Information processing device

Abstract

To properly project an image showing a radiation dose measurement region of a radiation imaging apparatus to a surface of a subject.SOLUTION: An information processing device for controlling an image showing a radiation dose measurement region of a radiation imaging apparatus for generating a radiation image of a subject to be projected to a surface of the subject includes: correction means for correcting a position and a size of an image showing the radiation dose measurement region in accordance with positional information of the subject; and generation means for generating an image showing the radiation dose measurement region to be projected to the surface of the subject in accordance with correction by the correction means.SELECTED DRAWING: Figure 7

Description

[Technical field]

[0001] The present disclosure relates to an information processing device, a radiation imaging system, a processing method for an information processing device, and a processing method and program for a radiation imaging system. [Background technology]

[0002] Radiation imaging devices with an Automatic Exposure Control (AEC) function are known. Such radiation imaging devices measure the amount of radiation during irradiation and can terminate the irradiation of radiation depending on the result. By incorporating an AEC function in a radiation imaging device, portability is improved, radiography becomes possible, and the number of imaging situations in which AEC can be used, such as in a mobile medical cart, is increased.

[0003] In AEC imaging, the radiation dose measurement area is limited to the area of ​​interest. At this time, the positions of the dose measurement region and the region of interest must match. Patent Document 1 discloses a method for confirming the positions of the dose measurement region and the region of interest. [Prior art documents] [Patent documents]

[0004] [Patent Document 1] JP 2018-50828 A Summary of the Invention [Problem to be solved by the invention]

[0005] Patent Document 1 describes a method of projecting a dose measurement region onto a radiation imaging device using a projector or the like. However, if a subject is located between the radiation imaging device and the radiation irradiation tube, the thickness of the subject is not taken into consideration, and the dose measurement region is projected at a position shifted from the position where it is actually desired to project the region.

[0006] This causes problems such as being unable to confirm whether the subject is in the correct position relative to the radiation imaging device, being unable to confirm whether the left / right, top / bottom positions of the subject are correct, and the position of the region of interest within the subject may shift from the dose measurement region of the radiation imaging device.

[0007] An object of the present disclosure is to enable an image indicating a dose measurement region of a radiation imaging device to be appropriately projected onto the surface of a subject. [Means for solving the problem]

[0008] The information processing device controls the projection of an image indicating a dose measurement area of ​​a radiation imaging device that generates a radiation image of a subject onto the surface of the subject, and has a correction means that corrects the position and size of the image indicating the dose measurement area in accordance with position information of the subject, and a generation means that generates an image indicating the dose measurement area to be projected onto the surface of the subject in accordance with the correction by the correction means. Effect of the Invention

[0009] According to the present disclosure, an image showing a dose measurement region of a radiation imaging device can be appropriately projected onto the surface of a subject. [Brief description of the drawings]

[0010] [Figure 1] FIG. 1 is a diagram illustrating an example of the configuration of a radiation imaging system. [Diagram 2] FIG. 13 is a diagram showing a state before the position of a dose measurement region is corrected. [Diagram 3] FIG. 1 is a diagram illustrating an example of the configuration of a radiation imaging apparatus. [Figure 4] FIG. 2 is a diagram illustrating an example of the configuration of an amplifier unit of a radiation imaging apparatus. [Diagram 5] 1 is a block diagram showing an example of a functional configuration of a radiation imaging apparatus; [Figure 6] FIG. 2 is a block diagram showing an example of a functional configuration of a console. [Figure 7] 13A and 13B are diagrams illustrating a calculation method for correcting the position of a dose measurement region and the position after the correction. [Figure 8] 13 is a flowchart showing a position correction process. [Figure 9] 13A and 13B are diagrams illustrating a calculation method for correcting the position of a dose measurement region and the position after the correction. [Figure 10] 13 is a flowchart showing a position correction process. [Figure 11] FIG. 1 is a diagram illustrating an example of the configuration of a radiation imaging system. [Figure 12] 13A and 13B are diagrams illustrating a calculation method for correcting the position of a dose measurement region and the position after the correction. [Figure 13] 13 is a flowchart showing a position correction process. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0011] Preferred embodiments will be described below with reference to the drawings. Note that the following embodiments do not limit the scope of the claims, and all of the combinations of features described in the embodiments are not necessarily essential solutions.

[0012] (First embodiment) 1 is a diagram showing an example of the configuration of a radiation imaging system 100 according to the first embodiment. The radiation imaging system 100 includes a radiation imaging apparatus 10, a control apparatus 20, a radiation generating apparatus 30, a console 40, a radiation tube 50, and a projector 60. The radiation imaging apparatus 10 includes a dose measurement area 70.

[0013] The radiation imaging device 10 can be operated using a battery and can communicate over both a wireless network and a wired network. Fig. 1 shows a configuration for wired network communication. The radiation imaging device 10 is connected to a control device 20 via a wired network.

[0014] A plurality of dose measurement regions 70, which are regions for measuring the radiation dose, are arranged in the radiation imaging device 10. The user specifies one or more dose measurement regions 70 to be used before imaging. The user may not explicitly select a dose measurement region 70, but may specify a dose measurement region 70 associated with a region to be imaged, etc. Information on the selected dose measurement region 70 is notified from the radiation imaging device 10 to the console 40.

[0015] The control device 20 and the console 40 are also connected to each other via a wired network. The radiation imaging apparatus 10, the control device 20, and the console 40 are capable of communicating with each other.

