JP6971673B2 - Ultrasound diagnostic equipment, image processing equipment and image processing program - Google Patents

Description

Embodiments of the present invention relate to an ultrasonic diagnostic apparatus, an image processing apparatus, and an image processing program.

Conventionally, an ultrasonic diagnostic apparatus has been put into practical use in which an ultrasonic scan is performed on a three-dimensional region in a subject to generate and display an MPR (Multi Planar Reconstruction) image or a VR (Volume Rendering) image. To display an MPR image or VR image, the image data generated by the reconstruction process or the rendering process is temporarily saved in the frame buffer, and this is displayed according to the display size of the display. Further, if necessary, a zoom function, that is, an enlargement / reduction function of the displayed image 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.

Japanese Unexamined Patent Publication No. 2013-414 Japanese Patent Publication No. 2015-5000083 Japanese Unexamined Patent Publication No. 2014-239841

An object 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 ultrasonic image data. The display control unit causes the display unit to display the display image data. The reception unit receives an operation on the display image data displayed on the display unit from the operator. When the reception unit accepts an enlargement operation for enlarging the display image data, the image generation unit enlarges the ultrasonic image data according to the enlargement operation, and a new display image after enlargement. Regenerate the data.

FIG. 1 is a block diagram showing a configuration example of the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 2 is a diagram for explaining a case of enlarging using the image data stored in the frame buffer. FIG. 3 is a diagram for explaining an expansion 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 the processing of the ultrasonic diagnostic apparatus according to the modified example of the first embodiment. FIG. 7 is a diagram for explaining the processing of the ultrasonic diagnostic apparatus according to the modified example of the first embodiment. FIG. 8 is a diagram for explaining the magnifying function of the ultrasonic diagnostic apparatus according to the second embodiment.

Hereinafter, the ultrasonic diagnostic apparatus, the image processing apparatus, and the image processing program according to the embodiment will be described with reference to the drawings. In the following, as an example, the case where the embodiment described below is applied to the ultrasonic diagnostic apparatus will be described, but the embodiment is not limited to this. For example, the embodiment is also applicable to an image processing apparatus capable of processing ultrasonic image data collected by an ultrasonic diagnostic apparatus.

(First Embodiment)
FIG. 1 is a block diagram showing a configuration example of the 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 device main body 100.

The ultrasonic probe 101 has a plurality of vibrators (for example, a piezoelectric vibrator), and these plurality of vibrators generate ultrasonic waves based on a drive signal supplied from a transmission / reception circuit 110 of the apparatus main body 100, which will be described later. do. Further, the plurality of vibrators included in the ultrasonic probe 101 receive the reflected wave from the subject P and convert it into an electric signal. Further, the ultrasonic probe 101 has a matching layer provided on the vibrator, a backing material for preventing the 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 reflected one after another on the discontinuity surface of the acoustic impedance in the body tissue of the subject P, and the reflected wave signal (echo signal). It is 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 in the discontinuity where the ultrasonic waves are reflected. The reflected wave signal when the transmitted ultrasonic pulse is reflected on the moving blood flow or the surface of the heart wall or the like depends on the velocity component of the moving body with respect to the ultrasonic transmission / reception direction due to the Doppler effect. And undergo 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 row, or a plurality of piezoelectric vibrators arranged in a row. Applicable regardless of whether the is a mechanical 4D (Dimension) ultrasonic probe that is mechanically swung, or a two-dimensional ultrasonic probe in which a plurality of piezoelectric vibrators are arranged in two dimensions in a grid pattern. It is possible.

The input device 102 has a mouse, a keyboard, a button, a panel switch, a touch command screen, a foot switch, a trackball, a joystick, and the like, and receives various setting requests from the operator of the ultrasonic diagnostic device 1 and causes the device body 100 to receive various setting requests. The various setting requests received are transferred.

The display 103 displays a GUI (Graphical User Interface) for the operator of the ultrasonic 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. Or display.

The device main body 100 is a device that generates display image data based on the reflected wave signal received by the ultrasonic probe 101. As shown in FIG. 1, the apparatus main body 100 includes, for example, 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 each other so as 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 transmitted ultrasonic waves at a predetermined rate frequency. Further, in the transmission delay unit, the pulse generator generates a delay time for each piezoelectric vibrator required for focusing the ultrasonic waves generated from the ultrasonic probe 101 in a beam shape and determining the transmission directivity. Give for each rate pulse. Further, the pulsar 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 of instantaneously changing the transmission frequency, transmission drive voltage, and the like in order to execute a predetermined scan sequence based on the instruction of the processing circuit 140 described later. In particular, the change of the transmission drive voltage is realized by a linear amplifier type transmitter circuit that can switch the value instantaneously or a mechanism that electrically switches a plurality of power supply units.

