b> 12 </ b> A, MPR image data is generated from the voxel data and stored in the frame buffer 170. For example, the image processing circuit 130 performs MPR processing on voxel data to generate MPR image data.

  As a specific example, a case will be described in which four-screen display for displaying the A-plane, B-plane, and C-plane MPR images and the VR image is performed. In this case, the image processing circuit 130 generates MPR image data for the A plane, the B plane, and the C plane, respectively. Then, the image processing circuit 130 stores the generated three MPR image data in three different frame buffers 170, respectively.

  The MPR image data has an X ″ axis direction and a Y ″ axis direction. For example, the MPR image data on the A plane is image data corresponding to the X′-Y ′ plane. Further, the MPR image data on the B surface is image data corresponding to the X′-Z ′ surface. Further, the MPR image data on the C plane is image data corresponding to the -Y'-Z 'plane. The size of the frame buffer 170 (frame buffer data) is, for example, 512 * 512 pixels.

  In step S <b> 12 </ b> B, VR image data is generated from the voxel data and stored in the frame buffer 170. For example, the image processing circuit 130 performs VR processing on voxel data to generate VR image data. For example, when four-screen display is performed, the image processing circuit 130 stores VR image data in a frame buffer 170 different from the MPR image data frame buffer 170. That is, when four-screen display is performed, four frame buffers 170 corresponding to the four screens are provided. Note that the number of pixels (size) of the frame buffer 170 is, for example, 512 * 512 pixels.

  In step S <b> 13, a display image is generated from the MPR image data and the VR image data and displayed on the display 103. In general, the number of pixels in the frame buffer is different from the number of pixels in the display 103. For this reason, for example, the display control function 141 performs interpolation processing such as linear interpolation, and displays the number of pixels of the image data stored in the frame buffer 170 according to the number of pixels of the display 103. As a specific example, when a four-screen display is performed on the display 103 of 700 * 800 pixels, the number of pixels on the X ″ ″-Y ″ ″ plane of each display image is 350 × 400 pixels.

  Here, the resolution of the ultrasonic image data is determined by the sampling interval (mm) of the data and the expansion of the sound field (mm). That is, the range direction is the sampling pitch in the depth direction and the pulse length of the ultrasonic wave, the azimuth direction is the interval between the scanning lines and the width in the azimuth direction of the ultrasonic beam, and the elevation direction is (frame pitch) = (probe of the probe) It is determined by the coarser one of (moving speed) / (frame rate) and the width of the ultrasonic beam in the slice direction. Here, as a reasonable case, let us consider a case where the data sampling interval and the sound field expansion are equal in the following initial state. That is, changing the sampling interval changes the resolution.

  First, as an initial state (a state displayed without using the zoom function), the resolution when the entire image of the collected area is displayed will be described. In addition, below, the resolution of the MPR image of A surface is demonstrated as a typical example among the four display images displayed by 4 screen display. Note that the resolution of other display images (B-side MPR image, C-side MPR image, and VR image) can be calculated in the same manner as the resolution of the A-side MPR image, and thus description thereof is omitted.

  When the entire image of the A plane is displayed from the three-dimensional raw data, voxel data of the X′-Y ′ plane of 1024 * 512 pixels is generated from the three-dimensional raw data of XY plane of 1024 * 512 pixels. In this case, the number of pixels of the three-dimensional raw data and the voxel data is the same. However, the three-dimensional raw data is the B-mode data of each frame due to camera shake when moving the ultrasonic probe 101, the undulation of the subject surface, and the like. Collected with the positional relationship shifted. As described above, when the entire three-dimensional raw data including the positional deviation is converted into voxel data, the resolution of the voxel data is reduced because the three-dimensional raw data is reduced and converted into voxel data. For example, when the three-dimensional raw data is reduced to 80%, the XY plane 1024 * 512 pixels of the three-dimensional raw data is converted into the X′-Y ′ plane 820 * 410 pixels of the voxel data.

  The same applies to the B-side MPR image. In other words, for example, when the probe is moved in a state where the frame interval in the Z-axis direction of the three-dimensional raw data is smaller than the sample pitch in the Z′-axis direction of the voxel data, the three-dimensional raw data is converted into voxel data. In such a state, frames are thinned out, and the resolution of the voxel data is lowered.

