Radiation imaging apparatus, control method thereof, radiation imaging system, and program

Abstract

To provide a technology to perform appropriate radiation imaging while achieving power saving.SOLUTION: A radiation imaging apparatus 100 for performing radiation imaging of a subject H includes: an image generation unit 120 for generating a radiation image on the basis of a radiation R made incident; and a state control unit 110 for performing control to shift the state from a stand-by state in which power consumption is smaller than in an imaging executable state in which the radiation R can be detected at the image generation unit 120 to the imaging executable state when at least one condition of positional relationships between a radiation generation device 200 for generating the radiation R and the radiation imaging apparatus 100, positional relationships between the subject H and the radiation imaging apparatus 100, and the posture of the subject H is brought into a given state in the radiation imaging.SELECTED DRAWING: Figure 2

Description

[Technical field]

[0001] The present disclosure relates to a radiography apparatus, a control method thereof, a radiography system, and a program. [Background technology]

[0002] In recent years, radiography devices that generate digital radiographic images based on incident radiation have become widespread, and the digitalization of radiography systems, including radiography devices, is progressing. This digitalization of radiography systems makes it possible to check radiographic images immediately after radiography, and has significantly improved workflow compared to conventional radiography methods that use film or CR devices.

[0003] Furthermore, wireless radiography devices have been developed, making it easier to handle the radiography devices. Such wireless radiography devices operate on batteries, so the number of images that can be captured with one charge leads to ease of use. In this case, in order to increase the number of images that can be captured, it is necessary to reduce the power consumption of the radiography device. In addition, in a digital radiography device, a certain waiting time is required to transition to an imaging-enabled state after canceling a standby state that consumes less power than an imaging-enabled state. Regarding the release of this standby state, Patent Document 1 describes a number of standby state release methods, since it is better for the operator who performs the radiography and the subject who is radiographed to have a short time before imaging. In addition, Patent Document 2 describes a technology that releases the standby state in response to the input of an imaging order, thereby enabling radiography to be performed quickly. [Prior art documents] [Patent documents]

[0004] [Patent Document 1] JP 2002-165142 A [Patent Document 2] JP 2002-272720 A Summary of the Invention [Problem to be solved by the invention]

[0005] In Patent Document 1, for example, from the standpoint of power saving, if a standby state release method is selected in which the time until the standby state is released is long compared to the waiting time until radiation is applied, the operator will have to wait longer, and will not be able to perform radiation imaging at the appropriate time.

[0006] Furthermore, in Patent Document 2, for example, if the conditions related to the execution of radiation imaging deviate from the given state after an imaging order is input, it is difficult to execute appropriate radiation imaging.

[0007] The present disclosure has been made in consideration of such problems, and has an object to provide a technique that can perform appropriate radiography while saving power. [Means for solving the problem]

[0008] The radiographic imaging device disclosed herein is a radiographic imaging device that performs radiographic imaging of a subject, and includes an image generating means that generates a radiographic image based on incident radiation, and a control means that performs control to transition from a standby state, which consumes less power than a radiographic imaging state in which the image generating means can detect the radiation, to the radiographic imaging state when at least one of the following conditions is met for the radiographic imaging: a positional relationship between a radiation generating device that generates the radiation and the radiographic imaging device, a positional relationship between the subject and the radiographic imaging device, and a posture of the subject. Effect of the Invention

[0009] According to the present disclosure, appropriate radiation imaging can be performed while saving power. [Brief description of the drawings]

[0010] [Figure 1] 1 is a diagram illustrating an example of a schematic configuration of a radiation imaging system according to a first embodiment of the present disclosure. [Diagram 2] 2 is a diagram showing an example of the internal functional configuration of the radiation imaging apparatus, the radiation generating apparatus, and the console shown in FIG. 1 in the radiation imaging system according to the first embodiment of the present disclosure. [Diagram 3] FIG. 3 illustrates the first embodiment of the present disclosure and is a diagram showing an example of an internal configuration of an image generating unit illustrated in FIG. 2. [Figure 4] 4 is a diagram illustrating an example of a functional configuration of the radiation imaging apparatus illustrated in FIGS. 2 and 3. FIG. [Diagram 5] 4A to 4C are diagrams illustrating a relationship between a state of a radiation imaging apparatus according to a first embodiment of the present disclosure and power consumption and the passage of time, and an example of an imaging flow of the radiation imaging apparatus. [Figure 6] 3 illustrates the first embodiment of the present disclosure and is a diagram showing an example of a display screen displayed on the display unit illustrated in FIG. 2. [Figure 7] FIG. 11 is a diagram illustrating an example of a schematic configuration of a radiation imaging system according to a second embodiment of the present disclosure. [Figure 8] 8 is a diagram showing an example of the internal functional configuration of a radiation imaging apparatus, a radiation generation apparatus, a console, and an IF box shown in FIG. 7 in a radiation imaging system according to a second embodiment of the present disclosure. FIG. [Figure 9] 13 is a diagram showing an example of drive timings of each device and a state of a radiation imaging device in a radiation imaging system according to a second embodiment of the present disclosure. FIG. [Figure 10] 10 is a flowchart showing an example of a processing procedure in a control method for a radiation imaging apparatus according to a second embodiment of the present disclosure. [Figure 11] FIG. 11 is a diagram illustrating an example of a schematic configuration of a radiation imaging system according to a third embodiment of the present disclosure. [Figure 12] 13 is a flowchart showing an example of a processing procedure in a control method for a radiation imaging apparatus according to a third embodiment of the present disclosure. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0011] Hereinafter, with reference to the drawings, a description will be given of a form (embodiment) for carrying out the present disclosure. Note that the embodiment of the present disclosure described below does not limit the scope of the claims, and not all of the combinations of features described in the embodiment of the present disclosure are necessarily essential as the means for solving the problems of the present disclosure. In addition, in the embodiment of the present disclosure described below, it is preferable to use X-rays as radiation, but the present disclosure is not limited to this, and other radiation such as α-rays, β-rays, and γ-rays can also be applied to the present disclosure.

[0012] (First embodiment) First, the first embodiment will be described.

[0013] FIG. 1 is a diagram showing an example of a schematic configuration of a radiation imaging system 10-1 according to a first embodiment of the present disclosure.

[0014] 1, radiation imaging system 10-1 includes radiation imaging apparatus 100, radiation generating apparatus 200, console 300 (referred to as "PC" in FIG. 1), and wireless access point 400 (referred to as "AP" in FIG. 1). Furthermore, radiation generating apparatus 200 includes radiation generating apparatus main body 210, radiation switch 220, and tube 230 which is a radiation irradiation unit. As an example, radiation imaging system 10-1 is in a form in which radiation generating apparatus 200, console 300, and wireless access point 400 are provided in a mobile cart K.