Further, the transmission / reception circuit 110 includes a preamplifier, an A / D (Analog / Digital) converter, a reception delay unit, an adder, and the like, and performs various processes on the reflected wave signal received by the ultrasonic probe 11 to reflect the reflected wave signal. 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 provides the delay time required to determine the reception directivity. The adder generates reflected wave data by performing addition processing of the reflected wave signal processed by the reception delay unit. The addition process of the adder emphasizes the reflection component from the direction corresponding to the reception directivity of the reflected wave signal, and the reception directivity and the transmission directivity form a comprehensive beam for ultrasonic transmission and reception.

When scanning the two-dimensional region of the subject P, the transmission / reception circuit 110 causes the ultrasonic probe 101 to transmit an ultrasonic beam in a two-dimensional direction. 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 causes the ultrasonic probe 101 to transmit an ultrasonic beam in the 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.

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, for example, and data (B mode data) in which the signal strength for each sample point is expressed by brightness. ) Is generated. Specifically, the signal processing circuit 120 generates data (B mode data) representing a tomographic image of a tissue and an echo component of a contrast medium. The B mode data generated by the signal processing circuit 120 is output to the image processing circuit 130.

Further, the signal processing circuit 120 generates, for example, motion information based on the Doppler effect of the moving body as data (Doppler data) extracted from each sample point in the scanning region from the reflected wave data received from the transmission / reception circuit 110. .. Specifically, the signal processing circuit 120 extracts blood flow components (color Doppler components) and tissue components (tissue Doppler components) from reflected wave data based on the Doppler effect, and moves objects such as average velocity, dispersion, and power. Generate data (Dopla data) that extracts information from multiple points. Here, the moving body is, for example, a blood flow, a tissue such as a heart wall, or a contrast medium. 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 distributed 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 scan line signal string of ultrasonic scanning, and are referred to as "Raw data (raw 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 scan line signal string. In this embodiment, the Raw data collected by ultrasonic scanning for 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 Doppler image data for display representing mobile information from the Doppler data generated by the signal processing circuit 120. The Doppler image data is speed image data, distributed image data, power image data, or image data in which these are combined.

Here, the image processing circuit 130 generally converts (scan-converts) a scanning line signal string (Raw data) of ultrasonic scanning into a scanning line signal string of a video format typified by a television or the like and displays it. Generate image data for. Specifically, the image processing circuit 130 generates display image data by performing coordinate conversion according to the scanning form of ultrasonic waves by the ultrasonic probe 101.

That is, the B mode data and the Doppler data are ultrasonic data (Raw data) before the scan conversion process, and the data generated by the image processing circuit 130 is display image data after the scan conversion process. Here, Raw data is also referred to as ultrasonic image data for the sake of facilitating the following explanation. Further, when the signal processing circuit 120 generates 3D Raw data (3D B mode data and 3D Doppler data), the image processing circuit 130 performs interpolation processing on the 3D Raw data to obtain boxel data. It may also generate 3D image data to be called. Here, in order to facilitate the following explanation, it is referred to as ultrasonic image data including three-dimensional Raw data and voxel data. Then, the image processing circuit 130 performs coordinate conversion and various rendering processes on the three-dimensional ultrasonic image data according to the ultrasonic scanning form by the ultrasonic probe 101, and performs two-dimensional image data, that is, display. Generate image data for.

Here, the "voxel data" represents, for example, data in which three-dimensional Raw data is incorporated into a predetermined three-dimensional data space. That is, for example, the image processing circuit 130 generates 3D B mode image data as voxel data by incorporating 3D B mode data into a predetermined 3D data space by coordinate conversion (interlacing). do. Further, the image processing circuit 130 generates 3D Doppler image data as voxel data by converting the coordinates of the 3D Doppler data into a predetermined 3D data space and incorporating the data. In other words, the data in the state before being allocated to the data space as voxel data (the state in which the interpolation process is not performed) is referred to as "Raw data". Further, in the following embodiments, "Raw data" and "voxel data" are collectively referred to as "ultrasonic image data".

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

Further, as shown in FIG. 1, the processing circuit 140 executes the display control function 141 and the reception function 142. 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 that can be executed by a computer. It is recorded in (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 a storage device and executing the program. In other words, the processing circuit 140 in the state where each program is read out has each function shown in the processing circuit 140 of FIG. The processing functions executed by the display control function 141 and the reception function 142 will be described later.

The internal storage circuit 150 stores control programs for ultrasonic transmission / reception, image processing, and display processing, diagnostic information (for example, patient ID, doctor's findings, etc.), and various data such as diagnostic protocols and various body marks. do. The internal storage circuit 150 is also used for storing image data stored in the image memory 160, if necessary. Further, 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 for storing 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. Further, 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, that is, Raw data stored in the image memory 160 can be called by the 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) for display on the display 103. For example, the display image data stored in the frame buffer 170 is converted into a display image having 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 typical as a method for collecting three-dimensional Raw data.

The first method is a method called the Sensor3D method. In the Sensor3D method, while acquiring the position information of the ultrasonic probe 101 that scans the two-dimensional scanning plane, the ultrasonic probe 101 is moved in a substantially vertical direction to the scanning plane, so that the two-dimensional structure of a plurality of frames having different positions can be obtained. This is a method of collecting Raw data as three-dimensional Raw data. In the Sensor3D method, each frame is not always evenly spaced, so voxel data in which sample positions are evenly spaced is generated based on the position information when the two-dimensional Raw data of each frame is collected. ..