  Next, frame buffer data for the X ″ -Y ″ plane 512 * 512 pixels is generated from the voxel data of the 1024 * 512 pixels on the X′-Y ′ plane. Here, since the number of pixels is reduced by a factor of two from the 1024 pixels of the X ′ axis to the 512 pixels of the X ″ axis for the same image, the resolution is lowered when the frame buffer data is generated. In the example of FIG. 2, the X′-Y ′ plane 820 * 410 pixels of the voxel data are converted into the X ″ -Y ″ plane 410 * 205 pixels of the frame buffer data.

  Then, when the frame buffer data is displayed, the resolution of the final display image is determined by converting it into 350 * 400 display pixels by interpolation processing. Also in the display, the number of pixels decreases from the X ″ axis 512 pixels to the X ″ ″ axis 350 pixels, so the resolution decreases. In the example of FIG. 2, the X ″ -Y ″ plane 410 * 205 pixels of the frame buffer data is converted into the X ″ ″-Y ″ ″ plane 280 * 140 pixels of the display image.

  Here, in S14A, when a display image is enlarged by the enlargement function, generally, priority is given to performance (processing time), and the interpolation processing pitch (mm) is made finer by using the frame buffer data in the initial state. Expanding.

  For example, when the length of one side is enlarged 4 times (when the area is enlarged 16 times), the size of the frame buffer data X ″ -Y ″ plane 410 × 205 pixels is enlarged by 1/4. The region 102 * 51 pixel is converted to the X ′ ″-Y ′ ″ plane 280 * 140 pixels of the display image to be enlarged four times, and the enlarged image is displayed on the display 103. In this case, not only the frame buffer data 102 * 51 pixels are displayed on the display 103, but a wider range of frame buffer data that can be displayed on the display 103 350 * 400 pixels is displayed. In order to simplify the description, it will be described as “the enlarged region of frame buffer data 102 * 51 pixels is displayed as a display image 280 * 140 pixels”. Although the object drawn in the image is enlarged and displayed, the resolution of the enlarged display image (enlarged image) is determined by the resolution of the frame buffer data having a resolution lower than that of the three-dimensional raw data. That is, when the frame buffer data is used for enlargement, the resolution is determined by the resolution of the enlargement area X ″ -Y ″ plane 102 * 51 pixels in the frame buffer data, so the resolution is higher than the resolution of the three-dimensional raw data. It will decline.

  Therefore, the ultrasonic diagnostic apparatus 1 according to the first embodiment includes the following configuration in order to improve the resolution of the enlarged image.

  That is, the ultrasonic diagnostic apparatus 1 according to the first embodiment includes an image processing circuit 130, a display control function 141, and a reception function 142. The image processing circuit 130 generates display image data from the ultrasonic image data. The display control function 141 displays the display image data on the display unit. The reception function 142 receives an operation on display image data displayed on the display unit from an operator. When the reception function 142 receives an enlargement operation for enlarging the display image data, the image processing circuit 130 enlarges the ultrasound image data in accordance with the enlargement operation, and creates a new one from the enlarged ultrasound image data. Regenerate display image data.

  For example, the ultrasonic diagnostic apparatus 1 enlarges the display image using three-dimensional raw data or voxel data having a higher resolution than the frame buffer data. Thereby, the ultrasonic diagnostic apparatus 1 can improve the resolution of the enlarged image.

  The enlargement function by the ultrasonic diagnostic apparatus 1 according to the first embodiment will be described with reference to FIGS. 3 and 4. 3 and 4 are diagrams for explaining an enlargement function by the ultrasonic diagnostic apparatus 1 according to the first embodiment. 3 and 4, the processing contents of S10 to S13 are the same as the processing contents of S10 to S13 shown in FIG.

  As shown in FIG. 3, in S14B, three-dimensional raw data is selected for enlargement. For example, the reception function 142 receives an enlargement operation for enlarging the display image on the display image displayed on the display 103 from the operator. Then, the reception function 142 notifies the image processing circuit 130 of information regarding the received enlargement operation. For example, the reception function 142 notifies the image processing circuit 130 of the center coordinates of the area to be enlarged and the enlargement ratio.

  When the information regarding the enlargement operation is notified from the reception function 142, the image processing circuit 130 selects the three-dimensional raw data for enlargement based on the notified information. For example, the image processing circuit 130 extracts an area to be enlarged from the three-dimensional raw data based on the center coordinates and the enlargement ratio of the area to be enlarged (region of interest). Then, the image processing circuit 130 regenerates the voxel data and the frame buffer data that are enlarged according to the enlargement ratio in order using the three-dimensional raw data of the extracted region.

