JP2012157550A - Radiographic imaging apparatus and method - Google Patents

Abstract

PROBLEM TO BE SOLVED: To reduce fatigue of the eyes of an observer when displaying a stereoscopic image of a radiation image for a set area.SOLUTION: A two-dimensional radiation image is displayed on a first monitor 9A, and setting of a region of interest including an abnormal shadow of a lesion or the like is received. A convergence angle determination part 8c determines a convergence angle for determining directions of imaging a breast so as to have a stereoscopic effect in displaying a stereoscopic image of only the region of interest ROI. The breast is captured from the two directions corresponding to the determined convergence angle to acquire two radiation images, and a stereoscopic image of the region of interest ROI in the two radiation images is displayed on a second monitor 9B having lower resolution than the first monitor 9A.

Description

  The present invention relates to a radiographic imaging apparatus and method for acquiring a plurality of radiographic images by imaging a subject from a plurality of different directions.

  Conventionally, it is known that stereoscopic viewing can be performed using parallax by displaying a plurality of images in combination. Such a stereoscopically viewable image (hereinafter referred to as a stereoscopic image or a stereo image) is generated from a plurality of images acquired by photographing the same subject from different directions.

  On the other hand, such stereoscopic images are used not only in the fields of digital cameras and televisions but also in the field of radiographic imaging. In other words, a subject is irradiated with radiation from different imaging directions, the radiation transmitted through the subject is detected by a radiation detector to obtain a plurality of radiation images, and a stereoscopic image is obtained using these radiation images. It has been done to display. By using such a stereoscopic image, it is possible to observe a radiographic image with a sense of depth, so that diagnosis can be performed more easily.

  In addition, tissue specimens around the lesion may be collected in hospital examinations. Recently, as a method of collecting tissue pieces without imposing a heavy burden on the patient, a hollow tissue sampling needle (hereinafter referred to as a living tissue) is used. A biopsy that punctures a patient (referred to as a meter reading) and collects tissue embedded in the needle cavity has attracted attention. A stereo biopsy device has been proposed as a device for performing such a biopsy.

  This stereo biopsy device can specify a three-dimensional position of a lesion while observing a stereoscopic image of a subject, and controls the tip of a biopsy needle to reach the specific position from a desired position. A tissue piece can be collected.

  By the way, when displaying the above-described stereoscopic image, a method of displaying the stereoscopic image on the first screen, enlarging the area designated there and displaying it on the second screen (see Patent Document 1), and A method is proposed in which a two-dimensional image that cannot be stereoscopically viewed is displayed in one display area on a display screen of a monitor, and a stereoscopic image of a corresponding part on the two-dimensional image is displayed in another display area (see Patent Document 2). Has been. In addition, a method has been proposed in which a region designated in a stereoscopic image is enlarged and displayed three-dimensionally, not a radiographic image (see Patent Document 3). According to these methods, since the designated area can be enlarged and displayed in the initially displayed stereoscopic image or two-dimensional image, the designated area can be confirmed in more detail.

JP 2008-85641 A JP 2007-26885 A JP 2008-160382 A

  When performing the stereo biopsy described above, a tissue piece is collected by specifying a three-dimensional position of a lesion while observing a stereoscopic image of the subject. Therefore, in order to accurately identify a lesion and collect a tissue piece, a stereoscopic image or a two-dimensional radiation image is displayed, the position of the lesion is identified in the displayed image, and a predetermined including the identified lesion is included. It is conceivable to set a range area on the image and to enlarge the set area for three-dimensional display.

  However, when the set area is enlarged and displayed three-dimensionally, the parallax of the corresponding tissue included in the plurality of radiation images for displaying the stereoscopic image is enlarged, so that the stereoscopic effect becomes very large. Stereoscopic viewing is difficult, and the eyes of the observer are greatly fatigued. Also, if the set area is simply enlarged, the information originally contained in the image of the set area is lost when performing interpolation for enlargement, and the displayed stereoscopic image is blurred. As a result, the lesion may not be accurately identified.

  The present invention has been made in view of the above circumstances, and an object thereof is to reduce observer's eye fatigue when displaying a stereoscopic image of a radiographic image of a set region.

The radiographic image capturing apparatus according to the present invention can acquire two radiographic images for displaying a stereoscopic image by capturing an image of a subject from two directions having a predetermined convergence angle, and can also acquire the object from a predetermined direction. An imaging means capable of acquiring one radiation image by imaging a specimen;
First display means for displaying the stereoscopic image based on the one radiographic image or the two radiographic images;
Input means for receiving a setting of a region of interest in the one radiographic image or the stereoscopic image;
A second display means for displaying a stereoscopic image of the region of interest in two radiation images having a convergence angle different from the predetermined convergence angle when displaying the stereoscopic image of only the region of interest; It is characterized by.

In the radiographic image capturing apparatus according to the present invention, when displaying a stereoscopic image of only the region of interest, a convergence angle determining unit that determines a convergence angle at the time of capturing so as to obtain a predetermined stereoscopic effect;
The imaging control unit may further include an imaging control unit that controls the imaging unit so as to acquire the two radiographic images having the different convergence angles by imaging the subject from the two directions having the determined convergence angles.

  In this case, the convergence angle determination means may be means for determining the convergence angle according to the size of the second display means and the size of the region of interest.

  The “predetermined stereoscopic effect” means a stereoscopic effect such that when an observer observes a stereoscopic image, the stereoscopic effect can be easily performed with little fatigue. Such a three-dimensional effect can be obtained from two radiographic images obtained by imaging with a convergence angle of about 3 to 10 degrees, for example.

Moreover, in the radiographic image capturing apparatus according to the present invention, the imaging unit is a unit that acquires the two radiographic images and the one radiographic image having the predetermined convergence angle,
When the second display means displays a stereoscopic image of only the region of interest, one of the two radiographic images having the predetermined convergence angle and the region of interest in the one radiographic image are displayed. Means for displaying a stereoscopic image may be used.

