JP2010279425A - Ultrasonic diagnostic apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an ultrasonic diagnostic apparatus capable of improving the efficiency in the ultrasonic diagnosis. <P>SOLUTION: A scan control part 13 repeatedly three-dimensionally scans an examination region via an ultrasonic probe 11 moved by a user. A subordinate volume data-set creating part 29 creates a plurality of subordinate volume data sets on a plurality of scan areas included in the examination region based on echo signals from the ultrasonic probe 11. A combination volume data set 31 combines the plurality of created subordinate volume data sets according to the positional relations between the plurality of scan areas to create a single combination volume data set. A body mark creating part 33 creates a body mark related to the examination region by processing images of the created combination volume data set. A display part 39 displays the created body mark. <P>COPYRIGHT: (C)2011,JPO&amp;INPIT

Description

  The present invention relates to an ultrasonic diagnostic apparatus that repeatedly and three-dimensionally scans an examination site of a subject via a moving ultrasonic probe.

  The ultrasonic diagnostic apparatus can obtain the state of the heart beat and the fetal movement in real time by a simple operation by simply touching the ultrasonic probe from the body surface. In addition, the scale of the system is small compared to other diagnostic equipment such as X-ray diagnostic equipment, X-ray computed tomography equipment, and magnetic resonance imaging equipment, making it easy to perform inspections while moving to the bedside, and simple diagnosis It can be said that it is a technique. Further, since ultrasonic waves are not affected by exposure unlike X-rays, the ultrasonic diagnostic apparatus can be used in obstetrics, home medical care, and the like.

  In recent years, volume scanning has become possible with a mechanical probe having a mechanically oscillating ultrasonic transducer or a two-dimensional array probe having a two-dimensionally arranged ultrasonic transducer. On the other hand, a technique called a panoramic view has been developed as a means for acquiring a volume data set relating to a wider scanning area. The panoramic view is a technique for scanning a test site from a plurality of directions while translating an ultrasonic probe and connecting a plurality of obtained volume data sets to obtain a single volume data set. A wide scanning area can be observed by the volume data set acquired in this way.

  However, the ultrasound diagnostic apparatus has a smaller scanning area for one scan than other diagnostic devices. Therefore, the user may not be able to determine the position of the ultrasonic image on the examination site simply by observing the ultrasonic image. In particular, the tendency becomes remarkable in a region with unclear direction such as a mammary gland. Therefore, when saving an ultrasound image or volume data set as a diagnostic result, it is common to manually paste and record a body mark indicating the scanning position on the ultrasound image or volume data set. is there. However, it is particularly troublesome to manually input body marks for the display (observation) cross-sectional position, the position of the scanned probe, and the like for the volume data set, and automation is expected.

  The body mark is a mark indicating the standard shape of the human body, and does not reflect the individual human body shape. Therefore, even if the position of the ultrasonic image or volume data relating to an individual is indicated on a body mark indicating a standard shape, the accuracy is lacking. In particular, the tendency becomes stronger in the examination site where the shape is easily changed, such as a breast. Therefore, it is difficult for the user to grasp the position of the ultrasound image and the volume data set on the examination site.

  An object of the present invention is to provide an ultrasonic diagnostic apparatus capable of improving the efficiency of ultrasonic diagnosis.

  An ultrasonic diagnostic apparatus according to a first aspect of the present invention is an ultrasonic diagnostic apparatus that repeatedly and three-dimensionally scans an examination site of a subject via a moving ultrasonic probe, and an echo from the ultrasonic probe. A sub-volume data set generation unit that generates a plurality of sub-volume data sets for a plurality of scanning regions included in the examination region based on the signal; and the generated plurality of sub-volume data sets for the plurality of scanning regions A combined volume data set generating unit that generates a single combined volume data set by combining according to the positional relationship between the body, and a body mark that generates a body mark related to the examination site by performing image processing on the generated combined volume data set A generating unit; and a display unit for displaying the generated body mark. And wherein the door.

  An object of the present invention is to provide an ultrasonic diagnostic apparatus that can improve the diagnostic efficiency of ultrasonic images.

1 is a diagram showing a configuration of an ultrasonic diagnostic apparatus according to an embodiment of the present invention. The figure which shows the relationship between the ultrasonic scan in 4D panoramic view which concerns on this embodiment, and the subvolume data set produced | generated by the ultrasonic scan. The figure for demonstrating a joint process by the joint volume data set production | generation part of FIG. The figure which shows the example of a display of the ultrasonic image displayed by the display control part of FIG. 1, and a three-dimensional body mark. The figure which shows the example of a display of the cross-section position mark and probe mark which are displayed on the three-dimensional body mark of FIG. The figure which shows an example of the three-dimensional body mark which concerns on the modification of this embodiment.

  Hereinafter, an ultrasonic diagnostic apparatus according to an embodiment of the present invention will be described with reference to the drawings.