[0015] The radiation imaging apparatus 100 is configured to be capable of wireless communication with the wireless access point 400. The radiation imaging apparatus 100 can be operated by a battery or an external power supply.

[0016] The radiation switch 220 includes a preparation request switch 221 that issues an instruction to the radiation generating device main body 210 to request the start of preparation for radiation irradiation, and an irradiation request switch 222 that issues an instruction to request radiation irradiation. The preparation request switch 221 and the irradiation request switch 222 are two-stage switches, and the preparation request switch 221 is always pressed before the irradiation request switch 222. As shown in Fig. 1, when the radiation imaging apparatus 100 is used together with the medical cart K, the radiation imaging apparatus 100 transmits a radiation image to the console 300 by wireless communication with the wireless access point 400. Note that the radiation imaging apparatus 100 is configured to be able to switch to a wired communication connection, for example, by using a unit not shown, instead of the wireless communication connection.

[0017] The console 300 is a control device that controls the operations of the radiation imaging apparatus 100 , the radiation generation apparatus 200 , and the wireless access point 400 .

[0018] In this embodiment, it is assumed that the radiation imaging apparatus 100 is driven in an imaging mode in which the radiation imaging apparatus 100 detects the start of radiation irradiation by itself and performs imaging operation. Therefore, in this embodiment, there is no connection for directly exchanging signals between the radiation imaging apparatus 100 and the radiation generating apparatus 200. However, the contents described in this embodiment can be similarly applied to an imaging mode in which the radiation imaging apparatus 100 and the radiation generating apparatus 200 perform a handshake to measure the radiation irradiation timing and perform imaging operation.

[0019] Fig. 2 is a diagram showing an example of the internal functional configuration of the radiation imaging apparatus 100, the radiation generating apparatus 200, and the console 300 shown in Fig. 1 in the radiation imaging system 10-1 according to the first embodiment of the present disclosure. In Fig. 2, the same components as those shown in Fig. 1 are denoted by the same reference numerals, and detailed description thereof will be omitted.

[0020] 2 illustrates a case where a subject H is radiographed in the radiation imaging system 10-1. In this case, the subject H is disposed at a position between the radiation generating device 200 (more specifically, the tube 230 of the radiation generating device 200) and the radiation imaging device 100 (more specifically, the image generating section 120 of the radiation imaging device 100). In this embodiment, the subject H is a subject such as a patient.

[0021] The radiation generating device main body 210 of the radiation generating device 200 generally controls the operation of the radiation generating device 200. The radiation generating device main body 210 has an irradiation permission receiving unit 211 that receives information on permission for irradiation of radiation R.

[0022] When the preparation request switch 221 is pressed by an operator performing radiography or the like, the radiation generating device 200 performs a preparation operation for irradiating radiation R. When the irradiation request switch 222 is pressed by an operator performing radiography or the like, the radiation generating device 200 irradiates radiation R from the tube 230. For example, even when the irradiation request switch 222 is pressed, irradiation of radiation R is not performed until preparation for irradiation of radiation R due to pressing of the preparation request switch 221 is completed, and radiation R is irradiated at the time when preparation for irradiation of radiation R is completed. Note that the preparation request switch 221 and the irradiation request switch 222 are often configured as an integrated two-stage switch.

[0023] The tube 230 of the radiation generating device 200 is disposed in a position directly facing the image generating section 120 of the radiation imaging device 100, with the subject H, which is the subject to be imaged, sandwiched between the tube 230 and the radiation imaging device 100 (more specifically, the image generating section 120 of the radiation imaging device 100). At this time, the radiation imaging device 100 is disposed according to the position and posture of the subject H and the part of the subject H to be imaged, so that the tube 230 can be moved freely to a certain extent so as to be directly facing the radiation imaging device 100 (more specifically, the image generating section 120). In the case of the mobile cart K applied to the radiation imaging system 10-1, since the radiation generating device 200 is used while being moved, the tube 230 is stored compactly in the mobile cart K when not imaging, and is pulled out from there when imaging, and preparations for imaging are made. In this embodiment, the tube 230 of the radiation generation device 200 is a radiation irradiation unit that irradiates radiation R toward the subject H and the radiation imaging device 100 (more specifically, the image generation unit 120 of the radiation imaging device 100). The tube 230, which is the radiation irradiation unit, is provided with a camera 231 that images the subject H and the radiation imaging device 100. The camera 231 moves in accordance with the movement of the tube 230, and can image the subject H and the radiation imaging device 100. Image data of the camera image captured by the camera 231 is transmitted to the console 300. At this time, the camera 231 and the console 300 may be connected by a wired cable such as a LAN cable or a USB cable, or may be connected by wireless communication such as WLAN or Bluetooth.

[0024] 2, the radiation imaging apparatus 100 includes a state control unit 110, an image generation unit 120, and a battery 130. In the radiation imaging apparatus 100, the state control unit 110 controls switching between a standby state, which consumes less power than the imaging-enabled state, and an imaging-enabled state.

[0025] The image generating section 120 is an image generating means that generates a radiation image based on the incident radiation R (including the radiation R that has passed through the subject H).

[0026] The battery 130 is an internal power supply means for enabling the radiation imaging apparatus 100 to operate even without a power supply from outside the radiation imaging apparatus 100. The battery 130 is often a battery that can be used repeatedly by charging, such as a lithium ion battery. The battery 130 may be incorporated in the radiation imaging apparatus 100 and cannot be removed from the radiation imaging apparatus 100, or may be removable from the radiation imaging apparatus 100. The battery 130 may be charged by a charger that can charge the battery 130 removed from the radiation imaging apparatus 100, or may be charged from another power source while incorporated in the radiation imaging apparatus 100.

[0027] The radiation imaging apparatus 100 operates by power supply from the battery 130, but when the battery 130 runs out of power, it becomes necessary to replace it with another battery or charge it from another power source, resulting in downtime and restrictions on use. For this reason, it is desirable to reduce the power consumption of the radiation imaging apparatus 100 as much as possible. In order to reduce the power consumption of the radiation imaging apparatus 100, it is also effective to extend the time in which the radiation imaging apparatus 100 is in a state with lower power consumption. For this reason, the state control unit 110 of the radiation imaging apparatus 100 performs control so as to shorten the time in the imaging-enabled state as much as possible and to lengthen the time in the standby state.

[0028] As shown in FIG. 2, the console 300 includes a data processing unit 310, a determination unit 320, and a display unit 330.

[0029] The data processing unit 310 processes image data of the camera image received from the camera 231, image data of the radiation image received from the radiation imaging device 100, etc. The data processing unit 310 performs processes on the image data, such as correction processing, noise reduction processing, filtering processing, enhancement processing, image conversion and deformation, and feature extraction and calculation.