  In this case, it is preferable that the radiographing direction of one radiographic image is between the radiographing directions of two radiographic images.

  Further, in this case, one of the two radiation images having the predetermined convergence angle at the time of displaying the stereoscopic image of the region of interest so that the stereoscopic image of the region of interest has a predetermined stereoscopic effect. Shift amount determination means for determining the shift amount of the image and the one radiographic image may be further provided.

  In this case, the shift amount determining means may be a means for determining the shift amount according to the size of the second display means and the size of the region of interest.

  In the radiographic image capturing apparatus according to the present invention, the second display means may be a means for displaying a stereoscopic image of the region of interest at an enlargement factor of an integer multiple of dot-by-dot.

  In the radiographic image capturing apparatus according to the present invention, the second display means may be a naked eye 3D monitor.

  In the radiographic image capturing apparatus according to the present invention, the first display unit may be a unit that displays the one radiographic image at an enlargement ratio that is an integer multiple of dot-by-dot.

  In the radiographic image capturing apparatus according to the present invention, the first display unit and the second display unit may be the same display unit.

The radiographic image capturing method according to the present invention can acquire two radiographic images for displaying a stereoscopic image by capturing an image of a subject from two directions having a predetermined convergence angle, and can also acquire the object from a predetermined direction. With the imaging means capable of acquiring one radiographic image by imaging the specimen, the one radiographic image or the two radiographic images are acquired,
Displaying the stereoscopic image based on the one radiographic image or the two radiographic images;
Receiving a setting of a region of interest in the one radiographic image or the stereoscopic image;
When displaying the stereoscopic image of only the region of interest, the stereoscopic image of the region of interest in two radiation images having a convergence angle different from the predetermined convergence angle is displayed.

  According to the present invention, two radiographic images for displaying a stereoscopic image are acquired by photographing a subject from two directions that have a predetermined convergence angle, or the subject is photographed from a predetermined direction. Thus, one radiation image is acquired. Next, a stereoscopic image based on one radiographic image or two radiographic images is displayed on the first display means, and setting of a region of interest is accepted in the single radiographic image or stereoscopic image. Then, when displaying the stereoscopic image of only the region of interest, the stereoscopic image of the region of interest in the two radiation images having a convergence angle different from the predetermined convergence angle is displayed on the second display unit.

  Thereby, since the stereoscopic image of the region of interest has a stereoscopic effect different from the stereoscopic effect of the stereoscopic image based on the two radiographic images having a predetermined convergence angle, stereoscopic viewing is facilitated. It is possible to reduce the fatigue of the eyes of the observer who observes the stereoscopic image of the region of interest.

  In addition, by determining the convergence angle at the time of imaging so as to have a predetermined stereoscopic effect, by capturing two radiation images with different convergence angles by imaging the subject from the two directions that become the determined convergence angle, A stereoscopic image of the region of interest in the two radiation images having different convergence angles is displayed on the second display means. As a result, the stereoscopic image of the region of interest has a predetermined stereoscopic effect, so that stereoscopic viewing is facilitated, and as a result, the fatigue of the eyes of the observer observing the stereoscopic image of the region of interest is reduced. be able to.

  Also, by determining the convergence angle according to the size of the second display means and the size of the region of interest, two new radiographic images that can display a stereoscopic image with an appropriate stereoscopic effect can be acquired.

  In addition, when two radiographic images having a predetermined convergence angle and one radiographic image are acquired, when displaying a stereoscopic image of only the region of interest, one of the two radiographic images having a predetermined convergence angle is displayed. By displaying the radiographic image and the stereoscopic image of the region of interest in one radiographic image, the stereoscopic image of the region of interest differs from the stereoscopic effect of the stereoscopic image based on the two radiographic images having a predetermined convergence angle. It will have. For this reason, stereoscopic viewing is facilitated, and as a result, it is possible to reduce fatigue of the eyes of the observer who observes the stereoscopic image of the region of interest. In addition, since it is not necessary to take two new radiographic images, the exposure dose to the subject can be reduced.

  In addition, one of the two radiographic images having a predetermined convergence angle and one radiation at the time of displaying the stereoscopic image of the region of interest so that the stereoscopic image of the region of interest has a predetermined stereoscopic effect. By determining the shift amount of the image, the stereoscopic image of the region of interest has a predetermined stereoscopic effect, so that stereoscopic viewing is facilitated. As a result, an observer who observes the stereoscopic image of the region of interest Eye fatigue can be reduced.

  Also, by determining the shift amount according to the size of the second display means and the size of the region of interest, it is possible to display a stereoscopic image with an appropriate stereoscopic effect.

  In addition, by displaying the stereoscopic image of the region of interest at an enlargement factor that is an integer multiple of dot-by-dot, information originally contained in the image in the region of interest is not lost. In particular, even if it is more than dot-by-dot, if the enlargement ratio is not an integer multiple, information will be lost due to interpolation calculation, but the information will be lost due to interpolation calculation by using an integer multiple enlargement ratio. There is no longer to do. Accordingly, since the stereoscopic image of the region of interest is not blurred or information is not lost, the lesion in the subject can be accurately specified in the displayed stereoscopic image of the region of interest.

  In addition, by displaying one radiographic image at an enlargement factor that is an integer multiple of dot-by-dot, information originally contained in the radiographic image is not lost. In particular, even if it is more than dot-by-dot, if the enlargement ratio is not an integer multiple, information will be lost due to interpolation calculation, but the information will be lost due to interpolation calculation by using an integer multiple enlargement ratio. There is no longer to do. Accordingly, since the radiographic image is not blurred or information is not lost, the lesion in the subject can be accurately specified in the displayed radiographic image.