  FIG. 1 is a diagram illustrating a configuration of an ultrasonic diagnostic apparatus according to the present embodiment. As shown in FIG. 1, the ultrasonic diagnostic apparatus includes an ultrasonic probe 11, a scanning control unit 13, a transmission unit 15, a reception unit 17, a B mode processing unit 19, a B mode image generation unit 21, a Doppler processing unit 23, and a Doppler image. Generation unit 25, storage unit 27, sub-volume data set generation unit 29, combined volume data set generation unit 31, body mark generation unit 33, three-dimensional image processing unit 35, display control unit 37, display unit 39, input unit 41, A network interface unit 43 and a system control unit 45 are provided.

  The ultrasonic probe 11 has a plurality of transducers arranged two-dimensionally. The ultrasonic probe 11 receives the drive signal from the transmission unit 15 and transmits ultrasonic waves toward the subject. The ultrasonic waves transmitted to the subject are successively reflected by the discontinuous surface of the acoustic impedance of the body tissue. The reflected ultrasonic wave is received by the ultrasonic probe 11 as an echo signal. The amplitude of this echo signal depends on the difference in acoustic impedance at the reflected discontinuous surface. In addition, when the transmitted ultrasound is reflected on the surface of a moving body such as a moving bloodstream or heart wall, the echo signal depends on the velocity component of the moving body in the ultrasound transmission direction due to the Doppler effect. Subject to frequency shift. Note that the ultrasonic probe 11 is not necessarily a two-dimensional array type as long as three-dimensional scanning is possible. For example, the ultrasonic probe 11 may be a mechanically swingable one-dimensional array type.

  The scanning control unit 13 controls the transmission unit 15 and the reception unit 17 to repeatedly perform three-dimensional scanning on the scanning region with ultrasonic waves. The scanning area is composed of a plurality of scanning surfaces, and the scanning surface is composed of a plurality of scanning lines. For example, the scanning control unit 13 performs two-dimensional scanning on one scanning plane by ultrasonically scanning a plurality of scanning lines in one scanning plane one by one sequentially from end to end. Thus, for example, the scanning control unit 13 performs three-dimensional scanning on one scanning region by two-dimensionally scanning a plurality of scanning surfaces in one scanning region one by one from the end to the end with ultrasonic waves. .

  In this embodiment, it is assumed that the size of the examination region is so large that it does not fit in a scanning area that can be scanned by one three-dimensional scanning. In order to ultrasonically scan such a wide examination site, the user moves the ultrasound probe 11 so that the entire examination site is scanned ultrasonically. In this way, the scanning control unit 13 repeatedly performs three-dimensional scanning of the examination site with ultrasonic waves via the ultrasonic probe 11 moved by the user. A technique for ultrasonically scanning a wide scanning area while moving the ultrasonic probe 11 and visualizing the wide scanning area with one image (or volume data) is called a 4D panoramic view. . Hereinafter, a scanning area that can be scanned in one three-dimensional scan is referred to as a sub-scanning area, an entire scanning target area of 4D panoramic view, that is, a set of sub-scanning areas is referred to as a full scanning area.

  The transmission unit 15 causes the ultrasonic probe 11 to repeatedly generate ultrasonic waves according to control by the scanning control unit 13. More specifically, the transmission unit 15 includes a rate pulse generation circuit, a transmission delay circuit, a drive pulse generation circuit, and the like (not shown). The rate pulse generation circuit repeatedly generates a rate pulse for each channel at a predetermined rate frequency frHz (cycle; 1 / fr second). The delay circuit focuses the ultrasonic wave into a beam for each channel and gives each rate pulse a delay time necessary to determine the transmission directivity. The drive pulse generation circuit applies a drive pulse to the ultrasonic probe 11 at a timing based on each delayed rate pulse. The ultrasonic probe 11 that has received the drive pulse generates ultrasonic waves.

  The transmission unit 15 has a function capable of instantaneously changing a transmission frequency, a transmission drive voltage, and the like in order to execute a predetermined scanning sequence according to the control by the scanning control unit 13. For example, the transmission drive voltage changing function is realized by a linear amplifier type transmission circuit capable of instantaneously switching the value or a mechanism capable of electrically switching a plurality of electric units.

  The receiving unit 17 repeatedly receives an echo signal from the ultrasonic probe 11 under the control of the scanning control unit 13 and generates an echo signal for each scanning line. More specifically, the reception unit 17 includes an amplifier circuit, an A / D converter, a reception delay circuit, an adder, and the like (not shown). The amplifier circuit receives the echo signal from the ultrasonic probe 11 and amplifies the received echo signal for each channel. The A / D converter converts the amplified echo signal from an analog signal to a digital signal for each channel. The reception delay circuit focuses the echo signal converted into the digital signal into a beam shape for each channel and gives a delay time necessary for determining the reception directivity. The adder adds the echo signals given delay times. By this addition processing, the reflection component from the direction corresponding to the reception directivity of the echo signal is emphasized, and an ultrasonic beam is formed by the reception directivity and the transmission directivity. One ultrasonic beam corresponds to one ultrasonic scan line. The echo signal for each scanning line is supplied to the B mode processing unit 19 and the Doppler processing unit 23.

