JP6162325B2 - Radiographic imaging system, radiographic imaging method, and radiographic imaging program - Google Patents

Description

  The present invention relates to a radiographic image capturing system, a radiographic image capturing method, and a radiographic image capturing program.

  Conventionally, a radiographic imaging apparatus that performs radiography for medical diagnosis is known. Examples of this type of radiographic imaging device include mammography that images the breast of a subject for the purpose of early detection of breast cancer and the like. In mammography, a technique for performing tomosynthesis imaging in which radiation is applied to a breast of a subject at different angles is known. In tomosynthesis imaging, a tomographic image is generated by reconstructing from a plurality of radiographic images captured by irradiating a subject with radiation with different angles of incidence on a radiation detection surface within a predetermined range.

  For example, U.S. Pat. No. 7,831,296 describes that mammography imaging and tomosynthesis imaging are performed with a single breast compression.

  In the technique described in US Pat. No. 7,831,296, mammography imaging and tomosynthesis imaging are performed with a single breast compression, but imaging conditions are determined before imaging regardless of the presence or type of lesions. Therefore, there is room for improvement in order to obtain an accurate radiographic image.

  The present invention provides a radiographic imaging system, a radiographic imaging method, and a radiographic imaging program capable of obtaining an accurate radiographic image while reducing the burden on a subject.

1st aspect of this invention is a radiographic imaging system, Comprising: The radiation source which irradiates radiation toward a subject's breast, The radiation irradiated from the radiation source and permeate | transmitted the breast, The input control signal Based on the above, a radiation image whose resolution expressed by the number of pixels per unit length is the first resolution and a radiation image whose resolution is the second resolution higher than the first resolution is generated. And a region of interest for detecting a region of interest from a two-dimensional image that is a radiation image of the breast generated by the radiation image generator by irradiating the radiation at a predetermined incident angle with respect to the breast. When capturing a two-dimensional image with the detection unit, the radiation source is irradiated with radiation at a predetermined incident angle from the radiation source, and the radiation image generation unit causes the radiation image with the first resolution or the second Release of resolution When a region of interest is not detected from the two-dimensional image by outputting a control signal for generating a ray image and the region of interest is not detected from the two-dimensional image , the radiation is emitted a plurality of times with different incident angles from the radiation source in the first incident angle range. Irradiate and output a control signal for generating a plurality of radiation images of the first resolution of the breast to the radiation image generation unit to execute the first tomosynthesis imaging, and the region of interest is detected from the two-dimensional image by the region of interest detection unit. If detected, the radiation image generation unit causes the radiation image generation unit to irradiate the radiation a plurality of times with different incident angles in a second incident angle range that is larger than the first incident angle range from the radiation source. A control unit that outputs a control signal for generating a plurality of resolution radiographic images and executes second tomosynthesis imaging.

A second aspect of the present invention is a radiographic imaging system, a radiation source that irradiates radiation toward a subject's breast, radiation that is irradiated from the radiation source and transmitted through the breast, and an input control signal Based on the above, a radiation image whose resolution expressed by the number of pixels per unit length is the first resolution and a radiation image whose resolution is the second resolution higher than the first resolution is generated. And a region of interest for detecting a region of interest from a two-dimensional image that is a radiation image of the breast generated by the radiation image generator by irradiating the radiation at a predetermined incident angle with respect to the breast. When capturing a two-dimensional image with the detection unit, the radiation source is irradiated with radiation at a predetermined incident angle from the radiation source, and the radiation image generation unit causes the radiation image with the first resolution or the second Release of resolution A control unit that outputs a control signal for generating a ray image, and a radiation source that is irradiated multiple times with different incident angles in a first incident angle range from a radiation source based on a detection result of a region-of-interest detection unit. First tomosynthesis imaging in which a plurality of first-resolution radiation images of the breast are generated by the image generation unit, or different incident angles from a radiation source in a second incident angle range larger than the first incident angle range. A display unit that performs a recommended display that recommends any of the second tomosynthesis imaging in which radiation is generated a plurality of times and the radiation image generation unit generates a plurality of radiation images of the second resolution of the breast; An input unit to which a selection result of tomosynthesis imaging or second tomosynthesis imaging is input, and the control unit is configured to input the first tomosynthesis imaging or the And it outputs a control signal for executing the second tomosynthesis photographing.

  In addition, according to a third aspect of the present invention, in the first aspect or the second aspect, the second incident angle range may include the first incident angle range.

  In addition, according to a fourth aspect of the present invention, in the third aspect, the first incident angle range and the second incident angle range of the radiographic imaging system are symmetrical ranges around a predetermined incident angle. It may be.

Further, a fifth aspect of the present invention, the in the first aspect any one of the fourth aspect, based on a plurality of radiographic images of the breast of the subject acquired from the radiological image generator breast A tomographic image generation unit that generates a tomographic image of the subject, and a display device that displays a tomographic image of the left and right breasts of the subject generated by the tomographic image generation unit, wherein the control unit When the first tomosynthesis imaging is executed for one and the second tomosynthesis imaging is executed for the other of the left and right breasts, the tomographic image generation unit obtains a radiographic image of one breast acquired by the first tomosynthesis imaging The first resolution is the resolution in the depth direction based on the first tomographic image, the first tomographic image having the first resolution is generated, and the depth based on the radiographic image of the other breast acquired by the second tomosynthesis imaging is obtained. Direction A second tomographic image having a second resolution higher than the first resolution and a second resolution higher than the first resolution is generated, and a first incident angle of the radiation image of the other breast is further generated. The resolution in the depth direction is the first resolution based on the radiographic image acquired in the range, and a third tomographic image having the second resolution is generated separately. A tomographic image and at least one of the second tomographic image and the third tomographic image of the other breast may be displayed.

  According to a sixth aspect of the present invention, in the fifth aspect, the display device may switchably display the second tomographic image and the third tomographic image of the other breast.

The seventh aspect of the present invention, in the fifth aspect or the sixth aspect, the control unit for the other first tomosynthesis imaging is running and the left and right breasts for one of the right and left breasts of the subject first When the tomosynthesis imaging of 2 is executed, the tomographic image generation unit further has a resolution in the depth direction based on the radiographic image acquired in the first incident angle range among the radiographic images of the other breast. A first tomographic image of the first breast, a second tomographic image of the other breast, a second tomographic image of the other breast, and a third tomographic image. You may display an image and at least one of a 4th tomographic image.

  According to an eighth aspect of the present invention, in the seventh aspect, the display device displays the second tomographic image, the third tomographic image, and the fourth tomographic image of the other breast in a switchable manner. May be.

  According to a ninth aspect of the present invention, in any one of the fifth to eighth aspects, the display device can switch to the third tomographic image after displaying the second tomographic image. It is good.

  According to a tenth aspect of the present invention, in any one of the fifth to ninth aspects, the display device can switch between a tomographic image of a breast and a tomographic image having a resolution different from that of the tomographic image. You may display the 1st mark showing whether it is possible and at least one of the 2nd mark showing whether it can switch to a tomographic image in which resolution differs from a tomographic image.

  An eleventh aspect of the present invention is the tenth aspect, wherein the display device uses the first mark and the second mark for a tomographic image of one breast obtained by the first tomosynthesis imaging. The fact that switching is impossible may be displayed, and the other tomographic image obtained by the second tomosynthesis imaging may be displayed using the first mark and the second mark.

A twelfth aspect of the present invention is a radiographic imaging method, a radiation source that irradiates radiation toward a breast of a subject, radiation that is irradiated from the radiation source and transmitted through the breast, and an input control signal Based on the above, a radiation image whose resolution expressed by the number of pixels per unit length is the first resolution and a radiation image whose resolution is the second resolution higher than the first resolution is generated. A radiation image capturing method of a radiation image capturing apparatus, the radiation source generating radiation at a predetermined incident angle with respect to the breast and generated by the radiation image generating unit A region-of-interest detection step for detecting a region of interest from a two-dimensional image, which is a radiographic image , and when capturing a two-dimensional image, radiation is applied to the breast from a radiation source at a predetermined incident angle, When the control signal for generating the first resolution radiographic image or the second resolution radiographic image is output to the image generation unit, and the region of interest is not detected from the two-dimensional image by the region of interest detection step, the radiation source To the first incident angle range, the incident angle is varied to irradiate the radiation a plurality of times, and the radiation image generating unit outputs a control signal for generating a plurality of radiation images of the first resolution of the breast. When tomosynthesis imaging is performed and the region of interest is detected from the two-dimensional image by the region of interest detection step, the radiation is varied from the radiation source in a second incident angle range that is larger than the first incident angle range. Is emitted a plurality of times, and the radiographic image generation unit outputs a control signal for generating a plurality of radiographic images of the second resolution of the breast to execute the second tomosynthesis imaging. Includes a control unit step, the.

A thirteenth aspect of the present invention is a radiographic imaging method, a radiation source that irradiates radiation toward a breast of a subject, radiation that is irradiated from the radiation source and transmitted through the breast, and an input control signal Based on the above, a radiation image whose resolution expressed by the number of pixels per unit length is the first resolution and a radiation image whose resolution is the second resolution higher than the first resolution is generated. A radiographic image capturing method of a radiographic image capturing apparatus comprising: a radiographic image generating unit configured to irradiate a radiation source at a predetermined incident angle with respect to a breast by a region-of-interest detection unit When detecting a region of interest from a two-dimensional image that is a radiographic image of a breast generated in step 2 and a two-dimensional image taken by the control unit, a predetermined incident angle from the radiation source to the breast is obtained. Release A step of outputting a control signal for causing the radiation image generation unit to generate a radiation image of the first resolution or a radiation image of the second resolution by irradiating a ray, and the detection result of the region of interest detection unit by the display unit Based on the first tomosynthesis, the radiation image generation unit generates a plurality of radiation images of the first resolution of the breast by irradiating the radiation source a plurality of times with different incident angles in the first incident angle range from the radiation source. The radiation image generating unit is irradiated with radiation at a second incident angle range that is larger than the first incident angle range from the radiation source or the radiation source, and the radiation image generating unit has the second resolution of the breast. A step of performing a recommended display for recommending any one of the second tomosynthesis imaging for generating a plurality of radiation images, and a first tomosynthesis imaging or a second tomosynthesis by the input unit. Comprising the steps of scan imaging of selection result is input, the control unit, based on an input by the input unit, and outputting a control signal to execute the first tomosynthesis imaging or second tomosynthesis imaging, a.

  14th aspect of this invention is a radiographic imaging program, Comprising: A computer WHEREIN: The site | part interest detection part of the radiographic imaging system which is any 1 aspect of the said 1st aspect to 11th aspect of this invention, and It is for functioning as a control unit.

  In the present invention, it is possible to provide a radiographic image capturing apparatus, a radiographic image capturing method, and a radiographic image capturing program capable of obtaining an accurate radiographic image while reducing the burden on the subject.

It is a top view which shows the structural example of the radiographic imaging apparatus which concerns on 1st Embodiment. It is a figure which shows the structural example at the time of imaging | photography of the radiographic imaging apparatus which concerns on 1st Embodiment. It is a figure for demonstrating at the time of imaging | photography of the radiographic imaging apparatus which concerns on 1st Embodiment. It is a block diagram which shows the structural example of the radiographic imaging system which concerns on 1st Embodiment. It is a figure which shows the 1st structural example of the radiation detector for performing a 1st binning process. It is a figure which shows the 2nd structural example of the radiation detector for performing a 1st binning process. It is a figure which shows the 1st structural example of a 1st radiation detector. It is a figure which shows the 2nd structural example of a 1st radiation detector. It is a flowchart which shows an example of the flow of the process performed with the radiographic imaging system which concerns on 1st Embodiment. It is a figure which shows the specific example of the high-resolution tomographic image containing the region-of-interest image obtained by 2nd tomosynthesis imaging | photography concerning 1st Embodiment. It is a figure which shows the specific example of the low-resolution tomographic image obtained by the 1st tomosynthesis imaging | photography concerning 1st Embodiment. It is a flowchart which shows an example of the flow of the process performed with the radiographic imaging system which concerns on 2nd Embodiment. It is a figure which shows the specific example of the tomographic image displayed on a display when a region of interest is not detected in both the left and right breasts. It is a figure which shows the specific example of the tomographic image displayed on a display when a region of interest is detected with respect to both the left and right breasts. It is a flowchart which shows an example of the flow of the process performed with the radiographic imaging system which concerns on 2nd Embodiment. It is a figure which shows the specific example of the tomographic image displayed on the display when a region of interest is detected on one side (specifically, the right breast). It is a flowchart which shows an example of the flow of the process performed with the radiographic imaging system which concerns on 3rd Embodiment. It is a figure which shows the specific example of the tomographic image displayed on the display when a region of interest is detected on one side (specifically, the right breast). It is a flowchart which shows an example of the flow of a process in case a region of interest is detected from both the right and left breasts N performed with the radiographic imaging system which concerns on 4th Embodiment. It is a figure which shows the specific example of the tomographic image displayed on a display when a site of interest is detected in the left and right breasts. It is the specific example which showed the case where it displayed with one button about resolution and resolution. It is a flowchart which shows an example of the flow of the process performed with the radiographic imaging system which concerns on 5th Embodiment. It is a figure which shows the specific example of the recommendation display which concerns on 4th Embodiment. It is a figure which shows the other specific example of the recommendation display which concerns on 4th Embodiment.

  Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. Note that this embodiment does not limit the present invention.

[First Embodiment]
As shown in FIGS. 1 to 3, the radiographic imaging device 10 according to the present exemplary embodiment uses radiation (for example, X-rays) with the breast N of the subject W as a subject in the standing state where the subject W stands. ), For example, mammography. In the following, the front side close to the subject W when the subject W faces the radiographic image capturing apparatus 10 at the time of imaging will be described as the front side of the radiographic image capturing apparatus 10. Further, the back side away from the subject W when the subject W faces the radiographic image capturing apparatus 10 will be described as the rear side of the radiographic image capturing apparatus 10. Further, the left-right direction of the subject W when the subject W faces the radiation image capturing apparatus 10 will be described as the apparatus left-right direction of the radiation image capturing apparatus 10. Refer to the arrows in FIGS. 1 and 2 for the front side, the rear side, and the left-right direction of the difference of the radiographic imaging device 10.

  Moreover, the imaging target of the radiographic imaging device 10 is not limited to the breast N, and may be, for example, another part of the human body, a living organism other than a human being, or an object (inorganic substance). The radiographic image capturing apparatus 10 may be an apparatus that captures the breast N of the subject W when the subject W is sitting on a chair (including a wheelchair) or the like. Any device may be used as long as the breast N of the subject W can be separately photographed while the upper body of the examiner W is standing.

  As shown in FIG. 1, the radiographic image capturing apparatus 10 includes a measurement unit 12 having a substantially C-shaped side view provided on the front side of the apparatus, and a base unit 14 that supports the measurement unit 12 from the rear side of the apparatus. .

  The measurement unit 12 compresses the breast N between the imaging surface 22 on which the planar imaging surface 20 that contacts the breast N of the subject W in the standing position is formed and the imaging surface 20 of the imaging table 22. And a holding part 28 that supports the imaging table 22 and the compression plate 26. Note that a member that transmits radiation is used for the compression plate 26. A sensor (not shown) for detecting the relative position of the compression plate 26 with respect to the imaging table 22 (particularly, the imaging surface 20) is provided inside the holding unit 28. The radiographic image capturing apparatus 10 can detect the thickness of the breast with this sensor.

  The measurement unit 12 includes a radiation source 30 such as a tube (see FIG. 4), a radiation irradiation unit 24, and a support unit 29. The radiation irradiation unit 24 irradiates inspection radiation from the radiation source 30 toward the imaging surface 20. The support unit 29 is separated from the holding unit 28 and supports the radiation irradiation unit 24.

  Further, the measuring unit 12 is provided with a rotation shaft 16, and the measuring unit 12 can rotate with respect to the base unit 14. The rotation shaft 16 is fixed to the support portion 29, and the rotation shaft 16 and the support portion 29 rotate integrally.

  Each of the rotating shaft 16 and the holding portion 28 is provided with a gear, and the holding portion 28 and the rotating shaft 16 are connected and rotated integrally by switching between the meshing state and the non-meshing state of the gears. And the rotation shaft 16 can be switched to the state of being separated from the holding portion 28 and idling.

  Note that switching between transmission and non-transmission of the rotational force of the rotating shaft 16 is not limited to this gear, and various mechanical elements can be used.

  The holding unit 28 supports the imaging table 22 and the radiation irradiation unit 24 by separating the imaging surface 20 and the radiation irradiation unit 24 by a predetermined interval. The holding unit 28 also holds the compression plate 26, and the interval between the compression plate 26 and the imaging surface 20 changes as the compression plate 26 slides on the holding unit 28.

  The imaging surface 20 with which the breast N abuts is made of, for example, carbon from the viewpoint of radiation transparency and strength. A radiation detector 42 for detecting radiation that has passed through the breast N and the imaging surface 20 is disposed inside the imaging table 22. The radiographic image capturing apparatus 10 generates image information indicating a radiographic image based on the radiation detected by the radiation detector 42, and generates a radiographic image by an image processing unit (see FIG. 4) described later. Detailed description of the generation of the radiation image will be described later.

  The radiographic imaging device 10 of the present exemplary embodiment irradiates the breast N as a subject with different incident angles (changes) with respect to the detection surface of the radiation detector 42 within a predetermined range. It is an apparatus that can perform imaging at different incident angles. Here, the incident angle refers to an angle formed by the normal line of the detection surface of the radiation detector 42 and the radiation axis. Here, the detection surface of the radiation detector 42 is a surface substantially parallel to the imaging surface 20.

  As shown in FIGS. 2 and 3, the radiographic image capturing apparatus 10 irradiates the breast N with a plurality of times by changing the incident angle with respect to the detection surface of the radiation detector 42 within a predetermined range. This is a device that performs so-called tomosynthesis imaging. Hereinafter, a predetermined range in which the incident angle in tomosynthesis imaging is varied is referred to as an “incident angle range”. Specific examples of the incident angle range include a range of ± 10 degrees or ± 20 degrees with respect to the normal line of the detection surface of the radiation detector 42.

  In the present embodiment, as shown in FIG. 3, the position of the radiation irradiation unit 24 is moved from the angle α by a predetermined angle θ, and the positions of the radiation irradiation unit 24 are n locations (imaging locations) P1 to Pn. Shooting is performed. Hereinafter, the incident angle of radiation with respect to the normal direction of the detection surface of the radiation detector 42 is referred to as “incident angle”.

  The imaging at each imaging location may be performed while continuously moving the radiation irradiation unit 24. As an imaging method for continuous movement, for example, the radiation irradiation unit 24 is irradiated with radiation from the radiation irradiation unit 24 to the breast N when it reaches each imaging position without stopping while moving the radiation irradiation unit 24. Also good. Moreover, you may image | photograph, moving the radiation irradiation part 24 intermittently. As an imaging method for intermittent movement, for example, the radiation irradiation unit 24 may be moved to each imaging location, and then temporarily stopped, and the radiation irradiation unit 24 may irradiate the breast N with radiation. . Also, when each imaging location is reached while moving the radiation irradiation unit 24, radiation is irradiated from the radiation irradiation unit 24 to the breast N, and after stopping, the radiation irradiation unit 24 is moved again. Also good.

  The radiographic image capturing apparatus 10 of the present embodiment performs tomosynthesis imaging in two types of incident angle ranges. Hereinafter, a small (narrow) incident angle range, which is an example of the first incident angle range of the disclosed technology, of two types of incident angle ranges is referred to as a “small incident angle range”. A large (wide) incident angle range which is an example of the second incident angle range of the disclosed technique is referred to as a “large incident angle range”. Values such as the incident angle range are stored in advance in the memory 43B in the control unit 46, for example. In the present embodiment, both the small incident angle range and the large incident angle range are symmetric with respect to the predetermined incident angle, and the predetermined incident angles in the small incident angle range and the large incident angle range are the same. It is said. Therefore, the small incident angle range is included in the large incident angle range. In the present embodiment, as a specific example, the predetermined incident angle is set as the angle in the normal direction of the detection surface of the radiation detector 42. The small incident angle range is included in the large incident angle range.

  2 and 3 respectively show the posture of the radiographic image capturing apparatus 10 and the position of the radiation irradiating unit 24 when tomosynthesis imaging is performed. As shown in FIGS. 2 and 3, tomosynthesis imaging is performed by tilting the support portion 29 that supports the radiation irradiation portion 24.

  In general, when tomosynthesis imaging is performed, the breast N of the subject W is irradiated with a plurality of (n) times of radiation. Therefore, in order to suppress the exposure dose, the dose of radiation for one time is lowered, and for example, normal two-dimensional imaging with n total times (irradiating the subject with radiation from a fixed position without moving the radiation source 30) The same dose of radiation as in normal shooting) is applied.

  In addition, the radiographic imaging apparatus 10 of the present embodiment performs both CC (Cranio & Caudal) imaging and MLO (Mediolateral-Oblique) imaging on the breast N. It is a device that can. When performing CC imaging, the orientation of the holding unit 28 is adjusted with the imaging surface 20 facing the vertical direction with respect to the ground, and the radiation irradiating unit 24 is perpendicular to the normal of the imaging surface 20 (that is, 0). The posture of the support portion 29 is adjusted to the position of degree. Thereby, radiation is irradiated from the radiation irradiation unit 24 to the breast N from the head side to the foot side of the subject W in the standing position, and CC imaging is performed. Further, in the case of performing MLO imaging, in general, the posture of the holding unit 28 is adjusted in a state in which the imaging table 22 is rotated by 45 ° or more and less than 90 ° compared to the case of performing CC imaging. Positioning is performed with the axilla of the subject W applied to the front side wall corner 22A. Thereby, radiation is irradiated from the radiation irradiation unit 24 to the breast N from the axial center side of the body of the subject W to the outside, and MLO imaging is performed.

  In addition, a chest wall surface 25 is formed on the surface of the imaging table 22 on the front side of the apparatus so that the chest part below the breast N of the subject W abuts when imaging is performed. The chest wall surface 25 is formed in a flat shape.

  In FIG. 4, the block diagram of an example of a structure of the radiographic imaging system 6 of this Embodiment is shown.

  The radiographic image capturing system 6 of this embodiment includes a radiographic image capturing device 10, an image processing device 50, and a display device 80.

  The radiographic image capturing apparatus 10 includes a radiation irradiation unit 24, a radiation detector 42, an operation panel 44, a control unit 46, and a communication I / F (interface) unit 48.

  The control unit 46 has a function of controlling the operation of the entire radiographic imaging apparatus 10. The control unit 46 includes a CPU (Central Processing Unit) 43A, a memory 43B including a ROM (Read Only Memory) and a RAM (Random Access Memory), a nonvolatile storage unit including an HDD (Hard Disk Drive), a flash memory, and the like. 43C. In the radiographic imaging device 10 according to the present exemplary embodiment, the control unit 46 includes an image processing unit 45 and a region-of-interest detection unit 47. For example, the image processing unit 45 and the region-of-interest detection unit 47 include the CPU 43A, the memory 43B, and It is partially contained in the storage unit 43C and the like. The control unit 46 is connected to the radiation irradiation unit 24, the radiation detector 42, the operation panel 44, and the communication I / F unit 48.

  When the control unit 46 receives an irradiation instruction from the operator using the exposure switch displayed on the instruction input unit 84, the radiation provided in the radiation irradiation unit 24 according to the imaging menu set based on the instructed exposure condition. Radiation is emitted from the source 30 to the imaging surface 20. In the present embodiment, the radiation source 30 emits cone beam radiation (for example, a conical X-ray beam).

  The radiation image generation unit 41 has a function of generating a radiation image of the subject based on the radiation transmitted through the subject. In the present embodiment, the radiation image generation unit 41 includes a radiation detector 42 and an image processing unit 45. The radiation detector 42 receives image radiation carrying image information, records the image information, and outputs the recorded image information. A specific example of the radiation detector 42 is an FPD (Flat Panel Detector) that arranges a radiation sensitive layer, converts radiation into digital data, and outputs the digital data. The radiation sensitive layer can be disposed substantially parallel to the imaging surface 20. When the radiation is irradiated, the radiation detector 42 outputs image information indicating a radiation image to the image processing unit 45 of the control unit 46. In the radiographic imaging device 10 of the present exemplary embodiment, the radiation detector 42 receives image radiation that has passed through the breast N and obtains image information indicating a radiographic image. Then, the image processing unit 45 performs necessary processes such as gain correction, offset correction, and defective pixel correction on the image information obtained by the radiation detector 42 to generate a radiation image. The position where the image processing unit 45 is provided is not limited to the present embodiment. For example, the image processing unit 45 may be provided in the radiation detector 42. Further, the image processing unit 45 may be provided in the image processing apparatus 50 as described later.

  Further, the radiation image generation unit 41 of the present embodiment generates radiation images with different resolutions. More specifically, the radiation detector 42 generates image information with a plurality of types of resolutions. More specifically, the radiation detector 42 performs a process of reading out a plurality of pixels collectively (a so-called binning process) and a process of reading out each pixel. That is, according to the radiation detector 42, image information indicating radiation images having two types of resolution can be obtained. When this image information is image-processed by the image processing unit 45, radiation images having two types of resolution are finally obtained. Details of the configuration of the radiation detector 42 capable of binning will be described later. In the present embodiment, the resolution refers to the density of pixels in the direction of the detection surface of the radiation detector 42. In general, the higher the resolution (higher resolution), the better the image quality.

  The region-of-interest detection unit 47 has a function of detecting a region of interest from the radiographic image generated by the image processing unit 45. In this embodiment, the site of interest refers to a site of interest when a user such as a doctor observes a radiographic image, and includes, for example, a site of mutation due to a lesion or the like. Specific examples of the mutation site include a mutation site suspected of calcification and a mutation site suspected of being a tumor. Information for detecting the region of interest is stored in the memory 43B of the control unit 46 or the like.

  In the present embodiment, the image processing unit 45 and the region-of-interest detection unit 47 are provided in the control unit 46 as a part of the control unit 46 in order to perform high-speed processing without going through the network 49. Explain, but not limited to this. The image processing unit 45 and the region of interest detection unit 47 may have a hardware configuration different from that of the control unit 46. In the case of another hardware configuration, for example, the image processing unit 45 and the region-of-interest detection unit 47 may be provided on the image processing device 50 side. When provided on the image processing device 50 side, information for detecting a mutation site by the site-of-interest detection unit 47 may be stored in the ROM 54 of the image processing device 50 or the like. Further, the image processing unit 45 and the region-of-interest detection unit 47 may have a hardware configuration or a software configuration that is executed by the CPU 43A executing a program. In that case, it may be software executed on the same computer as the computer on which software for controlling the entire radiographic imaging apparatus 10 is executed, or software executed on another computer.