1 is a schematic configuration diagram of a stereo breast image radiographing display system using a radiographic image radiographing apparatus according to a first embodiment of the present invention. The figure which looked at the arm part of the stereo breast image radiographing display system shown in FIG. 1 from the right direction of FIG. The figure which looked at the imaging stand of the stereo breast image radiographing display system shown in Drawing 1 from the upper part The block diagram which shows schematic structure inside the computer of the stereo breast image radiographing display system shown in FIG. The flowchart which shows the process performed in 1st Embodiment. Diagram showing the display of scout images Diagram showing the display of a stereo image of the region of interest Schematic configuration diagram of a stereo breast image radiographing display system using a radiographic image display device according to a second embodiment of the present invention. The flowchart which shows the process performed in 2nd Embodiment. Diagram showing a stereo image display of the entire breast Diagram showing the display of a stereo image of the region of interest The block diagram which shows schematic structure inside the computer of the stereo breast image radiography display system by 3rd Embodiment. The flowchart which shows the process performed in 3rd Embodiment

  Hereinafter, a stereo breast image capturing and displaying system using a radiographic image capturing apparatus according to a first embodiment of the present invention will be described with reference to the drawings. The mammography and display system according to the first embodiment of the present invention is a system that operates as a stereo biopsy device for breasts by attaching a detachable biopsy unit. First, a schematic configuration of the whole mammography / display system of the first embodiment will be described. FIG. 1 is a diagram showing a schematic configuration of a breast image radiographing display system in a state where a biopsy unit according to a first embodiment of the present invention is attached.

  As shown in FIG. 1, a breast image capturing and displaying system 1 according to the first embodiment includes a breast image capturing apparatus 10, a computer 8 connected to the breast image capturing apparatus 10, and a first monitor connected to the computer 8. 9A, a second monitor 9B, and an input unit 7.

  As shown in FIG. 1, the mammography apparatus 10 includes a base 11, a rotary shaft 12 that can move in the vertical direction (Z direction) with respect to the base 11, and can rotate. The arm part 13 connected with the base 11 is provided. FIG. 2 shows the arm 13 viewed from the right direction in FIG.

  The arm portion 13 has an alphabet C shape, and a radiation table 16 is attached to one end of the arm portion 13 so as to face the imaging table 14 at the other end. The rotation and vertical movement of the arm unit 13 are controlled by an arm controller 31 incorporated in the base 11.

  A radiation detector 15 such as a flat panel detector and a detector controller 33 that controls reading of a charge signal from the radiation detector 15 are provided inside the imaging table 14. The imaging table 14 includes a charge amplifier that converts a charge signal read from the radiation detector 15 into a voltage signal, a correlated double sampling circuit that samples a voltage signal output from the charge amplifier, a voltage A circuit board or the like provided with an AD conversion unit or the like for converting a signal into a digital signal is also installed.

  In addition, the photographing table 14 is configured to be rotatable with respect to the arm unit 13, and even when the arm unit 13 rotates with respect to the base 11, the direction of the photographing table 14 is fixed to the base 11. can do.

  The radiation detector 15 can repeatedly perform recording and reading of a radiation image, and may use a so-called direct type radiation detector that directly receives radiation to generate charges, or radiation. May be used as a so-called indirect radiation detector that converts the light into visible light and converts the visible light into a charge signal. As a radiation image signal reading method, a radiation image signal is read by turning on and off a TFT (thin film transistor) switch, or a radiation image signal by irradiating reading light. Although it is desirable to use a so-called optical readout system in which is read out, the present invention is not limited to this, and other types may be used.

  A radiation source 17 and a radiation source controller 32 are housed in the radiation irradiation unit 16. The radiation source controller 32 controls the timing of irradiating radiation from the radiation source 17 and the radiation generation conditions (tube current, time, tube current time product, etc.) in the radiation source 17.

  Further, in the central portion of the arm portion 13, a compression plate 18 disposed above the imaging table 14 to press and compress the breast, a support portion 20 that supports the compression plate 18, and a support portion 20 in the vertical direction ( A moving mechanism 19 for moving in the Z direction) is provided. The position of the compression plate 18 and the compression pressure are controlled by the compression plate controller 34. FIG. 3 is a view of the compression plate 18 shown in FIG. 1 as viewed from above. As shown in the drawing, the compression plate 18 can perform biopsy while the breast is fixed by the imaging table 14 and the compression plate 18. Thus, the opening 5 having a size of about 10 × 10 cm square is provided.

  The biopsis unit 2 is mechanically and electrically connected to the mammography display system 1 by inserting the base portion of the biopsy unit 2 into the opening of the support portion 20 of the compression plate 18 and attaching the lower end of the base portion to the arm portion 13. To be connected.

  The biopsy unit 2 includes a biopsy needle 21 that is punctured into the breast. The biopsy needle unit 22 is configured to be detachable, a needle support portion 23 that supports the biopsy needle unit 22, and the needle support portion 23 as a rail. And a moving mechanism 24 that moves the biopsy needle unit 22 in the X, Y, and Z directions shown in FIGS. 1 to 3 by moving the needle support part 23 in and out. The position of the tip of the biopsy needle 21 of the biopsy needle unit 22 is recognized and controlled as position coordinates (x, y, z) in a three-dimensional space by a needle position controller 35 provided in the moving mechanism 24. 1 is the X direction, the paper vertical direction in FIG. 2 is the Y direction, and the paper vertical direction in FIG. 3 is the Z direction.

  The computer 8 includes a central processing unit (CPU) and a storage device such as a semiconductor memory, a hard disk, and an SSD. The hardware 8 controls the control unit 8a, the radiation image storage unit 8b, the congestion as shown in FIG. An angle determination unit 8c and a display control unit 8d are configured.