  The B-mode processing unit 19 envelope-detects the echo signal from the receiving unit 17, and logarithmically compresses the echo signal that has been envelope-detected, thereby generating B-mode signal data that expresses the intensity of the echo signal in luminance. To do. The generated B-mode signal data is supplied to the B-mode image generation unit 21.

  The B-mode image generation unit 21 generates B-mode image data related to the scanning plane based on the B-mode signal from the B-mode processing unit 19. Specifically, the B-mode image generation unit 21 two-dimensionally arranges B-mode signal data on the memory according to the position information of the scanning line, and interpolates the B-mode signal between the scanning lines. By this arrangement processing and interpolation processing, B-mode image data composed of a plurality of pixels is generated. Each of the pixels constituting the B-mode image has a luminance value corresponding to the intensity of the derived B-mode signal. The generated B-mode image data is supplied to the storage unit 27.

  The Doppler processing unit 23 performs frequency analysis on the echo signal from the reception unit 17, extracts blood flow, tissue, and contrast agent echo components due to the Doppler effect, and expresses information such as average velocity, dispersion, and power in color. Generate data for The generated Doppler signal data is supplied to the Doppler image generation unit 25.

  The Doppler image generation unit 25 generates Doppler image data related to the scanning plane based on the Doppler signal from the Doppler processing unit 23. Specifically, the Doppler image generation unit 25 two-dimensionally arranges Doppler signal data on the memory according to the position information of the scanning line, and interpolates the Doppler signal between the scanning lines. By this arrangement processing and interpolation processing, Doppler image data composed of a plurality of pixels is generated. Each pixel constituting the Doppler image has a color value corresponding to the intensity of the derived Doppler signal. The generated Doppler image data is supplied to the storage unit 27.

  Note that data before being supplied to the B-mode image generation unit 21 and the Doppler image generation unit 25 may be referred to as raw data.

  The storage unit 27 stores B-mode image data from the B-mode image generation unit 21 and Doppler image data from the Doppler image generation unit 25. The storage unit 27 also stores the B mode subvolume data and Doppler subvolume data generated by the subvolume data set generation unit 29, and the B mode combined volume data set and Doppler combined volume generated by the combined volume data set generation unit 31. Data of various two-dimensional images generated by the three-dimensional image processing unit 35 is stored. Further, the storage unit 27 stores body mark data unique to the present embodiment generated by the body mark generation unit 33. The storage unit 27 stores various programs executed by the system control unit 45.

  The sub-volume data set generation unit 29 generates volume data related to the sub-scanning region (hereinafter referred to as a B-mode sub-volume data set) based on the B-mode signal. Specifically, the sub-volume data set generation unit 29 three-dimensionally arranges the B-mode image on the memory according to the position information of the scanning plane, and interpolates the B-mode image data between the scanning planes. By this arrangement processing and interpolation processing, a B-mode subvolume data set composed of a plurality of voxels is generated. Each voxel has a voxel value corresponding to the strength of the derived B-mode signal. Similarly, the sub-volume data set generation unit 29 generates volume data relating to the sub-scanning area (hereinafter referred to as “Doppler sub-volume data set”) based on the Doppler signal. Note that the B-mode subvolume data set and the Doppler subvolume data set are collectively referred to as a subvolume data set when they are not particularly distinguished. By repeating the three-dimensional scanning, the sub-volume data set generation unit 29 generates a plurality of sub-volume data sets relating to a plurality of sub-scanning areas.

  The combined volume data set generation unit 31 combines a plurality of B-mode sub-volume data sets according to the positional relationship between the plurality of sub-scanning areas, and generates a single volume data set (hereinafter referred to as a B-mode combined volume data set) for the full-scanning area. Will be called). Similarly, the combined volume data set generation unit 31 combines a plurality of Doppler sub-volume data sets according to the positional relationship with each other, and a single volume data set (hereinafter referred to as a Doppler combined volume data set) relating to the full scanning region. Generate). Details of the combined volume data set generation method will be described later. When there is no particular distinction between the B-mode combined volume data set and the Doppler combined volume data set, the combined volume data set will be called collectively.

  The body mark generation unit 33 performs image processing on the B-mode combined volume data set to generate two-dimensional image data related to the full scanning region. The image generated by the body mark generation unit 33 is used as a body mark in the present embodiment. Hereinafter, this image is referred to as a three-dimensional body mark. Details of the three-dimensional body mark generation process will be described later.

  The three-dimensional image processing unit 35 performs three-dimensional image processing on the B-mode combined volume data set and generates two-dimensional B-mode display image data. The three-dimensional image processing unit 35 performs three-dimensional image processing on the Doppler combined volume data set, and generates data of a two-dimensional Doppler display image. Examples of the three-dimensional image processing include MPR (multi planar reconstruction) processing, projection processing, volume rendering, surface rendering, and the like.

