Breast imaging apparatus

Abstract

To provide a breast imaging apparatus capable of achieving an appropriate arrangement of scattered ray removal grids according to an imaging mode.SOLUTION: A breast imaging apparatus includes: an imaging platform where the breast of a subject is placed and a detector for detecting a radiation ray transmitting the breast is stored; and a processor. Inside the imaging platform, there are provided a first grid and a second grid that can be switched to an imaging position and a retreat position according to imaging by each of a plurality of imaging modes, which are scattered ray removal grids capable of removing scattered rays generated by the scattering of the radiation ray in the breast. The processor acquires a result of reception of imaging mode selection by a user, and executes control of an arrangement state inside the imaging platform of the first grid and the second grid according to the selection of the imaging mode that has been acquired.SELECTED DRAWING: Figure 4

Description

[Technical field]

[0001] The present disclosure relates to mammography devices. [Background technology]

[0002] Patent Document 1 describes a mammography device in which radiolucent and radiopaque bodies constituting a grid are arranged to extend approximately parallel to the chest wall of the breast, and radiation output from a radiation source is irradiated onto a solid-state detector via the grid to capture a radiographic image of the breast.

[0003] Patent Document 2 describes an X-ray imaging device in which an anti-scatter grid having a plurality of partitions may be configured to be positioned relative to the X-ray imaging device such that each partition of the plurality of partitions extends along a direction substantially parallel to a coronal plane of the subject during imaging of the subject using the X-ray imaging device. The X-ray imaging device may be operable in a tomosynthesis mode for imaging of the subject's chest, and may include an anti-scatter grid disposed between a chest platform and an X-ray detector. [Prior art documents] [Patent documents]

[0004] [Patent Document 1] JP 2008-237631 A [Patent Document 2] Special Publication No. 2016-515877 Summary of the Invention [Problem to be solved by the invention]

[0005] In some cases, breast imaging is performed in multiple imaging modes, such as normal imaging, contrast energy subtraction imaging, tomosynthesis imaging, etc. In these cases, it is necessary to appropriately position the anti-scatter grid built into the imaging table according to the imaging mode.

[0006] The technique disclosed herein provides a mammography apparatus capable of realizing an appropriate arrangement of an anti-scatter grid according to an imaging mode. [Means for solving the problem]

[0007] A first aspect of the technology of the present disclosure is a breast imaging device comprising: an imaging table on which a subject's breast is placed and which houses a detector for detecting radiation that has passed through the breast; and a processor; inside the imaging table are provided first and second grids which are scatter removal grids capable of removing scattered rays caused when radiation is scattered in the breast and which can be switched between an imaging position and a retracted position depending on each of a plurality of imaging modes; the processor acquires a result of accepting a user's selection of an imaging mode, and controls the positioning state of the first and second grids inside the imaging table depending on the acquired selection of the imaging mode.

[0008] A second aspect of the technology disclosed herein is a breast imaging device according to the first aspect, in which a plurality of transmitting portions that transmit radiation and a plurality of absorbing portions that absorb radiation are arranged alternately in the anti-scatter grid, the boundary between the transmitting portions and the absorbing portions extends in one direction, and the extension direction of the boundary in the first grid and the extension direction of the boundary in the second grid intersect with each other.

[0009] A third aspect of the technology disclosed herein is a breast imaging device according to the second aspect, in which, on the imaging table, when the direction connecting the side of the chest wall on which the subject's chest wall is located and the opposite side of the chest wall is defined as the anterior-posterior direction, and the direction perpendicular to the anterior-posterior direction is defined as the left-right direction, the first grid has a boundary line extending in a direction parallel to the anterior-posterior direction, and the second grid has a boundary line extending in a direction parallel to the left-right direction.

[0010] A fourth aspect of the technology of the present disclosure is a breast imaging device according to the third aspect, in which the multiple imaging modes include a normal imaging mode in which imaging is performed by holding the radiation source in an opposing position to the imaging table, and when the normal imaging mode is selected, the first grid is positioned at the imaging position and the second grid is positioned at a retracted position.

[0011] A fifth aspect of the technology of the present disclosure is a breast imaging device according to the third aspect, wherein the multiple imaging modes include a first contrast imaging mode which is an imaging mode for diagnosis using contrast energy subtraction, and when the first contrast imaging mode is selected, the first grid is placed at the imaging position and the second grid is placed at a retracted position.

[0012] A sixth aspect of the technology of the present disclosure is a breast imaging device according to the third aspect, wherein the multiple imaging modes include a second contrast imaging mode which is an imaging mode for biopsy by contrast energy subtraction, and when the second contrast imaging mode is selected, the second grid is placed at the imaging position and the first grid is placed at the retracted position.

[0013] A seventh aspect of the technology of the present disclosure is a breast imaging device according to the third aspect, in which the multiple imaging modes include a tomosynthesis imaging mode in which a radiation source is moved to perform tomographic imaging of the breast, and when the tomosynthesis imaging mode is selected, both the first grid and the second grid are positioned in a retracted position.

[0014] An eighth aspect of the technology of the present disclosure is a breast imaging device according to the fourth, sixth and seventh aspects, wherein the multiple imaging modes include a continuous imaging mode in which at least two of the normal imaging mode, the second contrast imaging mode and the tomosynthesis imaging mode are performed consecutively in any order, and in the continuous imaging mode, the arrangement state of the first grid and the second grid is changed depending on each of the normal imaging mode, the second contrast imaging mode and the tomosynthesis imaging mode.

[0015] A ninth aspect of the technology of the present disclosure is a breast imaging device according to the eighth aspect, in which, in the continuous imaging mode, imaging in each mode in the continuous imaging mode can be performed while the breast remains compressed between the imaging table and the compression plate.

[0016] A tenth aspect of the technology of the present disclosure is a breast imaging device according to the first aspect, in which the movement of the first grid and the second grid between the imaging position and the retracted position inside the imaging stand is a linear movement.

[0017] An eleventh aspect of the technique of the present disclosure is a breast imaging device according to the first aspect, in which the processor is capable of outputting the arrangement state of the first grid and the second grid inside the imaging stand to the notification unit. Effect of the Invention

[0018] The technique disclosed herein provides a mammography apparatus capable of realizing an appropriate arrangement of an anti-scatter grid according to an imaging mode. [Brief description of the drawings]

[0019] [Figure 1] 1 is an external perspective view showing an example of the configuration of a mammography apparatus; [Diagram 2] 1 is an external side view showing an example of the configuration of a mammography apparatus. [Diagram 3] FIG. 2 is a diagram illustrating an example of a hardware configuration of an electrical system of a mammography apparatus. [Figure 4] FIG. 2 is a conceptual diagram showing an example of the function of a mammography apparatus. [Diagram 5] FIG. 2 is a conceptual diagram showing an example of the function of a mammography apparatus. [Figure 6] 1 is an external front view showing an example of the configuration of a mammography apparatus; [Figure 7] FIG. 2 is a conceptual diagram showing an example of the function of a mammography apparatus. [Figure 8] 1 is an external perspective view showing an example of the configuration of a mammography apparatus; [Figure 9] 1 is a perspective view showing an example of a protective cover and a biopsy unit being attached to and detached from a mammography apparatus; FIG. [Figure 10] 1 is an external front view showing an example of the configuration of a mammography apparatus; [Figure 11] FIG. 2 is a conceptual diagram showing an example of the function of the mammography apparatus. [Figure 12]1 is an external side view showing an example of the configuration of a mammography apparatus. [Figure 13] 1 is an external front view showing an example of the configuration of a mammography apparatus; [Figure 14] FIG. 2 is a conceptual diagram showing an example of the function of the mammography apparatus. [Figure 15] FIG. 11 is a diagram summarizing the different uses of grids in a mammography apparatus. [Figure 16] FIG. 2 is a conceptual diagram showing an example of the function of the mammography apparatus. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0020] Hereinafter, embodiments of the present disclosure will be described in detail with reference to the drawings.