The second method is a method called the Smart3D method. In the Smart3D method, the ultrasonic probe 101 is moved substantially vertically to the scanning plane to collect two-dimensional Raw data of a plurality of frames, and each frame (sample position) in the two-dimensional Raw data of a plurality of frames is equal. It is a method of collecting three-dimensional Raw data assuming that they are arranged at intervals. In this case, since it is assumed that the frames are arranged at equal intervals, voxel data does not necessarily have to be generated.

The third method is a method called the Mecha4D method. The Mecha4D method uses a mechanical 4D probe that mechanically oscillates a one-dimensional array (a group of oscillators) that scans a two-dimensional scanning plane in a direction substantially perpendicular to the scanning plane, and obtains three frames of two-dimensional Raw data. This is a method of collecting as dimensional Raw data. In the Mecha4D method, the positional relationship of the two-dimensional Raw data of each frame becomes known (equally spaced) due to the mechanical swing, and therefore the three-dimensional Raw data is generated based on this positional relationship. In this case, since the frames are arranged at equal intervals, 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 three-dimensionally performing ultrasonic scanning using a two-dimensional array type ultrasonic probe having a plurality of transducers arranged in a grid pattern. The sample positions of the 3D Raw data collected by the 2D array method are evenly spaced. In this case, voxel data does not necessarily have to be generated because the sample positions are evenly spaced.

In the first embodiment, the case where the three-dimensional Raw data is collected by the Sensor3D method will be described, but the embodiment is not limited to this, and the case where the data is collected by any collection method other than the Sensor3D method. It is also applicable to.

By the way, in general, the zoom function (enlargement function and reduction function) interpolates and displays the display image data stored in the frame buffer 170 according to the display size of the display 103. Therefore, 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, it is not possible to obtain a resolution higher than the resolution of the frame buffer 170. Further, since the resolution of the frame buffer 170 is usually inferior to the resolution of the image data (ultrasonic image data) which is the source of the display image data, it is not possible to obtain the resolution of the original image data even if the display image is enlarged. You can't do the same.

A case of enlarging using the image data stored in the frame buffer 170 will be described with reference to FIG. FIG. 2 is a diagram for explaining a case of enlarging using the image data stored in the frame buffer 170. FIG. 2 illustrates a series of processes until the three-dimensional Raw data is displayed on the display 103 in relation to the resolution of the image data at each stage. The meaning of the resolution of the image data at each stage exemplified by the numerical value is, for example, when the image data of 1024 * 512 pixels in the three-dimensional Raw data becomes 820 * 410 pixels in the boxel data, the image data in the same area is 3 In the sense that the dimensional Raw data is stored in 1024 * 512 pixels and the boxel data is stored in 820 * 410 pixels, therefore, the three-dimensional Raw data has better resolution. In FIG. 2, a case where the linear probe is moved in the elevation direction (direction perpendicular to the oscillator array) and three-dimensional Raw data is collected by the Sensor3D method will be described as an example.

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. Then, the generated three-dimensional Raw data is stored in the storage area (three-dimensional Raw data memory) in the image memory 160. In the following, the case where the B mode data is used as the three-dimensional Raw data will be described, but the case is not limited to this, and any form of Raw data (Dopla data or the like) that can be collected by the ultrasonic diagnostic apparatus 1 is used. May be. Further, the number of sample images of the image data illustrated below is only an example, and can be changed to any 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 (azimus 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, the Y-axis direction, and the Z-axis direction of the three-dimensional Raw data is, for example, 1024 * 512 * 400. That is, the three-dimensional Raw data exemplified in FIG. 2 is an image in which 400 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 the data.

In the Sensor3D method, the ultrasonic probe 101 is manually moved. Therefore, due to the influence of camera shake and the like, the B mode data of a plurality of frames are not always arranged in one direction and at equal intervals. Therefore, the position information at the time of collecting the B mode data of each frame is acquired by the position sensor (magnetic sensor, gyro sensor, etc.) and stored in the image memory 160 in association with the B mode data of each frame.

Subsequently, in S11, voxel data is generated from the three-dimensional Raw data. For example, the image processing circuit 130 reads the three-dimensional Raw data and the position information from the image memory 160. Then, the image processing circuit 130 performs interpolation processing using the position information on the three-dimensional Raw data whose sample positions are not necessarily at equal intervals, and generates voxel data in which the sample positions are arranged at equal intervals. Specifically, the image memory 160 has a data space (voxel data memory) for voxel data in which the number of samples is predetermined. Then, the image processing circuit 130 generates data corresponding to the voxel data memory by the interpolation processing of the three-dimensional Raw data, and incorporates the generated data into 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, the 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 S12A, 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 where a four-screen display for displaying the MPR image of the A side, the B side, and the C side and the VR image is performed will be described. In this case, the image processing circuit 130 generates MPR image data on the A side, the B side, and the C side, 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 ″ axial direction and a Y ″ axial 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'plane. Further, the MPR image data of the C plane is the image data corresponding to the −Y ′ −Z ′ plane. The size of the frame buffer 170 (frame buffer data) is, for example, 512 * 512 pixels.