  The display control unit 37 displays a B-mode image, a Doppler image, a B-mode display image, a Doppler display image, and a three-dimensional body mark to be displayed on the display unit 39. Hereinafter, when these B-mode images, Doppler images, B-mode display images, and Doppler display images to be displayed are not distinguished, they are collectively referred to as ultrasonic images. In addition, the display control unit 37 can continuously display (cine display) time-series ultrasonic images, and display characters, memories, and the like of various parameters. Further, the display control unit 37 displays various marks superimposed on the three-dimensional body mark in order to present the positional relationship between the displayed ultrasound image and the combined volume data set to the user. Details of these display processes will be described later.

  The display unit 39 includes a display device such as a CRT display, a liquid crystal display, an organic EL display, or a plasma display.

  The input unit 41 inputs scan conditions and various command signals according to instructions from the user. Specifically, the input unit 41 includes input devices such as a keyboard, a mouse, various buttons, and a touch key panel.

  The network interface unit 43 transmits various ultrasonic images, sub-volume data sets, combined volume data sets, three-dimensional body mark data, or various calculation results stored in the storage unit 27 via a network (not shown). It can be transferred to another external device.

  The system control unit 45 has a function as an information processing device (computer), and controls the operation of each unit of the ultrasonic diagnostic apparatus according to the present embodiment. The system control unit 45 reads various programs for executing ultrasonic scanning, image / volume data set generation, three-dimensional body mark generation, mark display, and the like from the storage unit 27 and develops them on its own memory. Execute processing according to the program.

  The details of the operation of the ultrasonic diagnostic apparatus according to this embodiment will be described below. Hereinafter, in order to specifically describe the operation, the examination site according to the present embodiment is the breast, and the operation of the present embodiment will be described under the condition of breast cancer screening. In the present embodiment, not only the breast is a processing target, but all parts such as the liver and pancreas can be processed.

(Ultrasonic scanning in 4D panoramic view)
First, ultrasound scanning in 4D panoramic view will be described. The 4D panoramic view is an extension of a so-called 2D panoramic view to three dimensions. FIG. 2 is a diagram illustrating a relationship between the ultrasonic scanning in the 4D panoramic view and the sub-volume data set SV. As shown in FIG. 2, the user moves the ultrasonic probe 11 so that the whole breast is scanned three-dimensionally. More specifically, the user moves the ultrasonic probe 11 to the next sub-scanning region SR every time the three-dimensional scanning of one sub-scanning region SR is completed. As described above, the user intermittently moves the ultrasonic probe 11 in accordance with the progress of the three-dimensional scanning. At this time, the user moves the ultrasonic probe 11 so that the same scanning region is included in the temporally adjacent sub-scanning regions SR, that is, partially overlaps.

  In breast examination, for example, the ultrasonic probe 11 is moved in a circumferential shape as shown in FIG. The start position of the ultrasonic scanning is not particularly limited, and may be started from anywhere. In this embodiment, the moving locus of the ultrasonic probe 11 is regarded as a clock face, and the ultrasonic scanning start position is called the 12 o'clock position, and the opposite side is called the 6 o'clock position. To do. The ultrasonic probe 11 may be moved along any locus such as a square shape or a zigzag shape, instead of being circumferential.

  In this way, every time the sub-scanning region SR is three-dimensionally scanned with ultrasonic waves by the scanning control unit 13, the sub-volume data generating unit 29 generates a sub-volume data set SV related to the three-dimensionally scanned sub-scanning region SR. Generated. For example, if n sub-scanning areas SV are three-dimensionally scanned, n sub-volume data sets SV are generated. Each sub-volume data set is arranged on an individual image space. Each image space is defined by a separate coordinate system.

(Generated volume data set generation process)
Based on the plurality of sub-volume data sets related to the full scan area generated in this way, the combined volume data set generation unit 31 generates a combined volume data set.

  FIG. 3 is a diagram for explaining a combined volume data set generation process (combined process) by the combined volume data generation unit 31. As shown in FIG. 3, the combining process includes a joining process and an interpolation process. In the joining process, first, two temporally adjacent subvolume data sets are read. Here, it is assumed that the earlier time is the sub-volume data set SV1, and the later time is the sub-volume data set SV2. The two subvolume data sets SV1, SV2 are spatially continuous. That is, the two subvolume data sets SV1 and SV2 include anatomically identical scanning areas. The combined volume data set generation unit 31 connects the sub volume data set SV1 and the sub volume data set SV2 using the same scanning area.

  More specifically, for example, the correlation coefficient is calculated while moving the subvolume data set SV2 so as to overlap the subvolume data set SV1. This process is performed under the image space of one of the two subvolume data sets SV1, SV2, for example, the image space of the subvolume data set SV1. Then, the relative position of the subvolume data set SV2 with respect to the subvolume data set SV1 when the correlation coefficient is maximized is calculated. The relative position is calculated, for example, at a position between the centers of the sub-volume data sets SV1 and SV2. Then, using the calculated relative position, the voxel value of each voxel constituting the sub-volume data set SV2 is replaced with the voxel value of the voxel on the image space of the corresponding sub-volume data set SV1. As a result, the sub-volume data set SV1 and the sub-volume data set SV2 are joined together. The calculated relative positions of the sub-volume data sets SV1 and SV2 are stored in the storage unit 27. At this time, it is desirable to use B-mode data for the correlation coefficient even if the Doppler data is also included.