  The controller 8a outputs predetermined control signals to the various controllers 31 to 35 to control the entire system. A specific control method will be described later.

  The radiation image storage unit 8 b stores a radiation image signal for each imaging angle acquired by the radiation detector 15.

  As will be described later, the convergence angle determination unit 8c has a predetermined stereoscopic effect when displaying a stereo image of only the region of interest set on the image displayed on the first monitor 9A on the second monitor 9B. Determine the angle of convergence during shooting.

  As will be described later, the display control unit 8d displays a two-dimensional image on the first monitor 9A, and displays a stereo image based on the two radiation images on the second monitor 9B.

  The input unit 7 is composed of a pointing device such as a keyboard and a mouse, for example, and a cursor is used to position a position such as an abnormal shadow in the two-dimensional image or the stereo image displayed on the first and second monitors 9A and 9B. It is configured so that it can be specified by. The input unit 7 receives an input of shooting conditions and an operation instruction by the operator.

  The first monitor 9 </ b> A displays a scout image acquired as will be described later using the radiographic image signal output from the computer 8 according to an instruction from the display control unit 8 d. The scout image is a two-dimensional radiation image (two-dimensional image) that cannot be stereoscopically viewed. Here, the first monitor 9A has a high resolution of, for example, about 2500 × 2000 pixels (≈5M) so that a two-dimensional image can be displayed at an enlargement ratio that is an integer multiple of dot-by-dot. In the present embodiment, it is assumed that the first monitor 9A displays the scout image GS at an enlargement rate that is one times the dot-by-dot.

  Here, by displaying dot-by-dot, when the enlargement ratio is 1, one pixel constituting the radiation image is displayed on one pixel of the first monitor 9A. For this reason, it is possible to display a radiographic image without losing information, thereby making it possible to accurately perform diagnosis using the radiographic image. In addition, when the enlargement ratio is set to 2 times or 3 times, one pixel constituting the radiation image is displayed on each of 2 × 2 pixels and 3 × 3 pixels of the first monitor 9A.

  Note that the enlargement factor is an integer multiple. If the enlargement factor is a magnification that includes a decimal, when an interpolation operation is performed on a radiographic image, the displayed image lacks information and is diagnosed. This is to prevent the inability to perform accurately.

  The second monitor 9B displays a stereo image using the two radiographic image signals output from the computer 8 in accordance with an instruction from the display control unit 8d. As a configuration, the stereo image can be stereoscopically viewed with the naked eye. It is a naked eye 3D monitor. As a monitor configuration for stereoscopically viewing a stereo image with the naked eye, for example, radiographic images based on two radiographic image signals are displayed using two screens, and one of these radiographic images is displayed using a half mirror or the like. Can be made to enter the right eye of the operator and the other radiation image can be made to enter the left eye of the operator to display a stereo image. Or it is good also as a structure which displays the stereo image based on two radiographic images by making the 2nd monitor 9B into 3D liquid crystal like a parallax barrier system and a lenticular system, for example.

  The second monitor 9B is not required to have the same resolution as the first monitor 9A, but can display a stereo image having a resolution necessary for diagnosis, for example, about 1920 × 1080 (≈2M) pixels. . Here, the second monitor 9B displays a stereo image of the region of interest designated in the scout image GS with an enlargement factor that is an integer multiple of dot-by-dot, as will be described later. In the present embodiment, it is assumed that the second monitor 9B displays a stereo image of the region of interest at a magnification that is 1 × dot-by-dot.

  Next, the operation of the mammography / display system of the first embodiment will be described with reference to the flowchart shown in FIG.

  First, the breast M is installed on the imaging table 14, and the breast is compressed with a predetermined pressure by the compression plate 18 (step ST1).

  Next, in the input unit 7, after various shooting conditions are input by the operator, an instruction to start shooting is input. At this time, it is assumed that the biopsy needle unit 22 is retracted upward and has not yet been punctured into the breast.

  Then, when there is an instruction to start photographing at the input unit 7, scout photographing is performed prior to photographing a stereo image of the breast M (step ST2). Specifically, first, the control unit 8a outputs a control signal to the radiation source controller 32 and the detector controller 33 so as to perform radiation irradiation and readout of a radiographic image signal in order to perform biopsy scout imaging. Here, since the arm unit 13 is in a position where the arm unit 13 is perpendicular to the imaging table 14 in the initial position, radiation is emitted from the radiation source 17 in accordance with this control signal, and the breast is vertically aligned. A radiation image taken from the direction (θ = 0 degree) is detected by the radiation detector 15, the radiation image signal is read out by the detector controller 33, and predetermined signal processing is performed on the radiation image signal. Then, it is memorize | stored in the radiographic image storage part 8b of the computer 8 as a radiographic image signal of the scout image GS.

  The scout image GS acquired by the scout shooting is displayed on the first monitor 9A by the display control unit 8c (step ST3). Since the scout image GS is displayed on the first monitor 9A at an enlargement ratio of 1 times dot-by-dot, it is a high-definition image with no missing information. While observing the scout image, the operator sets a region including an abnormal shadow such as a lesion visually recognized in the scout image as a region of interest (step ST4).

  FIG. 6 is a diagram for explaining setting of a region of interest. As illustrated in FIG. 6, the operator designates a rectangular region of interest ROI on the scout image GS displayed on the first monitor 9 </ b> A using a pointing device such as a mouse in the input unit 7. In the present embodiment, as will be described later, a stereo image of only the region of interest ROI is displayed on the second monitor 9B.