  The instruction input unit 84 has a function of setting various operation information including shooting conditions, various operation instructions, and the like. It should be noted that the function of the engineer moving the compression plate 26 up and down while sandwiching the patient's breast N before tilting, or tilting the support 29 (ie, the radiation irradiating unit 24) in order to perform CC imaging, MLO imaging, etc. An operation panel 44 is also provided. For example, the operation panel 44 is provided as a plurality of switches on the imaging table 22 of the radiographic imaging apparatus 10. Note that the operation panel 44 may be provided as a touch panel.

  The imaging conditions set by the instruction input unit 84 include information on radiographic imaging such as tube voltage, tube current, exposure conditions including irradiation time, and posture information. The posture information specified by the instruction input unit 84 includes information indicating an imaging position (including an incident angle and an incident angle range) when imaging is performed with radiation incident on the breast N at a plurality of incident angles. It is. In the present embodiment, as an example, the instruction input unit 84 functions as a display unit of the disclosed technology. However, the present invention is not limited to this. For example, the operation panel 44 may function as a display unit.

  Note that various operation information such as exposure conditions and posture information, various operation instructions, and the like may be set by an operator through the instruction input unit 84, or other control devices (for example, RIS: Radiology Information System). Or may be stored in advance in a storage unit in the control unit 46.

  When various information is set by the instruction input unit 84, the control unit 46 emits radiation from the radiation irradiation unit 24 according to the imaging menu set based on the set various information (breast N ) To capture a radiographic image. When performing tomosynthesis imaging on the breast N, the control unit 46 adjusts the posture of the holding unit 28 so that the imaging surface 20 faces upward, and the radiation irradiation unit 24 moves upward with respect to the imaging surface 20. The attitude of the support portion 29 is adjusted to the position. Then, as shown in FIG. 3, the control unit 46 rotates the support unit 29 to move the radiation irradiation unit 24 in an arc shape from the angle α to the angle θ based on the imaging conditions, and causes the radiation irradiation unit 24 to move. Radiation is emitted from the radiation source 30 provided. As a result, n radiation images having different radiation incident angles are obtained.

  The communication I / F unit 48 is a communication interface having a function for transmitting and receiving a captured radiographic image and various information via the network 49 between the radiographic image capturing apparatus 10 and the image processing apparatus 50. .

  The image processing apparatus 50 has a function (tomographic image generation unit 68) that generates a tomographic image reconstructed from the radiographic image acquired from the radiographic imaging apparatus 10. The image processing apparatus 50 has a function (not shown) for performing image processing for a doctor or the like to observe a tomographic image, a projection image described below, or the like on the display device 80. Hereinafter, a person who observes a captured radiographic image or generated tomographic image, or observes or diagnoses a region of interest or the like, such as a doctor, is referred to as a “user”. In addition, the radiation image obtained by the radiation detector 42 detecting radiation by tomosynthesis imaging in the radiation image capturing apparatus 10 is referred to as a “projection image”.

  The image processing apparatus 50 includes a CPU 52, ROM 54, RAM 56, HDD 58, communication I / F unit 60, image display instruction unit 62, instruction reception unit 64, tomographic image generation unit 68, and storage unit 74. These are connected to each other by a bus 75 such as a control bus or a data bus.

  The CPU 52 has a function of controlling the entire image processing apparatus 50 and the like. Specifically, the CPU 52 performs control by executing various programs 55 stored in the ROM 54. In the image processing apparatus 50 of the present embodiment, the case where the program 55 is stored in advance is shown. However, the present invention is not limited to this, and the program 55 is stored in a recording medium such as a CD-ROM or a removable disk. Alternatively, it may be installed in the ROM 54 or the like from a recording medium. The program 55 may be installed in the ROM 54 or the like from an external device via a communication line such as the Internet. The RAM 56 has a function of securing a work area when the CPU 52 executes the program 55. The HDD 58 has a function of storing and holding various data. In the present embodiment, the tomographic image generation unit 68 is described as being included in the image processing apparatus 50 as a part of the image processing apparatus 50, but the present invention is not limited to this. The tomographic image generation unit 68 may have a hardware configuration different from that of the image processing apparatus 50.

  The communication I / F unit 60 is a communication interface having a function for transmitting and receiving a radiographic image and various information captured between the image processing apparatus 50 and the radiographic image capturing apparatus 10 via the network 49. is there.

  The image display instruction unit 62 has a function of instructing the display 82 of the display device 80 to display a radiation image. In the present embodiment, the case where the image display instruction unit 62 is provided in the image processing apparatus 50 will be described. However, part or all of the functions of the image display instruction unit 62 are incorporated in the control unit 46. May be.

  The display device 80 according to the present embodiment has a function of displaying captured radiographic images, and includes a display 82 and an instruction input unit 84 on which radiographic images are displayed. The instruction input unit 84 may be, for example, a touch panel, a keyboard, a mouse, or the like. The instruction input unit 84 allows the user to input an instruction related to the display of the radiation image, the above-described imaging conditions, and the like. In addition, the user can instruct the start of shooting from the instruction input unit 84. When the display 82 and the instruction input unit 84 are touch panels, the display 82 and the instruction input unit 84 can be shared. The instruction receiving unit 64 has a function of receiving an instruction from the user input by the instruction input unit 84 of the display device 80.

  The tomographic image generation unit 68 has a function of reconstructing a plurality of projection images and generating a tomographic image parallel to the imaging surface 20 at a predetermined slice interval. In this embodiment, “parallel” is used, but it also includes substantially parallel which is a design error.

  As described above, in the radiographic image capturing apparatus 10 of the present embodiment, the breast N is pressed and fixed by the compression plate 26 in a state where the breast N is in contact with the imaging surface 20 of the imaging table 22. For this reason, in the radiographic imaging apparatus 10 of the present exemplary embodiment, the radiation incident angle with respect to the normal direction of the detection surface of the radiation detector 42 that is parallel to the imaging surface 20, and the tomographic image of the breast N The incident angle of radiation with respect to the normal direction of the tomographic plane is equal.

  The tomographic image generator 68 moves the radiation irradiator 24 (radiation source 30) to the positions P1, P2, P3,..., Pn, and at a predetermined slice interval from a plurality of projection images photographed at each position. A tomographic image is generated. Note that the position at which the region of interest is projected on the projection image differs depending on the incident angle of radiation with respect to the imaging surface 20. Therefore, the tomographic image generation unit 68 acquires imaging conditions when a projection image is captured from the radiation image capturing apparatus 10. The tomographic image generation unit 68 calculates the amount of movement of the region of interest between the plurality of projection images based on the incident angle of the radiation included in the imaging conditions, and based on a known reconstruction method such as a shift addition method. Reconstruct a tomographic image.

  In addition to the shift addition method, a conventionally known CT (Computed Tomography) reconstruction method can be used as the reconstruction method. For example, as a CT reconstruction method, an FBP method (Filtered Back Projection method) that is a typical method can be used. The FBP method is a reconstruction method in which tomographic parallel plane tomographic scanning is regarded as part of cone beam CT scanning and the filter back projection method is extended. Furthermore, an iterative reconstruction method described in JP2011-125698A can also be used. Although this iterative reconstruction method is also a reconstruction method for CT, it can also be applied to reconstruction when tomosynthesis imaging is performed, as in the FBP method.

  The tomographic image generation unit 68 can be realized by hardware, for example, hardware such as a general electronic circuit, ASIC (Application Specific Integrated Circuit), or FPGA (Field Programmable Gate Array).

  The tomographic image generation unit 68 can generate tomographic images having different resolutions from a projection image obtained by one tomosynthesis imaging. The upper limit of the resolution of the tomographic image generated by the tomographic image generation unit 68 is determined by the size (width) of the incident angle range when the projection image is captured. In the present embodiment, the resolution is the resolution in the normal direction (depth direction) of the tomography, and refers to the resolution in the normal direction of the detection surface of the radiation detector 42. As the incident angle range is larger (wider), the upper limit of the resolution of the tomographic image becomes higher and the resolution can be increased. When the incident angle range is large (wide), the region of interest can be projected to more different positions on the projection image, so that the resolution can be increased.

  Comparing tomographic images with the same thickness at the same height (position in the normal direction of the depth of the fault), the tomographic image with high resolution is included in the thickness according to the required height. Image information, that is, necessary image information is obtained. Therefore, the reconstructed tomographic image is an image with a sharp appearance. On the other hand, in the low-resolution tomographic image, what is included in the thickness is the required height and image information around the height, that is, extra image information is included. For this reason, the reconstructed tomographic image becomes an image that looks dull, as in the case of superimposing high-resolution tomographic images.

  Note that the tomographic image generation unit 68 can reduce the resolution of the tomographic image by generating a tomographic image using only a part of the captured projection images. For example, the resolution of the tomographic image can be lowered as compared with the case where all the projection images are used.

  In addition, the tomographic image generation unit 68 of the present embodiment can generate tomographic images with different resolutions. Specifically, a tomographic image having a resolution lower than the resolution of the projection image can be generated with the upper limit of the resolution of the projection image acquired from the radiation image generation unit 41. The resolution changing method may be a resolution changing method used for general images. Similarly to the binning process in the radiological image generation unit 41, which will be described in detail later, a process of adding pixel information of a plurality of pixels × a plurality of pixels is performed to reduce the number of apparent pixels and generate a low-resolution image. May be. Further, for example, similarly to the binning process in the radiation image generation unit 41 described later in detail, a thinning process using only pixel information of some of the plurality of pixels may be performed.

  The storage unit 74 has a function of storing projection information captured by the radiographic image capturing apparatus 10, image information representing each of the tomographic images generated by the tomographic image generation unit 68, and the like. A specific example of the storage unit 74 is a mass storage device such as a hard disk. In the present embodiment, the storage unit 74 also stores imaging conditions (such as an incident angle of radiation) in which a radiographic image is captured by the radiographic image capturing apparatus 10.

  Next, an example of a specific configuration of the radiation detector 42 capable of binning processing will be described. FIG. 5 is a diagram illustrating a first configuration example of the radiation detector 42.

  The radiation detector 42 receives radiation that has passed through the subject and outputs image information indicating a radiation image of the subject. As shown in FIG. 5, the radiation detector 42 accumulates in a scintillator (not shown) that emits light upon receiving radiation, a sensor unit S that generates light by receiving light generated by the scintillator, and the sensor unit S. A plurality of pixels 21 including two switching elements Tr1 and Tr2 for reading out the generated charges. Specific examples of the switching elements Tr1 and Tr2 include thin film transistors. Hereinafter, the switching element Tr1 is referred to as “transistor Tr1”, and the switching element Tr2 is referred to as “transistor Tr2”.

  The radiation detector 42 further includes a charge amplifier, an A / D (analog / digital) converter, a readout control IC (Integrated Circuit), etc., all of which are not shown. The radiation detector 42 according to the present embodiment is an indirect conversion type radiation detector that generates charges by irradiating the sensor unit S with light converted according to radiation by the scintillator, but is not limited thereto. . In the case of a direct conversion type radiation detector, a charge generation layer (for example, a layer whose main component is Se) that generates a charge upon receiving radiation and two switching elements that read out the charge accumulated in the charge generation layer are included. And a plurality of pixels 21.

  The plurality of pixels 21 are arranged in one direction (control wiring direction corresponding to the horizontal direction in FIG. 5, hereinafter referred to as “row direction”) and the cross direction with respect to the row direction (signal wiring direction corresponding to the vertical direction in FIG. 5). In a matrix). In FIG. 5, the arrangement of the pixels 21 is shown in a simplified manner. For example, 1024 × 1024 pixels 21 are arranged in the row direction and the column direction.

  The radiation detector 42 includes a plurality of control wirings G (G1 to G8 in FIG. 5), a plurality of control wirings M (M1 to M4 in FIG. 5), and a plurality of signal wirings D (in FIG. 5). D1 to D5) are provided so as to cross each other. The control wiring G is for controlling on / off of the transistor Tr1. The control wiring M is for controlling on / off of the transistor Tr2. The signal wiring D is provided for each column of the pixels 21 in order to read out the electric charge accumulated in the sensor unit S. The charge of each pixel 21 flowing from the signal wiring D becomes digital data (that is, an example of image information indicating a radiation image) through a charge amplifier, an A / D converter, etc. (not shown), and enters the image processing unit 45. Is output. A control signal flows through each control wiring G and M by a read control IC (not shown).

  The sensor unit S of each pixel 21 is provided with a semiconductor layer and a bias electrode that applies a bias voltage to the semiconductor layer. The bias electrode of each pixel 21 is connected to a common wiring (not shown). A bias voltage is applied from a power source (not shown) through the common wiring.

  A control signal for switching (ON / OFF) each transistor Tr1 flows through the control wiring G. When the control signal flows through each control line G, each transistor Tr1 is switched (ON / OFF). In addition, a control signal for switching (ON / OFF) each transistor Tr2 flows through the control wiring M. When the control signal flows through each control wiring M, each transistor Tr2 is switched (ON / OFF).