Further, in S12B, 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 frame buffer 170 of MPR image data. That is, when four screens are displayed, four frame buffers 170 corresponding to each of the four screens are provided. The number of pixels (size) of the frame buffer 170 is, for example, 512 * 512 pixels.

Then, in S13, a display image is generated from the MPR image data and the VR image data and displayed on the display 103. Generally, the number of pixels in the frame buffer is different from the number of pixels in the display 103. Therefore, for example, the display control function 141 performs interpolation processing such as linear interpolation to display 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 a 700 * 800 pixel display 103, the number of pixels on the X ″-Y ″ surface of each display image is 350 * 400 pixels.

Here, the resolution of the ultrasonic image data is determined by the data sampling interval (mm) and the sound field spread (mm). That is, the range direction is the sampling pitch and the ultrasonic pulse length in the depth direction, the azimuth direction is the interval between the scanning lines and the width in the directional direction of the ultrasonic beam, and the elevation direction is (frame pitch) = (probe). It is determined by the coarser of the movement speed) / (frame rate) and the width of the ultrasonic beam in the slice direction. Here, as a case where it makes sense, consider the case where the data sampling interval and the sound field spread are equivalent in the following initial state. That is, the resolution changes when the sampling interval is changed.

First, the resolution when the entire image of the collected area is displayed as the initial state (the state displayed without using the zoom function) will be described. In the following, among the four display images displayed on the four-screen display, the resolution of the MPR image on the A side will be described as a representative example. The resolutions of the other display images (MPR image on the B side, MPR image on the C side, and VR image) can be calculated in the same manner as the resolution of the MPR image on the A side, and thus the description thereof will be omitted.

When the entire image of the A plane is displayed from the 3D Raw data, voxel data of the X'-Y'plane 1024 * 512 pixels is generated from the 3D Raw data which is the XY plane 1024 * 512 pixels. In this case, the number of pixels of the 3D Raw data and the voxel data is the same, but the 3D Raw data is the B mode data of each frame due to camera shake when moving the ultrasonic probe 101, undulations on the surface of the subject, and the like. It is collected in a state where the positional relationship is out of alignment. In this way, when the entire three-dimensional Raw data including the positional deviation is converted into voxel data, the three-dimensional Raw data is reduced and converted into voxel data, so that the resolution of the voxel data is lowered. For example, when the 3D Raw data is reduced to 80%, the XY plane 1024 * 512 pixels of the 3D Raw data are converted into the X'-Y'plane 820 * 410 pixels of the voxel data.

The same applies to the MPR image on the B side. That is, for example, when the probe is moved in a state where the frame interval in the Z-axis direction of the 3D Raw data is smaller than the sample pitch in the Z'axis direction of the voxel data, the 3D Raw data is converted into voxel data. Will be in a state where frames are thinned out, and the resolution of voxel data will decrease.

Next, the frame buffer data of the X ″ -Y ″ surface 512 * 512 pixels is generated from the voxel data of the X ″ -Y ′ surface 1024 * 512 pixels. Here, since the number of pixels is reduced by half from 1024 pixels on the X'axis to 512 pixels on the X'axis for the same image, the resolution is lowered at the time of generating the frame buffer data. In the example of FIG. 2, the X ″ -Y ′ surface 820 * 410 pixels of the voxel data are converted into the X ″ -Y ″ surface 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 the frame buffer data into 350 * 400 display pixels by interpolation processing. Also in the display, the number of pixels is reduced from 512 pixels on the X ″ axis to 350 pixels on the X ″ axis, so that the resolution is lowered. In the example of FIG. 2, the X ″ -Y ″ surface 410 * 205 pixels of the frame buffer data is converted into the X ″-Y ″ surface 280 * 140 pixels of the display image.

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

For example, when the length of one side is expanded 4 times (when the area is expanded 16 times), the size of the X''-Y'' surface 410 * 205 pixels of the frame buffer data is expanded to 1/4. The area 102 * 51 pixels is converted to 280 * 140 pixels on the X'''-Y''' surface of the display image, so that the area 102 * 51 pixels is magnified four times, and the magnified 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 also a wider range of frame buffer data that can be displayed on the 350 * 400 pixels of the display 103 is displayed. Since it is only necessary to know the attachment, in order to simplify the explanation, it is described below that "the enlarged area 102 * 51 pixels of the frame buffer data is displayed as the display image 280 * 140 pixels" and the like. 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, which is lower in resolution than the three-dimensional Raw data. That is, when enlarging using the frame buffer data, the resolution is defined by the resolution of the enlarged area X''-Y'' surface 102 * 51 pixels in the frame buffer data, so that the resolution is higher than the resolution of the three-dimensional Raw data. It will drop.