  For example, as in S14A of FIG. 2, when the length of one side is expanded 4 times (when the area is expanded 16 times), the XY plane 1024 * 512 pixels of the three-dimensional raw data is changed to XY. A face of 256 * 128 pixels is selected and this image data is enlarged. That is, the three-dimensional raw data of 256 * 128 pixels on the XY plane is enlarged by being converted into voxel data of 820 * 410 pixels on the X′-Y ′ plane taking account of positional deviation. Then, the voxel data of 820 * 410 pixels in the X′-Y ′ plane is converted into frame buffer data of the X ″ -Y ″ plane 410 * 205. Then, the frame buffer data of the X ″ ″-Y ″ plane 410 * 205 pixels is converted into a display image of the X ″ ″-Y ″ ″ plane 280 * 140 pixels.

  That is, when the frame buffer data is enlarged four times (example in FIG. 2), the image data on the X ″ -Y ″ plane 102 * 51 pixels is displayed on the X ′ ″-Y ′ ″ plane 280 * 140 pixels. Therefore, the resolution is defined by the resolution of the frame buffer whose resolution is lower than that of the three-dimensional raw data, and the resolution is lowered. On the other hand, when the three-dimensional raw data is enlarged four times (example in FIG. 3), the three-dimensional raw data of 256 * 128 pixels on the XY plane is converted into the X ″ -Y ″ plane 410 * by the frame buffer 170. 205, and is displayed as a display image of the X ′ ″-Y ′ ″ plane 280 * 140. For this reason, when the four-dimensional expansion of the three-dimensional raw data is performed, the resolution as a whole does not decrease.

  That is, in the enlargement using the frame buffer data, the resolution is regulated (specified) by the frame buffer data X ″ -Y ″ plane 102 * 51 pixels whose resolution is lower than that of the three-dimensional raw data, and the three-dimensional raw data is used. In the enlargement, the resolution is regulated by 256 * 128 pixels of the three-dimensional raw data XY plane having a higher resolution than the frame buffer data. Therefore, by enlarging the display image using the three-dimensional raw data, the resolution of the enlarged image can be improved as compared with the case of enlarging using the frame buffer data, and the diagnostic ability can be improved.

  Further, as shown in FIG. 4, the voxel data is expanded in S14C. Note that the details of the enlargement processing using the voxel data are the same as the details of the enlargement processing using the three-dimensional raw data shown in FIG. 3 except that the image data to be enlarged is voxel data.

  For example, as in S14A of FIG. 2, when the length of one side is expanded 4 times (when the area is expanded 16 times), the X′-Y ′ surface 820 * 410 pixels of the voxel data is changed to X ′. -Y 'plane 205 * 102 pixels are selected. The voxel data of the X′-Y ′ plane 205 * 102 pixels is enlarged by being converted into the frame buffer data of the X ″ -Y ″ plane 410 * 205. Then, the frame buffer data of the X ″ ″-Y ″ plane 410 * 205 pixels is converted into a display image of the X ″ ″-Y ″ ″ plane 280 * 140 pixels.

  That is, when the frame buffer data is enlarged four times (example in FIG. 2), the image data on the X ″ -Y ″ plane 102 * 51 pixels is displayed on the X ′ ″-Y ′ ″ plane 280 * 140 pixels. On the other hand, when the voxel data is enlarged four times (example in FIG. 4), the voxel data of the XY plane 205 * 102 pixels becomes the X ″ -Y ″ plane 410 * 205 in the frame buffer 170. , X ′ ″-Y ′ ″ plane 280 * 140.

  That is, in the enlargement using the frame buffer data, the resolution is regulated (defined) by the X ″ -Y ″ plane 102 * 51 pixels, and in the enlargement using the voxel data, the X′-Y ′ plane 205 * 102. Resolution is governed by pixels. Therefore, by enlarging the display image using voxel data, the resolution of the enlarged image can be improved as compared with the case of enlarging using the frame buffer data, and the diagnostic ability can be improved. Also, in the expansion using voxel data, although the resolution is lower than the expansion using 3D raw data, conversion processing from 3D raw data to voxel data does not occur, which is advantageous in terms of performance. is there.

  Note that the contents of FIGS. 2 to 4 are merely examples, and the embodiment is not limited thereto. For example, the number of data (number of pixels) described with reference to FIGS. 2 to 4 is merely an example, and may be appropriately changed according to the configuration of the ultrasonic diagnostic apparatus 1.