[0016] The control device 20 and the radiation generation device 30 are connected by a dedicated line and communicate radiation irradiation requests, radiation irradiation permission, radiation irradiation stop, etc. During AEC imaging, the radiation imaging device 10 measures the radiation dose in the dose measurement area 70, and when the dose reaches a predetermined dose, transmits a radiation irradiation stop instruction to the control device 20. The control device 20 then instructs the radiation generation device 30 to stop radiation irradiation, and the radiation generation device 30 stops the radiation irradiation from the radiation tube 50.

[0017] The radiation tube 50 irradiates radiation to the radiation imaging device 10 through the subject 11. Furthermore, the projector 60 projects an image output from the console 40. The radiation tube 50 and the projector 60 are disposed at positions close to each other.

[0018] After the radiation irradiation is stopped, the radiation imaging device 10 generates image data from the distribution of the radiation dose, and transmits the image data to the console 40 via the control device 20. The console 40 displays the received image data.

[0019] Here, an example is shown in which a wired network and a dedicated line are connected, but this is not limiting. Various wired communications (Ethernet, UART, I2C, CAN, etc.) and wireless communications (wireless LAN, Bluetooth, UWB, infrared, ZigBee, NFC, public wireless, etc.) may also be used.

[0020] Fig. 2(a) is a plan view seen from above when the projector 60 projects an image of the dose measurement region 70 onto the subject 11 and the radiation imaging device 10. Fig. 2(b) is a front view seen from the front (projector 60 side) when the projector 60 projects an image of the dose measurement region 70 onto the subject 11 and the radiation imaging device 10. An image 71 of the dose measurement region 70 is projected onto the surface of the subject 11. Therefore, the image 71 of the dose measurement region 70 is closer to the center of the subject 11 and displayed in a smaller size than the dose measurement region 70.

[0021] 3 is a diagram showing an example of the configuration of the radiation imaging device 10. The radiation imaging device 10 includes an imaging region IR, a power supply circuit 140, a drive circuit 150, a readout circuit 160, a signal processing unit 170, a control unit 180, and a notification unit 190.

[0022] The imaging region IR has a plurality of pixels arranged to form a plurality of rows and a plurality of columns, a plurality of drive lines 110, and a plurality of signal lines 120. The plurality of drive lines 110 are arranged corresponding to the plurality of rows of pixels, and each drive line 110 corresponds to one of the pixel rows. The plurality of signal lines 120 are arranged corresponding to the plurality of columns of pixels, and each signal line 120 corresponds to one of the pixel columns.

[0023] The plurality of pixels includes a plurality of imaging pixels 101 used to acquire a radiation image, and one or more detection pixels 104 used to monitor the amount of radiation exposure.

[0024] The imaging pixel 101 includes a conversion element 102 that converts radiation into an electrical signal, and a switch element 103 that connects the conversion element 102 to a signal line 120 corresponding to a column of the imaging pixel 101 .

[0025] The detection pixel 104 includes a conversion element 105 that converts radiation into an electric signal, and a switch element 106 that connects the conversion element 105 to a signal line 120 corresponding to a column of the detection pixel 104. The detection pixel 104 is arranged so as to be included in a row and a column formed by a plurality of imaging pixels 101. In Fig. 1 and the subsequent figures, the imaging pixels 101 and the detection pixels 104 are distinguished from each other by applying different hatching to the conversion elements 102 and the conversion elements 105.

[0026] The conversion element 102 and the conversion element 105 may be composed of a scintillator that converts radiation into light and a photoelectric conversion element that converts light into an electrical signal. The scintillator is generally formed in a sheet shape so as to cover the imaging region IR and is shared by a plurality of pixels. Alternatively, the conversion element 102 and the conversion element 105 may be composed of a conversion element that directly converts radiation into an electrical signal.

[0027] The switch element 103 and the switch element 106 each include a thin film transistor (TFT) whose active region is made of a semiconductor such as amorphous silicon or polycrystalline silicon.

[0028] A first electrode of the conversion element 102 is connected to a first main electrode of the switch element 103, and a second electrode of the conversion element 102 is connected to a bias line 130. One bias line 130 extends in the column direction and is commonly connected to second electrodes of a plurality of conversion elements 102 arranged in the column direction. The bias line 130 receives a bias voltage Vs from a power supply circuit 140. Second main electrodes of the switch elements 103 of one or more imaging pixels 101 included in one column are connected to one signal line 120. Control electrodes of the switch elements 103 of one or more imaging pixels 101 included in one row are connected to one drive line 110.

[0029] A first electrode of the conversion element 105 is connected to a first main electrode of the switch element 106, and a second electrode of the conversion element 105 is connected to a bias line 130. A second main electrode of the switch element 106 is connected to one signal line 120. A control electrode of the switch element 106 is connected to one drive line 110.

[0030] The detection pixel 104 has the same pixel configuration as the imaging pixel 101, and is connected to a corresponding drive line 110 and a corresponding signal line 120. The imaging pixel 101 and the detection pixel 104 may be connected to the same signal line 120.

[0031] The drive circuit 150 is configured to supply drive signals to the pixels to be driven through the multiple drive lines 110 in accordance with control signals from the control unit 180. In this embodiment, the drive signals are signals for turning on the switch elements 103 and 106 included in the pixels to be driven. The switch elements 103 and 106 of each pixel are turned on by a high-level signal and turned off by a low-level signal. For this reason, this high-level signal is called a drive signal.

[0032] When a driving signal is supplied to a pixel, the signals stored in the conversion elements 102 and 105 of the pixel become available for reading by the readout circuit 160. When the driving line 110 is connected to the detection pixel 104, the driving line 110 is called a detection driving line 111.

[0033] The readout circuit 160 is configured to read out signals from a plurality of pixels through a plurality of signal lines 120. The readout circuit 160 includes a plurality of amplifiers 161, a multiplexer 162, and an analog-to-digital converter (hereinafter, referred to as an AD converter) 163.