Therefore, the ultrasonic diagnostic apparatus 1 according to the first embodiment has 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 has 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 ultrasonic image data. The display control function 141 causes the display unit to display the display image data. The reception function 142 receives an operation on the display image data displayed on the display unit from the operator. When the reception function 142 accepts the enlargement operation for enlarging the display image data, the image processing circuit 130 enlarges the ultrasonic image data according to the enlargement operation, and new from the enlarged ultrasonic image data. Regenerate the image data for display.

For example, the ultrasonic diagnostic apparatus 1 enlarges a displayed image by using three-dimensional Raw data or voxel data having a higher resolution than the frame buffer data. As a result, the ultrasonic diagnostic apparatus 1 can improve the resolution of the enlarged image.

The magnifying function of 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 the magnifying function of the ultrasonic diagnostic apparatus 1 according to the first embodiment. In FIGS. 3 and 4, the processing contents of S10 to S13 are the same as the processing contents of S10 to S13 shown in FIG. 2, and thus the description thereof will be omitted.

As shown in FIG. 3, in S14B, 3D Raw data is selected for enlargement. For example, the reception function 142 receives from the operator an enlargement operation for enlarging the display image on the display image displayed on the display 103. Then, the reception function 142 notifies the image processing circuit 130 of the 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.

Then, 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 a region to be expanded from the three-dimensional Raw data based on the center coordinates and the enlargement ratio of the region to be expanded (region of interest). Then, the image processing circuit 130 uses the three-dimensional Raw data of the extracted region to sequentially regenerate the voxel data and the frame buffer data enlarged according to the enlargement ratio.

For example, similar to S14A in FIG. 2, when the length of one side is expanded four times (when the area is expanded 16 times), the three-dimensional Raw data is XY from 1024 * 512 pixels on the XY plane. A surface 256 * 128 pixels is selected and this image data is magnified. 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 XY'plane with the positional deviation added. Then, the voxel data of the X ″ -Y ′ surface 820 * 410 pixels is converted into the frame buffer data of the X ″ −Y ″ surface 410 * 205. Then, the frame buffer data of the X ″ -Y ″ surface 410 * 205 pixels is converted into a display image of the X ″ −Y ″ surface 280 * 140 pixels.

That is, when the frame buffer data is magnified four times (example in FIG. 2), the image data of the X''-Y'' surface 102 * 51 pixels is displayed on the X''-Y'' surface 280 * 140 pixels. Therefore, the resolution is defined by the resolution of the frame buffer having a lower resolution than the three-dimensional Raw data, and the resolution is lowered. On the other hand, in the four-fold magnification of the three-dimensional Raw data (example in FIG. 3), the three-dimensional Raw data of 256 * 128 pixels on the XY plane is the X''-Y'' plane 410 * in the frame buffer 170. It becomes 205 and is displayed as a display image of the X'''-Y''' surface 280 * 140. Therefore, the resolution does not decrease as a whole when the three-dimensional Raw data is magnified four times.

That is, in the enlargement using the frame buffer data, the resolution is ruled (specified) in the frame buffer data X''-Y'' surface 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 the three-dimensional Raw data XY plane 256 * 128 pixels, which has 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 enlarged in S14C. The enlargement processing content using the voxel data is the same as the enlargement processing content using the three-dimensional Raw data shown in FIG. 3, except that the image data to be enlarged is the voxel data.

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

That is, when the frame buffer data is magnified four times (example in FIG. 2), the image data of the X''-Y'' surface 102 * 51 pixels is displayed on the X''-Y'' surface 280 * 140 pixels. On the other hand, in the case of quadrupling the voxel data (example in FIG. 4), the voxel data of the XY plane 205 * 102 pixels becomes the XY'' plane 410 * 205 in the frame buffer 170. , X'''-Y''' Displayed as a display image of surface 280 * 140.

That is, in the enlargement using the frame buffer data, the resolution is ruled (specified) in the X''-Y'' plane 102 * 51 pixels, and in the enlargement using the voxel data, the X'-Y' plane 205 * 102. Pixels regulate the resolution. Therefore, by enlarging the display image using the 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. In addition, although the resolution is lower in the enlargement using the voxel data than in the enlargement using the 3D Raw data, the conversion process from the 3D Raw data to the voxel data does not occur, which is advantageous in terms of performance. be.

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

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

The 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 the four-screen display is received from the operator.

In step S101, the processing circuit 140 determines whether or not to start the display. For example, when the processing circuit 140 receives an instruction from the operator to start the four-screen display, it determines that the display is to be started (step S101 affirmative), and starts the processing after step S102. If the display is not started (denial in step S101), the processing after step S102 is not started, and each processing function is in a standby state.

When step S101 is affirmed, 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 the three-dimensional Raw data and the position information from the image memory 160. Then, the image processing circuit 130 performs interpolation processing using the position information on the three-dimensional Raw data whose sample positions are not necessarily at equal intervals, and generates voxel data in which the sample positions are arranged at equal intervals.