[0030] The determination unit 320 determines whether or not the conditions for performing radiography of the subject H have reached a given state, using a predetermined criterion for the image data of the camera image processed by the data processing unit 310. In this embodiment, the conditions for performing radiography of the subject H include at least one of the following conditions: the positional relationship between the radiation generating device 200 and the radiation imaging device 100, the positional relationship between the subject H and the radiation imaging device 100, and the posture of the subject H. Specifically, as the positional relationship between the radiation generating device 200 and the radiation imaging device 100, it is preferable to apply the positional relationship between the tube 230, which is a radiation irradiation unit of the radiation generating device 200, and the image generating unit 120 of the radiation imaging device 100. In addition, as the positional relationship between the subject H and the radiation imaging device 100, it is preferable to apply the positional relationship between the subject H and the image generating unit 120 of the radiation imaging device 100. Then, the determination result by the determination unit 320 as to whether or not the conditions for performing radiography of the subject H have reached a given state is sent to the radiation imaging device 100 connected by wireless LAN via the wireless access point 400. Then, when the judgment unit 320 judges that the conditions for performing radiation imaging of the subject H described above have reached a given state, the state control unit 110 of the radiation imaging apparatus 100 controls the transition of the state of the radiation imaging apparatus 100 from a standby state to a state ready for imaging.

[0031] The display unit 330 is a display means for displaying various types of information and various types of images to an operator who performs radiography.

[0032] Fig. 3 illustrates the first embodiment of the present disclosure and is a diagram showing an example of the internal configuration of the image generating unit 120 illustrated in Fig. 2. As illustrated in Fig. 3, the image generating unit 120 includes a radiation detection unit 121, a driving circuit 122, a readout circuit 123, an imaging control means 124, a correction processing means 125, and a power supply means 126.

[0033] The radiation detection unit 121 includes a plurality of pixels 1211 arranged in a two-dimensional array to form a plurality of rows and a plurality of columns. Each of the plurality of pixels 1211 includes a conversion element 301 and a switch element 302.

[0034] The conversion element 301 converts the incident radiation R into an electric charge, which is an electric signal, and accumulates the electric charge. The conversion element 301 may be composed of a scintillator that converts the radiation R into visible light and a photoelectric conversion element that converts the visible light generated by the scintillator into an electric charge, or may be an element that directly converts the radiation R into an electric charge. A bias voltage is supplied to one terminal of the conversion element 301 from the power supply means 126 via a bias line 1214. The other terminal of the conversion element 301 is connected to a signal line 1213 via a switch element 302.

[0035] The switch element 302 transfers the charge accumulated in the conversion element 301 to the signal line 1213. The switch element 302 is composed of a transistor such as a TFT. The switch element 302 has a control terminal, and is turned on, i.e., conductive, when an on voltage is supplied to the control terminal, and is turned off, i.e., non-conductive, when an off voltage is supplied to the control terminal. The control terminal of the switch element 302 is connected to a drive line 1212 connected to the drive circuit 122. In addition, in the radiation detection unit 121, a plurality of drive lines 1212 extending in the row direction (horizontal direction in FIG. 3) are arranged side by side in the column direction (vertical direction in FIG. 3). The control terminals of the switch elements 302 of the pixels 1211 included in the same row are commonly connected to each drive line 1212. In addition, in the radiation detection unit 121, a plurality of signal lines 1213 extending in the column direction are arranged side by side in the row direction. To each signal line 1213, one main terminal of the switch element 302 of the pixels 1211 included in the same column is commonly connected.

[0036] The drive circuit 122 drives the radiation detection unit 121 in accordance with a control signal supplied from the imaging control means 124. Specifically, the drive circuit 122 supplies a drive signal to a control terminal of each switch element 302 through a drive line 1212. The drive circuit 122 sets the switch element 302 to an on state by setting the drive signal to an on voltage, and sets the switch element 302 to an off state by setting the drive signal to an off voltage. When the switch element 302 is in the on state, the charge accumulated in the conversion element 301 is transferred to the signal line 1213.

[0037] The readout circuit 123 reads out charges from the radiation detection unit 121 in accordance with a control signal supplied from the imaging control means 124, and generates a signal corresponding to the charges. Then, the readout circuit 123 supplies the generated signal to the correction processing means 125. As shown in FIG. 3, the readout circuit 123 has a sample hold circuit 1231, a multiplexer 1232, an amplifier 1233, and an A / D converter 1234. The sample hold circuit 1231 holds the charges read out from the conversion elements 301 in units of pixel rows. The multiplexer 1232 sequentially extracts the charges of one row of pixels held in the sample hold circuit 1231 and supplies them to the amplifier 1233. The amplifier 1233 amplifies the charges supplied from the multiplexer 1232 and supplies them to the A / D converter 1234 as an analog signal. The A / D converter 1234 converts the analog signal supplied from the amplifier 1233 into a digital signal (corresponding to image data of the above-mentioned radiation image) and supplies it to the correction processing means 125 .

[0038] The imaging control means 124 comprehensively controls the operation of the image generating section 120 .

[0039] The correction processing means 125 obtains image data of the captured image with reduced unnecessary dark charge components by performing dark correction, for example, to subtract image data of a dark image obtained only from dark charge components without irradiating radiation R from the image data of the radiation image converted into a digital signal. In this embodiment, the image data of the captured image is simply the image data of the radiation image.

[0040] The power supply means 126 supplies each main operating voltage such as a bias voltage, and can be operated by an external power supply or a power supply from a battery 130. For example, the power supply means 126 supplies a bias voltage to the conversion element 301 of the radiation detection unit 121 via a bias line 1214.

[0041] In this embodiment, it is assumed that the radiation imaging apparatus 100 detects the start of irradiation of radiation R by itself and operates in an imaging mode in which it transitions to a state in which electric charges are accumulated. In this case, the method of detecting the start of irradiation of radiation R may be a form in which irradiation of radiation R is detected by a dedicated sensor or a form in which the image generating unit 120 is used for detection, but the detection method is not limited thereto. In this embodiment, a method is adopted in which the start of irradiation of radiation R is detected by measuring a change in current caused by irradiation of radiation R while the switch element 302 is turned on / off in sequence to continue the operation of reading out electric charges from the radiation detection unit 121 to the readout circuit 123. In this embodiment, a state in which the start of irradiation of radiation R can be detected in the image generating unit 120 is regarded as an imaging-enabled state.

[0042] Fig. 4 is a diagram showing an example of the functional configuration of the radiation imaging apparatus 100 shown in Fig. 2 and Fig. 3. As shown in Fig. 4, the radiation imaging apparatus 100 has a functional configuration including a control unit 401, a driving unit 402, a sensor unit 403, and a power supply unit 404.

[0043] The control unit 401 includes, for example, the state control unit 110 shown in Fig. 2, and the imaging control means 124 and correction processing means 125 shown in Fig. 3. The drive unit 402 includes, for example, the drive circuit 122 shown in Fig. 3. The sensor unit 403 includes, for example, the radiation detection unit 121 and readout circuit 123 shown in Fig. 3. The power supply unit 404 includes, for example, the battery 130 shown in Fig. 2 and the power supply means 126 shown in Fig. 3.