  In the present embodiment, the resolution of the second monitor 9B is smaller than the resolution of the first monitor 9B. For this reason, the maximum size of the region of interest ROI is limited according to the difference in resolution between the first monitor 9A and the second monitor 9B. Here, when displaying a stereo image based on two radiographic images, it is necessary to represent information for one pixel of the left and right eyes of the observer by two pixels of the stereo image, so the resolution in the left-right direction of the stereo image is It is necessary to reduce the resolution of two radiation images to ½. For this reason, for example, the resolution of the first monitor 9A is 2500 × 2000 pixels, and the resolution of the second monitor 9B is 1920 × 1080 pixels. The first and second monitors 9A and 9B have a scout image GS and a stereo image, respectively. Is displayed at a magnification of 1 times the dot-by-dot, the vertical size of the region of interest ROI is 1920/2500, which is the vertical size of the scout image GS displayed on the first monitor 9A. The horizontal size of the region ROI is limited to 540/2000, which is the horizontal size of the scout image GS displayed on the first monitor 9A.

  When the region of interest ROI is set, the convergence angle determination unit 8c determines the convergence angle θ when shooting a stereo image (step ST5). Here, when the number of pixels of two radiographic images acquired by photographing a stereo image is 5M, when the entire stereo image based on the two radiographic images is displayed on the second monitor 9B, the size of the stereo image is the original size. The size of the radiation image is reduced to about 2/5. In the present embodiment, a region of interest ROI is set in the scout image GS, and a stereo image of only the region of interest ROI is displayed on the second monitor 9B at a magnification that is one times the dot-by-dot. For this reason, the stereo image of only the region of interest ROI displayed on the second monitor 9B has an enlargement factor of about 2.5 times compared to the case where the entire stereo image is displayed on the second monitor 9B.

  Here, in the case of performing stereo biopsy, when the entire stereo image is displayed on the second monitor 9B, the convergence angle θ is about ± 15 degrees, but when the stereo image is enlarged, the convergence angle θ is not reduced. Then, the stereoscopic effect is too strong to make stereoscopic viewing difficult, and the eyes of the observer observing the stereo image are greatly fatigued. For this reason, the convergence angle determination unit 8c displays the stereo image of the region of interest ROI on the second monitor 9B according to the enlargement ratio compared with the case where the entire stereo image is displayed on the second monitor 9B. θ is determined. For example, when the enlargement ratio is 2.5 times, the convergence angle θ is determined to be about 1/10 of ± 15 degrees (ie, ± 1.5 degrees). The relationship between the enlargement ratio and the convergence angle is stored in advance as a table in the storage unit of the computer 8, and the convergence angle determination unit 8c refers to this table to determine the convergence angle θ.

  Next, the control unit 8 a outputs information on the convergence angle θ determined by the convergence angle determination unit 8 c to the arm controller 31. Next, when there is an instruction to start photographing at the input unit 7, a stereo image of the breast M is photographed (step ST6). Then, the arm controller 31 receives the information on the convergence angle θ output from the control unit 8a. The arm controller 31 captures the image of the arm unit 13 based on the information on the convergence angle θ as shown in FIG. A control signal is output so as to rotate + θ degrees with respect to a direction perpendicular to the table 14. That is, in the present embodiment, the control signal is output so that the arm unit 13 is rotated +1.5 degrees with respect to the direction perpendicular to the imaging table 14.

  Then, according to the control signal output from the arm controller 31, the arm portion 13 rotates by +1.5 degrees. Subsequently, the control unit 8a outputs a control signal to the radiation source controller 32 and the detector controller 33 so as to perform radiation irradiation and readout of the radiation image signal. In response to this control signal, radiation is emitted from the radiation source 17, a radiation image obtained by photographing the breast from the +1.5 degree direction is detected by the radiation detector 15, and a radiation image signal is read by the detector controller 33, The radiographic image signal is subjected to predetermined signal processing and stored in the radiographic image storage unit 8b of the computer 8. The radiographic image signal stored in the radiographic image storage unit 8b by this imaging represents the radiographic image GR for the right eye.

  Next, as shown in FIG. 2, the arm controller 31 once returns the arm unit to the initial position, and then outputs a control signal so as to rotate by −θ degrees with respect to the direction perpendicular to the imaging table 14. That is, in the present embodiment, a control signal is output so that the arm unit 13 is rotated by −1.5 degrees with respect to a direction perpendicular to the imaging table 14.

  Then, according to the control signal output from the arm controller 31, the arm unit 13 rotates by -1.5 degrees. Subsequently, the control unit 8a outputs a control signal to the radiation source controller 32 and the detector controller 33 so as to perform radiation irradiation and radiation image reading. In response to this control signal, radiation is emitted from the radiation source 17, a radiation image obtained by photographing the breast from the −1.5 degree direction is detected by the radiation detector 15, and a radiation image signal is read by the detector controller 33. After the predetermined signal processing, the radiation image storage unit 8b of the computer 8 stores the signal. The radiographic image signal stored in the radiographic image storage unit 8b by this imaging represents the radiographic image GL for the left eye.

  Then, after the two radiographic image signals stored in the radiographic image storage unit 8b of the computer 8 are read from the radiographic image storage unit 8b, a region corresponding to the region of interest ROI is extracted, and the radiation of the extracted region is extracted. The image signal is subjected to predetermined signal processing and output to the second monitor 9B, and a stereo image of the region of interest ROI is displayed on the second monitor 9B (step ST7).

  FIG. 7 is a diagram schematically showing a display of a stereo image of the region of interest ROI. As shown in FIG. 7, a stereo image of only the region of interest ROI is displayed on the second monitor 9B. Since the stereo image of the region of interest ROI is displayed on the second monitor 9B at a magnification that is one time larger than the dot-by-dot, the second monitor 9B has a high definition with no missing information.

  Next, after the stereo image of the region of interest ROI is displayed as described above, the operator specifies abnormal shadows such as calcification and tumor in the breast, and subsequently wants to collect those tissues by the biopsy unit 2 In some cases, the operator specifies an abnormal shadow target on the stereo image displayed on the second monitor 9B (step ST8).