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

In step S104, the image processing circuit 130 causes the display 103 to display the display image data. For example, the display control function 141 generates a display image by performing interpolation processing such as linear interpolation to match the number of pixels of the display image data stored in the frame buffer 170 with the number of pixels of the display 103. Then, the display control function 141 causes the generated display image to be displayed on the display 103.

In step S105, the reception function 142 determines whether or not the enlargement operation (or reduction operation) has been accepted. For example, when the reception function 142 receives an enlargement operation (or a reduction operation) for enlarging the displayed image from the operator on the display image displayed on the display 103 (step S105 affirmative), the information regarding the accepted enlargement operation is received. Is notified to the image processing circuit 130, and the process proceeds to step S106. On the other hand, when the reception function 142 does not accept the enlargement operation (or reduction operation) from the operator (negation of step S105), the reception function 142 shifts to the process of 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 image processing circuit 130 is notified of the information regarding the enlargement operation 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 reduction) from the three-dimensional Raw data or voxel data. For example, the image processing circuit 130 regenerates the enlarged voxel data 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 S108, the display control function 141 causes the display 103 to display new display image data. For example, the display control function 141 causes the display 103 to display the enlarged frame buffer data generated from the three-dimensional Raw data or the voxel data.

In step S109, the processing circuit 140 determines whether or not to end the display. For example, when the processing circuit 140 receives an instruction from the operator to end the four-screen display, the processing circuit 140 determines that the display is ended (step S109 affirmative), and ends the processing procedure of FIG. If the display is not finished (denial in step S109), the process proceeds to step S105.

As described above, the ultrasonic diagnostic apparatus 1 according to the first embodiment enlarges the displayed image by using the ultrasonic image data having a higher resolution than the image data stored in the frame buffer 170. As a result, 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 the enlargement operation, the image processing circuit 130 performs the enlargement operation using the three-dimensional Raw data, and reproduces the new display image data after the enlargement. To be done. As a result, the ultrasonic diagnostic apparatus 1 can improve the resolution as compared with the case where the magnified image is generated by using the frame buffer data.

Further, for example, in the ultrasonic diagnostic apparatus 1, when the reception function 142 accepts the enlargement operation, the image processing circuit 130 performs the enlargement operation using the voxel data and reproduces the new display image data after the enlargement. To be done. As a result, the ultrasonic diagnostic apparatus 1 produces a high-resolution enlarged image as compared with the case of generating an enlarged image using the frame buffer data, although the resolution is lowered as compared with the enlargement using the three-dimensional Raw data. , Can be provided with fast processing time (response time).

In the first embodiment, the case where the enlargement is performed using the three-dimensional Raw data or the voxel data as the ultrasonic image data has been described, but which of the three-dimensional Raw data and the voxel data is used for the enlargement? Can be set as appropriate. For example, which of the three-dimensional Raw data and the voxel data is used for enlargement may be set in advance, or may be set according to the imaging region to be displayed. Further, it may be in the form of asking the operator each time whether to use the three-dimensional Raw data or the voxel data.

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

6 and 7 will be used to describe the processing of the ultrasonic diagnostic apparatus 1 according to the modified example of the first embodiment. 6 and 7 are diagrams for explaining the processing of the ultrasonic diagnostic apparatus 1 according to the modified example of the first embodiment. In addition, in FIG. 6 and FIG. 7, a case where four-screen display is performed will be described. Further, in FIGS. 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 side, the B side, and the C side and the VR image is displayed (S20). Markers 11, 12, and 13 are displayed as enlargement centers on the display image 10. The marker 11 indicates the expansion center in the MPR image on the A surface, the marker 12 indicates the expansion center in the MPR image on the B surface, and the marker 13 indicates the expansion center in the MPR image on the C surface.

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

Then, the operator rotates the rotary switch (enlargement button) 102B to enlarge the display image. In this case, the MPR images of the A side, the B side, and the C side included in the display image 20 are enlarged around the positions of the markers 11, 12, and 13.

Here, while the expansion is performed by the rotation operation of the rotary switch 102B, the expansion is performed using the frame buffer data stored in the frame buffer 170. For example, the display control function 141 expands the frame buffer data at the enlargement ratio specified by the rotation of the rotary switch 102B. Then, the display control function 141 generates a 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.

Then, when the operator determines that the desired enlargement ratio has been reached, 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 regarding the enlargement operation by the operator. When the reception function 142 notifies the information regarding the enlargement operation, 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 30 from the regenerated new display image data and displays it on the display 103 (S23).

As described above, when the reception function 142 accepts the enlargement operation, the display control function 141 enlarges the display image data according to the enlargement operation and displays it on the display 103. Then, after the enlargement operation is completed, the image processing circuit 130 enlarges the ultrasonic image data according to the enlargement operation, and regenerates new display image data after the enlargement. For example, the reception function 142 further accepts a confirmation operation for confirming the enlargement operation from the operator. Then, when the reception function 142 accepts the confirmation operation, the image processing circuit 130 enlarges the ultrasonic image data according to the enlargement operation and regenerates new display image data after enlargement. As a result, when the operator adjusts the enlargement ratio, it is possible to perform enlargement using the frame buffer data having a fast response time, and when the enlargement ratio is determined, the enlargement with improved resolution is possible. It becomes possible to display an image.