  In the signal wiring D, an electric power corresponding to the amount of electric charge accumulated in each pixel 21 according to the switching state (on / off state) of the transistor Tr1 of each pixel 21 and the switching state (on / off state) of the transistor Tr2. A signal flows through the transistor Tr1 or the transistor Tr2.

  In the present embodiment, as shown in FIG. 5, in the radiation detector 42, the arrangement relationship of the transistors Tr <b> 1, the transistor Tr <b> 2, and the sensor unit S is inverted between the even and odd lines of the control wiring G ( Inverted vertically in FIG.

  The radiographic image capturing apparatus 10 of the present embodiment can capture images with two different resolutions by the radiation detector 42 shown in FIG. In the present embodiment, the higher one of the two resolutions is called “high resolution”, and the lower one is called “low resolution”.

  That is, when high-resolution imaging is performed, a control signal for turning off the transistor Tr2 flows through the control wiring M. On the other hand, a control signal for turning on the transistor Tr1 sequentially flows through the control wiring G. In the pixel 21 in which the transistor Tr1 is on, the charge is read from the sensor unit S, and the charge of one pixel 21 is sequentially output to the signal wiring D.

  Further, when low-resolution imaging is performed, a control signal for turning off the transistor Tr1 flows through the control wiring G. On the other hand, a control signal for turning on the transistor Tr2 sequentially flows through the control wiring M. In the pixel 21 in which the transistor Tr2 is on, the charge from the sensor unit S is read and the charge is output to the signal wiring D. Accordingly, the charges output to one signal line D are output collectively from the charges of the four pixels 21, and the radiation having a lower resolution than the case where the transistor Tr2 is turned off and the transistor Tr1 is turned on through the subsequent processing. The image is finally obtained.

  Next, another configuration example of the radiation detector 42 capable of binning processing will be described. FIG. 6 is a diagram illustrating a second configuration example of the radiation detector 42.

  The radiation detector 42 shown in FIG. 6 has a pixel area except that a plurality of pixels 21 having a hexagonal shape are arranged in a two-dimensional honeycomb shape adjacent to each other to form a substantially rectangular area as a whole. This is the same as the configuration of the radiation detector 42 shown in FIG. Each pixel 21 receives the light converted by the scintillator, generates a charge, a charge storage capacitor 5 that stores the charge generated by the sensor unit 98, and reads the charge stored in the charge storage capacitor 5. 2 thin film transistors (hereinafter referred to as “transistors”) 4a and 4b.

  The arrangement of the pixels 21 in a honeycomb shape means that the first pixel rows and the second pixel rows are alternately arranged in a direction intersecting the column direction (vertical direction in FIG. 6), and the first Pixels 21 in two pixel rows are arranged corresponding to adjacent pixels in the first pixel row, and are shifted in the row direction by ½ of the arrangement pitch of the pixels 21 in the first pixel row. Is to be placed. In the first pixel row, a plurality of pixels 21 having a hexagonal pixel area and the same size are arranged in the row direction (horizontal direction in FIG. 6). In the second pixel row, a plurality of pixels 21 having the same size as the pixels 21 in the first pixel row and having a hexagonal pixel region are arranged in the row direction.

  The radiation detector 42 includes first control wirings G1-0 to G1-7 arranged corresponding to each pixel row. The first control wirings G1-0 to G1-7 are collectively referred to as “first control wiring G1”. In addition, the term “control line G” is used to collectively refer to other control lines described later. The gate electrode of the transistor 4a provided in each pixel 21 is connected to the first control wiring G1, and on / off of the transistor 4a is controlled in accordance with a control signal flowing through the first control wiring G1. Furthermore, the radiation detector 42 includes second control wirings G2-0 to G2-3 arranged corresponding to the respective pixel rows including the first control wirings G1-0 to G1-3, and a first control. And third control wirings G3-0 to G3-3 arranged corresponding to the respective pixel rows including the wirings G1-4 to G1-7. The second control wirings G2-0 to G2-3 are collectively referred to as “second control wiring G2”. The third control wirings G3-0 to G3-3 are collectively referred to as “third control wiring G3”. The gate electrode of the transistor 4b provided in the pixel 21 is connected to the second control wiring G2 and the third control wiring G3, and a control signal flowing through the second control wiring G2 and the third control wiring G3 is used. On / off of the transistor 4b is controlled.

  The radiation detector 42 includes a pixel row in which each of the first control wiring G1 and the second control wiring G2 is arranged, and each of the first control wiring G1 and the third control wiring G3. Many arranged pixel rows are arranged. Furthermore, the radiation detector 42 includes a plurality of signal wirings D1 to D6 that are generated in the sensor unit 103 in each pixel and are stored in the charge storage capacitor 5, and a common ground (common ground) wiring 31. Are provided. The signal wirings D1 to D6 are collectively referred to as “signal wiring D”. The charge of each pixel flowing from the signal wiring D becomes digital data (that is, an example of image information indicating a radiation image) through a charge amplifier, an A / D converter, etc. (not shown), and is sent to the image processing unit 45. It is done.

  Even when the radiation detector 42 shown in FIG. 6 is used, it is possible to perform imaging at two different resolutions (high resolution and low resolution).

  That is, when high-resolution imaging is performed, control for turning off the transistor 4b in each pixel 21 is applied to the second and third control wirings G2-0 to G2-3 and G3-0 to G3-3. A signal flows. Further, in order to turn on the transistor 4a in each pixel 21, a control signal is sequentially applied to each gate of the transistor 4a from the first control wirings G1-0 to G1-7. As a result, the transistors 4a in each pixel 21 in each pixel row are sequentially turned on, and charges are read from the sensor unit 98 via the transistors 4a. The charge of each pixel flowing from the signal wiring D becomes digital data (that is, an example of image information indicating a radiation image) through a charge amplifier, an A / D converter, etc. (not shown). Digital data of each pixel is sent to the image processing unit 45, and finally a high-resolution radiation image is obtained through image processing.

  As described above, in the radiation detector 42, the charge signal corresponding to each pixel 21 flows for each pixel row to each of the signal wirings D <b> 1 to D <b> 6 by acquiring high-resolution image information. Thereby, the image information which shows a radiographic image with the radiation irradiated to the radiation detector 42 can be obtained.

  On the other hand, when low-resolution imaging is performed, the second control wiring G2 and the third control wiring G3 are used. First, the relationship between the second control wiring G2 and the third control wiring G3 and each pixel 21 will be described. Among the plurality of pixels 21 shown in FIG. 6, for example, the four pixels P0 to P3 are the pixel group PG0, the four pixels P4 to P7 are the pixel group PG1, the four pixels P8 to P11 are the pixel group PG2, and the four pixels P12. ˜P15 is a pixel group PG3, and the four pixels P16 to P19 are a pixel group PG4. In these five pixel groups, the second control wiring G2-0 is connected to the gate electrodes of the transistors 4b of the pixel P0 of the pixel group PG0, the pixel P4 of the pixel group PG1, and the pixel P8 of the pixel group PG2. Has been. Further, the second control wiring G2-1 is connected to the gate electrodes of the transistors 4b of the pixels P1 to P3 of the pixel group PG0, the pixels P5 to P7 of the pixel group PG1, and the pixels P9 to P11 of the pixel group PG2. Yes.

  Similarly, the second control wiring G2-2 is connected to the gate electrodes of the transistors 4b of the pixel P12 of the pixel group PG3 and the pixel P16 of the pixel group PG4. A second control wiring G2-3 is connected to the gate electrodes of the pixels P13 to P15 of the pixel group PG3 and the pixels P17 to P19 of the pixel group PG4. Further, in the radiation detector 42, a pixel group (PG5 to PG9) each including pixels P20 to P23, pixels P24 to P27, pixels P28 to P31, pixels P32 to P35, and pixels P36 to P39, and a third Connections with the control lines G3-0 to G3-3 are the same as the connections between the pixel groups PG0 to PG4 and the second control lines G2-0 to G2-3.

  Next, the control of the transistors 4a and 4b when shooting at low resolution will be described. When a low-resolution imaging instruction is given to the radiation detector 42, each transistor 21a of each pixel 21 is turned off from the first control wiring G1-0 to G1-7 to turn off the transistor 4a of each pixel 21. A control signal is supplied to the gate electrode.

  Furthermore, a control signal for simultaneously turning on the corresponding transistors flows through the second control wirings G2-0 to G2-3. As a result, the transistors 4b of all the pixels 21 in the pixel groups PG0 to PG4 are turned on. Then, the charges accumulated in the charge accumulation capacitors 5 of the four pixels P0 to P3 of the pixel group PG0 are mixed, and the combined charge signal is output to the signal wiring D2. Similarly, the combined charge signal of the four pixels P12 to P15 of the pixel group PG3 is output to the signal wiring D3. Further, the combined charge signal of the four pixels P4 to P7 of the pixel group PG1 is output to the signal wiring D4. Further, the combined charge signal of the four pixels P16 to P19 of the pixel group PG4 is output to the signal wiring D5. Further, the combined charge signal of the four pixels P8 to P11 of the pixel group PG2 is output to the signal wiring D6.

  Next, control signals for simultaneously turning on the corresponding transistors flow through the third control wirings G3-0 to G3-3. Then, the transistors 4b of all the pixels 21 in the pixel groups PG5 to PG9 are turned on. As a result, the combined charge signal of the four pixels in the pixel group PG5 is output to the signal wiring D2. Further, the combined charge signal of the four pixels in the pixel group PG8 is output to the signal wiring D3. Further, the combined charge signal of the four pixels in the pixel group PG6 is output to the signal wiring D4. Further, the combined charge signal of the four pixels of the pixel group PG9 is output to the signal wiring D5. Further, the combined charge signal of the four pixels of the pixel group PG7 is output to the signal wiring D6.

  As described above, in the case of low-resolution imaging, for each of a plurality of pixel groups in which the four pixels 21 specified in advance among the plurality of pixels 21 provided in the radiation detector 42 are used as the pixel group 4 The charges accumulated in the individual pixels 21 are collected (binned), and the binned charges are output to the respective signal lines D. This means that image information can be acquired four times faster than high-resolution imaging by performing a 2 pixel × 2 pixel binning process in the radiation detector 42 for low-resolution imaging. To do.

  In the configuration examples of FIGS. 5 and 6, charge readout with different resolutions can be performed by switching a plurality of transistors to one pixel and switching between reading one pixel at a time or reading out a plurality of pixels collectively (binning processing). In other words, image information with different resolutions can be acquired. However, acquisition of image information with different resolutions (or acquisition of radiation images) is not limited to the above configuration example.

  For example, as another configuration example, there is a method in which an internal memory is provided in the radiation detector 42 and binning processing of 2 pixels × 2 pixels is performed in the internal memory. That is, the image information of all the pixels is once read into the internal memory, and in the case of high resolution, the image information (digital data) of each pixel is sent to the image processing unit 45 as it is, and in the case of low resolution, 2 × 2 pixels The operation of adding information (digital data) is performed in the internal memory and then sent to the image processing unit 45. In this case, the radiation detector 42 may be provided with one switching element for each pixel 21. Further, in the case of low resolution, a thinning process may be performed instead of the binning process in the internal memory of the radiation detector 42. When the thinning process is performed by the radiation detector 42, a method of reading only a part of the pixels 21 among the plurality of pixels 21, and reading out all the pixels 21, 2 pixels × 2 pixels in the internal memory of the radiation detector 42. There is a method of reading out only one pixel in the image processing unit 45 from among the pixel units. Further, the above-described pixel information addition (binning processing) and thinning-out processing may be performed in the image processing unit 45. In short, it is only necessary that the radiation image generation unit 41 has a function of generating radiation images having different resolutions.

  When performing binning processing or thinning-out processing by adding pixel information as in these other configuration examples, the radiation detector 42 is not limited to that shown in FIGS. 5 and 6, and a general radiation detector 42 is used. May be used. For example, the radiation detector 42 shown in FIG. 7 can be used for the first configuration example (see FIG. 5). The radiation detector 42 shown in FIG. 7 includes a plurality of pixels 21 arranged in a matrix including the sensor unit S and one transistor Tr, control wirings G1 to G4 corresponding to the first control wiring, and signal wiring D. , A common wiring 90, and a power source 92 for applying a bias voltage. In the radiation detector 42 shown in FIG. 7, imaging is performed in the same manner as in the case of performing high-resolution imaging in the radiation detector 42 shown in FIG.

  On the other hand, the radiation detector 42 shown in FIG. 8 can be used for the second configuration example (see FIG. 6). The radiation detector 42 illustrated in FIG. 8 includes a plurality of pixels 21 arranged in a honeycomb shape including the sensor unit 5 and one transistor 4, control wirings G1 to G4 corresponding to the first control wiring, and signal wiring D. Is provided. In the radiation detector 42 shown in FIG. 8, imaging is performed in the same manner as in the case of performing high-resolution imaging in the radiation detector 42 shown in FIG.

  By the way, in tomosynthesis imaging, a high-resolution tomographic image can be obtained as described above by increasing (widening) the incident angle range. On the other hand, since the incident angle range is widened, the imaging time is increased and the burden on the subject W is increased. Since the radiation irradiation unit 24 affects the entire time taken for imaging at different incident angles, the burden on the subject W increases as this time increases.