[0034] Each of the multiple signal lines 120 is connected to a corresponding one of the multiple amplifiers 161 in the read circuit 160. One signal line 120 corresponds to one amplifier 161.

[0035] The multiplexer 162 selects the multiple amplifiers 161 one by one in a predetermined order, and supplies a signal from the selected amplifier 161 to an AD converter 163. The AD converter 163 converts the supplied signal into a digital signal and outputs it to the signal processing unit 170.

[0036] The signals read out from the imaging pixels 101 are supplied to the signal processing unit 170, which performs processes such as calculation and storage on the signals. Specifically, the signal processing unit 170 includes a calculation unit 171 and a storage unit 172. The calculation unit 171 generates a radiographic image based on the signals read out from the imaging pixels 101, and supplies the radiographic image to the control unit 180.

[0037] The signals read out from the detection pixels 104 are supplied to the signal processing unit 170, which performs processing such as calculation and storage on the signals. Specifically, the signal processing unit 170 outputs information indicating irradiation of radiation to the radiation imaging device 10, based on the signals read out from the detection pixels 104. For example, the signal processing unit 170 detects irradiation of radiation to the radiation imaging device 10, and determines the irradiation dose and / or the accumulated irradiation dose of radiation.

[0038] The control unit 180 controls the drive circuit 150 and the readout circuit 160 based on information from the signal processing unit 170. The control unit 180 controls, for example, the start and end of exposure (accumulation of charges corresponding to irradiated radiation by the imaging pixels 101) based on information from the signal processing unit 170.

[0039] In order to determine the radiation exposure dose, the control unit 180 controls the drive circuit 150 to scan only the detection drive lines 111 and make only the signals of the detection pixels 104 readable. Next, the control unit 180 controls the readout circuit 160 to read out signals of columns corresponding to the detection pixels 104 and output them as information indicating the radiation exposure dose. Through such an operation, the radiation imaging device 10 can obtain exposure information of the detection pixels 104 during radiation exposure.

[0040] Fig. 4 is a circuit diagram showing a configuration example of the amplifier 161 of Fig. 3. The amplifier 161 includes a differential amplifier circuit AMP and a sample-and-hold circuit SH. The differential amplifier circuit AMP amplifies a signal appearing on the signal line 120 and outputs the amplified signal.

[0041] The control unit 180 can reset the potential of the signal line 120 by supplying a control signal φR to the switch element of the differential amplifier circuit AMP. The output from the differential amplifier circuit AMP can be held by a sample-and-hold circuit SH. The control unit 180 causes the sample-and-hold circuit SH to hold a signal by supplying a control signal φSH to the switch element of the sample-and-hold circuit SH. The signal held in the sample-and-hold circuit SH is read out by the multiplexer 162 in FIG. 3.

[0042] 5 is a diagram showing an example of the functional configuration of the radiation imaging apparatus 10. The radiation imaging apparatus 10 includes a dose measurement unit 201, a radiation irradiation stopping unit 202, an image forming unit 203, and a communication unit 204.

[0043] The dose measurement unit 201 measures radiation. The radiation irradiation stop unit 202 issues an instruction to stop radiation irradiation based on the result of measurement by the dose measurement unit 201. The image formation unit 203 forms an image from the received radiation. The communication unit 204 transmits and receives commands to and from external devices and transmits images.

[0044] The communication unit 204 is not limited to Ethernet, but may be any other communication device capable of communicating with the outside, such as Bluetooth, infrared, or UWB (Ultra-Wide Band) wireless communication.

[0045] The radiation imaging device 10 has one or more dose measurement regions 70 shown in Fig. 1 and Fig. 2. Each of the dose measurement regions 70 has imaging pixels 101 and detection pixels 104 shown in Fig. 3, corresponds to an imaging portion (region of interest) of a subject, and is a region in which a radiation dose is measured.

[0046] The radiation generating device 30 controls the radiation tube 50 to irradiate the radiation imaging device 10 with radiation via the subject 11. Then, the imaging pixels 101 and detection pixels 104 of the radiation imaging device 10 convert the radiation into electrical signals.

[0047] The dosimetry unit 201 corresponds to the signal processing unit 170 in Fig. 3. The dosimetry unit 201 periodically reads out signals from the detection pixels 104 in the dose measurement region 70, and measures the radiation dose in the dose measurement region 70 based on the signals. Then, the dosimetry unit 201 calculates an integrated value of the measured dose.

[0048] The radiation irradiation stopping unit 202 corresponds to the control unit 180 in FIG. 3, and outputs a radiation irradiation stopping signal to the radiation generating device 30 via the control device 20 when the integrated value of the dose calculated by the dose measuring unit 201 reaches a target value.

[0049] When the radiation generation device 30 receives the radiation irradiation stop signal, it controls the radiation tube 50 to stop irradiating radiation.

[0050] The image forming section 203 corresponds to the signal processing section 170 in Fig. 3. After the radiation irradiation is stopped, the image forming section 203 reads out signals from the imaging pixels 101 and generates a radiographic image based on the signals.

[0051] Fig. 6 is a diagram showing an example of the configuration of the console 40 in Fig. 1. The console 40 is an example of an information processing device, and includes a control unit 301, a distance input unit 302, a generation unit 304, and a correction unit 305. A display unit 303 and an operation unit 306 are connected to the console 40.

[0052] The control unit 301 communicates with the radiation imaging apparatus 10, and controls state transition instructions for imaging and image reception.