  In this way, all the sub-volume data sets (SV1 to SV7 in FIG. 3) are connected using the correlation between the two continuous sub-volume data sets SV1 and SV2. Next, data missing portions between spatially adjacent sub-volume data sets are interpolated by interpolation processing or extrapolation processing. More specifically, the voxel values of the voxels at the missing portion are interpolated linearly or nonlinearly based on a plurality of voxel values near the missing portion. A combined volume data set VD is generated by this interpolation processing. It should be noted that each voxel in the combined volume data set is assigned an identifier of the originating sub-volume data set and an identifier of the original B-mode image (or original Doppler image).

  As described above, when combining sub-volume data sets, the relative position between two consecutive sub-volume data sets is calculated. Using this relative position, the relative position of the other subvolume data set (hereinafter referred to as the reference subvolume data set) of the plurality of subvolume data sets (hereinafter referred to as the reference subvolume data set). Can be calculated).

(Absolute position calculation processing)
The absolute position is used to improve the accuracy of the relative position between the sub-volume data sets and to easily grasp the positional relationship. This absolute position is calculated by the combined volume data set generation unit 31 using the relative position between two consecutive sub volume data sets. Note that the reference subvolume data set is typically automatically set to the subvolume data set generated first, that is, the subvolume data set related to the 12 o'clock direction. However, any subvolume data set selected by the user via the input unit 41 can be set as the reference subvolume data set.

  An example of calculating the relative position (absolute position) of another subvolume data set with respect to the reference subvolume data set is shown below. As described above, in the process of generating the combined volume data set, the relative position between two consecutive subvolume data sets is calculated and stored. For example, if there are n subvolume data sets, n relative positions are calculated. The relative position of the reference volume data set is set, for example, at the center position of the reference volume data set. In order to calculate the absolute position of each sub-volume data set, the sum of all relative positions from the sub-volume data set to be calculated to the reference volume data set is calculated. For example, the absolute position of the third generated subvolume data set is calculated by the sum of the relative positions of the first, second, and third generated subvolume data sets. In this way, the absolute position of each subvolume data set is calculated. The calculated absolute position is stored in the storage unit 27 in association with the subvolume data set.

  By utilizing this absolute position, the subvolume data set can be arranged on the image space at the same position as the position on the real space. For example, by arranging the reference sub-volume data set in the image space at the same twelve o'clock position as in actual, the direction of the combined volume data set in the image space can be made the same as the direction in the real space. This makes it easy to grasp the positional relationship. The arrangement of the reference subvolume data set at the 12 o'clock position can be arranged by the user via the input unit 41. However, in order to reduce a user's trouble, it is good to arrange automatically.

  In the case of breast examination, it is impossible to determine whether the breast is left or right only by observing the combined volume data set, more specifically, an ultrasound image derived therefrom. Therefore, information for identifying left and right is assigned to the generated combined volume data set. In order to automatically assign this information, for example, a rule may be provided for the ultrasonic scanning method. Specifically, the rule is set such that the right chest is used when the ultrasound is scanned clockwise, and the left chest is used when the ultrasound is scanned counterclockwise. Based on the identifier of the sub-volume data set included in the combined volume data set and the absolute position of the voxel, the combined volume data set generation unit 31 determines whether the combined volume data set relates to the right breast or the left breast. It is determined whether it is related to. If it is determined that it is the right breast, the information indicating that it is the right breast is associated with the combined volume data set, and if it is determined that it is the left breast, the information indicating that it is the left breast. Associate.

  The above combining process utilized the correlation between the two subvolume data sets. However, the present embodiment need not be limited to this. For example, the coupling process may be performed using position information of an ultrasonic probe detected by a position sensor such as a magnetic sensor or an optical sensor. In this case, it is not necessary to include anatomically identical scanning areas in temporally adjacent sub-scanning areas.

(3D body mark generation process)
When the combined volume data set is generated, the body mark generation unit 33 performs a three-dimensional body mark generation process. First, the body mark generation unit 33 performs rendering processing on the combined volume data set to generate rendering image data. As rendering processing, surface rendering, volume rendering, and the like are possible. Hereinafter, it is assumed that the rendering processing is surface rendering that is considered particularly useful in the present embodiment. When performing surface rendering, it is necessary to set the viewpoint position and the line-of-sight direction (that is, the direction of the generated three-dimensional body mark). The viewpoint position and the line-of-sight direction may be set in advance or may be arbitrarily set by the user via the input unit 41.