[0021] In the following description, for convenience of explanation, the height direction, width direction, and front-rear direction (also called depth direction) of the breast imaging apparatus 10 are indicated by three arrows, X, Y, and Z. First, the height direction is indicated by arrow Z, and the direction indicated by arrow Z is the upward direction of the breast imaging apparatus 10, and the opposite direction is the downward direction. The height direction is the vertical direction. The width direction is indicated by arrow X perpendicular to arrow Z, and the direction indicated by arrow X is the rightward direction of the breast imaging apparatus 10, and the opposite direction is the leftward direction. The front-rear direction is indicated by arrow Y perpendicular to arrows Z and X, and the direction indicated by arrow Y is the forward direction of the breast imaging apparatus 10, and the opposite direction is the rearward direction. That is, in the breast imaging apparatus 10, the side of the stand 20 is the rearward direction, and the opposite side where the subject A stands (see FIG. 2) is the forward direction. In the following description, expressions using sides, such as upper, lower, left, right, front, and rear, have the same meaning as expressions using directions.

[0022] In this embodiment, the "vertical direction" refers to a vertical direction including an error that is generally acceptable in the technical field to which the technology of the present disclosure belongs and does not go against the spirit of the technology of the present disclosure, in addition to a completely vertical direction. Similarly, the "horizontal direction" refers to a horizontal direction including an error that is generally acceptable in the technical field to which the technology of the present disclosure belongs and does not go against the spirit of the technology of the present disclosure, in addition to a completely horizontal direction.

[0023] As shown in Figures 1 and 2, a breast imaging device 10 according to this embodiment is a radiographic device that irradiates radiation onto a breast M of a subject A, who is the subject, to obtain a radiographic image of the breast M. One example of the radiation is X-rays, but gamma rays may also be used. The subject A is positioned in front of the breast imaging device 10. The breast imaging device 10 is an example of a "breast imaging device" according to the technology of the present disclosure.

[0024] Mammography apparatus 10 is connected to console 11. Console 11 has a setting function for setting mammography apparatus 10 according to an imaging order, as well as a function for acquiring radiation images captured by mammography apparatus 10 and displaying the acquired radiation images. Console 11 is communicably connected to an image database server (not shown) via a network (not shown) such as a LAN (Local Area Network).

[0025] The console 11 includes a reception device 11A and an output device 11B. The reception device 11A receives input from a user. The reception device 11A is, for example, a keyboard and / or a mouse. The output device 11B displays an operation screen and / or an operating state of the breast imaging device 10, a radiation image, etc. to the user. The output device 11B is, for example, a liquid crystal display or an organic EL (Electro Luminescence) display.

[0026] The mammography apparatus 10 has a stand 20 and an arm 21. The stand 20 is composed of a base 20A placed on the floor of a radiography room and a support column 20B extending in the height direction from the base 20A. The arm 21 has a substantially C-shaped shape when viewed from the left side, and is connected to the support column 20B via a rotation shaft. The arm 21 is movable in the height direction relative to the support column 20B, so that the height of the arm 21 can be adjusted according to the height of the subject A. The arm 21 is also rotatable around a rotation shaft perpendicular to the support column 20B.

[0027] The arm 21 is composed of a radiation source housing section 22, a main body section 23, and an imaging table 24. A radiation source 25 is housed in the radiation source housing section 22. The radiation source 25 is equipped with a tube 25A. The radiation source housing section 22 has a housing structure having a longitudinal direction in the front-rear direction, for example. The breast M of the subject A is placed on the imaging table 24. A radiation detector 26 is housed in the imaging table 24. The main body section 23 integrally connects the radiation source housing section 22 and the imaging table 24. The main body section 23 holds the radiation source housing section 22 and the imaging table 24 in a predetermined position. Handrails 27 for the subject A to hold are provided on both sides of the main body section 23.

[0028] The breast M of the subject A is placed on the imaging table 24. The imaging table 24 has an imaging surface 24A on which radiation that has passed through the breast M is incident. A radiation detector 26 is housed in the imaging table 24. The imaging table 24 is an example of an "imaging table" according to the technology of the present disclosure.

[0029] The radiation source 25 irradiates radiation towards the breast M placed on the imaging table 24. The radiation emitted from the radiation source 25 passes through the compression plate 30 and then enters the breast M. The radiation detector 26 detects the radiation that has passed through the breast M and outputs a radiological image. The radiation detector 26 is called an FPD (Flat Panel Detector). The radiation detector 26 has a scintillator that converts radiation into visible light, and may be an indirect conversion type that converts the visible light emitted by the scintillator into an electrical signal, or a direct conversion type that directly converts radiation into an electrical signal. The radiation detector 26 is an example of a "detector" according to the technology of the present disclosure.

[0030] An irradiation field limiter 31 is provided between the radiation source 25 and the imaging table 24. The irradiation field limiter 31 is also called a collimator, and defines the irradiation field of radiation onto the imaging table 24.

[0031] A face guard 32 is attached to the radiation source housing 22. The face guard 32 is formed of or coated with a material that is not transparent to radiation, and protects the face of the subject A from radiation.

[0032] Between the imaging table 24 and the irradiation field limiter 31, there is provided a compression plate 30 that sandwiches and compresses the breast M between the imaging table 24. The compression plate 30 is made of a material that transmits radiation. The compression plate 30 is disposed at a position facing the imaging table 24. In this embodiment, the compression plate 30 is in a box shape with an open top side.

[0033] The moving mechanism 35 supports the compression paddle 30 so as to be movable between the radiation source 25 and the imaging table 24. In addition, the movable part 34 is disposed between the compression paddle 30 and the moving mechanism 35. The movable part 34 is slidably held on a rail 28 provided on the moving mechanism 35. The rail 28 extends in the vertical direction.

[0034] The moving mechanism 35 includes, for example, a motor (not shown), a motor driver (not shown), and a feed screw mechanism (not shown). The motor rotates in response to an electrical drive signal output by the motor driver, and moves the compression plate 30 via the feed screw mechanism.

[0035] The compression plate 30 is attached to a movable part 34. The movable part 34 moves in the up-down direction together with the compression plate 30 by a moving mechanism 35. The up-down direction functionally corresponds to the direction in which the compression plate 30 moves toward the imaging table 24 (i.e., downward) and the direction in which the compression plate 30 moves away from the imaging table 24 (i.e., upward). In this way, the compression plate 30 is configured to be movable in a manner that changes the distance from the imaging table 24.

[0036] A first grid 44 and a second grid 45 are provided inside the imaging table 24 as anti-scatter grids. As is well known, the anti-scatter grids remove scattered radiation generated when radiation passes through the breast M. The first grid 44 and the second grid 45 are disposed inside the imaging table 24 on the radiation source 25 side of the radiation detector 26. The first grid 44 and the second grid 45 are flat plate-shaped members, and include an absorbing portion 46 that transmits radiation and a transmitting portion 47 that absorbs radiation. A boundary line 48 is formed between the absorbing portion 46 and the transmitting portion 47. The directions in which the boundary lines 48 of the first grid 44 and the second grid 45 extend intersect with each other.

[0037] Specifically, in the first grid 44, the absorbing portions 46 and the transmitting portions 47 are arranged alternately, and the boundary lines 48 between the absorbing portions 46 and the transmitting portions 47 extend in the front-rear direction (i.e., the direction connecting the chest wall side and the anti-chest wall side of the subject A on the imaging surface 24A) inside the imaging table 24. In other words, the absorbing portions 46 and the transmitting portions 47 are arranged alternately in the left-right direction.