  The target may be specified using, for example, a pointing device such as a mouse in the input unit 7. Specifically, for example, an indicator for a three-dimensional cursor is displayed in each of two radiographic images constituting a stereo image, and a three-dimensional cursor that is a stereoscopic image composed of the two indicators is displayed by the input unit 7. The target may be specified by moving it. In addition, the position of the index in each of the radiographic images GL and GR is assumed to have the coordinate position set according to the shooting direction when the stereo image is shot so as to indicate the same position.

  When a target is designated by the operator, position information (x, y, z) of the designated target is acquired by the control unit 8a, and the control unit 8a obtains the position information from the needle position controller 35 of the biopsy unit 2. Output to.

  In this state, when a predetermined operation button is pressed in the input unit 7, a control signal for moving the biopsy needle 21 is output from the control unit 8 a to the needle position controller 35. The needle position controller 35 moves the biopsy needle 21 so that the tip of the biopsy needle 21 is positioned above the position indicated by the coordinates based on the position information value input previously.

  Thereafter, when the operator performs a predetermined operation for instructing the puncture of the biopsy needle 21 in the input unit 7, the position indicated by the coordinates of the tip of the biopsy needle 21 is controlled by the control unit 8 a and the needle position controller 35. The biopsy needle 21 is moved so that the biopsy needle 21 is placed, and the biopsy needle 21 punctures the breast (step ST9).

  As described above, according to the first embodiment, when a region of interest ROI is set in the two-dimensional scout image GS displayed on the first monitor 9A and a stereo image only of the region of interest ROI is displayed, a predetermined three-dimensional image is displayed. The convergence angle θ is determined so as to give a feeling, and a stereo image is taken with the determined convergence angle θ to obtain two radiation images GL and GR, and the region of interest ROI based on the two radiation images GL and GR is obtained. A stereo image is displayed on the second monitor 9B at an enlargement ratio of 1 by dot-by-dot.

  For this reason, since the stereo image of the region of interest ROI has a predetermined stereoscopic effect, it is easy to make a stereoscopic view, and as a result, the fatigue of the eyes of the observer who observes the stereo image of the region of interest ROI is reduced. be able to.

  In addition, by displaying the stereo image of the region of interest ROI at an enlargement factor that is an integer multiple of dot-by-dot or more, information originally contained in the image in the region of interest is not lost. In particular, even if it is more than dot-by-dot, if the enlargement ratio is not an integer multiple, information will be lost due to interpolation calculation, but the information will be lost due to interpolation calculation by using an integer multiple enlargement ratio. There is no longer to do. Accordingly, since the stereo image of the region of interest ROI is not blurred or information is not lost, the abnormal shadow in the breast M can be accurately identified in the stereo image displayed on the second monitor 9B.

  Further, since the convergence angle θ is determined according to the size of the second monitor 9B and the size of the region of interest ROI, two radiation images GL and GR that can display a stereoscopic image with an appropriate stereoscopic effect are acquired. Can do.

When a stereo image of the breast is taken, a grid may be arranged in front of the radiation detector 15 in order to prevent scattering of radiation transmitted through the breast M. However, when performing stereo biopsy, the convergence angle θ Is large, such as ± 15 degrees, and the attenuation of radiation by the grid increases, so the radiation dose needs to be increased. According to the first embodiment, when taking a stereo image, the convergence angle θ can be reduced, so that the attenuation of radiation by the grid is reduced. Therefore, according to the first embodiment, it is possible to reduce the radiation dose when taking a stereo image, and as a result, it is possible to reduce the exposure dose of the breast M as the subject. The second embodiment will be described. FIG. 8 is a diagram showing a schematic configuration of a breast image radiographing display system in a state where a biopsy unit according to the second embodiment of the present invention is attached. In the second embodiment, the same components as those in the first embodiment are denoted by the same reference numerals, and detailed description thereof is omitted here. The mammography display system 1A according to the second embodiment has the first embodiment in which the first monitor 9A is omitted, only the second monitor 9B is provided, and the region of interest ROI is set in the stereo image. And different.

  Next, the operation of the mammography / display system of the second embodiment will be described with reference to the flowchart shown in FIG. In the second embodiment, steps ST11 to ST13 of the breast setting, scout imaging, and scout image display processes are the same as the processes of steps ST1 to ST3 of the first embodiment. The detailed explanation is omitted.

  When the scout image is displayed and the breast is positioned, the control unit 8a reads the convergence angle θ for photographing a preset stereo image, and outputs the read information on the convergence angle θ to the arm controller 31. To do. In the second embodiment, since biopsy is performed, θ = ± 15 degrees is preliminarily stored as information on the convergence angle θ at this time. An angle of ± 10 degrees may be used.

  Next, when there is an instruction to start photographing at the input unit 7, the first stereo image of the breast M is photographed (step ST14). The shooting of the first stereo image is the same as the processing in step ST6 in the first embodiment except that the convergence angle θ is ± 15 degrees, and thus detailed description thereof is omitted. Then, after the two radiographic image signals stored in the radiographic image storage unit 8b of the computer 8 are read from the radiographic image storage unit 8b, predetermined signal processing is performed and output to the second monitor 9B. A stereo image of the entire breast is displayed on the monitor 9B (step ST15). When the number of pixels of two radiographic images acquired by photographing a stereo image is 5M, when the entire stereo image based on the two radiographic images is displayed on the second monitor 9B, the image is reduced to about 2/5. Is done.

  While observing the stereo image of the entire breast displayed on the second monitor 9B, the operator sets a region including an abnormal shadow such as a lesion as a region of interest (step ST16).

  FIG. 10 is a diagram for explaining setting of a region of interest in the second embodiment. As shown in FIG. 10, the operator designates a region of interest ROI on the whole breast stereo image displayed on the second monitor 9 </ b> B by using a pointing device such as a mouse in the input unit 7.