  Therefore, the control unit 46 according to the present embodiment captures a two-dimensional image before tomosynthesis imaging. In addition, the control unit 46 analyzes and detects the presence / absence of the region of interest from the obtained radiographic image by the region-of-interest detection unit 47. The control unit 46 determines imaging conditions for tomosynthesis imaging including the incident angle range based on the analysis result. The control unit 46 performs tomosynthesis imaging under the determined imaging conditions, so that tomosynthesis imaging can be performed under appropriate imaging conditions.

  Specifically, in the radiographic imaging device 10 of the present exemplary embodiment, the region-of-interest detection unit 47 of the control unit 46 converts a radiographic image obtained by capturing a two-dimensional image before tomosynthesis imaging to CAD (Computer Aided). The region of interest is detected by performing analysis using an analysis technique such as Diagnosis. Further, the control unit 46 determines imaging conditions for tomosynthesis imaging according to the presence / absence of a region of interest.

  For example, a technique described in Japanese Patent Application Laid-Open No. 2011-120747 is adopted for detection of a region of interest in the control unit 46 (region of interest detection unit 47). When detecting an abnormal shadow candidate (region of interest) in the breast based on a radiographic image obtained by imaging, a technique using an iris filter process or the like as described in the above publication (JP-A-10-97624) And a technique using a morphological filter (see also JP-A-8-294479) can detect an abnormal shadow candidate (region of interest). Needless to say, the techniques and techniques used for detecting the region of interest are not limited to these.

  In the present embodiment, when the region of interest is not detected by the control unit 46 (region of interest detection unit 47), the control unit 46 performs tomosynthesis imaging under the first condition in which the incident angle range is set to the small incident angle range. I do. On the other hand, when the region of interest is detected, the control unit 46 performs control to perform tomosynthesis imaging under the second condition in which the incident angle range is set to the large incident angle range. In the following, tomosynthesis imaging performed under the first condition is referred to as “first tomosynthesis imaging”, and tomosynthesis imaging performed under the second condition is referred to as “second tomosynthesis imaging”. When doing so, it is called “tomosynthesis photography”.

  In the present embodiment, the region-of-interest detection unit 47 of the control unit 46 is described as detecting the region of interest. However, for example, when the processing capability of the region-of-interest detection unit 47 of the control unit 46 is low, an image is displayed. The processing device 50 may be provided with the function of the region-of-interest detection unit 47. Of the imaging conditions for performing tomosynthesis imaging in the present embodiment, the exposure condition determination method may be as follows, for example. That is, the control unit 46 analyzes the density of the two-dimensional image captured prior to tomosynthesis imaging. Then, a single irradiation dose in tomosynthesis imaging may be determined as an irradiation dose in which the shade of the projection image obtained by tomosynthesis imaging falls within a predetermined range.

  Next, the operation in the radiation image capturing system 6 will be described. FIG. 9 is a flowchart illustrating an example of a process flow (radiation image capturing method) performed by the control unit 46 in the radiation image capturing system 6 according to the present embodiment.

  First, the user brings the breast N of the subject W into contact with the imaging surface 20 of the radiographic imaging device 10. When an operation instruction to start compression is given from the user in this state, the control unit 46 of the radiographic image capturing apparatus 10 moves the compression plate 26 toward the imaging surface 20 and compresses the breast N in step S100.

  Subsequently, in step S102, the control unit 46 performs first imaging for acquiring a two-dimensional image (radiation image) of the breast N prior to tomosynthesis imaging described later. The first imaging is performed with the radiation irradiation unit 24 at a predetermined incident angle with respect to the breast N. Specifically, the radiation determined according to the thickness of the breast N detected by the radiographic imaging device 10 in a state where the radiation irradiation unit 24 is in a vertical position (the center position in FIG. 2) with respect to the imaging table 22. The breast N is imaged by the amount. Generally, as the thickness of the breast N increases, the dose of radiation that reaches the radiation detector 42 (transmits through the breast N) decreases. Therefore, in the radiographic imaging apparatus 10 of the present embodiment, the correspondence relationship between the predetermined incident angle, the thickness of the breast N, and the radiation dose to be irradiated is stored in the memory 43B in the control unit 46 in advance. The image processing unit 45 performs necessary processing such as gain correction, offset correction, and defective pixel correction on the image information of the breast N obtained from the radiation detector 42 to generate a radiation image of the breast N. Note that, for example, a RAW format (Raw image format) is applied as the format of the radiation image generated here. Based on the first imaging result, imaging conditions for tomosynthesis imaging to be performed later are determined.

  In the next step S104, the region-of-interest detection unit 47 of the control unit 46 analyzes the radiation image generated by the image processing unit 45 as described above, and detects the region of interest.

  In the next step 106, the region-of-interest detection unit 47 of the control unit 46 determines whether or not there is a region of interest (is detected). If a region of interest is detected, the process proceeds to step S108. On the other hand, if the region of interest is not detected, the process proceeds to step S110.

  In step S108, the control unit 46 sets a high resolution and a large incident angle range as imaging conditions for tomosynthesis imaging. That is, the control unit 46 performs control so that the radiation detector 42 does not perform binning processing and sets the incident angle range in acquiring the projection image of the breast N to the large incident angle range. Thus, when a region of interest is detected, tomosynthesis imaging with high resolution and a large incident angle range can be performed to obtain a projection image and a high-resolution tomographic image necessary for observation of the region of interest. It becomes possible. After the control unit 46 sets the tomosynthesis imaging conditions, the process proceeds to step S112.

  On the other hand, in step S110, the control unit 46 sets a low-resolution and small incident angle range as the imaging condition for tomosynthesis imaging. Specifically, the control unit 46 controls the radiation detector 42 to perform a binning process and set the incident angle range in acquiring a projection image of the breast N to a small incident angle range. By shooting at low resolution, processing time such as image processing is shortened compared to shooting at high resolution. By capturing an incident angle range when performing tomosynthesis imaging within a small incident angle range, imaging time is shortened compared to when capturing within a large incident angle range. Therefore, when the region of interest is not detected, it is possible to perform imaging while reducing the burden on the subject W due to the compression of the breast N. After the control unit 46 sets the tomosynthesis imaging conditions, the process proceeds to step S112.

  In step S112, the radiographic imaging device 10 performs tomosynthesis imaging according to the set imaging conditions for tomosynthesis imaging. That is, the radiographic image capturing apparatus 10 starts tomosynthesis imaging by moving the support unit 29 to the maximum angle of the set incident angle range, for example, by performing imaging while moving the support unit 29 one by one. A plurality of projection images corresponding to the incident angle range is taken. The radiographic image capturing at each position will be described in detail. The image processing unit 45 performs gain correction, offset correction, defective pixel correction, and the like on the image information obtained by the radiation detector 42 in which the presence or absence of binning processing is set. The radiation image (projection image) of the RAW format or the like is generated by performing the necessary processing. When tomosynthesis imaging is completed, the process proceeds to step S114.

  In step S114, the control unit 46 releases the fixation of the breast N by the compression plate 26. The fixation of the breast N is released, for example, by moving the compression plate 26 away from the imaging surface 20.

  In next step S <b> 116, the control unit 46 outputs the captured radiation image to the image processing apparatus 50.

  In the next step S118, the tomographic image generation unit 68 of the image processing apparatus 50 performs the above-described image processing such as the FBP method based on the projection image output by the control unit 46, and generates a tomographic image. Note that the tomographic image generation unit 68 of the present embodiment generates a low-resolution and low-resolution tomographic image when the region of interest is not detected and the first tomosynthesis imaging is performed. In addition, the tomographic image generation unit 68 has a high resolution and a high resolution (a higher resolution than the tomographic image obtained by the first tomosynthesis imaging) when the region of interest is detected and the second tomosynthesis imaging is performed. Is generated. In the present embodiment, the tomographic image generation unit 68 does not particularly process the resolution of the tomographic image. Therefore, the resolution of the generated tomographic image is the same as that of the projection image (of the radiation detector 42). ) Depends on resolution. Specifically, if errors and the like are ignored, the resolution when the projection image is captured and the resolution of the tomographic image generated by the tomographic image generation unit 68 are the same.

  Note that the slice thickness of the tomographic image generated by the tomographic image generation unit 68 is not particularly limited, and an initial value stored in the storage unit 74, the RAM 56, or the like may be used, or the user may use the instruction input unit 84 or the like. The value indicated by may be used.

  In the next step S120, the image display instruction unit 62 displays the generated tomographic image on the display 82 of the display device 80, and then the present process is terminated.

  10A and 10B show specific examples of tomographic images displayed on the display 82. FIG. FIG. 10A shows a specific example of a high-resolution and high-resolution tomographic image obtained by the second tomosynthesis imaging. Although FIG. 10A shows a tomographic image including a region of interest image, the tomographic image does not include a region of interest depending on the position (height) of the tomography. FIG. 10B shows a specific example of a low-resolution and low-resolution tomographic image obtained by the first tomosynthesis imaging.

  Note that the display method of the tomographic image by the image display instruction unit 62 is not particularly limited, and may be sequentially displayed on the display 82 in the height (depth) direction, or when the region of interest is detected, You may display the tomographic image containing a site | part first. A plurality of tomographic images (tomographic images having different positions in the height direction of the same subject) may be displayed side by side. In addition, the user may instruct how to display the information using the instruction input unit 84.

  As described above, the radiographic image capturing apparatus 10 can perform two-dimensional image capturing, detection of a region of interest, setting of an imaging condition according to the detection result, and tomosynthesis imaging with only one compression of the breast N. Intelligent device.

  In the radiographic image capturing apparatus 10, a region of interest is detected by the region-of-interest detection unit 47 from a radiographic image captured before tomosynthesis imaging (that is, a two-dimensional image of the breast N obtained by the first imaging), and the detection result Based on the above, the photographing conditions are determined and tomosynthesis photographing is performed. If the region of interest is not detected, the binning process is performed and the first tomosynthesis imaging is performed with the radiation incident angle range set to the small incident angle range. Further, the tomographic image generation unit 68 of the image processing device 50 generates a low-resolution and low-resolution tomographic image from the captured projection image, and the image display instruction unit 62 displays the tomographic image on the display device 80. Since the radiographic image capturing apparatus 10 performs binning processing and captures images at a low resolution, the processing time for image processing and the like can be shortened compared to capturing at a high resolution. Since the incident angle range is small (narrow), the time required for imaging can be shortened, and the burden on the subject W can be reduced.

  On the other hand, when the region of interest is detected, the second tomosynthesis imaging is performed without performing the binning process and setting the radiation incident angle range to the large incident angle range. Further, the tomographic image generation unit 68 of the image processing device 50 generates a high-resolution and high-resolution tomographic image from the captured projection image, and causes the display device 80 to display the tomographic image by the image display instruction unit 62. Since the radiographic image capturing apparatus 10 displays a high-resolution and high-resolution tomographic image, the user can obtain an accurate radiographic image for observing the region of interest.

[Second Embodiment]
Next, a second embodiment will be described. In addition, the same code | symbol is attached | subjected about the part similar to the radiographic imaging system 6 which concerns on 1st Embodiment, and detailed description is abbreviate | omitted. In the radiographic imaging system 6 of the present embodiment, the generation and display of tomographic images are different from those of the first embodiment.

  Since the configuration of the radiographic image capturing system 6 is the same as that of the radiographic image capturing system 6 (see FIGS. 1 to 8) of the first embodiment, the description thereof is omitted.

  An operation in the radiographic image capturing system 6 of the present embodiment will be described. FIG. 11 is a flowchart illustrating an example of a process flow (radiation image capturing method) performed in the radiation image capturing system 6 according to the present embodiment.

  Since the process of each step of step S100 to S116 is the same as the process (refer FIG. 9) performed by the control part 46 of 1st Embodiment, detailed description is abbreviate | omitted.

  When an operation instruction to start compression is given from the user, the control unit 46 compresses the breast N with the compression plate 26 in step S100. In the next step S102, the control unit 46 images the breast N with a dose according to the thickness of the breast N, and acquires a two-dimensional image. In the next step S104, the region-of-interest detection unit 47 of the control unit 46 analyzes the radiation image generated by the image processing unit 45 and detects the region of interest. In the next step 106, the region-of-interest detection unit 47 of the control unit 46 determines whether or not there is a region of interest (is detected). When the region of interest is detected, the process proceeds to step S108, and the control unit 46 sets the binning processing non-execution and the large incident angle range as imaging conditions for tomosynthesis imaging. On the other hand, if the region of interest is not detected, the process proceeds to step S110, and the control unit 46 sets the binning process and the small incident angle range as imaging conditions for tomosynthesis imaging. When shooting conditions are set in step S108 or S110, the process proceeds to step S112. In step S112, the radiographic imaging device 10 performs tomosynthesis imaging according to the set imaging conditions. When the tomosynthesis imaging is completed, the control unit 46 releases the fixation of the breast N in the next step S114. In next step S <b> 116, the control unit 46 outputs the captured radiation image to the image processing apparatus 50.

  In the radiographic imaging system 6 of this Embodiment, it progresses to step S120 after step S116. In step S120, the tomographic image generation unit 68 of the image processing apparatus 50 determines whether tomosynthesis imaging of the left and right breasts N of the same subject W is performed. When only tomosynthesis imaging of one of the breasts N has been performed, the process returns to step S100, and the processing of steps S100 to S116 is repeated to perform tomosynthesis imaging of the other breast N that has not been imaged. On the other hand, if tomosynthesis imaging is performed on both the left and right breasts N, the process proceeds to step S122.