[0044] The control unit 401 is a component that controls the driving unit 402 and communicates with the outside. The control unit 401 may be composed of, for example, a CPU and its peripheral circuits, such as memories such as flash and DRAM, and a wireless / wired communication interface. The driving unit 402 may be composed of a programmable logic circuit such as an FPGA or a CPLD. The power supply unit 404 may supply power individually to the control unit 401, the driving unit 402, and the sensor unit 403. The control unit 401 and the driving unit 402 are configured functionally separately, but they do not need to be separate devices, and may be configured as a single device such as an ASIC in which a CPU and a logic circuit are packaged together, or an FPGA with a built-in CPU. Even in this case, it is desirable to configure the control unit 401 and the driving unit 402 so that power can be supplied individually.

[0045] In the present disclosure, a state in which power consumption is smaller than that in the imaging-enabled state is defined as the standby state of the radiation imaging apparatus 100. Specifically, the standby state refers to a state in which the power is turned off for each functional component in FIG. 4. For example, the standby state of the radiation imaging apparatus 100 may be a state in which the control unit 401 is kept operating to control the radiation imaging apparatus 100, but at least one of the drive unit 402 and the sensor unit 403, which are necessary only during imaging, is turned off. Also, for example, the standby state of the radiation imaging apparatus 100 may be a state in which the drive unit 402 and the sensor unit 403 are kept in a reset state while being supplied with power, or a state in which they are not driven. Also, for example, the standby state of the radiation imaging apparatus 100 may be a state in which only a state in which communication with the console 300 is possible is maintained in order to minimize power consumption, and the CPU of the control unit 401 is started only when a trigger such as an external interrupt is received.

[0046] FIG. 5 is a diagram showing the relationship between the state of the radiation imaging apparatus 100 according to the first embodiment of the present disclosure and power consumption and time lapse, and an example of an imaging flow of the radiation imaging apparatus 100. In FIG. 5, in an area showing the relationship between the state of the radiation imaging apparatus 100 and power consumption and time lapse, the state of the radiation imaging apparatus 100 is illustrated inside each block, and the horizontal axis shows time lapse, and the vertical axis shows the magnitude of power consumption. As shown in FIG. 5, when the radiation imaging apparatus 100 is in a standby state, the power consumption is smaller than when the radiation imaging apparatus 100 is in an imaging-enabled state. Conversely, when the radiation imaging apparatus 100 is in an imaging-enabled state, the power consumption is larger than when the radiation imaging apparatus 100 is in a standby state. In addition, in FIG. 5, in an area showing the imaging flow of the radiation imaging apparatus 100, the imaging flow of the radiation imaging apparatus 100 when the radiation imaging apparatus 100 is in a certain state is shown.

[0047] When performing radiography using the mobile cart K, an operator such as a technician performing radiography moves the mobile cart K to the bedside of the subject who is the subject H, and starts preparation for radiography. During this radiography preparation period, the state of the radiography apparatus 100 is in a standby state. Next, the operator confirms the subject, the imaging part, and the conditions based on the imaging order received in advance, and then sets the radiography apparatus 100 to match the part and conditions to be imaged of the subject who is the subject H, and adjusts the subject's posture. The operator also moves the tube 230 of the radiation generating apparatus 200 and adjusts it so that the tube 230 faces the subject who is the subject H and the radiation imaging apparatus 100 directly. At this time, the operator adjusts the relative positional relationship between the tube 230 of the radiation generating apparatus 200 and the radiation imaging apparatus 100 so that they are in a state suitable for performing radiography. Here, the state suitable for performing radiography means, for example, that the tube 230 and the radiation imaging apparatus 100 are at a predetermined distance. Furthermore, the state suitable for performing radiation imaging is, for example, an angle at which radiation R is incident perpendicularly, and a positional relationship in which radiation R irradiated from the tube 230 is irradiated to an intended area of ​​the radiation imaging device 100. In particular, the angle at which radiation R is incident is affected by deterioration of image quality due to oblique incidence of radiation R. The camera 231 attached to the tube 230 of the radiation generating device 200 images the radiation imaging device 100 during the imaging preparation period. The method of analyzing and determining the above-mentioned distance, angle, and positional relationship from the camera image captured by the camera 231 can be implemented in various feasible ways, for example, markers can be placed at the four corners of the radiation imaging device 100, and the image can be processed to perform the above-mentioned determination. In this case, for example, the shape and size of the four markers in the captured image, the distance between the markers, and the like are extracted by image processing, and a determination is made based on whether or not the state meets a predetermined condition. Note that the shape and number of the markers are not important as long as the desired detection and determination can be performed. Such processing may be executed by a processor such as a CPU, or may be performed by a hardware circuit such as an FPGA or an ASIC, or may be configured to be shared. Such processing is performed, for example, inside the console 300 (the data processing unit 310 and the determination unit 320).

[0048] Through such processing, it is assumed that the determination unit 320 of the console 300 has determined that the positional relationship between the tube 230 of the radiation generating device 200 and the radiation imaging device 100 has become a given state for radiation imaging. In this case, since radiation imaging is expected to be performed without waiting for a long time, the state control unit 110 of the radiation imaging device 100 controls the state of the radiation imaging device 100 to transition from a standby state to an imaging-enabled state, using the determination result of the determination unit 320 as a trigger. This time point corresponds to the time point (1) in FIG. 5. Note that in this embodiment, the determination may be made in consideration of the positional relationship between the subject H and the radiation imaging device 100 and the posture of the subject H, instead of or in addition to the positional relationship between the tube 230 of the radiation generating device 200 and the radiation imaging device 100 described above. From the image data of the camera image obtained by photographing the subject H and the radiation imaging device 100 by the camera 231, it can be determined whether the position of the subject H matches the imaging site and procedure of the subject H instructed in the imaging order. Furthermore, it is possible to determine whether the imaging region of the subject H is correctly within the imaging area of ​​the radiation imaging apparatus 100 from image data of the camera image obtained by capturing an image of the subject H and the radiation imaging apparatus 100 by the camera 231. From the above, the determination unit 320 can determine whether at least one of the conditions of the positional relationship between the radiation generation device 200 and the radiation imaging apparatus 100, the positional relationship between the subject H and the radiation imaging apparatus 100, and the posture of the subject H is in a given state for radiation imaging. Then, when the determination result of the above-mentioned determination unit 320 indicates that at least one of the above-mentioned conditions is in a given state for radiation imaging, the state control unit 110 of the radiation imaging apparatus 100 performs control to transition the state of the radiation imaging apparatus 100 from the standby state to an imaging-enabled state.