  Here, in the second embodiment, the maximum size of the region of interest ROI is limited according to the difference in the number of pixels of the stereo image of the entire breast and the resolution of the second monitor 9B. For example, when the number of pixels of the stereo image of the whole breast is 2500 × 2000 pixels and the resolution of the second monitor 9B is 1920 × 1080 pixels, the size of the region of interest ROI in the vertical direction is the stereo image displayed on the second monitor 9B. The horizontal size of the region of interest ROI is limited to 1080/2000, which is the horizontal size of the stereo image displayed on the second monitor 9B.

  When the region of interest ROI is set, the convergence angle determination unit 8c determines the convergence angle θ for capturing the second stereo image (step ST17). Note that the process of determining the convergence angle θ is the same as the process of step ST5 in the first embodiment, and thus detailed description thereof is omitted.

  Next, the control unit 8 a outputs information on the convergence angle θ determined by the convergence angle determination unit 8 c to the arm controller 31. Next, when there is an instruction to start imaging at the input unit 7, a second stereo image of the breast M is captured (step ST18). Since the shooting of the second stereo image is the same as the process in step ST6 in the first embodiment, detailed description thereof is omitted.

  Then, two new radiographic image signals acquired by capturing the second stereo image stored in the radiographic image storage unit 8b of the computer 8 are read from the radiographic image storage unit 8b, and then the region of interest ROI. Is extracted, the radiographic image signal of the extracted region is subjected to predetermined signal processing and output to the second monitor 9B, and a stereo image of the region of interest ROI is displayed on the second monitor 9B ( Step ST19). In this case, in order to facilitate stereoscopic viewing of the stereo image of the region of interest ROI, a two-dimensional image based on only one of the two radiation images GL and GR is displayed so as to eliminate the stereoscopic effect of the entire breast. It is preferable.

  FIG. 11 is a diagram schematically showing the display of a stereo image of the region of interest ROI. As shown in FIG. 11, on the second monitor 9B, a window W1 is set on the stereo image of the entire breast, and a stereo image of the region of interest ROI is displayed in the set window W1. Note that the stereo image of the region of interest ROI is displayed in the window W1 at a magnification that is one time larger than the dot-by-dot, so that the window W1 has a high definition with no missing information.

  Then, target specification (step ST20) and perforation (step ST21) are performed in the same manner as the processing of steps ST8 and ST9 of the first embodiment, and the processing ends.

  As described above, also in the second embodiment, since the stereo image of the region of interest ROI has a predetermined stereoscopic effect, stereoscopic viewing is facilitated, and as a result, an observer who observes the stereo image of the region of interest ROI. Can reduce eye fatigue.

  Next, a third embodiment of the present invention will be described. Note that the stereo breast image radiographing display system according to the third embodiment has the same configuration as the stereo mammography radiographing display system according to the second embodiment, and only the processing performed in the computer 8 is different. The detailed description about is omitted. FIG. 12 is a block diagram showing a schematic configuration inside a computer of a stereo breast image radiographing display system according to the third embodiment. The third embodiment is different from the first embodiment in that a shift amount determining unit 8e is provided instead of the convergence angle determining unit 8c of the computer 8 in the second embodiment.

  Here, in the second embodiment, two new radiation images are acquired based on the determined convergence angle, but in the third embodiment, a scout image and a stereo image of the entire breast are displayed. The stereo image of the region of interest ROI is displayed on the second monitor 9B using one of the two radiographic images. Here, two radiographic images for displaying a stereo image of the whole breast are GL1 and GR1, and a radiographic image used for displaying a stereo image of the region of interest ROI is a radiographic image GL1. Note that the radiographic image GR1 may be used to display a stereo image of the region of interest ROI.

  Next, the operation of the breast image radiographing display system of the third embodiment will be described with reference to the flowchart shown in FIG. Note that in the third embodiment, steps ST31 to ST36 of breast installation, scout imaging, scout image display, first stereo image imaging, whole breast stereo image display, and region of interest setting processing are performed. Since it is the same as the process of step ST11 to step ST16 of the second embodiment, detailed description is omitted.

  When the region of interest ROI is set, the scout image GS and the radiation when the stereo image of the region of interest ROI is displayed by the shift amount determination unit 8e so that the stereoscopic effect of the stereo image of the region of interest ROI becomes appropriate. The shift amount of the image GL1 is determined (step ST37). Specifically, the shift amount determination unit 8e, when displaying the stereo image of the region of interest ROI on the second monitor 9B, according to the enlargement ratio compared with the case where the entire stereo image is displayed on the second monitor 9B, Determine the shift amount. For example, when the enlargement ratio is 2.5 times, the same stereoscopic effect as two radiographic images taken at a convergence angle of about 1/10 of ± 15 degrees (ie, ± 1.5 degrees) can be obtained. Determine the shift amount. The relationship between the enlargement ratio and the shift amount is stored in advance as a table in the storage unit of the computer 8, and the shift amount determination unit 8e refers to this table to determine the shift amount.

  Then, the image signals of the scout image GS and the radiation image GL1 stored in the radiation image storage unit 8b of the computer 8 are read out, the region corresponding to the region of interest ROI is extracted, and the extracted radiation image signal of the region is obtained. Predetermined signal processing is performed and output to the second monitor 9B so that the determined shift amount is obtained, and a stereo image of the region of interest ROI is displayed on the second monitor 9B (step ST38). In this case, in order to facilitate stereoscopic viewing of the stereo image of the region of interest ROI, a two-dimensional image based on only one of the two radiation images GL1 and GR1 is displayed so as to eliminate the stereoscopic effect of the entire breast. It is preferable.

  Then, target designation (step ST39) and perforation (step ST40) are performed in the same manner as the processing of steps ST8 and ST9 of the first embodiment, and the processing is terminated.