[0038] In the second grid 45, the absorbing portions 46 and the transmitting portions 47 are alternately arranged, and the boundary line 48 between the absorbing portions 46 and the transmitting portions 47 extends in the left-right direction. In other words, the absorbing portions 46 and the transmitting portions 47 are alternately arranged in the front-rear direction. As a result, in the second grid 45, the central axis of the radiation beam and the direction in which the boundary line 48 extends are substantially aligned, so that vignetting of the radiation is suppressed in stereoscopic imaging. The absorbing portions 46 are an example of an "absorbing portion" according to the technology of the present disclosure, and the transmitting portions 47 are an example of a "transmitting portion" according to the technology of the present disclosure. The boundary line 48 is an example of a "boundary line" according to the technology of the present disclosure. The first grid 44 is an example of a "first grid" according to the technology of the present disclosure. The second grid 45 is an example of a "second grid" according to the technology of the present disclosure.

[0039] Examples of the material for the absorbing portion 46 include a thin film of lead, etc. Examples of the material for the transmitting portion 47 include aluminum, paper, and carbon fiber, etc.

[0040] Here, the breast imaging device 10 according to the present embodiment is capable of imaging in a plurality of imaging modes. The plurality of imaging modes include a normal imaging mode, a tomosynthesis imaging mode, a contrast energy subtraction imaging mode for diagnosis, and a contrast energy subtraction imaging mode for biopsy. One of these imaging modes is selected, and then radiation imaging is performed. The imaging conditions (e.g., whether or not the radiation source 25 moves, whether or not the anti-scatter grid oscillates, etc.) differ for each imaging mode. Therefore, it is required to change the arrangement state of the anti-scatter grid according to the imaging mode. Therefore, the first grid 44 and the second grid 45 are switchable between an imaging position and a retracted position according to each imaging in a plurality of imaging modes. Specifically, the first grid 44 and the second grid 45 are movable between an imaging device facing the detection surface 26A of the radiation detector 26 and a retracted position retracted from the imaging position in the imaging table 24.

[0041] 3, the mammography apparatus 10 includes a control device 16. A drive mechanism 50 for moving the first grid 44 and the second grid 45 is provided inside the imaging table 24. The drive mechanism 50 moves the first grid 44 and the second grid 45 under the control of the control device 16.

[0042] The control device 16 includes, for example, a processor 16A, a non-volatile memory (NVM) 16B, a random access memory (RAM) 16C, and an external interface (I / F) 16D. The processor 16A, the NVM 16B, the RAM 16C, and the external interface 16D are electrically connected via a bus 16E. The processor 16A is an example of a "processor" according to the technology of the present disclosure.

[0043] The processor 16A is, for example, a CPU (Central Processing Unit) and controls each part. The RAM 16C is a memory in which information is temporarily stored, and is used as a work memory by the processor 16A. The NVM 16B is a non-volatile storage device that stores various programs and various parameters. An example of the NVM 16B is a flash memory (for example, an EEPROM (Electrically Erasable and Programmable Read Only Memory) and / or an SSD (Solid State Drive)). Note that the flash memory is merely an example, and may be another non-volatile storage device such as an HDD (Hard Disk Drive), or may be a combination of two or more types of non-volatile storage devices.

[0044] The external I / F 16D controls the exchange of information between the control device 16 and the drive mechanism 50. The external I / F 16D outputs, for example, a signal to the drive mechanism 50 for controlling the operation of the drive mechanism 50.

[0045] The drive mechanism 50 includes a motor driver 50A, a motor 50B, and an encoder 50C. The motor driver 50A operates the motor 50B based on a signal output from the processor 16A via the external I / F 16D. The motor 50B rotates in response to an electrical drive signal output from the motor driver 50A, and moves the first grid 44 and the second grid 45 via a power transmission mechanism (e.g., a feed screw mechanism) not shown. The encoder 50C converts the mechanical displacement amount of the rotation of the motor 50B into an electrical signal and outputs it to the processor 16A.

[0046] As described above, the first grid 44 and the second grid 45 provided inside the imaging stand 24 have different arrangements of the boundary lines 48. Therefore, the first grid 44 and the second grid 45 are required to be appropriately arranged according to the imaging mode.

[0047] In view of the above circumstances, in breast imaging apparatus 10 according to the present embodiment, processor 16A in control device 16 reads position control program 52 from NVM 16B and executes read position control program 52 on RAM 16C. As a result, processor 16A operates as acquisition unit 16A1, position control unit 16A2, and output unit 16A3.

[0048] As an example, as shown in Fig. 4, first, the selection of an imaging mode is accepted by the user via the reception device 11A in the console 11. In the example shown in Fig. 4, the mouse 11A1 is operated as the reception device 11A, and the normal imaging mode is selected via the pointer 54 on the operation screen displayed on the display 11B1. In the normal imaging mode, radiation imaging is performed in a state in which the radiation source 25 is held in a position facing the imaging table 24. Note that, here, CC imaging (CC; Cranio-Caudal) is performed as the imaging technique in which the breast M is compressed from the cranial-caudal direction of the subject and imaged, but MLO imaging (MLO; Medio-Lateral) may also be performed in which the breast M is compressed from a direction inclined to the cranial-caudal direction of the subject and imaged.

[0049] The console 11 outputs selected mode information 56, which is information indicating the imaging mode selected by the user, to the control device 16 of the mammography apparatus 10. In other words, the console 11 outputs the result of accepting the imaging mode selection by the user.

[0050] In the processor 16A, the acquisition unit 16A1 acquires the selection mode information 56 from the console 11. That is, the acquisition unit 16A1 acquires the result of accepting the selection of the shooting mode by the user. The acquisition unit 16A1 also acquires a grid position table 58 from the NVM 16B. The grid position table 58 is a table in which the shooting mode is input information and the grid arrangement corresponding to each shooting mode (i.e., the positions of the first grid 44 and the second grid 45 on the shooting stand 24) is output information. The acquisition unit 16A1 outputs the selection mode information 56 and the grid position table 58 to the position control unit 16A2.

[0051] Note that, here, an example has been described in which the position control unit 16A2 derives the grid arrangement by using the grid position table 58, but this is merely one example. A grid position arithmetic formula may be used instead of the grid position table 58. The grid position arithmetic formula is a formula in which the shooting mode is an independent variable and the grid arrangement according to each shooting mode is a dependent variable. The position control unit 16A2 derives the grid arrangement by using the grid position arithmetic formula.

[0052] The position control unit 16A2 controls the arrangement state of the first grid 44 and the second grid 45 inside the imaging stand 24 in response to the imaging mode selected by the user. Specifically, the position control unit 16A2 uses a grid position table 58 to derive a grid arrangement corresponding to the imaging mode indicated by the selected mode information 56. Then, the position control unit 16A2 controls the driving mechanism 50 to achieve the derived grid arrangement. Specifically, the position control unit 16A2 outputs a control signal to the driving mechanism 50 to move the first grid 44 and the second grid 45 to the derived grid arrangement.

[0053] The driving mechanism 50 operates under the control of the position control unit 16A2, and moves the first grid 44 and the second grid 45 to a grid arrangement according to the imaging mode. In the example shown in Fig. 4, since the normal imaging mode is selected by the user, the first grid 44 is arranged at the imaging position, and the second grid 45 is arranged at the retracted position. In this manner, the position control unit 16A2 executes control of the arrangement state of the first grid 44 and the second grid 45 inside the imaging stand 24 according to the imaging mode selected by the user.

[0054] 5, as an example, as a result of control of the arrangement states of the first grid 44 and the second grid 45 by the position control unit 16A2, the first grid 44 is arranged at the imaging position 24B, and the second grid 45 is arranged at the retracted position 24C. Here, the first grid 44 and the second grid 45 are allowed to move linearly inside the imaging stand 24. Here, inside the imaging stand 24, the first grid 44 and the second grid 45 are allowed to move linearly along the front-rear direction.