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

Then, the operator performs a reduction operation of 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 side, the B side, and the C side 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 the enlargement ratio specified by the rotation of the rotary switch 102B. Then, the display control function 141 generates a 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 the image data included in the area corresponding to the area of interest of the display image 30, and does not store the image data outside the area of interest. Therefore, the image data is not displayed in the entire area of the display image 40, and the image data in a part of the area stored in the frame buffer 170 is displayed. The operator adjusts to a desired enlargement ratio by this operation.

Then, when the operator determines that the desired enlargement ratio has been reached, 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 regarding the reduction operation by the operator. When the reception function 142 notifies the information regarding the reduction operation, 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).

In this way, the reception function 142 receives from the operator a reduction operation for reducing the display image displayed on the display 103. Then, when the reception function 142 accepts the reduction operation, the display control function 141 reduces the display image data according to the reduction operation, and displays the reduced 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 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 adjusts the enlargement ratio, the frame buffer data having a fast response time can be used for reduction, and when the enlargement ratio is determined, the display area is expanded. A reduced image can be displayed.

The contents of FIGS. 6 and 7 are merely examples, and are not limited to the contents shown in the drawings. For example, in FIGS. 6 and 7, a case where the rotary switch 102B is accepted as a confirmation operation for confirming the enlargement operation has been described, but the embodiment is not limited to this. For example, the reception function 142 may determine that the enlargement operation has been completed and perform the enlargement when the operation is not 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 expands the ultrasonic 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 the image processing circuit 130 expands the ultrasonic image data for a new display after the enlargement. Image data may be regenerated.

Further, in the above-described embodiment, the case where the center coordinates and the enlargement ratio of the area to be expanded are specified as the enlargement operation has been described, but the embodiment is not limited to this. For example, the region of interest can be set on the MPR images of the A, B, and C planes, and the region of interest can be expanded by pressing the switch. That is, the reception function 142 receives from the operator a setting operation for setting an area of interest on the display image data displayed on the display 103 as an enlargement operation. Then, when the reception function 142 accepts the setting operation, the image processing circuit 130 expands and expands the area of the ultrasonic image data corresponding to the area of interest according to the size of the area of interest for the display image data. New display image data is regenerated from the subsequent ultrasonic image data.

Further, in the above-described embodiment, it is also possible to receive an instruction for initialization (initialization). For example, the operator may want to view an image at an initial magnification when a display image enlarged or reduced to an arbitrary enlargement ratio according to the above-described embodiment is displayed on the display 103. In this case, when the operator gives an instruction for initialization (such as pressing the initialization button), the reception function 142 notifies the image processing circuit 130 of this instruction. Then, the image processing circuit 130 regenerates the image data in the initial state according to the notified instruction. For example, the image processing circuit 130 uses the original 3D Raw data to sequentially regenerate the voxel data and the frame buffer data at a magnification at which the entire 3D Raw data is drawn.

(Second embodiment)
In the first embodiment, a configuration in which the Sensor3D method can be applied as a method for collecting three-dimensional Raw data has been illustrated, but the configuration is not necessarily limited to this. 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, it can be realized with a simple configuration.

The magnifying function of the ultrasonic diagnostic apparatus 1 according to the second embodiment will be described with reference to FIG. 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 Smart3D method (S40). For example, the signal processing circuit 120 generates image data in which two-dimensional B-mode data of a plurality of frames 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 treated as if the sample positions are arranged at equal intervals. Therefore, 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 the displayed image (S42).

Therefore, when the enlargement operation is performed in the second embodiment, the image processing circuit 130 selects the enlarged 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 displays the regenerated MPR image data and VR image data on the display 103.

According to this, the ultrasonic diagnostic apparatus 1 according to the second embodiment can be realized with a simpler configuration and the performance is improved as compared with the configuration according to the first embodiment. In the example of FIG. 8, the case where the Smart3D method is applied has been described, but when the Mecha4D method or the two-dimensional array method is applied, the enlargement function can be realized by the same configuration.

(Other embodiments)
In addition to the above-described embodiments, various different embodiments may be performed.

Further, the wording "processor (circuit)" used in the above description is, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an integrated circuit for a specific application (Application Specific Integrated Circuit: ASIC), or a programmable device. It means a circuit such as a logical device (for example, a simple programmable logic device (SPLD), a complex programmable logic device (CPLD), and a field programmable gate array (FPGA)). do. The processor realizes the function by reading and executing the program stored in the storage circuit 150. Instead of storing the program in the storage circuit 150, the program may be directly incorporated in the circuit of the processor. In this case, the processor realizes the function by reading and executing the program embedded in the circuit. It should be noted that each processor of the present embodiment is not limited to the case where each processor is configured as a single circuit, and a plurality of independent circuits may be combined to form one processor to realize its function. good. Further, a plurality of components in each figure may be integrated into one processor to realize the function.