  Further, in FIGS. 2 to 4, the case where the ultrasonic probe 101 is a linear probe has been described for the sake of simplification. However, the present invention is not limited thereto, and an ultrasonic probe having an arbitrary shape such as a convex probe or a sector probe is used. 101 is applicable.

  A processing procedure of the ultrasonic diagnostic apparatus 1 according to the first embodiment will be described with reference to FIG. FIG. 5 is a flowchart showing a processing procedure of the ultrasonic diagnostic apparatus 1 according to the first embodiment. The processing procedure shown in FIG. 5 is started, for example, when an instruction to start four-screen display is received from the operator.

  In step S101, the processing circuit 140 determines whether to start display. For example, when receiving an instruction from the operator to start four-screen display, the processing circuit 140 determines that display is to be started (Yes at Step S101), and starts processing after Step S102. If the display is not started (No at Step S101), the processing after Step S102 is not started, and each processing function is in a standby state.

  If step S101 is positive, in step S102, the image processing circuit 130 generates voxel data from the three-dimensional raw data. For example, the image processing circuit 130 reads out three-dimensional raw data and position information from the image memory 160. Then, the image processing circuit 130 performs interpolation processing using position information on the three-dimensional raw data whose sample positions are not necessarily equally spaced, and generates voxel data in which the sample positions are evenly spaced.

  In step S103, the image processing circuit 130 generates display image data from the voxel data. For example, the image processing circuit 130 performs MPR processing on voxel data to generate MPR image data. The image processing circuit 130 performs VR processing on the voxel data to generate VR image data.

  In step S <b> 104, the image processing circuit 130 displays the display image data on the display 103. For example, the display control function 141 generates a display image by performing interpolation processing such as linear interpolation and matching the number of pixels of the display image data stored in the frame buffer 170 with the number of pixels of the display 103. The display control function 141 displays the generated display image on the display 103.

  In step S105, the reception function 142 determines whether an enlargement operation (or reduction operation) has been received. For example, when the reception function 142 receives an enlargement operation (or reduction operation) for enlarging the display image on the display image displayed on the display 103 from the operator (Yes in step S105), information regarding the accepted enlargement operation Is sent to the image processing circuit 130, and the process proceeds to step S106. On the other hand, when the reception function 142 does not receive an enlargement operation (or reduction operation) from the operator (No at Step S105), the reception function 142 proceeds to the process at Step S109.

  In step S106, the image processing circuit 130 enlarges or reduces the three-dimensional raw data or voxel data according to the enlargement operation (or reduction operation). For example, when the information regarding the enlargement operation is notified from the reception function 142, the image processing circuit 130 expands the three-dimensional raw data or the voxel data based on the notified information.

  In step S107, the image processing circuit 130 regenerates new display image data after enlargement (or after reduction) from the three-dimensional raw data or voxel data. For example, the image processing circuit 130 regenerates the voxel data after enlargement and the frame buffer data in order from the three-dimensional raw data. Alternatively, for example, the image processing circuit 130 regenerates the enlarged frame buffer data from the voxel data.

  In step S <b> 108, the display control function 141 displays new display image data on the display 103. For example, the display control function 141 displays the enlarged frame buffer data generated from the three-dimensional raw data or the voxel data on the display 103.

  In step S109, the processing circuit 140 determines whether or not to end the display. For example, when receiving an instruction from the operator to end the four-screen display, the processing circuit 140 determines that the display is to be ended (Yes at Step S109), and ends the processing procedure of FIG. If the display is not terminated (No at Step S109), the process proceeds to Step S105.

  As described above, the ultrasound diagnostic apparatus 1 according to the first embodiment enlarges a display image using ultrasound image data having a higher resolution than the image data stored in the frame buffer 170. Thereby, the ultrasonic diagnostic apparatus 1 can improve the resolution of the enlarged image and improve the diagnostic ability.

  For example, in the ultrasonic diagnostic apparatus 1, when the reception function 142 accepts an enlargement operation, the image processing circuit 130 performs an enlargement operation using the three-dimensional raw data and reproduces new enlarged display image data. To do. Thereby, the ultrasound diagnostic apparatus 1 can improve the resolution as compared with a case where an enlarged image is generated using the frame buffer data.