[0053] Distance input unit 302 has a function of inputting distances such as the distance to subject 11 and the body thickness of subject 11. The distance may be measured by geometric calculation based on the relationship between a measuring tape provided with radiation tube 50 or the angle and length of an arm connected to radiation tube 50, the position at the time of installation, and the position of a standing pedestal or lying pedestal on which radiation imaging device 10 is set. Alternatively, distance may be measured using a laser. Alternatively, distance may be calculated from image data acquired by a visible light camera, and the method of measuring distance is not limited.

[0054] The measured distance may be input to the distance input unit 302 by directly communicating data from the distance measuring device, or may be input via the operation unit 306 such as a keyboard.

[0055] The display unit 303 displays a screen for issuing control instructions for the radiation imaging apparatus 10 and a screen for displaying captured images.

[0056] The generation unit 304 generates an image 71 including the dose measurement region 70 to be projected by the projector 60 .

[0057] 2(a) and (b), the correction unit 305 corrects the image 71 of the dose measurement region 70 projected onto the subject 11 so that the image 71 is positioned at the same position as the dose measurement region 70 of the radiation imaging device 10. A specific correction method will be described later.

[0058] The operation unit 306 is used to operate the screen of the display unit 303 using a mouse, a keyboard, a touch panel, or the like.

[0059] FIG. 7 is a diagram showing a calculation method for position correction performed by the correction unit 305 in FIG. 6 and a position after correction, and is a diagram obtained by cutting out the upper half of the plan view in FIG. 2(a).

[0060] When an image of the dose measurement region 70 is projected from the projector 60 onto the radiation imaging device 10, if the image is set to be in the same position as the dose measurement region 70, then if a subject 402 is present, an image 71 of the dose measurement region 70 is projected onto the subject 402. The subject 402 is, for example, a human body.

[0061] Correction unit 305 corrects the position of image 71 so that image 401 is projected at the position of image 401 on subject 402. Image 71 is the image before correction, and image 401 is the image after correction.

[0062] This position correction allows the photographer to grasp the position of the dose measurement region 70 of the radiation imaging device 10 hidden by the subject 402 when aligning the subject 402, making the alignment easier.

[0063] This is particularly effective for alignment when an internal organ of the subject 402 to be confirmed is located near the radiation imaging device 10. In addition, when multiple dose measurement regions 70 are enabled, this is effective for overall position adjustment by aligning the left and right and top and bottom of multiple images 71.

[0064] Here, "a" is the distance from the center position of the radiation imaging device 10 to the side of the target in the dose measurement region 70, and is a value that can be determined from the design value of the radiation imaging device 10. "b" is the distance from the position where the side of the target in the image 401 is projected onto the radiation imaging device 10 to the center position of the radiation imaging device 10 when radiation or light is irradiated from the radiation tube 50 or the projector 60 and corrected from the position of the image 71 to the position of the image 401. "c" is a value obtained by subtracting a from b.

[0065] “d1” is the distance between the radiation tube 50 or the projector 60 and the surface of the subject 402. “d2” is the body thickness of the subject 402, and is the distance between the surface of the subject 402 and the surface of the radiation imaging device 10.

[0066] "b" can be calculated as (d1+d2)×a / d1. "c" can be calculated as ba(=d2×a / d1).

[0067] Further, auxiliary lines 411 , 412 and 413 are auxiliary lines which indicate the paths of irradiation from the radiation tube 50 and the projector 60 .

[0068] The correction unit 305 performs correction so that the area of ​​the image 401 indicating the dose measurement area 70 projected onto the surface of the subject 402 and the dose measurement area 70 of the radiation imaging device 10 substantially coincide with each other when observed from a point a predetermined distance away from the subject toward the projector 60. The predetermined distance is the distance between the subject and the photographer that is assumed when the photographer aligns the subject. Specifically, the distance may be, for example, a distance corresponding to the distance between the console 40 operated by the photographer and the radiation imaging device 10.

[0069] As described above, the radiation imaging apparatus 10 includes the dose measurement region 70 and generates a radiation image of the subject 402. The console 40 controls the radiation imaging apparatus 10 so that the image 401 indicating the dose measurement region 70 is projected onto the surface of the subject 402. The correction unit 305 corrects the position and size of the image 401 indicating the dose measurement region 70 in accordance with the values ​​of d1 and d2. The generation unit 304 generates the image 401 indicating the dose measurement region 70 to be projected onto the surface of the subject 402 in accordance with the correction by the correction unit 305.

[0070] Fig. 8 is a flowchart showing a processing method of the console 40. Fig. 8 is a flowchart showing a process of correcting the position of the image 71 in Fig. 7 to the position of the image 401, and each value is referred to in Fig. 7.

[0071] First, in step S501, the correction unit 305 determines a side to be calculated in the dose measurement region 70 in Fig. 7. For example, the correction unit 305 determines a side on the center side of the radiation imaging device 10 (a side coinciding with the auxiliary line 411) in the dose measurement region 70 in Fig. 7 as a side to be calculated.

[0072] Next, in step S502, the correction unit 305 obtains the value of “a” based on the design information of the radiation imaging device (FPD) 10.

[0073] Next, in step S503, distance input unit 302 inputs the values ​​of d1 and d2. The values ​​of d1 and d2 are an example of position information of subject 402. The value of d1 is a value measured by a tape measure from radiation tube 50 and manually inputted into operation unit 306. The value of d2 is obtained by measuring the body thickness of subject 402 with a tape measure and manually inputting the value into operation unit 306. An example of a tape measure is shown, but the distance may also be obtained by a distance measuring device using a laser or infrared rays, a method of obtaining the distance from information on the position angle of an arm, or a visible light camera. When the measurement can be performed by a device, the input may be directly inputted from the device without manual intervention.