[0055] In the processor 16A, the output unit 16A3 is capable of outputting information indicating the arrangement state of the first grid 44 and the second grid 45 inside the imaging stand 24. Specifically, the output unit 16A3 acquires information indicating the arrangement state of the first grid 44 and the second grid 45 and outputs it to the console 11. In the console 11, the output device 11B displays the arrangement state of the first grid 44 and the second grid 45. In the example shown in FIG. 5, a window including text indicating the arrangement state of the first grid 44 and the second grid 45 is displayed on the screen of the display 11B1. The output device 11B and the display 11B1 are an example of a "notification unit" according to the technology of the present disclosure.

[0056] Although the embodiment in which the output device 11B is the display 11B1 has been described above, this is merely an example. The output device 11B may be a speaker and / or an indicator lamp in addition to or instead of the display 11B1.

[0057] After confirming that the grid arrangement is suitable for the selected imaging mode, the user starts radiography of the breast M. In the example shown in Fig. 5, the normal imaging mode is selected, and imaging is performed with the radiation source 25 held in a position facing the imaging table 24. In addition, the first grid 44 is swung left and right during imaging. This makes it possible to remove vignetting caused by the absorbing portions 46.

[0058] Next, a case where the diagnostic contrast energy subtraction imaging mode is selected as the imaging mode will be described. The diagnostic contrast energy subtraction imaging mode is an example of the "first contrast imaging mode" according to the technique of the present disclosure.

[0059] As an example, as shown in FIG. 6, a mammography apparatus 10 has a function of performing contrast imaging. A contrast agent using iodine with ak absorption end of 33 keV (hereinafter simply referred to as "contrast agent") is generally used as a contrast agent for contrast imaging. The mammography apparatus 10 takes a breast M administered with a contrast agent as a subject, irradiates the breast M with radiation R of a first energy lower than the k absorption end of the contrast agent to capture a low energy image with the radiation detector 26, and irradiates the breast M with radiation R of a second energy higher than the k absorption end of the contrast agent to capture a high energy image with the radiation detector 26. The specific first and second energies are determined based on the k absorption end of the contrast agent as well as the specifications of the mammography apparatus 10, the desired image quality of the radiation image, and the exposure of the subject, and are generally preferably 22 keV to 49 keV.

[0060] The contrast agent and tissues such as mammary glands have different absorption characteristics of radiation R. Therefore, the high-energy image captured as described above clearly captures the contrast agent in addition to body tissues such as mammary glands and fat. The low-energy image captures almost no contrast agent and clearly captures body tissues such as mammary glands. Therefore, a difference image showing the difference between the low-energy image and the high-energy image can be an image in which the mammary gland structure has been removed and the contrast agent is clearly captured. This type of imaging is called contrast energy subtraction imaging. Then, a diagnosis of the breast M (e.g., determining the presence or absence and type of a lesion) is performed using the difference image obtained by contrast energy subtraction imaging.

[0061] In the diagnostic contrast energy subtraction radiography, similarly to normal radiography, radiography is performed with the radiation source 25 held at a position vertically facing the radiography table 24. In addition, the first grid 44 is swung left and right during radiography. This makes it possible to eliminate vignetting caused by the absorbing parts 46.

[0062] 7, the selection of an imaging mode by the user is received at the console 11. Here, diagnostic contrast energy subtraction imaging is selected. The console 11 outputs selected mode information 56 to the breast imaging apparatus 10. That is, the console 11 outputs the result of receiving the selection of the imaging mode by the user.

[0063] In the processor 16A, the acquisition unit 16A1 acquires the selection mode information 56 from the console 11. The acquisition unit 16A1 also acquires a grid position table 58 from the NVM 16B. The position control unit 16A2 uses the grid position table 58 to derive a grid arrangement according to the shooting mode indicated by the selection mode information 56. Then, the position control unit 16A2 controls the drive mechanism 50 to achieve the derived grid arrangement.

[0064] 7, the diagnostic contrast energy subtraction imaging mode has been selected by the user, so the first grid 44 is placed at the imaging position and the second grid 45 is placed at the retracted position. In this manner, the position controller 16A2 controls the arrangement of the first grid 44 and the second grid 45 inside the imaging table 24 in response to the selection of the imaging mode by the user.

[0065] Next, a case where the contrast energy subtraction imaging mode for biopsy is selected as the imaging mode will be described. The contrast energy subtraction imaging mode for biopsy is an example of the "second contrast imaging mode" according to the technology of the present disclosure. First, the biopsy unit 39 will be described as a premise for the contrast energy subtraction imaging for biopsy.

[0066] As an example, as shown in Figs. 8 and 9, a biopsy unit 39 is attached to the breast imaging device 10. The biopsy unit 39 is a unit that collects tissue from within the breast M in order to perform a biological tissue collection test. The biopsy unit 39 includes a main body 40, an adjustment unit 41, a needle holding unit 42, and a puncture needle 43. The adjustment unit 41 is movable relative to the main body 40, and this adjusts the insertion position, insertion angle, and insertion amount of the puncture needle 43 into the breast M. The needle holding unit 42 holds the puncture needle 43. The puncture needle 43 has a double structure of, for example, an outer needle and an inner needle. An example of a procedure for collecting tissue using such a puncture needle 43 is as follows. The puncture needle 43 is inserted into the breast M, and when the tip of the puncture needle 43 reaches the position of the tissue to be collected, the inner needle is protruded from the outer needle, and tissue is collected in a tissue collection area formed in the inner needle. After the tissue is sampled by the inner needle, the inner needle is housed in the outer needle, and the puncture needle 43 is pulled out from the breast M. This allows the target tissue to be sampled from within the breast M. In addition, an opening is provided on the bottom surface of the compression plate 30A, and the puncture needle 43 is inserted into the breast M through the opening. The compression plate 30A is attached to a movable part 34 by a pair of support arms 33.

[0067] When a biopsy is performed using the biopsy unit 39, a protective cover 37 is placed on the imaging table 24. The protective cover 37 protects the imaging surface 24A from the puncture needle 43. In other words, the protective cover 37 prevents the puncture needle 43 from contacting the imaging surface 24A. The protective cover 37 includes a flat protective member 37A and a front wall 37B bent from the front end of the protective member 37A. The breast M is placed on the protective member 37A. The protective member 37A is made of a material that is capable of transmitting radiation (e.g., acrylic resin, etc.). The size of the protective member 37A is within a range capable of supporting the breast M, and the thickness of the protective member 37A is strong enough to support the breast M.

[0068] When a biopsy is performed, the biopsy unit 39 and the protective cover 37 are attached to the mammography apparatus 10. In other words, the biopsy unit 39 and the protective cover 37 are detachable from the mammography apparatus 10. The protective cover 37 is attached to the imaging table 24 of the mammography apparatus 10, for example, by utilizing magnetic attraction using a magnet. Specifically, a magnet is attached to the protective cover 37, and the magnet is magnetically attracted to a magnetizing plate provided on the imaging table 24, thereby attaching the protective cover 37 to the imaging table 24. Note that this is merely an example, and for example, the protective cover 37 may be attached to the imaging table 24 via an adhesive sheet, or the protective cover 37 may be attached to the imaging table 24 by fitting a part of the protective cover 37 into a recess provided in the imaging table 24.

[0069] After protective cover 37 is attached to imaging stand 24, biopsy unit 39 is placed on imaging stand 24. Specifically, main body 40 of biopsy unit 39 is placed above rear end 37C of protective cover 37. Note that biopsy unit 39 may be controlled to operate only when protective cover 37 is attached to imaging stand 24.

[0070] Additionally, the compression paddle 30A is a compression paddle for the biopsy unit 39, and is attached to the mammography apparatus 10 by replacing it with the compression paddle 30 for mammography when a biopsy is not being performed.