  For example, in the ultrasound diagnostic apparatus 1, when the reception function 142 accepts an enlargement operation, the image processing circuit 130 performs an enlargement operation using voxel data and reproduces new enlarged display image data. To do. As a result, the ultrasonic diagnostic apparatus 1 reduces the resolution as compared with the enlargement using the three-dimensional raw data, but the high-resolution enlarged image as compared with the case where the enlarged image is generated using the frame buffer data. , Can be provided with fast processing time (response time).

  In the first embodiment, the case where enlargement is performed using three-dimensional raw data or voxel data as ultrasonic image data has been described. Which of three-dimensional raw data and voxel data is used for enlargement? Can be appropriately set. For example, it may be set in advance which of the three-dimensional raw data and the voxel data is used for the enlargement, or may be set according to the imaging part to be displayed. Moreover, the form which confirms to an operator every time which 3D Raw data and voxel data are used may be sufficient.

(Modification of the first embodiment)
In the example described in the above embodiment, since the image generation process is performed again from the three-dimensional raw data or voxel data, it takes a longer processing time than the case of enlarging using the frame buffer data. . Therefore, in the modification of the first embodiment, processing for reducing the influence of the processing time and improving performance will be described.

  Processing of the ultrasonic diagnostic apparatus 1 according to the modification of the first embodiment will be described with reference to FIGS. 6 and 7. 6 and 7 are diagrams for explaining the processing of the ultrasonic diagnostic apparatus 1 according to the modification of the first embodiment. 6 and 7, a case where four screen display is performed will be described. 6 and 7, a case where enlargement or reduction is continuously performed will be described.

  As shown in FIG. 6, in the initial state, the display image 10 including the MPR images of the A surface, the B surface, and the C surface and the VR image is displayed (S20). In this display image 10, markers 11, 12, and 13 are displayed as the enlargement centers. The marker 11 indicates the expansion center in the A-plane MPR image, the marker 12 indicates the expansion center in the B-plane MPR image, and the marker 13 indicates the expansion center in the C-plane MPR image.

  Then, for example, the operator rotates the trackball 102A to move the markers 11, 12, and 13 to the center position of the region of interest (S21).

  Then, the operator performs an enlargement operation of the display image by rotating the rotary switch (enlargement button) 102B. In this case, the A-plane, B-plane, and C-plane MPR images included in the display image 20 are enlarged around the positions of the markers 11, 12, and 13.

  Here, while enlarging by the rotation operation of the rotary switch 102B, enlargement is performed using the frame buffer data stored in the frame buffer 170. For example, the display control function 141 enlarges the frame buffer data at an enlargement ratio designated by the rotation of the rotary switch 102B. Then, the display control function 141 generates the display image 20 from the enlarged frame buffer data and displays it on the display 103 (S22). The operator adjusts to a desired enlargement ratio (size of the region of interest) by this operation.

  When the operator determines that the desired enlargement ratio has been achieved, the operator presses the rotary switch 102B. When the reception function 142 receives the pressing of the rotary switch 102B, the reception function 142 notifies the image processing circuit 130 of information related to the enlargement operation by the operator. When the information regarding the enlargement operation is notified from the reception function 142, the image processing circuit 130 expands the three-dimensional raw data or the voxel data based on the notified information. That is, the image processing circuit 130 regenerates new enlarged display image data from the three-dimensional raw data or voxel data. Then, the display control function 141 generates the display image 30 from the regenerated new display image data and displays it on the display 103 (S23).

  As described above, when the reception function 142 receives the enlargement operation, the display control function 141 enlarges the display image data in accordance with the enlargement operation and causes the display 103 to display the display image data. Then, after the enlargement operation is completed, the image processing circuit 130 enlarges the ultrasound image data in accordance with the enlargement operation, and regenerates new enlarged display image data. For example, the reception function 142 further receives a confirmation operation for confirming the enlargement operation from the operator. Then, when the reception function 142 receives the confirmation operation, the image processing circuit 130 enlarges the ultrasound image data in accordance with the enlargement operation, and regenerates new enlarged display image data. As a result, when the operator is adjusting the enlargement ratio, enlargement can be performed using frame buffer data with a quick response time, and when the enlargement ratio is determined, the resolution is improved. An image can be displayed.

  Next, a case where a reduction operation is performed on the display image 30 enlarged in S23 of FIG. 6 will be described with reference to FIG. As shown in FIG. 7, the operator moves each marker 11, 12, 13 to the center position of the region of interest by rotating the trackball 102A, for example (S31).