[0074] Next, in step S504, the correction unit 305 calculates the value of c by the formula c=d2×a / d1, thereby correcting the target side of the image 71 to the target side of the image 401.

[0075] Next, in step S505, the correction unit 305 determines whether or not the above calculation has been performed for all sides of the dose measurement region 70. In this example, the dose measurement region 70 is a rectangle, so the correction unit 305 calculates four sides for one dose measurement region 70. In addition, when two dose measurement regions 70 are specified, the correction unit 305 determines whether or not the calculation has been performed for eight sides.

[0076] If the calculation has not been performed for all sides in step S505, the correction unit 305 changes the side to be calculated and returns to step S502. For example, the correction unit 305 calculates the side that coincides with the auxiliary line 413 next to the side that coincides with the auxiliary line 411.

[0077] If the calculation has been completed for all sides in step S505, the process proceeds to step S506. In step S506, the generation unit 304 generates an image 401 in which the image of the dose measurement region 70 is moved by the value c of each side when projected onto the radiation imaging device 10. Then, the generation unit 304 projects the image 401 onto the subject 402 via the projector 60.

[0078] Through the above processing, the correction unit 305 can correct the projection position of the image 71 of the dose measurement region 70 to the projection position of the image 401.

[0079] In this embodiment, an example in which the dose measurement region 70 is a rectangle has been shown, but the dose measurement region 70 may be a polygon other than a rectangle. If the dose measurement region 70 includes a curve, the correction unit 305 can apply a method of performing correction calculations using vertices and the like as calculation objects and interpolating between the corrected points. If the dose measurement region 70 is a circle, the correction unit 305 can apply a method of performing correction calculations using the center and radius as calculation objects. If the dose measurement region 70 is an ellipse, the correction unit 305 can apply a method of performing correction calculations using the focal point and the distance from the focal point on the ellipse as calculation objects.

[0080] Although an example has been shown in which there is no object between the radiation imaging apparatus 10 and the subject 402, there may be a pedestal device or the like that covers the radiation imaging apparatus 10.

[0081] As described above, according to this embodiment, the console 40 projects the image 401 indicating the dose measurement region 70 onto the surface of the subject 402 via the projector 60. This allows the photographer to check whether the left / right, top / bottom positions of the subject 402 are correct with respect to the radiation imaging apparatus 10.

[0082] Second embodiment The second embodiment has the same configuration as the first embodiment, but the correction method is different because the purpose of correcting the projected image is different. Other configurations of the second embodiment are the same as those of the first embodiment, so a description of the overlapping parts will be omitted.

[0083] The purpose of the image correction in the second embodiment is to present to the operator within what range a region of interest (such as an organ) within the subject should be placed.

[0084] FIG. 9 is a diagram showing a calculation method for position correction performed by the correction unit 305 according to the second embodiment and a position after correction, and is a diagram showing an upper half of the plan view of FIG. 2(a).

[0085] Reference numeral 602 denotes a region of interest inside the object 402. "d3" denotes the distance between the surface of the object 402 and the center of the region of interest 602. Image 601 is the image after correction.

[0086] Reference numerals 611 and 613 denote optical paths emitted from the radiation tube 50 and the projector 60, and indicate optical paths passing through the ends of the region of interest 602 and the dosimetry region .

[0087] Reference numerals 612 and 614 denote optical paths emitted from the radiation tube 50 and the projector 60 when correcting the image of the dose measurement region 70, and indicate optical paths passing through the edge of the image 601 of the dose measurement region 70.

[0088] f is the difference between the edge of the region of interest 602 and the edge of the dose measurement region 70 of the radiation imaging device 10. g is the distance from the position where the target side of the dose measurement region 70 is projected onto the radiation imaging device 10 to the point where the optical path 612 that passes through the edge of the image 601 when corrected to the image 601 reaches the radiation imaging device 10.

[0089] g is expressed by the following equation. g=a×d3 / d1

[0090] f is expressed by the following equation. f = a - (d1 + d3) × a / (d1 + d2) =(d2-d3)×a / (d1+d2)

[0091] The correction unit 305 performs correction so that an area of ​​an image 601 indicating a dose measurement region 70 projected onto the surface of the subject 402 when observed from a point a predetermined distance away from the subject toward the projector 60, substantially matches an area projected onto the region of interest 602 when projected from the projector 60 onto the dose measurement region 70 of the radiation imaging device 10 via the region of interest 602 inside the subject 402. The projector 60 is an example of a projection device, and projects the image 601 onto the surface of the subject 402.

[0092] Fig. 10 is a flowchart showing a processing method of the console 40 according to the second embodiment. Fig. 10 is a flowchart showing a process for correcting the position of the image 601 in Fig. 9, and each value is referred to Fig. 9.

[0093] First, in step S701, the correction unit 305 determines a side to be calculated in the dose measurement region 70 in Fig. 9. For example, the correction unit 305 determines a side on the center side of the radiation imaging device 10 (a side coinciding with the auxiliary line 611) in the dose measurement region 70 in Fig. 9 as a side to be calculated.

[0094] Next, in step S702, the correction unit 305 obtains the value of “a” based on the design information of the radiation imaging device (FPD) 10.

[0095] Next, in step S703, the distance input unit 302 inputs the values ​​of d1 and d3. The values ​​of d1 and d3 are an example of position information of the subject 402. The value of d1 is a value measured with a tape measure from the radiation tube 50 and is manually input via the operation unit 306. The value of d3 is a value estimated from the internal structure and position of a typical subject 402.

[0096] Next, in step S704, the correction unit 305 corrects the side of the object in the image 601 by calculating the value of g using the formula g=a×d3 / d1.