[0071] 10, for example, when a biopsy is performed, a puncture needle 43 is inserted into the breast M while the breast M is compressed by a compression plate 30A. In this case, it is required to accurately identify the position of the tissue (e.g., diseased tissue) to be sampled from the breast M. For this reason, as described below, when a biopsy is performed, stereoscopic imaging may be performed in which radiation R is irradiated toward the breast from two directions, left and right, with different irradiation angles relative to the imaging table 24 in order to three-dimensionally identify the position of the tissue to be sampled in the breast M.

[0072] During a biopsy, contrast energy subtraction imaging may be performed to grasp the position of the tissue to be biopsied in the breast M in three dimensions. In stereoscopic imaging, the irradiation position of radiation R is changed in the left-right direction, and imaging is performed multiple times while changing the irradiation angle of radiation R. Then, imaging is performed using radiation R of different energy at each irradiation angle in the left-right direction in stereoscopic imaging (i.e., contrast energy subtraction imaging). This makes the tissue to be biopsied clearer in the image, and makes it easier to grasp the three-dimensional position. In this way, contrast energy subtraction imaging for biopsy is performed by combining stereoscopic imaging and contrast energy subtraction imaging.

[0073] 11, as an example, the selection of an imaging mode by the user is received at the console 11. Here, contrast energy subtraction imaging for biopsy is selected. The console 11 outputs selected mode information 56 to the breast imaging apparatus 10. That is, the console 11 outputs the result of receiving the selection of the imaging mode by the user.

[0074] In the processor 16A, the acquisition unit 16A1 acquires the selection mode information 56 from the console 11. The acquisition unit 16A1 also acquires a grid position table 58 from the NVM 16B. The position control unit 16A2 uses the grid position table 58 to derive a grid arrangement according to the shooting mode indicated by the selection mode information 56. Then, the position control unit 16A2 controls the drive mechanism 50 to achieve the derived grid arrangement.

[0075] In the example shown in FIG. 11, the biopsy contrast energy subtraction imaging mode is selected by the user, so that the first grid 44 is placed at the retracted position and the second grid 45 is placed at the imaging position. As described above, stereoscopic imaging is performed in the biopsy contrast energy subtraction imaging. When stereoscopic imaging is performed, in the breast imaging device 10, imaging is performed in a state in which the first grid 44 is moved to the opposite chest wall side (i.e., the main body 23 side) inside the imaging table 24. In the first grid 44, the boundary line 48 between the absorbing portion 46 and the transmitting portion 47 extends in a direction perpendicular to the moving direction of the tube 25A. Therefore, when imaging is performed by moving the tube 25A using the first grid 44, the central axis of the beam of radiation and the boundary line 48 are perpendicular to each other, so that there is a lot of vignetting of radiation. On the other hand, in the second grid 45, the boundary line 48 extends in a direction parallel to the moving direction of the tube 25A. Therefore, even if imaging is performed by moving the tube 25A, vignetting of radiation is less likely to occur. Therefore, in the contrast energy subtraction imaging for biopsy, the first grid 44 is placed at the retracted position, and the second grid 45 is placed at the imaging position.

[0076] 12, the second grid 45 is a so-called focusing grid. That is, in the second grid 45, the multiple boundary surfaces between the absorbing portion 46 and the transmitting portion 47 are not parallel, and the extended surfaces of the multiple boundary surfaces are inclined in a manner that they are focused into a single straight line that passes through the focal position F of the bulb 25A and is parallel to the boundary surfaces. In this example, the focal position F of the bulb 25A is disposed on the front end face 45A1 side of the second grid 45, so that the inclination angle of the multiple boundary surfaces gradually increases from the front end face 45A1 toward the rear. By making the second grid 45 such a focusing grid, vignetting of the radiation R is more suppressed than in a parallel grid in which the multiple boundary surfaces are parallel.

[0077] Next, a case where the tomosynthesis imaging mode is selected as the imaging mode will be described. As an example, as shown in Fig. 13, in tomosynthesis imaging, a radiation source is moved to perform tomography of the breast M. That is, in tomosynthesis imaging, imaging of the breast M is performed from a plurality of irradiation positions with different irradiation angles in order to obtain a tomographic image of the breast M. Projection images of the breast M from the plurality of irradiation positions obtained by tomosynthesis imaging are subjected to image reconstruction processing and used to generate a tomographic image of the breast M.

[0078] 14, as an example, the selection of an imaging mode by the user is accepted at the console 11. Here, tomosynthesis imaging is selected. The console 11 outputs selected mode information 56 to the breast imaging apparatus 10. That is, the console 11 outputs the result of accepting the selection of the imaging mode by the user.

[0079] In the processor 16A, the acquisition unit 16A1 acquires the selection mode information 56 from the console 11. The acquisition unit 16A1 also acquires a grid position table 58 from the NVM 16B. The position control unit 16A2 uses the grid position table 58 to derive a grid arrangement according to the shooting mode indicated by the selection mode information 56. Then, the position control unit 16A2 controls the drive mechanism 50 to achieve the derived grid arrangement.

[0080] In the example shown in FIG. 14, the tomosynthesis imaging mode is selected by the user, and therefore the first grid 44 and the second grid 45 are disposed at the retracted positions. In tomosynthesis imaging, unlike normal imaging or contrast energy subtraction imaging, the radiation dose reaching the radiation detector 26 is increased when imaging is performed without using a scatter reduction grid, and the quality of the radiation image is improved. In addition, in tomosynthesis imaging, the influence of contrast reduction due to scattered radiation is smaller than in normal imaging or contrast energy subtraction imaging. Therefore, in tomosynthesis imaging, imaging is performed with the first grid 44 and the second grid 45 disposed at the retracted positions. In this manner, the position control unit 16A2 controls the arrangement state of the first grid 44 and the second grid 45 inside the imaging table 24 in response to the imaging mode selected by the user.

[0081] Fig. 15 summarizes the imaging modes and grids used in breast imaging apparatus 10 according to this embodiment. As shown in Fig. 15, in normal imaging, first grid 44 is used. In first grid 44, boundary line 48 extends in the front-rear direction. The grids are arranged such that first grid 44 is placed at the imaging position and second grid 45 is placed at the retracted position.

[0082] In addition, in the case of diagnostic contrast energy subtraction imaging (i.e., diagnostic energy subtraction imaging), a first grid 44 is used. In the first grid 44, a boundary line 48 extends along the front-rear direction. The grids are arranged such that the first grid 44 is arranged at the imaging position and the second grid 45 is arranged at the retracted position.

[0083] In addition, in the case of biopsy contrast energy subtraction imaging (i.e., biopsy energy subtraction imaging), the second grid 45 is used. In the second grid 45, the boundary line 48 extends in the left-right direction (i.e., the moving direction of the tube 25A). The grids are arranged such that the first grid 44 is arranged at the retracted position and the second grid 45 is arranged at the imaging position.

[0084] In the case of tomosynthesis imaging, neither the first grid 44 nor the second grid 45 is used. The grid arrangement state is a state in which both the first grid 44 and the second grid 45 are arranged in the retracted positions. In this way, the grid arrangement state is changed according to the imaging mode selected by the user.

[0085] As described above, in the breast imaging device 10 according to the present embodiment, the first grid 44 and the second grid 45 are provided inside the imaging table 24 as anti-scatter grids. The first grid 44 and the second grid 45 are switchable between an imaging position and a retreated position according to imaging in each of a plurality of imaging modes. In the control device 16 of the breast imaging device 10, the acquisition unit 16A1 of the processor 16A acquires a result of accepting the selection of the imaging mode by the user. In addition, the position control unit 16A2 controls the arrangement state of the first grid 44 and the second grid 45 inside the imaging table 24 according to the selection of the imaging mode acquired by the acquisition unit 16A1. As a result, even in the breast imaging device 10 in which different types of anti-scatter grids are built inside the imaging table 24, it is possible to realize an appropriate arrangement of the anti-scatter grid according to the imaging mode selected by the user.