  When the rendering image is generated, the body mark generation unit 33 reduces the rendering image at a predetermined reduction rate, and generates reduced image data. The matrix size of the generated reduced image is smaller than the matrix size of the rendering image. The reduction process is performed by a generally spread algorithm, and for example, an average pixel method, a nearest neighbor method, a bilinear method, or a bicubic method is employed. The reduction ratio and the reduced image matrix size may be set in advance or may be arbitrarily set by the user via the input unit 41. The reduced image data generated in this way is stored in the storage unit 27 as a three-dimensional body mark.

(Display processing)
Next, the display process of the three-dimensional body mark and the display process of various marks by the display image control unit 37 will be described. First, the display process of the three-dimensional body mark will be described.

  FIG. 4 is a diagram illustrating a layout example of a display screen of the three-dimensional body mark BM and the ultrasonic image I generated by surface rendering. As shown in FIG. 4, the three-dimensional body mark BM is a body mark that describes the actual breast (one breast) of the subject during the ultrasonic scanning. The three-dimensional body mark BM is typically for assisting in grasping the position and direction of the ultrasonic image I being displayed. Therefore, the viewpoint position of the three-dimensional body mark BM is preferably set outside the breast surface. Thereby, the user can grasp the appearance of the breast of the subject by observing the three-dimensional body mark BM.

  In order to make it easy to grasp the position, the initial direction of the three-dimensional body mark BM is preferably arranged so that the 12 o'clock position is upward on the display screen and the 6 o'clock position is downward on the display screen. . During the generation process of the combined volume data set, the user may arrange so via the input unit 41.

  As an ultrasonic image, a surface rendering image or a volume rendering image based on B-mode image data and Doppler image data may be displayed. In this case, the line-of-sight direction of the displayed surface rendering image or volume rendering image and the line-of-sight direction of the three-dimensional body mark typically typically coincide with each other. It is conceivable that the user rotates the line-of-sight direction of the surface rendering image and volume rendering image displayed via the input unit 41. In this case, the line-of-sight direction of the three-dimensional body mark may be linked to the line-of-sight direction of the surface rendering image or volume rendering image displayed on the display unit 39. In this case, each time the surface rendering image or volume rendering image displayed on the display unit 39 is rotated via the input unit 41, the displayed three-dimensional body mark is also automatically rotated.

  When the matrix size of the ultrasound image is large and cannot be displayed in the display screen, the ultrasound image is reduced and displayed, or only the ROI set by the user via the input unit 41 is cut out and displayed. Or better.

  Next, mark display processing will be described. Types of marks according to the present embodiment include a direction mark for indicating the direction of the three-dimensional body mark BM, a position mark for indicating the position of the ultrasonic image, and the like.

(Direction mark display processing)
As shown in FIG. 4, orientation marks for grasping the top, bottom, left and right are marked at predetermined positions of the three-dimensional body mark BM. For example, “12” in FIG. 4 indicates the direction at 12:00, “L” indicates the left chest, and “6” indicates the direction at 6 o'clock. Specifically, as described above, the voxel of the combined volume data set is assigned the absolute position or the relative position, and the identifier of the sub volume data set that is derived. The display control unit 37 specifies voxels located in the 12 o'clock direction and voxels located in the 6 o'clock direction from these pieces of information. Then, the display control unit 37 displays a “12” mark and a “6” mark at each position of the three-dimensional body mark BM corresponding to the specified position of each voxel.

(Position mark display processing)
The ultrasonic image I shown in FIG. 4 is generated by the original B-mode image generated by the B-mode image generation unit 21, the original Doppler image generated by the Doppler image generation unit 25, or the three-dimensional image processing unit 35. In the case of an MPR image, a cross-sectional position mark indicating the cross-sectional position of the ultrasonic image I may be displayed on the three-dimensional body mark BM. Hereinafter, for the sake of specific description, it is assumed that the ultrasonic image to be displayed (observed) is an original B-mode image.

  FIG. 5 is a diagram illustrating a display example of the position mark displayed on the three-dimensional body mark. As shown in FIG. 5, a cross-sectional position mark CM indicating the cross-sectional position of the original B-mode image is displayed on the three-dimensional body mark. As described above, the identifier of the original B-mode image is assigned to the voxel of the combined volume data set. Therefore, the cross-sectional position of the original B-mode image on the three-dimensional body mark BM can be specified based on this identifier. The display control unit 37 displays the cross-sectional position mark CM at the cross-sectional position on the specified three-dimensional body mark BM. For example, the cross-sectional position mark CM may be displayed in a different color or brightness from other regions on the three-dimensional body mark BM, or may be blinked. Further, the cross-sectional position mark CM may not only indicate the cross-sectional position but may indicate only the outline or corner of the cross-sectional position. Of course, when the user changes the cross-sectional position via the input unit 41, the position of the cross-sectional position mark CM moves in conjunction with the changed display cross-section. Of course, this function is not limited to the original B-mode image in the display section.