Further, in the above-described embodiment, the image processing circuit 130 is an example of an image processing unit. Further, the display control function 141 is an example of the display control unit. The reception function 142 is an example of the 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 of the illustrated devices is a functional concept, and does not necessarily have to be physically configured as shown in the figure. That is, the specific form of distribution / integration of each device is not limited to the one shown in the figure, and all or part of them may be functionally or physically distributed / physically in arbitrary units according to various loads and usage conditions. Can be integrated and configured. Further, each processing function performed by 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.

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

Further, the image processing method described in the above-described embodiment can be realized by executing an image processing program prepared in advance 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. Further, this image processing method can also be executed by recording on a computer-readable recording medium such as a hard disk, flexible disk (FD), CD-ROM, MO, or DVD, and reading 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 some embodiments of the present invention have been described, these embodiments are presented as examples and are not intended to limit the scope of the invention. These embodiments can be implemented in various other embodiments, and various omissions, replacements, and changes can be made without departing from the gist of the invention. These embodiments and variations thereof are included in the scope of the invention described in the claims and the equivalent scope thereof, as are included in the scope and gist of the invention.

1 Ultrasonic diagnostic device 130 Image processing circuit 140 Processing circuit 141 Display control function 142 Reception function

Claims (10)

An image generator that generates an MPR (Multi Planar Reconstruction) image or a VR (Volume Rendering) image , which is image data for display, from ultrasonic image data.
A display control unit that displays the display image data on the display unit,
It is equipped with a reception unit that accepts operations on the display image data displayed on the display unit from the operator.
When the reception unit receives an enlargement operation for enlarging the display image data, the display control unit enlarges the display image data according to the enlargement operation and displays it on the display unit.
After the enlargement operation is completed , the image generation unit enlarges the ultrasonic image data according to the enlargement operation, and regenerates new display image data after enlargement.
Ultrasonic diagnostic equipment. The ultrasonic image data is three-dimensional Raw data including image data corresponding to a plurality of scanning planes.
When the reception unit accepts the enlargement operation, the image generation unit enlarges the three-dimensional Raw data according to 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.
When the reception unit accepts the enlargement operation, the image generation unit enlarges the voxel data according to the enlargement operation and regenerates new enlarged display image data.
The ultrasonic diagnostic apparatus according to claim 1. The reception unit further receives a confirmation operation for confirming the enlargement operation from the operator.
When the reception unit accepts the confirmation operation, the image generation unit enlarges the ultrasonic image data according to the enlargement operation and regenerates the new display image data after enlargement.
The ultrasonic diagnostic apparatus according to any one of claims 1 to 3. The image generation unit expands the ultrasonic image data according to the enlargement operation when the enlargement operation is not performed for a certain period of time after the reception unit receives the enlargement operation, and the enlarged image is described. Regenerate new display image data,
The ultrasonic diagnostic apparatus according to any one of claims 1 to 3. As the enlargement operation, the reception unit receives from the operator a setting operation for setting an area of interest on the display image data displayed on the display unit.
When the reception unit receives the setting operation, the image generation unit expands the area of the ultrasonic image data corresponding to the area of interest according to the size of the area of interest for the display image data. And regenerate the new display image data after enlargement.
The ultrasonic diagnostic apparatus according to any one of claims 1 to 5. The reception unit receives from the operator a reduction operation for reducing the display image data displayed on the display unit.
When the reception unit receives the reduction operation, the display control unit reduces the display image data according to the reduction operation, and displays the reduced reduced image data on the display unit.
After the reduction operation is completed, the image generation unit reduces the ultrasonic image data according to the reduction operation, and 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 according to any one of claims 1 to 6. 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 and incorporating them into a predetermined data space based on the position information.
The ultrasonic diagnostic apparatus according to any one of claims 1 to 7. An image generator that generates an MPR (Multi Planar Reconstruction) image or a VR (Volume Rendering) image , which is image data for display, from ultrasonic image data.
A display control unit that displays the display image data on the display unit,
It is equipped with a reception unit that accepts operations on the display image data displayed on the display unit from the operator.
When the reception unit receives an enlargement operation for enlarging the display image data, the display control unit enlarges the display image data according to the enlargement operation and displays it on the display unit.
After the enlargement operation is completed , the image generation unit enlarges the ultrasonic image data according to the enlargement operation, and regenerates new display image data after enlargement.
Image processing device. An MPR (Multi Planar Reconstruction) image or a VR (Volume Rendering) image , which is image data for display, is generated from the ultrasonic image data.
The display image data is displayed on the display unit, and the display is displayed.
An operation for the display image data displayed on the display unit is received from the operator, and the operation is received.
When an enlargement operation for enlarging the display image data is accepted, the display image data is enlarged according to the enlargement operation and displayed on the display unit.
After the enlargement operation is completed, 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.

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