  In step S122, the tomographic image generation unit 68 of the image processing apparatus 50 determines whether a region of interest has been detected. If no region of interest is detected in both the left and right breasts N by the process in step S104, the process proceeds to step S124.

  In step S124, the tomographic image generation unit 68 performs image processing such as the FBP method described above based on the projection image output from the control unit 46, and generates a tomographic image. The tomographic image generation unit 68 generates low-resolution and low-resolution tomographic images for both the left and right breasts N because the first tomosynthesis imaging was performed without detecting the region of interest.

  In the next step S126, the image display instruction unit 62 displays the generated tomographic images of the left and right breasts N on the display 82 of the display device 80. FIG. 12 shows a specific example of a low-resolution and low-resolution tomographic image displayed on the display 82 when the region of interest is not detected for both the left and right breasts N. The tomographic image display method may be the same as in step S120 of the first embodiment. When displaying tomographic images of the left and right breasts N, it is preferable to align the left and right heights (positions in the depth direction).

  In the next step S128, the image display instruction unit 62 inputs a button 99A, which is an example of the second mark of the disclosed technique, and a button 99B, which is an example of the first mark of the disclosed technique, to the display device 80. Displayed on the unit 84. In the present embodiment, since the display 82 and the instruction input unit 84 are shared, the button 99A and the button 99B are substantially displayed on the display 82 together with the tomographic image.

  In the present embodiment, the button 99A displayed on the display 82 together with the tomographic image indicates whether or not the resolution of the displayed tomographic image can be switched, and the resolution of the displayed tomographic image is high. It has a function of displaying two types of information indicating which of the low resolutions. When the button 99A is in the active state, it means that the resolution of the displayed tomographic image can be switched. Further, when the button 99A is in an inactive state, it means that it is impossible to switch the resolution of the displayed tomographic image. The button 99B has two types of information indicating whether the resolution of the displayed tomographic image can be switched and whether the resolution of the displayed tomographic image is high resolution or low resolution. It has a function to display. When the button 99B is in the active state, it means that the resolution of the displayed tomographic image can be switched. Further, when the button 99B is in an inactive state, it means that the resolution of the displayed tomographic image cannot be switched. The buttons 99A and 99B are collectively referred to as “button 99”.

  When the button 99 is in an inactive state, the radiographic imaging system 6 does not react particularly even when the user operates the button 99. In the present embodiment, the color of the button 99 represents the level of resolution or the level of resolution of the displayed tomographic image. In the present embodiment, the thickness of the line of the button 99 indicates whether the button 99 is in an active state or an inactive state. For example, a thick button 99 line represents an active state, and a thin button 99 line represents an inactive state. Note that the method of displaying two types of information using the button 99 is not limited to the present embodiment, and the button 99 may be displayed by appropriately combining the size of the button 99, blinking, and color shading. For example, the color of the button 99 may indicate the resolution, and the color shading may indicate the active or inactive state. In the present embodiment, two types of information are displayed by one button 99, but the buttons to be displayed may be different for each information.

  The button 99A for each of the left and right breasts N displayed on the instruction input unit 84 in step S128 represents that the button 99A is in an inactive state and has a low resolution. Both buttons 99B indicate an inactive state and low resolution.

  In the next step S130, the image display instruction unit 62 determines whether or not to end this process. In both the left and right breasts N, when no region of interest is detected, since both are low-resolution and low-resolution tomographic images, switching of tomographic images is not performed. Therefore, when this process is not terminated, the process enters a standby state and continues to display the tomographic image and the button 99. On the other hand, when the user gives an instruction for termination using the instruction input unit 84, the present process is terminated.

  On the other hand, if a region of interest is detected in both the left and right breasts N in step S122, the process proceeds to step S132.

  In step S132, the tomographic image generation unit 68 performs image processing such as the FBP method described above based on the projection image output from the control unit 46, and generates a tomographic image. The tomographic image generation unit 68 generates a high-resolution and high-resolution tomographic image for both the left and right breasts N because the region of interest has been detected and the second tomosynthesis imaging has been performed.

  In the next step S 134, the image display instruction unit 62 displays the generated tomographic images of the left and right breasts N on the display 82 of the display device 80. FIG. 13 shows a specific example of a tomographic image displayed on the display 82 when a region of interest is detected for both the left and right breasts N. In the initial state, the tomographic image shown in FIG. 13A is displayed. The tomographic image display method may be the same as in step S126.

  In the next step S136, the image display instruction unit 62 causes the button 99 to be displayed on the instruction input unit 84 of the display device 80. A button 99A for each of the left and right breasts N displayed on the instruction input unit 84 represents that the button is active and has high resolution. Both buttons 99B indicate an inactive state and high resolution.

  In the next step S138, the instruction receiving unit 64 determines whether or not there is a switching instruction. If there is no switching instruction, the process proceeds to step S144. On the other hand, if a switching instruction is given by the user operating button 99A, the process proceeds to step S140. In step S140, the tomographic image generation unit 68 generates a tomographic image with a resolution corresponding to the switching instruction. As described above, the low-resolution tomographic image generation method by the tomographic image generation unit 68 may be binning processing or thinning-out processing. Note that the “low resolution” in this case is the same or approximately the same resolution as the low-resolution projection image captured by the radiation detector 42. In addition, when switching to high resolution is instructed, the tomographic image generation unit 68 selects a tomographic image whose position in the height (depth) direction coincides from already generated high resolution tomographic images. Just choose.

  In the next step S142, the image display instruction unit 62 displays the generated tomographic image and the corresponding button 99 on the display 82, and then proceeds to step S144. FIG. 13B shows a case where the resolution of the tomographic image of the left breast N is switched from the initial state (see FIG. 13A). FIG. 13 (3) shows a case where the resolution of the tomographic image of the left and right breasts N is switched from the initial state (see FIG. 13 (1)). FIG. 13 (4) shows a case where the resolution of the tomographic image of the right breast N is switched from the initial state (see FIG. 13 (1)).

  In step S144, the image display instruction unit 62 determines whether or not to end this process. If the present process is not terminated, the process returns to step S138 and the present process is repeated. On the other hand, when the user gives an instruction for termination using the instruction input unit 84, the present process is terminated.

  On the other hand, if a region of interest is detected in either one of the left and right breasts N in step S122, the processes in steps S200 to S216 shown in FIG. 14 are performed.

  In step S200, the tomographic image generation unit 68 performs image processing such as the FBP method described above based on the projection image output from the control unit 46, and generates a tomographic image. Note that since the first tomosynthesis imaging has been performed for the breast N from which the region of interest has not been detected, the tomographic image generation unit 68 generates only a low-resolution and low-resolution tomographic image. On the other hand, since the second tomosynthesis imaging was performed on the breast N from which the region of interest was detected, the tomographic image generation unit 68 has a high-resolution and high-resolution tomographic image and a high-resolution and low-resolution tomographic image. And generate both. In the case of generating a low-resolution tomographic image, a projection image in a small incident angle range may be selected from the projection image obtained by the second tomosynthesis imaging, and the tomographic image may be generated by the selected projection image.

  In the next step S <b> 202, the image display instruction unit 62 displays the generated tomographic images of the left and right breasts N on the display 82 of the display device 80. FIG. 15 shows a specific example of a tomographic image displayed on the display 82 when a region of interest is detected on one side (specifically, the right breast N). In the present embodiment, the tomographic image shown in FIG. 15A is displayed as the initial state. The breast N in which the region of interest has not been detected (left in FIG. 15) displays a low-resolution and low-resolution tomographic image. Further, the breast N from which the region of interest is detected (right in FIG. 15) displays a high-resolution and low-resolution tomographic image.

  In the next step S204, the image display instruction unit 62 displays the button 99 on the instruction input unit 84 of the display device 80. As shown in FIG. 15A, the button 99A for the left breast N displayed on the instruction input unit 84 in the initial state represents an inactive state and a low resolution. The button 99B represents an inactive state and low resolution. On the other hand, the button 99A for the right breast N represents an active state and high resolution. The button 99B represents an active state and low resolution.

  Since the button 99 for the right breast N represents the active state, the user can recognize that the resolution and resolution of the tomographic image can be switched. Therefore, when it is desired to perform switching, the user issues a switching instruction using the button 99. In the display device 80 of the present embodiment, since the instruction input unit 84 is a touch panel and is shared with the display 82, the user instructs (touch operation) the button 99 itself (screen of the display 82). Not limited to this. For example, only the two types of information described above may be performed on the button 99, and the user may perform a switching instruction from an instruction input unit 84 such as a keyboard provided separately from the display 82. For example, when the user wants to observe a region of interest or the like and wants to observe a high-resolution tomographic image, the user gives a switching instruction.

  In the next step S206, the instruction receiving unit 64 determines whether or not there is a switching instruction. If there is no switching instruction, the process proceeds to step S216. On the other hand, if a switching instruction is given by the user operating button 99A or button 99B, the process proceeds to step S208. In step S208, the instruction receiving unit 64 determines whether or not the switching instruction is resolution switching. If the resolution is switched, the process proceeds to step S210. In this case, since both the high-resolution and low-resolution tomographic images have already been generated, the tomographic image generation unit 68 determines the position in the height (depth) direction from the already generated high-resolution tomographic images. Select a matching tomographic image. Then, after displaying the selected tomographic image and the button 99 corresponding to the tomographic image on the display 82, the process proceeds to step S216.

  On the other hand, if the switching instruction is not resolution, the process proceeds to step S212. In this case, since switching of the resolution has been instructed, the tomographic image generation unit 68 generates a tomographic image with a resolution corresponding to the instruction. The generation method of the low-resolution tomographic image by the tomographic image generation unit 68 may be the same as that in step S140, for example.

  In the next step S214, the image display instruction unit 62 displays the generated tomographic image and the corresponding button 99 on the display 82, and then proceeds to step S216. FIG. 15 (2) shows a case where the resolution of the tomographic image of the right breast N is switched from the initial state (see FIG. 15 (1)). FIG. 15 (3) shows a case where the resolution of the tomographic image of the right breast N is switched from the initial state (see FIG. 15 (1)). FIG. 15 (4) shows a case where the resolution and resolution of the tomographic image of the right breast N are switched from the initial state (see FIG. 15 (1)).

  In step S216, the image display instruction unit 62 determines whether or not to end this process. If this process is not terminated, the process returns to step S216 to repeat this process. On the other hand, when the user gives an instruction for termination using the instruction input unit 84, the present process is terminated.

  As described above, in the radiographic image capturing apparatus 10 according to the present embodiment, the site-of-interest detection unit 47 determines the site of interest from the radiographic image (two-dimensional image), similarly to the radiographic image capture apparatus 10 according to the first embodiment. If the region of interest is detected and the region of interest is not detected, the binning process is performed, and the incident angle range of the radiation is set as the small incident angle range. When a region of interest is detected, the binning process is not performed, and the radiation incident angle range is set as the large incident angle range, and tomosynthesis imaging is performed.

  Accordingly, the radiographic image capturing apparatus 10 of the present embodiment can obtain an accurate radiographic image while reducing the burden on the subject W, similarly to the radiographic image capturing apparatus 10 of the first exemplary embodiment. .

  In the radiographic imaging system 6 of the present embodiment, when a region of interest is detected in both the left and right breasts N, a high-resolution tomographic image is generated and displayed for both the left and right breasts N, If no region of interest is detected in both breasts N, a low-resolution tomographic image is generated and displayed for both the left and right breasts N. When a region of interest is detected in one of the left and right breasts N, a low-resolution and high-resolution tomographic image of one breast N in which the region of interest is detected is generated, and the other region in which the region of interest is not detected is generated. A low-resolution tomographic image of the breast N is generated, and low-resolution tomographic images of the left and right breasts N are displayed.

  In tomosynthesis imaging of the breast N, the user may want to compare tomographic images of the left and right breasts N. If the resolution of the tomographic image is different, the image quality and the appearance of the image may be different.

  In the radiographic imaging system 6 according to the present embodiment, the tomographic images of the left and right breasts N can be displayed with the same resolution, so that the left and right breasts N can be easily compared.

  Further, in the radiographic imaging system 6 of the present embodiment, whether or not the display can be switched to a tomographic image having a different resolution and whether the displayed tomographic image is a high resolution or a low resolution. The representing button 99A is displayed on the display 82 of the display device 80 together with the tomographic image. In addition, the display of the display device 80 includes a button 99B indicating whether the display can be switched to a tomographic image having a different resolution and whether the displayed tomographic image is high resolution or low resolution together with the tomographic image. 82 is displayed.

  When a region of interest is detected, the user may want to observe the region of interest using a high-resolution tomographic image. In the radiographic imaging system 6 of the present embodiment, the display is switched to a high-resolution tomographic image in accordance with an instruction input from the user in response to the button 99, so that a tomographic image suitable for observation of a region of interest is displayed. It can be performed.

  As described above, in the radiographic imaging system 6 of the present embodiment, the left and right breasts N can be easily compared, and the resolution and resolution of the tomographic image in which the region of interest is detected can be switched as desired by the user. it can.