  In this way, by displaying the cross-sectional position mark CM on the three-dimensional body mark BM, it is possible to clearly present to the user where the displayed ultrasonic image is a visualization of the subject's breast. . This is because, for example, the three-dimensional body mark BM does not represent the standard shape of the human body like a conventional body mark, but represents the shape of the subject to be examined. The breast has a different shape and size depending on the subject, and even if it is the same subject, it differs depending on the method of examination. By generating a three-dimensional body mark based on the combined volume data set acquired at the time of inspection, an optimum body mark (three-dimensional body mark) can be presented for each inspection. Further, as described above, the initial orientation of the three-dimensional body mark is fixed by setting the reference subvolume data set to be arranged at a predetermined position on the display screen (in the above example, the back). Can be. Thereby, the user can easily determine which position of the breast the ultrasonic image is visualized.

  In breast cancer screening, observation of the mammary gland is important. Since the mammary gland travels in a complex manner, it is difficult to determine where the mammary gland is located on the breast only by looking at the ultrasound image. However, by displaying the three-dimensional body mark and the position mark of the ultrasonic image superimposed on the three-dimensional body mark, the user can easily grasp the position of the mammary gland being observed in the breast.

  Furthermore, a probe mark PM for indicating the position and orientation of the ultrasonic probe for acquiring an ultrasonic image corresponding to the cross-sectional position mark CM may be displayed on the three-dimensional body mark BM. The position of the probe mark PM is determined by the display control unit 37 according to the position of the cross section of the ultrasonic image, and the direction of the probe mark PM is determined according to the direction of the cross section of the ultrasonic image. Specifically, the probe mark PM is displayed at such a position and orientation that an ultrasonic image is acquired as an original B-mode image. By displaying the probe mark PW, the user can more easily grasp the position and orientation of the ultrasonic image.

  When the ultrasonic image is an MPR image, a plurality of MPR images related to a plurality of cross-sectional positions may be displayed on one screen. In this case, the plurality of cross sections may be displayed with different colors and brightness. For example, in ultrasonic diagnosis, an examination site is often diagnosed by displaying three MPR images related to three cross sections on one screen. In this case, the colors and luminances of all three cross sections may be displayed in different colors. Thereby, the position of each cross section can be grasped clearly and easily.

  Further, when a surface rendering image or a volume rendering image is displayed as the ultrasound image I, an ROI mark indicating the display area (3D ROI) of these ultrasound images may be displayed on the 3D body mark BM. In this case, in order to make it easier to grasp the position of the ultrasonic image, a line-of-sight mark indicating the line-of-sight direction of the ultrasonic image may be displayed on the three-dimensional body mark BM.

  Thus, the ultrasonic diagnostic apparatus according to this embodiment can improve the efficiency of ultrasonic diagnosis.

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

(Modification 1)
In the 4D panoramic view, the breasts on both sides may be scanned ultrasonically. In this case, since ultrasonic scanning is performed twice for each one, two combined volume data sets are generated. The combined volume data set generation unit 31 according to the first modification combines the two combined volume data sets to generate a single combined volume data set for both breasts. In Modification 1, the combined volume data set for one breast is referred to as a one-side combined volume data set, and the combined volume data set for both breasts is referred to as a two-sided combined volume data set. Various methods can be considered as a method of combining the one-side combined volume data sets. For example, there is a method of combining two one-side combined volume data sets with a predetermined interval or an interval set by the user via the input unit 41. Further, when a position sensor is provided in the ultrasonic probe 11, the ultrasonic probe 11 may be coupled according to position information supplied from the position sensor. In addition, when ultrasonic scanning of both breasts is performed once, a two-sided combined volume data set may be generated using the correlation between the sub-volume data sets as described in the present embodiment.

  Then, the body mark generation unit 33 performs image processing on the generated two-sided combined volume data set as described above, and generates three-dimensional body mark data regarding both breasts as shown in FIG. All the display processes described in the present embodiment can be applied to the three-dimensional body mark for both breasts. For example, the cross-sectional position mark, line-of-sight direction mark, ROI mark, probe mark, or orientation mark of the displayed ultrasonic image can be displayed on the three-dimensional body mark according to the modification. Note that “R” in FIG. 6 is a mark indicating the right breast.

  Further, it is possible to generate a single ultrasonic image data covering the breasts on both sides based on the both-side combined volume data set. Since the breasts on both sides can be ultrasonically diagnosed with one image, it is easy to determine which side of the breast is being observed. Further, it is possible to reduce the trouble of setting the cross-sectional position in each one-side combined volume data set, which is necessary for displaying both breasts on one screen. Therefore, it is expected that diagnostic efficiency is improved by displaying a wide range of ultrasound images related to the breasts on both sides.

(Modification 2)
One of the methods for visualizing blood flow in ultrasonic diagnosis is a contrast mode using a contrast agent. In this contrast mode, a contrast agent is administered to a predetermined part of the subject, and three-dimensional scanning is repeatedly performed via the ultrasonic probe 11 applied to the vicinity of the predetermined part. Then, a harmonic signal is extracted from the obtained echo signal, and harmonic image data is generated based on the extracted harmonic signal. The harmonic (harmonic) signal mainly consists of an echo signal from the contrast agent. Therefore, only the blood flow contrasted with the contrast agent is depicted in the generated harmonic image. Note that the echo signal includes a fundamental signal in addition to the harmonic signal. The fundamental (reference wave) signal is the center frequency of the echo signal and is the same as the center frequency of the transmission wave. The fundamental signal mainly consists of echo signals from the tissue.