[0049] When preparation for imaging is complete, the operator sequentially presses preparation request switch 221 and irradiation request switch 222 to start irradiating radiation R from tube 230 of radiation generation device 200 toward subject H and radiation imaging device 100 (image generation section 120). This point in time corresponds to point (2) in Fig. 5. Upon detecting the start of irradiation of radiation R, radiation imaging device 100 performs an imaging operation for capturing a radiographic image of subject H (imaging operation state).

[0050] When the radiographic image of the subject H is taken, the radiographic imaging apparatus 100 starts transmitting (transferring) image data of the radiographic image to the console 300. This point corresponds to point (3) in FIG. 5. Since it is not necessary to be in an imaging-enabled state (imaging operation state) during the transfer of image data of the radiographic image, the state control unit 110 of the radiographic imaging apparatus 100 controls the transition from the imaging-enabled state (imaging operation state) to a standby state in order to save power. Note that when an FPGA or the like is used as an offloader for the transfer of image data, the transition from the imaging-enabled state to the standby state may be made through multiple steps, such as turning off the power of the driving circuit when imaging is completed, and further turning off the power of the FPGA when the transfer is completed.

[0051] Furthermore, in this embodiment, the state control unit 110 of the radiation imaging apparatus 100 may be configured to control the transition to a standby state when the image generation unit 120 reads out charges (electrical signals) related to a radiation image after transitioning to a state capable of imaging.

[0052] In the console 300, after performing necessary image processing on the image data of the received radiation image, the image data is displayed on the display unit 330 so that the operator can check the radiation image. Then, the operator checks the radiation image displayed on the display unit 330, and if there is no problem, ends the imaging flow. The radiation imaging apparatus 100 may transmit image data of a radiation image that has not been subjected to any correction processing to the console 300, or may perform correction processing inside the radiation imaging apparatus 100. For example, correction processing may be performed to reduce dark current components of the image data of a radiation image, processing to correct the uniformity of the in-plane distribution of the sensitivity of the radiation detection unit 121, and other processing to reduce noise components. Since a personal computer used in the console 300 generally has a higher processing capacity than a processor in the radiation imaging apparatus 100, a form in which only light-load processing is performed inside the radiation imaging apparatus 100 is conceivable.

[0053] At the time (1) in FIG. 5, after the state of the radiation imaging apparatus 100 has transitioned from the standby state to the imaging-enabled state, it may become out of the given state suitable for radiation imaging before radiation imaging is performed. For example, a case may be considered in which the subject, who is the subject H, moves, causing a positional relationship between the subject H and the radiation imaging apparatus 100 (image generating unit 120) to shift. In this way, when the conditions related to the implementation of radiation imaging become out of the given state, the state control unit 110 of the radiation imaging apparatus 100 controls the state of the radiation imaging apparatus 100 to transition from the imaging-enabled state to the standby state, since appropriate radiation imaging cannot be performed. In addition, when the conditions related to the implementation of radiation imaging become out of the given state, it is desirable to notify the operator so that the operator notices the state. For example, when the conditions related to the implementation of radiation imaging become out of the given state, the state control unit 110 of the radiation imaging apparatus 100 controls the display unit 330 of the console 300 to display the state. At this time, the display unit 330 constitutes a notification means for notifying the operator. In this embodiment, the notification means is not limited to the display unit 330, and also includes a form in which the notification content is output as a sound from, for example, a sound output unit (not shown) provided in the console 300. In this embodiment, the above-mentioned notification means is not limited to a form in which it is provided only in the console 300, and may be provided in, for example, the radiation imaging apparatus 100 or the radiation generating apparatus 200 instead of or in addition to the console 300. The above-mentioned notification means notifies in a manner that allows the user to know that a given state suitable for imaging has been reached or is in a given state, and that a state has deviated from the given state suitable for imaging or is in a state that is not in the given state.

[0054] Fig. 6 illustrates the first embodiment of the present disclosure, and is a diagram showing an example of a display screen 600 displayed on the display unit 330 illustrated in Fig. 2. In Fig. 6, the same components as those illustrated in Fig. 2 and Fig. 3 are denoted by the same reference numerals, and detailed description thereof will be omitted.

[0055] The display screen 600-1 shown in FIG. 6(a) shows a display area 610 for displaying a camera image captured by the camera 231, and an imaging part display area 620 for selecting an imaging part. Here, the display area 610 depicts the subject H captured by the camera 231 and the image generating unit 120 (radiation detection unit 121). The imaging part display area 620 depicts a chest 621, an abdomen 622, and so on. Specifically, the display screen 600-1 shown in FIG. 6(a) shows that the chest 621 has been selected as the imaging part. The display screen 600-1 shown in FIG. 6(a) shows a case where the positional relationship between the subject H depicted in the display area 610 and the image generating unit 120 is in a given state suitable for imaging the chest 621 of the subject H.

[0056] 6(b) shows a case where the positional relationship between the subject H drawn in the display area 610 and the image generating section 120 is not a given state suitable for imaging the chest 621 of the subject H. For this reason, the display screen 600-2 shown in FIG. 6(b) displays warning display information 611 for notifying that the state is not suitable for imaging the chest 621 of the subject H.

[0057] The posture of the subject H, etc., can be recognized by image processing to determine whether it matches the body part to be imaged specified in the imaging order, and the result can be displayed as a display screen 600 on the display unit 330 of the console 300, so that the operator can check it. However, even if the display unit 330 displays it, there is a possibility that the operator will perform imaging without realizing it, so that a configuration may be adopted in which the imaging possible state is maintained so as to prevent ineffective exposure due to irradiation with radiation R but not being able to image the subject.

[0058] So far, a case has been described in which a camera image captured by the camera 231 is used to determine whether or not a given state is suitable for imaging, and the state transition of the radiation imaging device 100 is controlled. In this case, the given state suitable for imaging can be determined based on the imaging order described above. However, in this embodiment, the present invention is not limited to a form in which a camera image captured by the camera 231 is used. For example, a form in which output data of a detection sensor that detects at least one of a position and a movement is used instead of or in addition to the camera image captured by the camera 231 can also be applied. In this case, a sensor including at least one of an acceleration sensor, a gyro sensor, and a geomagnetic sensor can be applied as the detection sensor. In this case, the detection sensor is attached to the tube 230 of the radiation generating device 200 and the radiation imaging device 100, respectively. In this case, it is possible to determine whether or not the conditions related to the implementation of radiation imaging, including the relative positional relationship between them, are a given state suitable for imaging, based on the output data of these detection sensors. Note that any means other than the above-mentioned detection sensor can be used as long as it can similarly obtain the relative positional relationship, etc. Furthermore, the camera 231 may be configured to be combined with the detection sensor described above to determine the positional relationship between the tube 230 of the radiation generation device 200 and the radiation imaging device 100, the positional relationship between the subject H and the radiation imaging device 100, and the posture of the subject H. In this case, the state control unit 110 may perform control to transition from the standby state to the imaging-enabled state using the determination result determined by the determination unit 320 based on the output data of the detection sensor that the conditions related to the execution of radiation imaging have reached a given state. Furthermore, the state control unit 110 may perform control to transition from the standby state to the imaging-enabled state using the determination result determined by the determination unit 320 based on the camera image captured by the camera 231 and the output data of the detection sensor.