[0086] Furthermore, for example, since the first grid 44 and the second grid 45 can be arranged inside the imaging table 24, the anti-scatter grid can be arranged closer to the detection surface 26A of the radiation detector 26 than when the anti-scatter grid is arranged outside the imaging table 24, thereby improving the effect of eliminating scattered rays.

[0087] Furthermore, in the mammography device 10 according to this embodiment, in the anti-scatter grid, a plurality of transmitting portions 47 and a plurality of absorbing portions 46 are arranged alternately, and a boundary line 48 between the transmitting portions 47 and the absorbing portions 46 extends in one direction. The extension direction of the boundary line 48 in the first grid 44 and the extension direction of the boundary line 48 in the second grid 45 intersect with each other. This makes it possible to arrange an appropriate anti-scatter grid according to the imaging mode selected by the user, even if the directions of the boundary lines 48 in the first grid 44 and the second grid 45 are different from each other.

[0088] Furthermore, in the breast imaging apparatus 10 according to this embodiment, the direction in which the boundary line 48 of the first grid 44 extends is parallel to the front-rear direction, and the direction in which the boundary line 48 of the second grid 45 extends is parallel to the left-right direction. This makes it possible to arrange an appropriate anti-scatter grid according to the imaging mode selected by the user, even if the directions of the boundary lines 48 of the first grid 44 and the second grid 45 are perpendicular to each other.

[0089] In the mammography device 10 according to the present embodiment, the multiple imaging modes include a normal imaging mode in which imaging is performed with the radiation source 25 held at a position facing the imaging table 24 in the vertical direction. When the normal imaging mode is selected, the first grid 44 is placed at the imaging position, and the second grid 45 is placed at the retracted position. In the case of normal imaging, the anti-scatter grid is swung while the radiation source 25 is held at a position facing the imaging table 24. Thus, the first grid 44 whose boundary line 48 is oriented in the front-back direction (i.e., the depth direction of the imaging table) is used, while the second grid 45 whose boundary line 48 is oriented in the left-right direction is retracted. This allows an appropriate anti-scatter grid to be placed according to the imaging mode selected by the user.

[0090] In addition, in the breast imaging apparatus 10 according to the present embodiment, the multiple imaging modes include an imaging mode using diagnostic contrast energy subtraction imaging (i.e., diagnostic energy subtraction imaging mode). When the diagnostic energy subtraction imaging mode is selected, the first grid 44 is placed at the imaging position, and the second grid 45 is placed at the retracted position. In the case of diagnostic energy subtraction imaging, the anti-scatter grid is swung while the radiation source 25 is held at a position facing the imaging table 24. Therefore, the first grid 44 whose boundary line 48 is oriented in the front-back direction (i.e., the depth direction of the imaging table 24) is used, while the second grid 45 whose boundary line 48 is oriented in the left-right direction is retracted. This allows an appropriate anti-scatter grid to be placed according to the imaging mode selected by the user.

[0091] In addition, in the breast imaging device 10 according to the present embodiment, the multiple imaging modes include an imaging mode using contrast energy subtraction imaging for biopsy (i.e., biopsy energy subtraction imaging mode). When the biopsy energy subtraction imaging mode is selected, the second grid 45 is placed at the imaging position, and the first grid 44 is placed at the retreated position. In biopsy, in order to collect a lesion, the radiation source 25 is moved and stereo imaging is performed, thereby confirming the position of the lesion in the breast M three-dimensionally. In this case, the second grid 45 is stationary. Therefore, in the case of biopsy energy subtraction imaging, the second grid 45 whose boundary line 48 is oriented in the left-right direction is used. On the other hand, the first grid 44 whose boundary line 48 is oriented in the front-back direction is retreated. This allows an appropriate anti-scatter grid to be placed according to the imaging mode selected by the user.

[0092] In addition, the second grid 45 is a scatter-removal grid suitable for stereoscopic imaging. That is, when a biopsy is performed, stereoscopic imaging may be performed to grasp the position of the tissue to be biopsied in the breast M in three dimensions. In stereoscopic imaging, the irradiation position of the radiation R is changed in the left-right direction, and imaging is performed multiple times while changing the irradiation angle of the radiation R. According to this configuration, the second grid 45 can be arranged in a position in which the boundary line 48 of the absorbing portion 46 and the transmitting portion 47 of the second grid 45 extends parallel to the left-right direction. Therefore, compared to the case in which the boundary line 48 is arranged in a position parallel to the front-rear direction, it is possible to suppress vignetting of the effective radiation R (radiation other than scattered radiation) that is obliquely incident from the tube 25A to the imaging surface 24A. This is because, when the second grid 45 is arranged in a position in which the boundary line 48 extends parallel to the front-rear direction, the absorbing portion 46 extending parallel to the boundary line 48 intersects with the central axis of the flux of the radiation R connecting the focal point of the tube 25A and the imaging surface 24A. That is, since the moving direction of the bulb 25A and the extending direction of the absorbing portion 46 are perpendicular to each other, the absorbing portion 46 causes vignetting of the radiation R irradiated from the bulb 25A.

[0093] Furthermore, in a biopsy, stereo imaging and contrast energy subtraction imaging may be combined to obtain a breast image in which the biopsy target, which is densely packed with neovascularization, is emphasized. This configuration is particularly effective in such a case. In contrast energy subtraction imaging, the contrast is likely to decrease because the difference between two images captured with radiation of different energies is taken. In this configuration, the use of the second grid 45 suppresses the incidence of scattered radiation, so that the decrease in contrast can be suppressed. As a method for suppressing the decrease in contrast, it is possible to increase the gain of the signal output by the radiation detector 26 in the image correction process. However, since increasing the gain also increases noise, the method using the second grid 45 is preferable.

[0094] In addition, in the breast imaging apparatus 10 according to this embodiment, the multiple imaging modes include a tomosynthesis imaging mode in which tomography of the breast M is performed while moving the radiation source 25. When the tomosynthesis imaging mode is selected, both the first grid 44 and the second grid 45 are placed in the retracted position. In tomosynthesis imaging, the influence of scattered radiation on the imaging results is small compared to other imaging methods, so an anti-scatter grid is not used. Therefore, the first grid 44 and the second grid 45 are placed in the retracted position. This allows an appropriate anti-scatter grid to be placed according to the imaging mode selected by the user.

[0095] Furthermore, in the mammography apparatus 10 according to this embodiment, the first grid 44 and the second grid 45 move linearly between the imaging position and the retracted position inside the imaging table 24. Because the anti-scatter grid moves linearly inside the imaging table 24, this contributes to a smaller size of the imaging table 24 compared to rotational movement. In particular, when the linear movement is along the front-rear direction, the space in the depth direction of the imaging table 24 can be used effectively.

[0096] In addition, in the breast imaging apparatus 10 according to this embodiment, in the processor 16A of the control device 16, the output unit 16A3 outputs the arrangement state of the first grid 44 and the second grid 45 inside the imaging stand 24 to the display 11B1. The arrangement state of the first grid 44 and the second grid 45 is displayed on the screen of the display 11B1. The user can confirm the arrangement state of the first grid 44 and the second grid 45 inside the imaging stand 24 by visually checking the screen of the display 11B1. This makes it easy for the user to grasp the arrangement of the anti-scatter grid inside the imaging stand 24.

[0097] (Modification) In the above embodiment, the breast imaging device 10 is described by taking an example in which one of the multiple imaging modes is executed, but the technology of the present disclosure is not limited to this. In this modification, the imaging modes include a continuous imaging mode in which two or more of the multiple imaging modes are executed consecutively.

[0098] As an example, as shown in Fig. 16, the console 11 accepts the selection of an imaging mode by the user. Here, continuous imaging is selected. As an example of continuous imaging, normal imaging, tomosynthesis imaging, and biopsy energy-sub-imaging are taken consecutively in this order. The console 11 outputs selected mode information 56 to the breast imaging device 10. That is, the console 11 outputs the result of accepting the selection of the imaging mode by the user.