  Considering the case where this contrast mode is utilized in the present embodiment, a subvolume data set based on a harmonic signal (hereinafter referred to as a harmonic subvolume data set) is used for calculating the relative position. Since only the blood flow is depicted in the harmonic subvolume data set, the calculation accuracy of the relative position between two consecutive subvolume data sets is lowered.

  Therefore, the B-mode processing unit 19 according to the second modification of the present embodiment extracts a fundamental (fundamental wave) signal and a harmonic (harmonic) signal from the echo signal using a filter. The extracted fundamental signal and harmonic signal are supplied to the B-mode processing unit 19. The B-mode processing unit 19 generates fundamental image data related to the scanning plane based on the supplied fundamental signal. In addition, the B-mode processing unit 19 generates harmonic image data regarding the same scanning plane based on the supplied harmonic signal. Then, the sub-volume data set generation unit 29 generates a fundamental sub-volume data set related to the sub-scanning area based on the plurality of fundamental images, and similarly generates a harmonic sub-volume data set related to the sub-scanning area based on the plurality of harmonic images. Generate.

  The combined volume data set generation unit 31 combines a plurality of fundamental subvolume data sets according to the relative positions of each other, and generates a single fundamental combined volume data set for the full scan region. Similarly, the combined volume data set generation unit 31 combines a plurality of harmonic subvolume data sets according to their relative positions, and generates a single harmonic combined volume data set for the full scan region. The relative position used in the binding process is calculated using a fundamental subvolume data set consisting mainly of tissue components. Accordingly, the relative position calculation accuracy is improved as compared with the case where the harmonic subvolume data set is used as in the normal contrast mode.

  In the second modification, the body mark generation unit 33 generates three-dimensional body mark data based on the fundamental combined volume data set in order to clearly display the breast. When displaying a harmonic image (contrast image), the cross-sectional position is displayed on the three-dimensional body mark according to the second modification.

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

  As described above, according to the present invention, it is possible to provide an ultrasonic diagnostic apparatus capable of improving the efficiency of ultrasonic diagnosis.

  DESCRIPTION OF SYMBOLS 11 ... Ultrasonic probe, 13 ... Scanning control part, 15 ... Transmission part, 17 ... Reception part, 19 ... B mode processing part, 21 ... B mode image generation part, 23 ... Doppler processing part, 25 ... Doppler image generation part, 27 ... Storage unit, 29 ... Sub-volume data set generation unit, 31 ... Combined volume data set generation unit, 33 ... Body mark generation unit, 35 ... 3D image processing unit, 37 ... Display control unit, 39 ... Display unit, 41 ... Input unit, 43 ... Network interface unit, 45 ... System control unit

Claims (5)

In an ultrasonic diagnostic apparatus that repeatedly and three-dimensionally scans an examination site of a subject with an ultrasonic wave via a moving ultrasonic probe,
A sub-volume data set generating unit that generates a plurality of sub-volume data sets related to a plurality of scanning regions included in the examination site based on an echo signal from the ultrasonic probe;
A combined volume data set generation unit configured to combine the plurality of generated sub-volume data sets according to a positional relationship between the plurality of scanning regions to generate a single combined volume data set;
A body mark generation unit for generating a body mark related to the examination site by performing image processing on the generated combined volume data set;
A display unit for displaying the generated body mark;
An ultrasonic diagnostic apparatus comprising:   The body mark generation unit generates rendering image data by rendering the combined volume data set with a predetermined line-of-sight position and direction, and generates the body mark by reducing the generated rendering image. The ultrasonic diagnostic apparatus according to claim 1. Further comprising an image generation unit for generating ultrasonic image data based on the echo signal;
The display unit displays a cross-sectional position on the body mark of the generated ultrasonic image on the body mark.
The ultrasonic diagnostic apparatus according to claim 1.   The ultrasonic diagnostic apparatus according to claim 3, wherein the display unit displays a mark indicating a position and a direction of an ultrasonic probe for acquiring the ultrasonic image on the body mark according to the cross-sectional position. The subvolume data set generation unit generates a plurality of fundamental wave subvolume data sets related to the plurality of scanning regions based on a fundamental wave component included in the echo signal, and based on a harmonic component included in the echo signal Generating a plurality of harmonic subvolume data sets for the plurality of scanning regions,
The combined volume data set generation unit generates a single fundamental wave combined volume data set based on the plurality of generated fundamental wave subvolume data sets, and generates the plurality of generated harmonic subvolume data sets. To generate a single harmonic coupled volume data set based on
The body mark generation unit generates the body mark based on the generated fundamental wave coupling volume data,
The image generation unit generates the ultrasonic image data based on the generated harmonic coupled volume data set.
The ultrasonic diagnostic apparatus according to claim 3.

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