[0097] Next, in step S705, the correction unit 305 determines whether the above calculation has been performed for all sides of the dose measurement region 70. If the calculation has not been performed for all sides, the correction unit 305 changes the side to be calculated and returns to step S702. If the calculation has been performed for all sides, the process proceeds to step S706.

[0098] In step S706, the generation unit 304 generates an image 601 in which the image of the dose measurement region 70 is moved by the g value of each side when projected onto the radiation imaging device 10. Then, the generation unit 304 projects the image 601 onto the subject 402 via the projector 60.

[0099] Through the above processing, the correction unit 305 can correct the projection position of the image 601 of the dose measurement region 70.

[0100] 9 and 10, the dose measurement region 70 is a rectangle, but the dose measurement region 70 may be a polygon other than a rectangle. If the dose measurement region 70 includes a curve, the correction unit 305 can apply a method of performing correction calculations using vertices and the like as calculation objects and interpolating between the corrected points. If the dose measurement region 70 is a circle, the correction unit 305 can apply a method of performing correction calculations using the center and radius as calculation objects. If the dose measurement region 70 is an ellipse, the correction unit 305 can apply a method of performing correction calculations using the focal point and the distance from the focal point on the ellipse as calculation objects.

[0101] Furthermore, the correction unit 305 and the generation unit 304 may simultaneously generate the image 401 in FIG. 7 of the first embodiment and the image 601 in FIG. 9 of the second embodiment, and generate and project both the image 401 and the image 601 simultaneously.

[0102] As described above, according to this embodiment, the console 40 projects the image 601 onto the surface of the subject 402 via the projector 60. This allows the photographer to check whether the left, right, top, and bottom positions of the subject 402 are correct with respect to the radiation imaging apparatus 10. At this time, the position of the region of interest 602 inside the subject 402 can be made to coincide with the position of the dose measurement region 70 of the radiation imaging apparatus 10.

[0103] (Third embodiment) In the third embodiment, some values ​​measured by a measuring tape or the like in the first embodiment are calculated by a visible light camera. Other configurations of the third embodiment are the same as those of the first embodiment, so a description of the overlapping parts will be omitted.

[0104] Fig. 11 is a diagram showing an example of the configuration of a radiation imaging system 100 according to the third embodiment. The radiation imaging system 100 in Fig. 11 is obtained by adding a visible light camera 80 to the radiation imaging system 100 in Fig. 1. The visible light camera 80 is disposed near the radiation tube 50 and the projector 60. The visible light camera 80 transmits a captured image to the console 40.

[0105] FIG. 12 is a diagram showing a calculation method for position correction performed by the correction unit 305 according to the third embodiment and a position after correction, and is a diagram showing an upper half of the plan view of FIG. 2(a).

[0106] When an image of the dose measurement region 70 is projected from the projector 60 onto the radiation imaging device 10, if the position of the image is set to be the same as the position of the dose measurement region 70, then in the case where a subject 402 is present, an image 901 of the dose measurement region 70 is projected onto the subject 402. The correction unit 305 corrects the position of the image 901 so that an image 902 of the dose measurement region 70 is projected onto the subject 402.

[0107] Here, "a" is the distance from the center position of the radiation imaging device 10 to the side of the target in the dose measurement region 70, and is a value that can be determined from the design values ​​of the radiation imaging device 10. "b" is the distance from the position where the side of the target in image 902 is projected onto the radiation imaging device 10 to the center position of the radiation imaging device 10 when radiation or light is irradiated from the radiation tube 50 or projector 60 and corrected from the position of image 901 to the position of image 902. "c" is a value obtained by subtracting a from b.

[0108] “d1” is the distance between the radiation tube 50 or the projector 60 and the surface of the subject 402. “d2” is the body thickness of the subject 402, and is the distance between the surface of the subject 402 and the surface of the radiation imaging device 10.

[0109] "b" can be calculated as (d1+d2)×a / d1. "c" can be calculated as ba(=d2×a / d1). Further, auxiliary lines 911 , 912 , 913 and 914 are auxiliary lines that indicate the paths of irradiation from the radiation tube 50 and the projector 60 .

[0110] "e" is the distance between corresponding sides of images 901 and 902. The correction unit 305 calculates the value of e based on image data acquired by the visible light camera 80. "d1" is measured with a tape measure. Then, the correction unit 305 can calculate the value of d2 from the formula d2=e×d1 / (ae) without measuring d2. Next, the correction unit 305 can calculate the value of c from the formula c=d2×a / d1.

[0111] Fig. 13 is a flowchart showing a processing method of the console 40 according to the third embodiment. Fig. 13 is a flowchart showing a process of correcting the position of the image 902 in Fig. 12, and each value is referenced to Fig. 12.

[0112] First, in step S1001, the correction unit 305 determines a side to be calculated in the dose measurement region 70 in Fig. 12. For example, the correction unit 305 determines a side on the center side of the radiation imaging device 10 (a side coinciding with the auxiliary line 911) in the dose measurement region 70 in Fig. 12 as a side to be calculated.

[0113] Next, in step S1002, the correction unit 305 obtains the value of “a” based on the design information of the radiation imaging device (FPD) 10.

[0114] Next, in step S1003, distance input unit 302 inputs the value of d1. The value of d1 is an example of position information of subject 402. The value of d1 is a value measured by a tape measure from radiation tube 50 and is manually input to operation unit 306.