  Then, the operator performs a reduction operation on the display image 30 by rotating the rotary switch (enlargement button) 102B in the reverse direction (S32). In this case, the MPR images of the A plane, the B plane, and the C plane included in the display image 30 are reduced around the positions of the markers 11, 12, and 13.

  Here, while the reduction is performed by the rotation operation of the rotary switch 102B, the reduction is performed using the frame buffer data stored in the frame buffer 170. For example, the display control function 141 reduces the frame buffer data at an enlargement rate designated by the rotation of the rotary switch 102B. Then, the display control function 141 generates the display image 40 from the reduced frame buffer data and displays it on the display 103 (S32). In this case, the frame buffer 170 stores image data included in a region corresponding to the region of interest of the display image 30 and does not store image data outside the region of interest. For this reason, image data is not displayed in the entire area of the display image 40, and image data of a part of the area stored in the frame buffer 170 is displayed. The operator adjusts to a desired enlargement ratio by this operation.

  When the operator determines that the desired enlargement ratio has been achieved, the operator presses the rotary switch 102B. When the reception function 142 receives the pressing of the rotary switch 102B, the reception function 142 notifies the image processing circuit 130 of information related to the reduction operation by the operator. When the information regarding the reduction operation is notified from the reception function 142, the image processing circuit 130 expands the three-dimensional raw data or the voxel data based on the notified information. That is, the image processing circuit 130 regenerates new enlarged display image data from the three-dimensional raw data or voxel data. Then, the display control function 141 generates a display image 50 from the regenerated new display image data and displays it on the display 103 (S33).

  As described above, the reception function 142 receives a reduction operation for reducing the display image displayed on the display 103 from the operator. Then, when the reception function 142 accepts a reduction operation, the display control function 141 reduces the display image data according to the reduction operation, and displays the reduced image data on the display 103. Then, after the reduction operation is completed, the image processing circuit 130 reduces the ultrasonic image data according to the reduction operation, and regenerates new reduced image data after the reduction. Then, the display control function 141 causes the display 103 to display the regenerated new reduced image data. As a result, when the operator is adjusting the enlargement ratio, it is possible to perform reduction using the frame buffer data with a quick response time, and when the enlargement ratio is determined, the display area is expanded. A reduced image can be displayed.

  6 and 7 are merely examples, and are not limited to the illustrated contents. For example, in FIGS. 6 and 7, the case where the pressing of the rotary switch 102 </ b> B is accepted as the confirmation operation for confirming the enlargement operation has been described, but the embodiment is not limited thereto. For example, the reception function 142 may determine that the enlargement operation has been completed and perform enlargement when the operation has not been performed for a certain period of time after receiving the enlargement operation by rotating the rotary switch 102B. That is, the image processing circuit 130 enlarges the ultrasound image data according to the enlargement operation when the enlargement operation is not performed for a certain period of time after the reception function 142 accepts the enlargement operation, and a new display for enlargement is displayed. Image data may be regenerated.

  In the above-described embodiment, the case where the center coordinates and the enlargement ratio of the area to be enlarged are designated as the enlargement operation has been described. However, the embodiment is not limited to this. For example, the region of interest can be enlarged by setting a region of interest on the MPR images of the A, B, and C surfaces and pressing a switch. That is, the reception function 142 receives a setting operation for setting a region of interest on display image data displayed on the display 103 as an enlargement operation from the operator. Then, when the reception function 142 receives the setting operation, the image processing circuit 130 expands the area of the ultrasound image data corresponding to the region of interest according to the size of the region of interest with respect to the display image data. New display image data is regenerated from the later ultrasonic image data.

  In the embodiment described above, it is also possible to accept an instruction for initialization. For example, when the display image enlarged or reduced to an arbitrary enlargement ratio according to the above-described embodiment is displayed on the display 103, the operator may want to view the image at an initial magnification. In this case, when the operator gives an instruction for initialization (such as pressing an initialization button), the reception function 142 notifies the image processing circuit 130 of this instruction. Then, the image processing circuit 130 regenerates the initial image data in accordance with the notified instruction. For example, the image processing circuit 130 regenerates the voxel data and the frame buffer data in order using the original three-dimensional raw data at a magnification at which the entire three-dimensional raw data is rendered.