  Further, in the radiographic imaging system 6 of the present embodiment, when the region of interest is detected, the button 99 is in an active state, so that the user recognizes whether or not the region of interest has been detected by the button 99. Can be made. For example, in the case where a tomographic image having no region of interest image (position where there is no region of interest) is displayed, the user can easily recognize whether or not the region of interest has been detected in the breast N.

[Third Embodiment]
Next, a third embodiment will be described. In addition, about the part similar to the radiographic imaging system 6 which concerns on said each embodiment, the same code | symbol is attached | subjected and detailed description is abbreviate | omitted. In the radiographic image capturing system 6 of the present embodiment, the processing (Steps S200 to S216, see FIG. 14) in the case where a region of interest is detected in one breast N in the third embodiment is different.

  Therefore, here, processing when a region of interest is detected in one breast N will be described. FIG. 16 is a flowchart showing an example of the flow of processing when a region of interest is detected in one breast N performed by the radiographic imaging system 6 according to the present embodiment.

  In the present embodiment, steps S201 to S205 are provided instead of steps S200 to S204 (see FIG. 14) of the processing performed by the image processing apparatus 50 of the second embodiment.

  In step S201, the tomographic image generation unit 68 performs image processing such as the FBP method described above based on the projection image output by the control unit 46, and generates a tomographic image. Note that since the first tomosynthesis imaging has been performed for the breast N from which the region of interest has not been detected, the tomographic image generation unit 68 generates only a low-resolution and low-resolution tomographic image. On the other hand, since the second tomosynthesis imaging was performed on the breast N from which the region of interest was detected, the tomographic image generation unit 68 has a high-resolution and high-resolution tomographic image and a high-resolution and low-resolution tomographic image. And three types of tomographic images of lower resolution and lower resolution. In the case of generating a low-resolution tomographic image, a projection image in a small incident angle range may be selected from the projection image obtained by the second tomosynthesis imaging, and the tomographic image may be generated by the selected projection image.

  In the next step S <b> 203, the image display instruction unit 62 displays the generated tomographic images of the left and right breasts N on the display 82 of the display device 80. FIG. 17 shows a specific example of a tomographic image displayed on the display 82 when a region of interest is detected on one side (specifically, the right breast N). In the present embodiment, the tomographic image shown in FIG. 17A is displayed as the initial state. Both the left and right breasts N display low-resolution and low-resolution tomographic images.

  In the next step S205, the image display instruction unit 62 displays the button 99 on the instruction input unit 84 of the display device 80. As shown in FIG. 17A, the button 99A for the left breast N displayed on the instruction input unit 84 in the initial state represents an inactive state and a low resolution. The button 99B represents an inactive state and low resolution. On the other hand, the button 99A for the right breast N represents an active state and low resolution. The button 99B represents an active state and low resolution.

  Since the button 99 for the right breast N represents the active state, the user can recognize that the resolution and resolution of the tomographic image can be switched.

  Since the processing of the next steps S206 to S216 is the same as the processing performed by the image processing apparatus 50 of the second embodiment, detailed description thereof is omitted.

  As described above, in the radiographic imaging system 6 of the present embodiment, when a region of interest is detected in one breast N, as a default, both the left and right breasts N have low resolution and low resolution tomographic images. Is displayed.

  Thereby, in the radiographic imaging system 6 of this Embodiment, since the tomographic image with which both the resolution and the resolution were equal is displayed, it can make it easy to perform right-and-left comparison.

[Fourth Embodiment]
Next, a fourth embodiment will be described. In addition, the same code | symbol is attached | subjected about the part similar to the radiographic imaging system 6 which concerns on 1st Embodiment, and detailed description is abbreviate | omitted. In the radiographic image capturing system 6 of the present embodiment, the processing when a region of interest is detected from both the left and right breasts N is different from the second and third embodiments.

  Since the configuration of the radiographic image capturing system 6 is the same as that of the radiographic image capturing system 6 (see FIGS. 1 to 8) of the first embodiment, the description thereof is omitted.

  An operation in the radiographic image capturing system 6 of the present embodiment will be described. In the radiographic image capturing system 6 of the present embodiment, the processing when a region of interest is detected from both the left and right breasts N is different from the second and third embodiments. Therefore, a process when a region of interest is detected from both the left and right breasts N will be described.

  FIG. 18 is a flowchart showing an example of the flow of processing when a region of interest is detected from both the left and right breasts N performed by the radiographic image capturing system 6 according to the present embodiment.

  In the present embodiment, steps S402 to S416 are provided instead of steps S132 to S142 (see FIG. 11) of the processing performed by the image processing apparatus 50 of the second embodiment. The other processes are the same as the processes (see FIG. 11) performed by the image processing apparatus 50 according to the second embodiment, and a description thereof will be omitted.

  In the present embodiment, when the region of interest is detected in both the left and right breasts N in step S122, the process proceeds to step S402.

  In step S402, the tomographic image generation unit 68 performs image processing such as the FBP method described above based on the projection image, and generates a tomographic image. Note that since the region of interest is detected for both the left and right breasts N and the second tomosynthesis imaging is performed, the tomographic image generation unit 68 generates a high-resolution and high-resolution tomographic image for both the left and right breasts N and a low resolution. A low-resolution tomographic image and two types of tomographic images are generated. In the case of generating a low-resolution tomographic image, a projection image in a small incident angle range may be selected from the projection image obtained by the second tomosynthesis imaging, and the tomographic image may be generated by the selected projection image.

  In the next step S <b> 404, the image display instruction unit 62 displays the generated low-resolution and low-resolution tomographic images of the left and right breasts N on the display 82 of the display device 80. FIG. 19 shows a specific example of a tomographic image displayed on the display 82 when a region of interest is detected in the left and right breasts N. FIG. 19A shows a case where a low-resolution and low-resolution tomographic image is displayed on both the left and right breast N images. In the present embodiment, in the initial state, both the left and right breast N images are displayed with low resolution and low resolution tomographic images.

  In next step S <b> 406, the image display instruction unit 62 displays the button 99 on the instruction input unit 84 of the display device 80. The buttons 99A for the left and right breasts N displayed on the instruction input unit 84 both indicate an active state and a low resolution. Further, the buttons 99B for the left and right breasts N both indicate an active state and low resolution. Since the button 99 represents the active state, the user can recognize that the resolution of the tomographic image can be switched. Therefore, when switching is desired, the user issues a switching instruction using the button 99.

  In the next step S <b> 408, the instruction receiving unit 64 determines whether or not there has been a switching instruction from the instruction input unit 84. If there is no switching instruction, the process proceeds to step S416. On the other hand, if there is a switching instruction, the process proceeds to step S410.

  In step S <b> 410, the image display instruction unit 62 displays a high-resolution and high-resolution tomographic image of the left and right breasts N on the display 82 of the display device 80. FIG. 19 (2) shows a case where a high-resolution and high-resolution tomographic image is displayed on both the left and right breast N images.

  In the next step S <b> 412, the image display instruction unit 62 displays the button 99 on the instruction input unit 84 of the display device 80. The buttons 99A for the left and right breasts N displayed on the instruction input unit 84 both indicate an active state and high resolution. Further, the buttons 99B for the left and right breasts N both indicate an active state and high resolution. Since the button 99 represents the active state, the user can recognize that the resolution of the tomographic image can be switched.

  In the next step S414, the instruction receiving unit 64 determines whether the instruction input unit 84 has received a switching instruction. If there is no switching instruction, the process proceeds to step S416. On the other hand, if there is a switching instruction, the process returns to step S404 and the above processing is repeated.

  In step S416, the image display instruction unit 62 determines whether or not to end this process. If this process is not terminated, the process returns to step S2414, enters a standby state, and continues to display the tomographic image and the button 99. On the other hand, when the user gives an instruction for termination using the instruction input unit 84, the present process is terminated.

  Further, FIG. 19 shows a case where a tomographic image including a region-of-interest image is displayed for both the left and right breasts N, but the tomographic image to be displayed is not limited to this. In the case where the position of the region of interest in the left and right breasts N is different, one of them may be a tomographic image including the image of the region of interest, and the other may be a tomographic image at the same position as the position of one depth direction. .

  As described above, in the radiographic image capturing apparatus 10 according to the present embodiment, the site-of-interest detection unit 47 determines the site of interest from the radiographic image (two-dimensional image), similarly to the radiographic image capture apparatus 10 according to the first embodiment. If the region of interest is detected and the region of interest is not detected, the binning process is performed, and the incident angle range of the radiation is set as the small incident angle range. When a region of interest is detected, the binning process is not performed, and the radiation incident angle range is set as the large incident angle range, and tomosynthesis imaging is performed.

  Accordingly, the radiographic image capturing apparatus 10 of the present embodiment can obtain an accurate radiographic image while reducing the burden on the subject W, similarly to the radiographic image capturing apparatus 10 of the first exemplary embodiment. .

  Further, in the radiographic imaging system 6 of the present embodiment, when a region of interest is detected in both the left and right breasts N, both the left and right breasts N have low resolution and low resolution tomographic images, and high resolution and high levels. A resolution tomographic image is generated, and low-resolution tomographic images of the left and right breasts N are displayed.

  In the radiographic imaging system 6 of this embodiment, first, low-resolution tomographic images of the left and right breasts N are displayed regardless of the detection of the region of interest. Therefore, like the radiographic image capturing system 6 of the second embodiment, the radiographic image capturing system 6 of the present exemplary embodiment can easily compare the left and right breasts N.

  In the radiographic imaging system 6 of the present embodiment, the button 99A and the button 99B are used as one button 99C in order to switch tomographic images between two types of low resolution and low resolution and high resolution and high resolution. Also good. FIG. 20 shows a specific example in which the resolution and the resolution are displayed with one button. In the case shown in FIG. 20, since only one button 99C has to be provided, it is possible to simplify the user's trouble of giving instructions.

[Fifth Embodiment]
Next, a fifth embodiment will be described. In addition, about the part similar to the radiographic imaging system 6 which concerns on said each embodiment, the same code | symbol is attached | subjected and detailed description is abbreviate | omitted. The radiographic image capturing system 6 according to the present exemplary embodiment is different from the first exemplary embodiment in that a recommended display for recommending whether to perform the first tomosynthesis image capturing or the second tomosynthesis image capturing is performed for the user. Different.

  Since the configuration of the radiographic image capturing system 6 is the same as that of the radiographic image capturing system 6 (see FIGS. 1 to 8) of the first embodiment, the description thereof is omitted.

  An operation in the radiographic image capturing system 6 of the present embodiment will be described. FIG. 21 is a flowchart showing an example of a process flow (radiation image capturing method) performed in the radiation image capturing system 6 according to the present embodiment.

  In the process performed by the control unit 46 of the present embodiment, steps S107 to S111 are provided instead of steps S108 and S110 (see FIG. 9) of the process performed by the control unit 46 of the first embodiment. Yes.

  Since the process of each step of step S100 to S106 is the same as the process (refer FIG. 9) performed by the control part 46 of 1st Embodiment, detailed description is abbreviate | omitted.

  When an operation instruction to start compression is given from the user, the control unit 46 compresses the breast N with the compression plate 26 in step S100. In the next step S102, the control unit 46 images the breast N with a dose according to the thickness of the breast N, and acquires a two-dimensional image. In the next step S104, the region-of-interest detection unit 47 analyzes the radiation image generated by the image processing unit 45 and detects the region of interest. In the next step 106, the region-of-interest detection unit 47 determines whether or not there is a region of interest (is detected).

  In the present embodiment, if a region of interest is detected in step 106, the process proceeds to step S107. In step S107, the image display instructing unit 62 of the image processing apparatus 50 performs the tomosynthesis imaging with a high resolution (no binning process) and a large incident angle range as the imaging conditions (hereinafter, “recommended”). Display ") is displayed on the display 82 of the display device 80.

  22A and 22B show specific examples of recommendation display when the second tomosynthesis imaging is recommended. FIG. 22A is a specific example of the recommended display performed when the instruction input unit 84 is a touch panel or the like. In FIG. 22A, the detection of the region of interest and the recommended type of tomosynthesis imaging (second) are displayed, and a selection button of “Yes” or “No” is displayed. The user refers to the recommendation display and selects one by the instruction input unit 84. Specifically, the user operates either “Yes” or “No” on the display 82 (screen).

  FIG. 22B is a specific example of recommendation display performed when the instruction input unit 84 is a keyboard or the like. In FIG. 22B, the detection of the region of interest and the recommended type of tomosynthesis imaging (first or second) are displayed, and a display prompting input of “1” or “2” is performed for selection. . The user refers to the recommendation display and operates one of the instructions using the instruction input unit 84. Specifically, the user operates either “1” or “2” such as a keyboard or a numeric keypad.

  On the other hand, if the region of interest is not detected in step 106, the process proceeds to step S109. In step S109, the image display instructing unit 62 of the image processing apparatus 50 displays a recommended display of the first tomosynthesis photographing that performs tomosynthesis photographing in a low resolution (with binning process) and small incident angle range as photographing conditions. 82 is displayed. The recommended display in this case may indicate that the region of interest has not been detected and the recommended type of tomosynthesis imaging (first). For example, in the recommended display shown in FIG. 22 above, “the part of interest was detected” is changed to “the part of interest was not detected”, and the type of tomosynthesis imaging to be recommended (recommended) is the first. Change to

  The recommendation display is not limited to the specific example shown in FIG. Any type of tomosynthesis imaging (first or second) to be recommended may be displayed to prompt the user to select which tomosynthesis imaging to perform.