[0059] In this embodiment, an example has been described in which the camera images captured by the camera 231 and the output data of the detection sensor are processed by the console 300, but the present invention is not limited to the console 300 as long as the unit is capable of receiving and processing data. For example, the tube 230 of the radiation generating device 200 may be provided with a unit having this function, or the data may be sent to the radiation imaging device 100 and processed by a processor or hardware within the radiation imaging device 100.

[0060] The threshold value when determining that a given state is suitable for imaging and transitioning from the standby state to the imaging-enabled state and the threshold value when determining that a given state is not suitable for imaging and transitioning from the imaging-enabled state to the standby state may be the same, or may be different with hysteresis. Also, a plurality of threshold values ​​may be prepared so that an appropriate threshold value can be selected according to each system. For example, when using a radiation imaging device 100 that takes time to transition from the standby state to the imaging-enabled state, it is necessary to start the transition from the standby state to a certain extent before irradiating radiation R, so in that case, convenience is not impaired by setting the threshold value to a low level.

[0061] As described above, in the radiation imaging apparatus 100 according to the first embodiment, when the conditions for performing radiation imaging are in a given state, the state control unit 110 performs control to transition from a standby state, which consumes less power than the imaging-enabled state, to a imaging-enabled state. According to this configuration, appropriate radiation imaging can be performed while saving power, and radiation imaging can be performed without impairing the convenience of the operator.

[0062] Second Embodiment Next, a second embodiment will be described. In the following description of the second embodiment, matters common to the first embodiment will be omitted, and only matters different from the first embodiment will be described.

[0063] Fig. 7 is a diagram showing an example of a schematic configuration of a radiography system 10-2 according to a second embodiment of the present disclosure. In Fig. 7, the same components as those shown in Fig. 1 are denoted by the same reference numerals, and detailed description thereof will be omitted. As an example, the radiography system 10-2 is provided in a radiography room S.

[0064] The radiation imaging apparatus 100-1 and the radiation imaging apparatus 100-2 are radiation imaging apparatuses arranged in a radiation imaging room S. These radiation imaging apparatuses 100-1 and 100-2 can be operated by a battery or an external power supply, like the radiation imaging apparatus 100 in the first embodiment.

[0065] In addition to the radiation imaging apparatuses 100-1 and 100-2, the radiation imaging room S is provided with a wireless access point 400 and a console 300 for controlling the radiation imaging apparatuses 100-1 and 100-2. The radiation imaging room S is also provided with a radiation generating apparatus main body 210, a radiation switch 220, and a tube 230 as the radiation generating apparatus 200. The radiation imaging room S is also provided with a generating apparatus IF unit 510 (indicated as "IF" in FIG. 7) for adjusting the timing between the radiation imaging apparatuses 100-1 and 100-2 and the radiation generating apparatus main body 210, and a power supply unit 520 (indicated as "Pwr" in FIG. 7). The power supply unit 520 is a device for supplying power (electricity) to the radiation imaging apparatus 100 (for example, the radiation imaging apparatus 100-2 in FIG. 7). The power supply unit 520 has an interface capable of wired communication in addition to supplying power, and can relay communication between the radiation imaging apparatus 100 (for example, the radiation imaging apparatus 100-2 in FIG. 7) and each communication device. The radiation imaging apparatus 100-1 operates on a battery and transmits radiation images to the console 300 through wireless communication with the wireless access point 400. The radiation imaging apparatus 100-2 is connected to the power supply unit 520, operates on external power supply, and performs wired communication.

[0066] Fig. 8 is a diagram showing an example of the internal functional configuration of the radiation imaging apparatuses 100-1 and 100-2, the radiation generating apparatus 200, the console 300, and the IF box 500 shown in Fig. 7 in a radiation imaging system 10-2 according to the second embodiment of the present disclosure. In Fig. 8, the same components as those shown in Fig. 7 are denoted by the same reference numerals, and detailed description thereof will be omitted.

[0067] The IF box 500 shown in Fig. 8 includes a switch unit 530 in addition to the generator IF unit 510 and the power supply unit 520 shown in Fig. 7. The switch unit 530 has a function of switching Ethernet communication of each device, for example.

[0068] 8, the radiation imaging apparatuses 100-1 and 100-2 and the IF box 500 are connected by wireless communication via the wireless access point 400, but can perform wired communication and receive power supply from the IF box 500 via a cable. In this case, if the cable is a dedicated cable formed by bundling a cable for Ethernet communication and a cable for power supply, handling is easy.

[0069] When the preparation request switch 221 is pressed, the radiation generating apparatus 200 transmits information of a preparation start request to the radiation imaging apparatus 100-1. Also, when the irradiation request switch 222 is pressed, the radiation generating apparatus 200 transmits information of an irradiation request to the radiation imaging apparatuses 100-1 and 100-2. When the radiation generating apparatus main body 210 receives information of permission to irradiate radiation R by the irradiation permission receiving unit 211 when the radiation generating apparatus main body 210 is in a state in which irradiation of radiation R is possible, the radiation generating apparatus 200 irradiates radiation R from the tube 230. A camera 231 is attached to the tube 230 as in the first embodiment. Here, the camera 231 is connected to the console 300 via the switch unit 530 of the IF box 500 by Ethernet.

[0070] Console 300 processes image data of the camera image of camera 231 received via IF box 500 in data processing unit 310, and uses the result to make a determination similar to that in the first embodiment in determination unit 320. Determination unit 320 transmits the determination result to radiation imaging apparatuses 100-1 and 100-2 via IF box 500.

[0071] As shown in Fig. 8, the radiation imaging apparatuses 100-1 and 100-2 have a state control unit 110, an image generation unit 120, and a battery 130. In the radiation imaging apparatuses 100-1 and 100-2, similarly to the radiation imaging apparatus 100 in the first embodiment, the state control unit 110 switches between a standby state in which power consumption is lower than that of the imaging-enabled state and an imaging-enabled state. As shown in Fig. 8, the state control unit 110 has an acquisition unit 111, a preparation request receiving unit 112 that receives a radiation preparation request, and a state transition mode determination unit 113. The image generation unit 120 is an image generating means that generates a radiation image based on the incident radiation R, and has the same configuration as in Fig. 3.