[0099] In the processor 16A, the acquisition unit 16A1 acquires the selection mode information 56 from the console 11. The acquisition unit 16A1 also acquires a grid position table 58 from the NVM 16B. The position control unit 16A2 uses the grid position table 58 to derive a grid arrangement according to the imaging mode indicated by the selection mode information 56. Here, the grid position table 58 indicates a grid arrangement for normal imaging and a grid arrangement for tomosynthesis imaging. Then, the position control unit 16A2 controls the drive mechanism 50 to achieve the derived grid arrangement according to each imaging mode in the continuous imaging.

[0100] In the example shown in FIG. 16, the continuous imaging mode is selected by the user. First, grid arrangement according to the normal imaging mode is performed. That is, the first grid 44 is arranged at the imaging position, and the second grid 45 is arranged at the retreat position. After imaging of the breast M in the normal imaging mode, grid arrangement according to the tomosynthesis imaging mode is performed. That is, the first grid 44 and the second grid 45 are arranged at the retreat position. Then, after imaging of the breast M in the tomosynthesis imaging mode, grid arrangement according to the biopsy energy sub-imaging mode is performed. That is, the first grid 44 is arranged at the retreat position, and the second grid 45 is arranged at the imaging position. In this way, the position control unit 16A2 controls the arrangement state of the first grid 44 and the second grid 45 inside the imaging table 24 according to each imaging mode of the continuous imaging mode. That is, the arrangement state of the first grid 44 and the second grid 45 is changed according to each imaging mode of the continuous imaging mode.

[0101] In the continuous imaging mode, imaging can be performed in each mode in the continuous imaging mode while the breast M remains compressed between the imaging table 24 and the compression plate 30A. In other words, imaging is performed during the continuous imaging mode without changing the compression height (i.e., the height of the compression plate 30A relative to the imaging table 24). In the example shown in Fig. 16, normal imaging, tomosynthesis imaging, and biopsy energy-sub imaging are performed consecutively while the breast M remains compressed.

[0102] As described above, in the mammography device 10 according to this modification, the imaging modes include a continuous imaging mode. The continuous imaging mode is an imaging mode in which, for example, normal imaging, tomosynthesis imaging, and biopsy energy-subimaging are performed in this order. The position controller 16A2 controls the arrangement of the first grid 44 and the second grid 45 according to each imaging mode of the continuous imaging mode. That is, in the continuous imaging mode in which a plurality of imaging modes are combined, the arrangement of the first grid 44 and the second grid 45 is controlled according to each mode. This allows an appropriate anti-scatter grid to be arranged according to the imaging mode selected by the user even in the continuous imaging mode.

[0103] For example, when a user selects a different shooting mode after shooting in a certain shooting mode, the user must select the shooting mode each time. In this configuration, if the user selects the continuous shooting mode, shooting in a plurality of shooting modes is performed continuously, so that the user's workload (e.g., the workload of selecting and confirming the mode) is reduced.

[0104] Furthermore, in the breast imaging apparatus 10 according to this modification, imaging can be performed in each imaging mode of the continuous imaging mode while the breast M is compressed by the compression plate 30A in the continuous imaging mode. Therefore, imaging is performed in each imaging mode of the continuous imaging mode under the same conditions without changing the compression conditions of the breast M. As a result, even when imaging is performed in different imaging modes, the compression conditions are the same, which facilitates tasks such as comparing radiation images.

[0105] In the above modification, an example in which normal imaging, tomosynthesis imaging, and biopsy energy-sub-imaging are performed in succession in this order as the continuous imaging mode has been described, but the technology of the present disclosure is not limited to this. For example, the continuous imaging mode may be a combination of any two or more of normal imaging, tomosynthesis imaging, diagnostic energy-sub-imaging, and biopsy energy-sub-imaging. In addition, the order in which each imaging mode is performed in the continuous imaging mode is not particularly limited.

[0106] In the above embodiment, an example in which the arrangement state of the physical anti-scatter grid is controlled is described, but the technology of the present disclosure is not limited to this. For example, it may be possible to select an imaging method (so-called virtual grid) that removes the influence of scattered rays by image processing without using a physical anti-scatter grid (e.g., the first grid 44 and the second grid 45). In this case, the technology described in Japanese Patent No. 6006193 can be adopted as a method for removing scattered rays.

[0107] In the above embodiment, an example in which the radiation source 25 moves along the left-right direction has been described, but the technology of the present disclosure is not limited to this. In this case, the boundary line 48 of the second grid 45 is aligned along the movement direction of the radiation source 25 (a direction other than the left-right direction), and the boundary line 48 of the first grid 44 extends in a direction perpendicular to the boundary line 48 of the second grid 45.

[0108] In the above embodiment, an example in which the boundary lines 48 of the first grid 44 and the second grid 45 are perpendicular to each other has been described, but the technology of the present disclosure is not limited to this. For example, the boundary lines 48 of the first grid 44 and the second grid 45 may intersect in a manner other than perpendicular to each other.

[0109] In the above embodiment, an example has been described in which the directions of the boundary line 48 are different between the first grid 44 and the second grid 45, but the technology of the present disclosure is not limited to this. For example, the grid densities of the first grid 44 and the second grid 45 may be different.

[0110] In the above embodiment, an example has been described in which two anti-scatter grids, the first grid 44 and the second grid 45, are provided inside the imaging table 24, but the technology of the present disclosure is not limited to this. For example, three or more anti-scatter grids may be provided inside the imaging table 24.

[0111] In the above embodiment, an example has been described in which the console 11 is separate from the mammography apparatus 10, but the technology of the present disclosure is not limited to this. For example, the console 11 may be integrated with the mammography apparatus 10.

[0112] In the above embodiment, an example in which stereo imaging and contrast energy subtraction imaging are combined is described, but the technology of the present disclosure is not limited to this. For example, a configuration in which only stereo imaging is performed may be used.

[0113] In the above embodiment, an example in which stereoscopic imaging is performed by moving radiation source 25 in the left-right direction has been described, but the technology of the present disclosure is not limited to this. For example, radiation source 25 may be a so-called multi-ray source that includes a plurality of tubes arranged in the left-right direction and irradiates radiation R from each of the tubes. In a multi-ray source, since a plurality of tubes are arranged in the left-right direction, it is possible to perform stereoscopic imaging by using, for example, the tubes at both ends in the left-right direction.

[0114] The above description and illustrations are detailed descriptions of the parts related to the technology of the present disclosure, and are merely an example of the technology of the present disclosure. For example, the above description of the configuration, function, action, and effect is an example of the configuration, function, action, and effect of the parts related to the technology of the present disclosure. Therefore, it goes without saying that unnecessary parts may be deleted, new elements may be added, or replacements may be made to the above description and illustrations, within the scope of the gist of the technology of the present disclosure. In addition, in order to avoid confusion and to facilitate understanding of the parts related to the technology of the present disclosure, the above description and illustrations omit explanations of technical common sense that do not require explanation in order to enable the implementation of the technology of the present disclosure.

[0115] All publications, patent applications, and standards mentioned in this specification are herein incorporated by reference to the same extent as if each individual publication, patent application, or standard was specifically and individually indicated to be incorporated by reference.

[0116] The following supplementary notes are further disclosed regarding the above embodiment.