  Thus, in the third embodiment, the shift amounts of the scout image GS and the radiation image GL1 at the time of displaying the stereo image of the region of interest ROI are set so that the stereo image of the region of interest ROI has a predetermined stereoscopic effect. It is a decision. For this reason, it becomes easy to stereoscopically view the stereo image of the region of interest ROI, and as a result, it is possible to reduce the fatigue of the eyes of the observer who observes the stereo image of the region of interest ROI. In addition, since it is not necessary to take a second stereo image, the exposure dose to the breast M, which is the subject, can be reduced.

  Here, in the third embodiment, the shift amount between the scout image GS and the radiation image GL1 is determined. However, the region of interest is determined using the scout image GS and the radiation image GL1 without determining the shift amount. An ROI stereo image may be displayed. Even in this case, since the stereo image of the region of interest ROI has a smaller stereoscopic effect than the first stereo image, it is easy to make a stereoscopic view. As a result, the eyes of the observer observing the stereo image of the region of interest ROI A feeling of fatigue can be reduced.

  In the first to third embodiments, the second monitor 9B is a naked-eye 3D monitor. However, a monitor that performs stereoscopic viewing by using polarizing glass may be used. In this case, as the configuration of the second monitor 9B, radiographic images based on two radiographic image signals are displayed using two screens, and one of these radiographic images is displayed on the right eye of the operator by using a polarizing glass. It is possible to adopt a configuration in which a stereo image is displayed by making the other radiation image incident on the left eye of the operator. Further, for example, a configuration may be adopted in which two radiographic images are shifted and displayed by being shifted by a predetermined shift amount, and a stereo image is displayed by observing this with a polarizing glass.

  In the first to third embodiments, one embodiment of the radiographic image capturing apparatus of the present invention is applied to a stereo breast image capturing and displaying system. However, the subject of the present invention is not limited to the breast. For example, the present invention can be applied to a radiographic imaging display system that images a chest, a head, and the like.

DESCRIPTION OF SYMBOLS 1 Mammography imaging display system 2 Biooptic unit 7 Input part 8 Computer 8a Control part 8b Radiation image memory | storage part 8c Convergence angle determination part 8d Display control part 8e Shift amount determination part 9A 1st monitor 9B 2nd monitor 10 Mammography apparatus 13 Arm unit 14 Imaging table 15 Radiation detector 17 Radiation source 18 Compression plate 21 Biopsy needle 22 Biopsy needle unit 31 Arm controller 32 Radiation source controller 33 Detector controller 34 Compression plate controller 35 Needle position controller

Claims (11)

Two radiographic images for displaying a stereoscopic image can be acquired by imaging the subject from two directions having a predetermined convergence angle, and one radiation can be acquired by imaging the subject from a predetermined direction. Photographing means capable of acquiring images;
First display means for displaying the stereoscopic image based on the one radiographic image or the two radiographic images;
Input means for receiving a setting of a region of interest in the one radiographic image or the stereoscopic image;
A second display means for displaying a stereoscopic image of the region of interest in two radiation images having a convergence angle different from the predetermined convergence angle when displaying the stereoscopic image of only the region of interest; A radiographic imaging device characterized by the above. A convergence angle determining means for determining a convergence angle at the time of shooting so as to obtain a predetermined stereoscopic effect when displaying a stereoscopic image of only the region of interest;
An imaging control means for controlling the imaging means to acquire the two radiographic images having the different convergence angles by imaging the subject from the two directions having the determined convergence angles, The radiographic imaging apparatus according to claim 1.   The radiographic image capturing apparatus according to claim 2, wherein the convergence angle determination unit is a unit that determines the convergence angle according to a size of the second display unit and a size of the region of interest. The imaging unit is a unit that acquires two radiographic images and the one radiographic image having the predetermined convergence angle,
When displaying the stereoscopic image of only the region of interest, the second display means displays one of the two radiographic images having the predetermined convergence angle and the region of interest in the one radiographic image. The radiographic image capturing apparatus according to claim 1, wherein the radiographic image capturing apparatus is a means for displaying a stereoscopic image.   One of the two radiographic images having the predetermined convergence angle at the time of displaying the stereoscopic image of the region of interest and the 1 so that the stereoscopic image of the region of interest has a predetermined stereoscopic effect 5. The radiographic image capturing apparatus according to claim 4, further comprising shift amount determining means for determining a shift amount of two radiographic images.   The radiographic image capturing apparatus according to claim 5, wherein the shift amount determining unit is a unit that determines the shift amount according to a size of the second display unit and a size of the region of interest.   The said 2nd display means is a means to display the stereoscopic vision image of the said area | region of interest with the expansion rate of the integer multiple more than a dot-by-dot, The any one of Claim 1 to 6 characterized by the above-mentioned. Radiation image display device.   The radiographic image capturing apparatus according to claim 1, wherein the second display unit is a naked-eye 3D monitor.   The radiation according to any one of claims 1 to 8, wherein the first display means is means for displaying the one radiation image at an enlargement factor that is an integer multiple of dot-by-dot. Image shooting device.   9. The radiographic imaging apparatus according to claim 1, wherein the first display unit and the second display unit are the same display unit. Two radiographic images for displaying a stereoscopic image can be acquired by imaging the subject from two directions having a predetermined convergence angle, and one radiation can be acquired by imaging the subject from a predetermined direction. The one radiographic image or the two radiographic images are acquired by imaging means capable of acquiring an image,
Displaying the stereoscopic image based on the one radiographic image or the two radiographic images;
Receiving a setting of a region of interest in the one radiographic image or the stereoscopic image;
A radiographic imaging method comprising: displaying a stereoscopic image of the region of interest in two radiographic images having a convergence angle different from the predetermined convergence angle when displaying a stereoscopic image of only the region of interest.

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