(Second Embodiment)
In the first embodiment, the configuration in the case where the Sensor3D method is applicable as a three-dimensional raw data collection method is illustrated, but the configuration is not necessarily limited thereto. For example, when the Sensor3D method is not applied and any of the Smart3D method, the Mecha4D method, and the two-dimensional array method is applied, the sensor 3D method can be realized with a simple configuration.

  With reference to FIG. 8, an enlargement function by the ultrasonic diagnostic apparatus 1 according to the second embodiment will be described. FIG. 8 is a diagram for explaining an enlargement function by the ultrasonic diagnostic apparatus 1 according to the second embodiment.

  As shown in FIG. 8, for example, three-dimensional raw data is collected by the Smart 3D method (S40). For example, the signal processing circuit 120 generates image data in which a plurality of frames of two-dimensional B-mode data are arranged in the elevation direction as three-dimensional raw data. In this case, the image processing circuit 130 processes the three-dimensional raw data on the assumption that the sample positions in the B-mode data of a plurality of frames are arranged at equal intervals.

  That is, the three-dimensional raw data used in the second embodiment is handled as sample positions arranged at equal intervals. For this reason, the image processing circuit 130 can generate MPR image data and VR image data from the three-dimensional raw data without generating the voxel data described in the first embodiment. Then, the image processing circuit 130 stores the generated MPR image data and VR image data in the frame buffer 170 (S41A, S41B), and displays a display image (S42).

  Therefore, when an enlargement operation is performed in the second embodiment, the image processing circuit 130 selects an enlargement area of the three-dimensional raw data (S43). Then, the image processing circuit 130 regenerates the enlarged MPR image data and VR image data from the three-dimensional raw data, and causes the display 103 to display the regenerated MPR image data and VR image data.

  According to this, the ultrasonic diagnostic apparatus 1 according to the second embodiment can be realized with a simple configuration as compared with the configuration according to the first embodiment, and the performance is also improved. In the example of FIG. 8, the case where the Smart 3D method is applied has been described, but the enlargement function can be realized with the same configuration even when the Mecha 4D method or the two-dimensional array method is applied.

(Other embodiments)
In addition to the above-described embodiment, various other forms may be implemented.

  Further, the term “processor (circuit)” used in the above description is, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an application specific integrated circuit (ASIC), or a programmable. Means circuits such as logic devices (for example, Simple Programmable Logic Device (SPLD), Complex Programmable Logic Device (CPLD), and Field Programmable Gate Array (FPGA)) To do. The processor implements a function by reading and executing a program stored in the storage circuit 150. Instead of storing the program in the storage circuit 150, the program may be directly incorporated into the processor circuit. In this case, the processor realizes the function by reading and executing the program incorporated in the circuit. Note that each processor of the present embodiment is not limited to being configured as a single circuit for each processor, but may be configured as a single processor by combining a plurality of independent circuits to realize the function. Good. Furthermore, a plurality of components in each figure may be integrated into one processor to realize the function.

  In the above-described embodiment, the image processing circuit 130 is an example of an image processing unit. The display control function 141 is an example of a display control unit. The reception function 142 is an example of a reception unit. Each configuration of the image processing unit, the display control unit, and the reception unit may be realized as software, may be realized as hardware, or may be realized as a mixture of software and hardware.

  Further, each component of each illustrated apparatus is functionally conceptual, and does not necessarily need to be physically configured as illustrated. In other words, the specific form of distribution / integration of each device is not limited to the one shown in the figure, and all or a part of the distribution / integration is functionally or physically distributed in arbitrary units according to various loads or usage conditions. Can be integrated and configured. Further, all or a part of each processing function performed in each device may be realized by a CPU and a program analyzed and executed by the CPU, or may be realized as hardware by wired logic.

  In addition, among the processes described in the above-described embodiments, all or a part of the processes described as being automatically performed can be manually performed, or the processes described as being manually performed All or a part of the above can be automatically performed by a known method. In addition, the processing procedure, control procedure, specific name, and information including various data and parameters shown in the above-described document and drawings can be arbitrarily changed unless otherwise specified.

  The image processing method described in the above-described embodiment can be realized by executing a prepared image processing program on a computer such as a personal computer or a workstation. This image processing method can be distributed via a network such as the Internet. The image processing method can also be executed by being recorded on a computer-readable recording medium such as a hard disk, a flexible disk (FD), a CD-ROM, an MO, and a DVD, and being read from the recording medium by the computer. .

  According to at least one embodiment described above, the resolution of the enlarged image can be improved.