[0117] <Appendix 1> an imaging table on which a breast of a subject is placed and which accommodates a detector for detecting radiation that has passed through the breast; a processor; a first grid and a second grid are provided inside the imaging table, the first grid and the second grid being switchable between an imaging position and a retreat position in accordance with imaging in each of a plurality of imaging modes; the first grid and the second grid are switchable between an imaging position and a retreat position in accordance with imaging in each of a plurality of imaging modes; The processor is Acquire a result of accepting a shooting mode selection by a user; Controlling the arrangement of the first grid and the second grid inside the imaging stand in accordance with the acquired selection of the imaging mode. Mammography equipment. <Appendix 2> in the anti-scatter grid, a plurality of transmitting portions that transmit the radiation and a plurality of absorbing portions that absorb the radiation are arranged alternately, and a boundary line between the transmitting portions and the absorbing portions extends in one direction; The direction in which the boundary lines in the first grid extend and the direction in which the boundary lines in the second grid extend cross each other. 2. A mammography apparatus as described in claim 1. <Appendix 3> In the above-mentioned imaging table, a direction connecting the chest wall side where the subject's chest wall is located and the opposite side of the chest wall is defined as a front-back direction, and a direction perpendicular to the front-back direction is defined as a left-right direction. The first grid has a direction in which the boundary line extends parallel to the front-rear direction, The second grid has a boundary line extending in a direction parallel to the left-right direction. 3. A mammography apparatus as described in claim 2. <Appendix 4> the plurality of imaging modes includes a normal imaging mode in which imaging is performed while a radiation source is held at a position facing the imaging table, When the normal shooting mode is selected, the first grid is disposed at the shooting position, and the second grid is disposed at the retracted position. 4. A breast imaging apparatus according to any one of claims 1 to 3. <Appendix 5> the plurality of imaging modes includes a first contrast imaging mode which is an imaging mode for diagnosis by contrast energy subtraction; When the first contrast imaging mode is selected, the first grid is placed at the imaging position, and the second grid is placed at the retracted position. 4. A breast imaging apparatus according to any one of claims 1 to 3. <Appendix 6> The plurality of imaging modes includes a second contrast imaging mode which is an imaging mode for biopsy by contrast energy subtraction; When the second contrast imaging mode is selected, the second grid is placed at the imaging position, and the first grid is placed at the retracted position. 4. A breast imaging apparatus according to any one of claims 1 to 3. <Appendix 7> the plurality of imaging modes includes a tomosynthesis imaging mode for performing tomographic imaging of the breast by moving a radiation source; When the tomosynthesis imaging mode is selected, both of the first grid and the second grid are placed at the retracted position. 4. A breast imaging apparatus according to any one of claims 1 to 3. <Appendix 8> The plurality of imaging modes includes a continuous imaging mode in which at least two of the normal imaging mode, the second contrast imaging mode, and the tomosynthesis imaging mode are performed consecutively in any order; In the continuous imaging mode, the arrangement states of the first grid and the second grid are changed according to each of the normal imaging mode, the second contrast imaging mode, and the tomosynthesis imaging mode. 8. A mammography apparatus as claimed in claim 4, claim 6 and claim 7. <Appendix 9> In the continuous imaging mode, imaging can be performed in each mode while the breast is kept compressed between the imaging table and the compression plate. 9. A mammography apparatus as described in claim 8. <Appendix 10> Within the imaging stand, the first grid and the second grid are moved linearly between the imaging position and the retracted position. 10. A mammography apparatus according to any one of claims 1 to 9. <Appendix 11> The processor is capable of outputting an arrangement state of the first grid and the second grid inside the imaging stand to a notification unit. 11. A mammography apparatus according to any one of claims 1 to 10. [Explanation of symbols]

[0118] 10 Mammography equipment 11 Console 11A Reception device 11A1 Mouse 11B Output device 11B1 Display 16 Control device 16A Processor 16A1 Acquisition Department 16A2 Position control unit 16A3 Output section 16B NVM 16C RAM 16D External I / F 16E Bus 20 Stand 20A Pedestal 20B Post 21 Arm 22 Radiation source housing 23 Main body 24 Photo stand 24A Shooting surface 24B Shooting location 24C Evacuation position 25 Radiation source 25A tube 26 Radiation Detector 26A Detection surface 27 Handrail 28 Rail 30,30A Compression plate 31 Irradiation field limiter 32 Face Guard 33 Support Arm 34 Moving parts 35 Moving mechanism 37 Protective cover 37A Protective materials 37B Front wall 37C Rear end 39 Biopsy Unit 40 Main body 41 Adjustment part 42 Needle holding part 43 Puncture needle 44 First Grid 45 Second Grid 46 Absorption section 47 Transparent part 48 Border 50 Drive mechanism 50A Motor Driver 50B Motor 50C Encoder 52 Position control program 54 Pointer 56 Selection mode information 58 Grid Location Table A. Subject F Focus position R Radiation M Breast X,Y,Z Arrows

Claims

1. an imaging table on which a breast of a subject is placed and which accommodates a detector for detecting radiation that has passed through the breast; a processor; a first grid and a second grid are provided inside the imaging table, the first grid and the second grid being switchable between an imaging position and a retreat position in accordance with imaging in each of a plurality of imaging modes; and The processor, Acquire a result of accepting a shooting mode selection by a user; Controlling the arrangement state of the first grid and the second grid inside the imaging stand in response to the acquired selection of the imaging mode. Mammography equipment.

2. in the anti-scatter grid, a plurality of transmitting portions that transmit the radiation and a plurality of absorbing portions that absorb the radiation are arranged alternately, and a boundary line between the transmitting portions and the absorbing portions extends in one direction; The direction in which the boundary line in the first grid extends and the direction in which the boundary line in the second grid extends intersect with each other.

2. The mammography apparatus of claim 1.

3. In the case where, on the imaging stand, a direction connecting the chest wall side where the subject's chest wall is located and the opposite side of the chest wall is defined as a front-back direction, and a direction perpendicular to the front-back direction is defined as a left-right direction, The first grid has a direction in which the boundary line extends parallel to the front-rear direction, The second grid has a direction in which the boundary line extends parallel to the left-right direction.

3. The mammography apparatus according to claim 2.

4. the plurality of imaging modes includes a normal imaging mode in which imaging is performed while a radiation source is held at a position facing the imaging table, When the normal shooting mode is selected, the first grid is disposed at the shooting position, and the second grid is disposed at the retracted position.

4. The mammography apparatus according to claim 3.

5. the plurality of imaging modes includes a first contrast imaging mode which is an imaging mode for diagnosis by contrast energy subtraction; When the first contrast imaging mode is selected, the first grid is placed at the imaging position, and the second grid is placed at the retracted position.

4. The mammography apparatus according to claim 3.

6. the plurality of imaging modes includes a second contrast imaging mode which is an imaging mode for biopsy by contrast energy subtraction; When the second contrast imaging mode is selected, the second grid is placed at the imaging position, and the first grid is placed at the retracted position.

4. The mammography apparatus according to claim 3.

7. the plurality of imaging modes includes a tomosynthesis imaging mode for performing tomographic imaging of the breast by moving a radiation source; When the tomosynthesis imaging mode is selected, both of the first grid and the second grid are disposed at the retracted position.

4. The mammography apparatus according to claim 3.

8. the plurality of imaging modes includes a continuous imaging mode in which at least two of the normal imaging mode, the second contrast imaging mode, and the tomosynthesis imaging mode are performed consecutively in any order; In the continuous imaging mode, the arrangement states of the first grid and the second grid are changed depending on each of the normal imaging mode, the second contrast imaging mode, and the tomosynthesis imaging mode.

8. A mammography apparatus according to claim 4, claim 6, or claim 7.

9. In the continuous imaging mode, imaging can be performed in each mode while the breast is kept compressed between the imaging table and the compression plate.

9. The mammography apparatus according to claim 8.

10. Within the imaging stand, the first grid and the second grid are moved linearly between the imaging position and the retracted position.

2. The mammography apparatus of claim 1.

11. The processor is capable of outputting an arrangement state of the first grid and the second grid inside the imaging stand to a notification unit.

2. The mammography apparatus of claim 1.

Images