[0115] Next, in step S1004, the generation unit 304 projects an image 901 indicating the dose measurement region 70 onto the subject 402 via the projector 60. The visible light camera 80 is an example of a visible light imaging device, and captures an image of the surface of the subject 402. The correction unit 305 calculates the value of x based on the image data captured by the visible light camera 80, as shown in FIG. 12. The value of x is the distance from the center position of the radiation imaging device 10 to the side of the target in the image 901. Next, the correction unit 305 calculates the value of e by the equation e=ax. The value of e is the amount of deviation of the image 901 from the image 902.

[0116] Next, in step S1005, the correction unit 305 calculates the value of d2 by the formula d2=e×d1 / (ae).

[0117] Next, in step S1006, the correction unit 305 calculates the value of c by the formula c=d2×a / d1, thereby correcting the target side of the image 901 to the target side of the image 902.

[0118] Next, in step S1007, the correction unit 305 determines whether the above calculation has been performed for all sides of the dose measurement region 70. If the calculation has not been performed for all sides, the correction unit 305 changes the side to be calculated and returns to step S1002. If the calculation has been performed for all sides, the process proceeds to step S1008.

[0119] In step S1008, the generation unit 304 generates an image 902 in which the image of the dose measurement region 70 is moved by the value c of each side when projected onto the radiation imaging device 10. Then, the generation unit 304 projects the image 902 onto the subject 402 via the projector 60.

[0120] Through the above processing, the correction unit 305 can correct the projection position of the image 902 of the dose measurement region 70.

[0121] In this embodiment, an example in which the dose measurement region 70 is a rectangle has been shown, but the dose measurement region 70 may be a polygon other than a rectangle. If the dose measurement region 70 includes a curve, the correction unit 305 can apply a method of performing correction calculations using vertices and the like as calculation objects and interpolating between the corrected points. If the dose measurement region 70 is a circle, the correction unit 305 can apply a method of performing correction calculations using the center and radius as calculation objects. If the dose measurement region 70 is an ellipse, the correction unit 305 can apply a method of performing correction calculations using the focal point and the distance from the focal point on the ellipse as calculation objects.

[0122] (Other embodiments) The present disclosure can also be realized by a process in which a program for implementing one or more functions of the above-described embodiments is supplied to a system or device via a network or a storage medium, and one or more processors in a computer of the system or device read and execute the program. It can also be realized by a circuit (e.g., ASIC) for implementing one or more functions.

[0123] It should be noted that the above-described embodiments are merely illustrative of specific examples of implementing the present disclosure, and the technical scope of the present disclosure should not be interpreted as being limited by these embodiments. In other words, the present disclosure can be implemented in various forms without departing from its technical concept or main features.

[0124] The disclosure of this embodiment includes the following configuration, method, and program. (Configuration 1) 1. An information processing device that controls a radiation imaging device for generating a radiation image of a subject so as to project an image indicating a dose measurement region onto a surface of the subject, a correction means for correcting a position and a size of an image showing the dose measurement region according to position information of the subject; a generating means for generating an image indicating the dose measurement region to be projected onto a surface of the subject in accordance with the correction by the correcting means; 13. An information processing device comprising: (Configuration 2) The information processing device described in configuration 1, characterized in that the correction means performs correction so that an area of ​​an image indicating the dose measurement area projected onto the surface of the subject and a dose measurement area of ​​the radiation imaging device approximately coincide with each other when observed from a point located a predetermined distance away from the subject toward the projection device. (Configuration 3) The information processing device described in configuration 1, characterized in that the correction means performs correction so that, when observed from a point located a predetermined distance away from the subject toward the projection device, an area of ​​an image indicating the dose measurement area projected onto the surface of the subject approximately coincides with an area projected onto the dose measurement area of ​​the radiation imaging device when projected from a projection device that projects the image onto the dose measurement area of ​​the radiation imaging device via a region of interest inside the subject. (Configuration 4) 4. The information processing device according to any one of configurations 1 to 3, wherein the position information of the subject includes a distance between a projection device that projects the image and a surface of the subject. (Configuration 5) 3. The information processing device according to claim 2, wherein the position information of the subject includes a distance between a projection device that projects the image and a surface of the subject, and a distance between the surface of the subject and a surface of the radiation imaging device. (Configuration 6) 4. The information processing device according to claim 3, wherein the position information of the subject includes a distance between a projection device that projects the image and a surface of the subject, and a distance between the surface of the subject and the region of interest. (Configuration 7) The information processing device according to configuration 4, wherein the correction means calculates an amount of shift of an image showing the dose measurement region based on image data of the surface of the subject captured by a visible light imaging device, and performs correction based on the amount of shift of the image and a distance between a projection device that projects the image and the surface of the subject. (Configuration 8) 8. The information processing device according to any one of configurations 1 to 7, wherein the dose measurement region is a region where a dose of radiation is measured. (Configuration 9) The information processing device according to configuration 8, wherein the radiation imaging device measures the radiation dose in the dose measurement area, and outputs a radiation irradiation stop signal when an integrated value of the measured dose reaches a target value. (Configuration 10) 10. The information processing device according to any one of configurations 1 to 9, wherein the subject is a human body. (Configuration 11) An information processing device according to any one of configurations 1 to 10, a projection device that projects an image showing the dose measurement area onto a surface of the subject; A radiation imaging system comprising: (Configuration 12) 12. The radiation imaging system according to configuration 11, further comprising a radiation imaging device that includes the dose measurement region and generates a radiation image of the subject. (Configuration 13) The radiation imaging system described in configuration 12, characterized in that the radiation imaging device measures the radiation dose in the dose measurement area and outputs a radiation irradiation stop signal when the integrated value of the measured dose reaches a target value. (Configuration 14) 14. The radiation imaging system according to configuration 13, further comprising a radiation generating device that controls the radiation imaging device to irradiate radiation through the subject. (Configuration 15) 15. The radiation imaging system according to configuration 14, wherein the radiation generation device controls to stop irradiating radiation when the radiation irradiation stop signal is input. (Method 1) 1. A processing method for an information processing device that controls a radiation imaging device that generates a radiation image of a subject so as to project an image indicating a dose measurement region onto a surface of the subject, comprising: a correction step of correcting a position and a size of an image showing the dose measurement region according to position information of the subject; a generating step of generating an image indicating the dosimetry region to be projected onto a surface of the subject in accordance with the correction of the correcting step; 13. A processing method for an information processing apparatus comprising: (Method 2) 1. A processing method for a radiation imaging system that controls a radiation imaging device that generates a radiation image of a subject so as to project an image indicating a dose measurement region onto a surface of the subject, comprising: a correction step of correcting a position and a size of an image showing the dose measurement region according to position information of the subject by an information processing device; a generating step of generating, by the information processing device, an image indicating the dose measurement region to be projected onto a surface of the subject in accordance with the correction made in the correcting step; a projection step of controlling a projection device to project an image showing the dose measurement region onto a surface of the subject; 13. A processing method for a radiation imaging system, comprising: (Program 1) A program for causing a computer to execute the processing method according to Method 1 or 2. [Explanation of symbols]