[0072] In the second embodiment, there are a plurality of modes in which the radiation imaging apparatuses 100-1 and 100-2 transition from a standby state to a radiography-enabled state, and an appropriate mode is selected according to the characteristics of the apparatus and the radiography conditions. The state transition mode determination unit 113 performs this function, determines which of the power states of the radiation imaging apparatuses 100-1 and 100-2 should be used as a trigger to cause a state transition, and reflects this in the operation of the state control unit 110.

[0073] Here, a case will be described in which radiation imaging apparatuses 100-1 and 100-2 have two state transition modes. In the following description, when the radiation imaging apparatuses 100-1 and 100-2 are not distinguished from each other and are described as a representative, they will simply be referred to as radiation imaging apparatus 100.

[0074] The first state transition mode is the same as that described in the first embodiment, and images of subject H and radiation imaging apparatus 100 are captured using camera 231 attached to tube 230. In this mode, the image data of the camera image is used to trigger the radiation imaging apparatus 100 to transition from a standby state to a state ready for imaging when a given state suitable for imaging is reached. This mode is referred to as the "imaging preparation completion trigger mode."

[0075] The second state transition mode is a mode in which the radiation imaging apparatus 100 transitions from a standby state to an imaging-enabled state, triggered by pressing the preparation request switch 221 of the radiation generation apparatus 200. This mode is referred to as a "preparation request switch trigger mode."

[0076] Next, the preparation request switch trigger mode will be described. The preparation request receiving unit 112 of the radiation imaging apparatus 100 is a receiving unit that receives information of a radiation preparation request (information including preparation start information for irradiation of radiation R) from the radiation generating apparatus 200. An accumulation time Ta for accumulating electric charges generated by radiation R irradiated in the radiation imaging apparatus 100 is set by the console 300 that receives an imaging order from an in-hospital system or the like. The radiation imaging apparatus 100 acquires information on the accumulation time Ta as part of information related to imaging using the acquisition unit 111. The characteristics of the radiation generating apparatus 200 include an irradiation preparation time when the radiation generating apparatus 200 transitions from a standby state to a state in which irradiation of radiation R is possible. At this time, in this embodiment, time information required for the radiation generating apparatus 200 to prepare for irradiation is referred to as an irradiation preparation time Tg. This irradiation preparation time Tg includes a time until the rotation state of the rotating anode of the tube 230 becomes stable and the in-plane distribution of radiation R becomes uniform, and is a time that differs depending on the tube 230 of the radiation generating apparatus 200. The irradiation preparation time in the radiation generating device 200 of the medical cart K as exemplified in the first embodiment is often longer than the irradiation preparation time in the radiation generating device 200 of the radiography room S in the second embodiment. For example, even if the irradiation request switch 222 is pressed, no irradiation request is issued until the irradiation preparation time Tg has elapsed, and an irradiation request is issued at the time when the irradiation preparation time Tg has elapsed. The preparation request switch 221 and the irradiation request switch 222 are often configured as an integrated two-stage switch. In the present embodiment, the above-mentioned radiation irradiation characteristics are characteristics calculated using, for example, irradiation preparation start information of the radiation R in the radiation generating device 200 and irradiation preparation completion information of the radiation R in the radiation generating device 200.

[0077] In this embodiment, the time information for the radiation imaging apparatus 100 to transition from the standby state to the imaging-enabled state is referred to as imaging preparation time Tp. This imaging preparation time Tp includes the time from when power is supplied to the radiation detection unit 121 until the charge accumulation characteristics are stabilized and artifacts disappear, so that the imaging-enabled state is not immediately reached after the standby state is released and a certain period of time is required. As one of the means for quickly stabilizing the charge accumulation characteristics during this state transition, the drive circuit 122 drives the radiation detection unit 121 during the state transition to continuously discharge dark charge components. In this embodiment, the drive for stabilizing the charge accumulation characteristics during the state transition is called preparatory drive, which is distinguished from the drive in which the drive circuit 122 is operated together with the readout circuit 123 and the accumulated charge is read out as image data of a radiation image. The radiation detection unit 121 generally has a characteristic that the imaging preparation time Tp can be shortened by performing preparatory drive, and the imaging preparation time can be further shortened by increasing the number of preparatory drives per unit time. The accumulation time Ta is the time during which the operation of the drive circuit 122 and the readout circuit 123 is stopped, the switch element 302 is turned off, and the charge generated by the irradiated radiation R is accumulated. In general, the longer the accumulation time Ta, the longer the imaging preparation time Tp. In this embodiment, the imaging preparation time Tp is defined as the time required to transition from the standby state to the imaging-enabled state, and includes the time required to start up the parts required to start the transition from the standby state before the preparatory drive is performed. For example, it includes the recovery time from the suspend mode of the CPU, the power-on and configuration time and initialization time of the FPGA, the time from the power-on of the sensor to the power stabilization, etc.

[0078] 9 is a diagram showing an example of the drive timing of each device and the state of the radiation imaging device 100 in the radiation imaging system 10-2 according to the second embodiment of the present disclosure. Operation in the latter mode will be described with reference to this FIG.

[0079] The operator checks the contents of the imaging on the console 300 according to the imaging order received from a server in the hospital or the like. At that time, the necessary accumulation time Ta is acquired from the imaging conditions linked to the imaging order, and the imaging preparation time Tp of the radiation imaging apparatus 100 according to the accumulation time Ta is calculated. As described above, the imaging preparation time Tp is correlated with the accumulation time Ta, and the imaging preparation time Tp generally becomes longer as the accumulation time Ta becomes longer. This relationship is a characteristic unique to the radiation imaging apparatus 100, and can be set in advance using a catalog value or the like. The console 300 instructs the radiation imaging apparatus 100 (radiation imaging apparatus 100-1 in the example shown in FIG. 7) to the accumulation time Ta as a part of imaging condition information. In addition, the radiation imaging apparatus 100 acquires the irradiation preparation time Tg of the radiation generating apparatus 200 from the imaging conditions. The irradiation preparation time Tg can be obtained by setting time information required for the irradiation preparation of the radiation generating apparatus 200 in advance in the radiation imaging apparatus 100. The irradiation preparation time Tg can be obtained from the specification values ​​and design values ​​of the radiation generating device 200, and can be set by the installer when installing the radiation imaging device 100. Also, information for identifying the radiation generating device 200 or irradiation preparation time information may be included in the protocol and acquired from the console 300. In the case of the radiation generating device 200 whose irradiation preparation time is fixed regardless of the irradiation conditions, the irradiation preparation time can be determined by information for identifying the radiation generating device 200 used for imaging. Also, a configuration may be adopted in which the radiation imaging device 100 communicates with the radiation generating device 200 and acquires the irradiation preparation time Tg. Also, a method may be adopted in which the console 300 or another device communicates with the radiation generating device 200, acquires the irradiation preparation time Tg, and then notifies the radiation imaging device 100 of the acquired information. The irradiation preparation time Tg may be acquired from the radiation generating device 200, or the radiation R may be actually irradiated without placing the subject H, and the irradiation preparation time Tg at that time may be measured. The irradiation preparation time Tg may vary slightly even when the radiation R is irradiated under the same conditions, and may also change when the irradiation conditions such as the tube voltage of the tube 230 are changed. Therefore, the irradiation preparation time Tg may be specified by the average value, minimum value, maximum value, etc., or may be set as a different value for each irradiation condition.This information may be acquired every time the radiation imaging apparatus 100 is started or initialized, or may be acquired when the radiation generating apparatus 200 is changed or the irradiation conditions are changed. Furthermore, the information may be stored and managed as parameters in the radiation imaging apparatus 100, the console 300, another device, etc., linked to the type of the radiation generating apparatus 200, individual radiation imaging technique, irradiation conditions, etc.