  In response to the recommendation display in step S107 or step S109, the user selects either the first or second tomosynthesis imaging and instructs the instruction input unit 84. Therefore, in the next step S111, the control unit 46 sets shooting conditions for tomosynthesis shooting in accordance with the instruction received by the instruction receiving unit 64. When the first tomosynthesis imaging is instructed, the binning process is performed as an imaging condition, and a small incident angle range is set. When the second tomosynthesis imaging is instructed, the binning process is not performed as the imaging condition. And a large incident angle range is set.

  Since the process of each step of following step S112-S120 is the same as the process (refer FIG. 9) performed by the control part 46 of 1st Embodiment, detailed description is abbreviate | omitted.

  In step S112, the control unit 46 performs tomosynthesis imaging according to the set imaging conditions. When the tomosynthesis imaging is completed, the control unit 46 releases the fixation of the breast N in the next step S114. In next step S <b> 116, the control unit 46 outputs the captured radiation image to the image processing apparatus 50. In the next step S118, the tomographic image generation unit 68 of the image processing apparatus 50 performs the above-described image processing such as the FBP method based on the projection image to generate a tomographic image. In the next step S120, the image display instruction unit 62 displays the generated tomographic image on the display 82 of the display device 80, and then the present process is terminated.

  Needless to say, the recommended display executed by the image display instruction unit 62 in this embodiment may be performed in combination with each of the above embodiments.

  In the present embodiment, the case where the recommended display is performed on the display 82 of the display device 80 has been described. In that case, the operation panel 44 functions as a display unit of the disclosed technology.

  Further, in the present embodiment, the case where the recommended display is performed regardless of whether or not the region of interest is detected has been described, but the present invention is not limited to this, and the recommended display may be performed only in either case.

  As described above, in the radiographic image capturing apparatus 10 according to the present embodiment, the site-of-interest detection unit 47 determines the site of interest from the radiographic image (two-dimensional image), similarly to the radiographic image capture apparatus 10 according to the first embodiment. If the region of interest is detected and the region of interest is not detected, the binning process is performed, and the incident angle range of the radiation is set as the small incident angle range. Further, when a region of interest is detected, the binning process is not performed, and the radiation incident angle range is set as the large incident angle range, and tomosynthesis imaging is performed.

  Therefore, in the radiographic imaging device 10 of the present exemplary embodiment, an accurate radiographic image can be obtained while reducing the burden on the subject W, as in the radiographic imaging device 10 of the first exemplary embodiment. .

  Further, in the radiographic image capturing system 6 of the present embodiment, recommended display for recommending either the first tomosynthesis imaging (small incident angle range) or the second tomosynthesis imaging (large incident angle range) is performed. If the region of interest is not detected, the first tomosynthesis imaging is recommended. If the region of interest is detected, the second tomosynthesis imaging is recommended.

  Thereby, the user can select execution of appropriate tomosynthesis imaging according to the presence or absence of the region of interest.

  In the radiation image capturing system 6 of each of the above embodiments, the example in which the incident angle range of tomosynthesis imaging can be switched to two types has been described. However, the present invention is not limited to this and may be three or more types. In the case of a configuration that can be switched to three or more types, it is possible to set the photographing conditions for tomosynthesis photographing more finely. For example, the region-of-interest detection unit 47 detects the size of the region of interest and the type of lesion (calcification, tumor, etc.) estimated from the size of the region of interest, and the incident angle range according to the detected size and type May be different.

  Note that a program for executing each step of processing performed in the radiographic imaging system 6 described in each of the above embodiments may be a program 55. Further, for example, each process performed in each of the radiographic image capturing apparatus 10 and the image processing apparatus 50 may be distributed and stored in the memory 43B or the ROM 54 in each apparatus.

  Moreover, the radiation in each said embodiment is not specifically limited, X-ray, a gamma ray, etc. can be applied.

  In addition, the configurations and operations of the radiation image capturing system 6, the radiation image capturing apparatus 10, and the radiation detector 42 described in the above embodiments are merely examples, and the situation is within the scope of the present invention. Needless to say, it can be changed accordingly.

  The disclosure of Japanese application 2014-070319 is incorporated herein by reference in its entirety.

  All documents, patent applications, and technical standards mentioned in this specification are to the same extent as if each individual document, patent application, and technical standard were specifically and individually stated to be incorporated by reference, Incorporated herein by reference.

Claims (14)

A radiation source that emits radiation toward the breast of the subject;
A radiation image in which the resolution represented by the number of pixels per unit length is a first resolution based on the radiation irradiated from the radiation source and transmitted through the breast, and the input control signal, and the resolution A radiological image generation unit that generates any of radiographic images having a second resolution higher than the first resolution;
A region-of-interest detection unit that detects a region of interest from a two-dimensional image that is a radiation image of the breast generated by the radiation image generation unit by the radiation source emitting radiation to the breast at a predetermined incident angle; ,
When capturing the two-dimensional image , the radiation source is irradiated with radiation at the predetermined incident angle from the radiation source, and the radiation image generation unit causes the radiation image of the first resolution or the When a control signal for generating a radiographic image of the second resolution is output and the region of interest is not detected from the two-dimensional image by the region-of-interest detection unit, the incident angle is within the first incident angle range from the radiation source. The radiation image generation unit is configured to output a control signal for generating a plurality of radiation images of the first resolution of the breast to perform first tomosynthesis imaging, If the region of interest from the two-dimensional image is detected by the region of interest detector, different incidence angle at a second incidence angle range greater than the first incident angle range of the radiation source A control unit that emits radiation a plurality of times and outputs a control signal for generating a plurality of radiation images of the second resolution of the breast to the radiation image generation unit to execute second tomosynthesis imaging. ,
A radiographic imaging system comprising: A radiation source that emits radiation toward the breast of the subject;
A radiation image in which the resolution represented by the number of pixels per unit length is a first resolution based on the radiation irradiated from the radiation source and transmitted through the breast, and the input control signal, and the resolution A radiological image generation unit that generates any of radiographic images having a second resolution higher than the first resolution;
A region-of-interest detection unit that detects a region of interest from a two-dimensional image that is a radiation image of the breast generated by the radiation image generation unit by the radiation source emitting radiation to the breast at a predetermined incident angle; ,
When capturing the two-dimensional image , the radiation source is irradiated with radiation at the predetermined incident angle from the radiation source, and the radiation image generation unit causes the radiation image of the first resolution or the A control unit that outputs a control signal for generating a radiographic image of the second resolution;
Based on the detection result of the region-of-interest detection unit, the radiation source is irradiated multiple times with different incident angles within a first incident angle range, and the radiation image generation unit causes the first of the breast to be irradiated. First tomosynthesis imaging for generating a plurality of radiographic images of the resolution, or irradiating the radiation a plurality of times with different incident angles in a second incident angle range larger than the first incident angle range from the radiation source A display unit for performing a recommended display for recommending any of the second tomosynthesis imaging in which the radiographic image generation unit generates a plurality of radiographic images of the second resolution of the breast;
An input unit for inputting a selection result of the first tomosynthesis imaging or the second tomosynthesis imaging,
The control unit outputs a control signal for executing the first tomosynthesis imaging or the second tomosynthesis imaging based on an input from the input unit.
Radiation imaging system. The second incident angle range includes the first incident angle range.
The radiographic imaging system of Claim 1 or Claim 2.   4. The radiographic imaging system according to claim 3, wherein the first incident angle range and the second incident angle range are symmetrical ranges around the predetermined incident angle. 5. A tomographic image generating unit that generates a tomographic image of the breast based on a plurality of radiographic images of the subject's breast acquired from the radiological image generating unit;
A display device for displaying a tomographic image of the subject's left and right breasts generated by the tomographic image generation unit,
When the control unit executes the first tomosynthesis imaging for one of the left and right breasts of the subject and the second tomosynthesis imaging for the other of the left and right breasts, the tomographic image generation unit Based on the radiographic image of the one breast acquired by the first tomosynthesis imaging, the resolution in the depth direction is the first resolution, a first tomographic image having the first resolution is generated, and the first tomographic image is generated. A second resolution in which the resolution in the depth direction is higher than the first resolution based on the radiographic image of the other breast acquired by the second tomosynthesis imaging, and is higher than the first resolution. And the resolution in the depth direction is the first resolution based on the radiographic image acquired in the first incident angle range among the radiographic images of the other breast. Yes The third tomographic images having the second resolution is generated separately,
The display device displays the first tomographic image of the one breast and the at least one of the second tomographic image and the third tomographic image of the other breast;
The radiographic imaging system of any one of Claims 1-4. The display device displays the second tomographic image and the third tomographic image of the other breast in a switchable manner;
The radiographic imaging system according to claim 5. When the control unit performs the first tomosynthesis imaging for one of the left and right breasts of the subject and performs the second tomosynthesis imaging for the other of the left and right breasts,
Further, the tomographic image generation unit has a resolution in the depth direction based on a radiographic image acquired in the first incident angle range among the radiographic images of the other breast, which is the first resolution, Separately generating a fourth tomographic image of the first resolution,
The display device displays the first tomographic image of the one breast and at least one of the second tomographic image, the third tomographic image, and the fourth tomographic image of the other breast. To
The radiographic imaging system according to claim 5 or 6. The display device displays the second tomographic image, the third tomographic image, and the fourth tomographic image of the other breast in a switchable manner;
The radiographic imaging system according to claim 7. The display device can switch to the third tomographic image after displaying the second tomographic image.
The radiographic imaging system of any one of Claims 5-8. The display device includes a tomographic image of the breast, a first mark indicating whether switching to a tomographic image having a resolution different from that of the tomographic image, and a tomographic image having a resolution different from that of the tomographic image. Displaying at least one of the second marks indicating whether switching is possible,
The radiographic imaging system of any one of Claims 5-9. The display device displays that the switching is impossible by the first mark and the second mark for the tomographic image of the one breast obtained by the first tomosynthesis imaging, For the other tomographic image obtained by second tomosynthesis imaging, it is displayed that switching is possible by the first mark and the second mark.
The radiographic imaging system according to claim 10. Based on the radiation source that emits radiation toward the breast of the subject, the radiation that is irradiated from the radiation source and transmitted through the breast, and the input control signal, the number of pixels per unit length is expressed. A radiological image comprising: a radiological image whose resolution is a first resolution; and a radiological image generation unit that generates either a radiographic image whose second resolution is higher than the first resolution. A radiographic imaging method for an imaging device,
A region-of-interest detection step of detecting a region of interest from a two-dimensional image which is a radiation image of the breast generated by the radiation image generation unit by the radiation source emitting radiation to the breast at a predetermined incident angle; ,
When capturing the two-dimensional image , the radiation source is irradiated with radiation at the predetermined incident angle from the radiation source, and the radiation image generation unit causes the radiation image of the first resolution or the When a control signal for generating a radiographic image of the second resolution is output and the region of interest is not detected from the two-dimensional image by the region of interest detection step, the incident angle is within the first incident angle range from the radiation source. The radiation image generation unit is configured to output a control signal for generating a plurality of radiation images of the first resolution of the breast to perform first tomosynthesis imaging, If the region of interest from the two-dimensional image is detected by the region of interest detection step, at a second incidence angle range greater than the first incident angle range of the radiation source A radiation signal is emitted a plurality of times at different angles of incidence, and a control signal for generating a plurality of radiation images of the second resolution of the breast is output to the radiation image generation unit to execute second tomosynthesis imaging A control step;
A radiographic imaging method comprising: Based on the radiation source that emits radiation toward the breast of the subject, the radiation that is irradiated from the radiation source and transmitted through the breast, and the input control signal, the number of pixels per unit length is expressed. A radiological image comprising: a radiological image whose resolution is a first resolution; and a radiological image generation unit that generates either a radiographic image whose second resolution is higher than the first resolution. A radiographic imaging method for an imaging device,
The region of interest detection unit detects the region of interest from a two-dimensional image that is a radiographic image of the breast generated by the radiation image generation unit when the radiation source irradiates the breast with a predetermined incident angle. And steps to
When capturing the two-dimensional image by the control unit, the radiation source is irradiated with radiation at the predetermined incident angle from the radiation source, and the radiation image generation unit has the first resolution. Outputting a control signal for generating a radiographic image or a radiographic image of the second resolution;
Based on a detection result of the region-of-interest detection unit, the display unit irradiates the radiation image a plurality of times with different incident angles in a first incident angle range from the radiation source, and causes the radiation image generation unit to transmit the breast The first tomosynthesis imaging for generating a plurality of radiation images of the first resolution of the first, or the radiation from the radiation source in a second incident angle range larger than the first incident angle range. Irradiating a plurality of times and performing a recommended display for recommending any of the second tomosynthesis imaging in which the radiation image generation unit generates a plurality of radiation images of the second resolution of the breast;
A step of inputting a selection result of the first tomosynthesis imaging or the second tomosynthesis imaging by the input unit;
Outputting a control signal for executing the first tomosynthesis imaging or the second tomosynthesis imaging based on an input from the input unit by the control unit;
A radiographic imaging method comprising:   The radiographic imaging program for functioning a computer as a region of interest detection part and control part of a radiographic imaging system given in any 1 paragraph of Claims 1-11.