[0125] 10 Radiation imaging device, 20 Control device, 30 Radiation generator, 40 Console, 50 Radiation tube, 60 Projector, 70 Dose measurement area, 80 Visible light camera, 11,402 Subject

Claims

1. 1. An information processing device that controls a radiation imaging device for generating a radiation image of a subject so as to project an image indicating a dose measurement region onto a surface of the subject, a correction means for correcting a position and a size of an image showing the dose measurement region according to position information of the subject; a generating means for generating an image indicating the dose measurement region to be projected onto a surface of the subject in accordance with the correction by the correcting means; 13. An information processing device comprising:

2. 2. The information processing device according to claim 1, wherein the correction means performs correction so that, when observed from a point a predetermined distance away from the subject toward the projection device, an area of ​​an image indicating the dose measurement area projected onto the surface of the subject and a dose measurement area of ​​the radiation imaging device approximately coincide with each other.

3. 2. The information processing device according to claim 1, wherein the correction means performs correction so that, when observed from a point a predetermined distance away from the subject toward the projection device, an area of ​​an image indicating the dose measurement area projected onto the surface of the subject approximately coincides with an area projected onto the dose measurement area of ​​the radiation imaging device when projected from a projection device that projects the image onto the dose measurement area of ​​the radiation imaging device via a region of interest inside the subject.

4. The information processing apparatus according to claim 1 , wherein the position information of the subject includes a distance between a projection device that projects the image and a surface of the subject.

5. 3 . The information processing apparatus according to claim 2 , wherein the position information of the subject includes a distance between a projection device that projects the image and a surface of the subject, and a distance between the surface of the subject and a surface of the radiation imaging device.

6. The information processing apparatus according to claim 3 , wherein the position information of the subject includes a distance between a projection device that projects the image and a surface of the subject, and a distance between the surface of the subject and the region of interest.

7. 5. The information processing device according to claim 4, wherein the correction means calculates an amount of shift of an image showing the dose measurement region based on image data of the surface of the subject captured by a visible light imaging device, and performs correction based on the amount of shift of the image and a distance between a projection device that projects the image and the surface of the subject.

8. 2. The information processing apparatus according to claim 1, wherein the dose measurement area is an area in which a dose of radiation is measured.

9. 9. The information processing apparatus according to claim 8, wherein the radiation imaging apparatus measures a radiation dose in the dose measurement area, and outputs a radiation irradiation stop signal when an integrated value of the measured dose reaches a target value.

10. 2. The information processing apparatus according to claim 1, wherein the subject is a human body.

11. An information processing device according to any one of claims 1 to 10; a projection device that projects an image showing the dose measurement area onto a surface of the subject; A radiation imaging system comprising:

12. The radiation imaging system according to claim 11 , further comprising a radiation imaging device that includes the dose measurement area and generates a radiation image of the subject.

13. The radiation imaging system according to claim 12 , wherein the radiation imaging device measures a radiation dose in the dose measurement area, and outputs a radiation irradiation stop signal when an integrated value of the measured dose reaches a target value.

14. 14. The radiation imaging system according to claim 13, further comprising a radiation generating device that controls the radiation imaging device to irradiate radiation through the subject.

15. 15. The radiation imaging system according to claim 14, wherein the radiation generation device performs control so as to stop irradiating radiation when the radiation irradiation stop signal is input.

16. 1. A processing method for an information processing device that controls a radiation imaging device that generates a radiation image of a subject so as to project an image indicating a dose measurement region onto a surface of the subject, comprising: a correction step of correcting a position and a size of an image showing the dose measurement region according to position information of the subject; a generating step of generating an image indicating the dosimetry region to be projected onto a surface of the subject in accordance with the correction of the correcting step; 13. A processing method for an information processing apparatus comprising:

17. 1. A processing method for a radiation imaging system that controls a radiation imaging device that generates a radiation image of a subject so as to project an image indicating a dose measurement region onto a surface of the subject, comprising: a correction step of correcting a position and a size of an image showing the dose measurement region according to position information of the subject by an information processing device; a generating step of generating, by the information processing device, an image indicating the dose measurement region to be projected onto a surface of the subject in accordance with the correction made in the correcting step; a projection step of controlling a projection device to project an image showing the dose measurement region onto a surface of the subject; 13. A processing method for a radiation imaging system, comprising:

18. A program for causing a computer to execute the processing method according to claim 16 or 17.

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