  Although several embodiments of the present invention have been described, these embodiments are presented by way of example and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the spirit of the invention. These embodiments and their modifications are included in the scope and gist of the invention, and are also included in the invention described in the claims and the equivalents thereof.

DESCRIPTION OF SYMBOLS 1 Ultrasonic diagnostic apparatus 130 Image processing circuit 140 Processing circuit 141 Display control function 142 Reception function

Claims (11)

An image generation unit that generates display image data from ultrasonic image data;
A display control unit for displaying the display image data on a display unit;
A reception unit that receives an operation on the display image data displayed on the display unit from an operator;
When the receiving unit receives an enlargement operation for enlarging the display image data, the image generation unit enlarges the ultrasonic image data according to the enlargement operation, and performs a new display for enlargement Regenerate image data,
Ultrasound diagnostic device. The ultrasonic image data is three-dimensional raw data including image data corresponding to a plurality of scanning planes,
The image generation unit enlarges the three-dimensional raw data according to the enlargement operation when the accepting unit accepts the enlargement operation, and regenerates new display image data after enlargement.
The ultrasonic diagnostic apparatus according to claim 1. The ultrasonic image data is voxel data in which three-dimensional raw data including image data corresponding to a plurality of scanning planes is incorporated in a predetermined data space,
The image generation unit enlarges the voxel data according to the enlargement operation when the accepting unit accepts the enlargement operation, and regenerates new display image data after enlargement.
The ultrasonic diagnostic apparatus according to claim 1. The display control unit, when the reception unit receives the enlargement operation, causes the display image data to be enlarged according to the enlargement operation and displayed on the display unit,
The image generation unit enlarges the ultrasonic image data according to the enlargement operation after the enlargement operation is completed, and regenerates the new display image data after enlargement.
The ultrasonic diagnostic apparatus as described in any one of Claims 1-3. The reception unit further receives a confirmation operation for confirming the enlargement operation from an operator,
The image generation unit enlarges the ultrasonic image data according to the enlargement operation when the accepting unit accepts the confirmation operation, and regenerates the new display image data after enlargement.
The ultrasonic diagnostic apparatus according to claim 4. The image generation unit enlarges the ultrasonic image data according to the enlargement operation when the enlargement operation is not performed for a certain period of time after the accepting unit accepts the enlargement operation, and Regenerate new image data for display,
The ultrasonic diagnostic apparatus according to claim 4. The reception unit receives a setting operation for setting a region of interest on the display image data displayed on the display unit from the operator as the enlargement operation,
The image generation unit enlarges the region of the ultrasound image data corresponding to the region of interest according to the size of the region of interest with respect to the display image data when the receiving unit receives the setting operation. Regenerating the new display image data after enlargement,
The ultrasonic diagnostic apparatus as described in any one of Claims 1-6. The receiving unit receives a reduction operation for reducing the display image data displayed on the display unit from an operator;
The display control unit reduces the display image data according to the reduction operation when the reception unit receives the reduction operation, and causes the display unit to display the reduced image data reduced.
The image generation unit, after the reduction operation is completed, reduces the ultrasound image data according to the reduction operation, regenerates new reduced image data after reduction,
The display control unit causes the display unit to display the regenerated new reduced image data.
The ultrasonic diagnostic apparatus as described in any one of Claims 1-7. The ultrasonic image data is three-dimensional raw data including raw data corresponding to a plurality of scanning planes and position information at the time of collecting each raw data corresponding to the plurality of scanning planes,
The image generation unit generates voxel data by interpolating each Raw data corresponding to the plurality of scanning planes into a predetermined data space based on the position information,
The ultrasonic diagnostic apparatus as described in any one of Claims 1-8. An image generation unit that generates display image data from ultrasonic image data;
A display control unit for displaying the display image data on a display unit;
A reception unit that receives an operation on the display image data displayed on the display unit from an operator;
When the receiving unit receives an enlargement operation for enlarging the display image data, the image generation unit enlarges the ultrasonic image data according to the enlargement operation, and performs a new display for enlargement Regenerate image data,
Image processing device. Generate image data for display from ultrasound image data,
Displaying the display image data on a display unit;
Receiving an operation on the display image data displayed on the display unit from an operator;
When an enlargement operation for enlarging the display image data is accepted, the ultrasonic image data is enlarged according to the enlargement operation, and new enlarged display image data is regenerated.
An image processing program that causes a computer to execute each process.