[0080] Here, it is assumed that radiation imaging is performed by the radiation imaging apparatus 100-1 shown in FIG. 7, and furthermore, as shown in FIG. 9, the irradiation preparation time Tg≧the imaging preparation time Tp.

[0081] 9, the operator presses the preparation request switch 221 and the irradiation request switch 222. In response to this, the radiation generating device 200 prepares for irradiation of radiation R over an irradiation preparation time Tg. Until irradiation preparation is complete, no radiation irradiation request is issued to the radiation imaging apparatus 100-1 even if the irradiation request switch 222 is pressed. The preparation request issued by pressing the preparation request switch 221 is transmitted to the radiation imaging apparatus 100-1 via the IF box 500 and the wireless access point 400, and is received by the preparation request receiving unit 112.

[0082] In response to this, the radiation imaging apparatus 100-1 starts transition from the standby state in step S102 of FIG. 9, executes preparatory driving for a required time, and completes transition to an imaging-enabled state.

[0083] 9, after the irradiation preparation time Tg has elapsed, the radiation generating apparatus 200 completes preparation for radiation irradiation, and the irradiation permission receiving unit 211 receives radiation irradiation permission issued from the radiation imaging apparatus 100-1. Upon receiving the irradiation permission, the radiation generating apparatus 200 irradiates radiation R from the tube 230, and the radiation imaging apparatus 100-1 enters an accumulation state and accumulates electric charge, and then reads out the electric charge to complete the imaging operation. Correction and transfer of image data of the radiation image are the same as in the first embodiment, and transition of the radiation imaging apparatus 100-1 to a standby state after the imaging operation is also the same as in the first embodiment.

[0084] In the imaging mode in which the pressing of the preparation request switch 221 of the radiation generating device 200 is used as a trigger to transition the radiation imaging device 100-1 to a state in which imaging is possible, the standby state can be maintained until just before radiation imaging, which is very effective in reducing power consumption.

[0085] However, if the irradiation preparation time Tg≧the imaging preparation time Tp, there is always a waiting time caused by the radiation generating device 200, but if the irradiation preparation time Tg<the imaging preparation time Tp, the operator must wait until irradiation for a time longer than the irradiation preparation time Tg. As described above, the irradiation preparation time Tg differs depending on the radiation generating device 200, and may also vary depending on the imaging conditions even for the same radiation generating device 200. Therefore, in this embodiment, the state transition mode determination unit 113 determines an appropriate mode based on the magnitude relationship between the irradiation preparation time Tg and the imaging preparation time Tp.

[0086] Fig. 10 is a flowchart showing an example of a processing procedure in a control method for a radiation imaging apparatus 100 according to the second embodiment of the present disclosure. Specifically, in this embodiment, radiation imaging is performed by the radiation imaging apparatus 100-1 shown in Fig. 7, so Fig. 10 is a flowchart showing an example of a processing procedure in a control method for the radiation imaging apparatus 100-1.

[0087] When the process of the flowchart shown in FIG. 10 starts, first, in step S201, the acquisition unit 111 acquires the irradiation preparation time Tg of the radiation generation device 200.

[0088] Next, in step S202, the acquisition unit 111 acquires the charge accumulation time Ta in the radiation imaging apparatus 100.

[0089] Next, in step S203, the acquisition unit 111 acquires the shooting preparation time Tp based on the accumulation time Ta acquired in step S202.

[0090] Subsequently, in step S204, the state transition mode determination unit 113 determines whether or not the imaging preparation time Tp acquired in step S203 is equal to or less than the irradiation preparation time Tg acquired in step S201.

[0091] As a result of the determination in step S204, if the imaging preparation time Tp is equal to or shorter than the irradiation preparation time Tg (S204 / Y), the process proceeds to step S205. In step S205, the state transition mode determination unit 113 selects the above-mentioned preparation request switch trigger mode. Thereafter, in step S206, the radiation imaging apparatus 100 performs radiation imaging in the preparation request switch trigger mode selected in step S205.

[0092] On the other hand, if the result of the determination in step S204 is that the imaging preparation time Tp is not equal to or less than the irradiation preparation time Tg (the imaging preparation time Tp is greater than the irradiation preparation time Tg) (S204 / N), the process proceeds to step S207. In step S207, the state transition mode determination unit 113 selects the imaging preparation completion trigger mode described above. Thereafter, in step S208, the radiation imaging apparatus 100 performs radiation imaging in the imaging preparation completion trigger mode selected in step S207.

[0093] When the process of step S206 is completed, or when the process of step S208 is completed, the process of the flowchart shown in FIG. 10 is completed.

[0094] 7, the state transition mode determination unit 113 is configured inside the radiation imaging apparatus 100, but is not limited thereto as long as the same operation can be performed, and for example, the state transition mode determination unit 113 may be configured inside the console 300. When the state transition mode determination unit 113 is configured inside the console 300, the radiation imaging apparatus 100 acquires information on the determined mode from the state transition mode determination unit 113 of the console 300 and performs subsequent processing.

[0095] In the second embodiment, the shooting preparation completion trigger mode uses image data of a camera image captured by a camera 231 provided on a tube 230, but a form using output data of a detection sensor as in the case described in the first embodiment is also applicable.

[0096] 10, if the imaging preparation time (Tp) of the radiation imaging apparatus 100 is equal to or shorter than the irradiation preparation time (Tg) of the radiation generating apparatus 200 (S204 / Y), the state control unit 110 of the radiation imaging apparatus 100 performs the following control in step S205. Specifically, if a request for preparation for irradiation of radiation R is made to the radiation generating apparatus 200 in step S205, the state control unit 110 performs control to transition the state of the radiation imaging apparatus 100 from a standby state to an imaging-enabled state. Also, in the example shown in FIG. 10, if the imaging preparation time (Tp) of the radiation imaging apparatus 100 is longer than the irradiation preparation time (Tg) of the radiation generating apparatus 200 (S204 / N), the state control unit 110 of the radiation imaging apparatus 100 performs the following control in step S207. Specifically, in step S207, as in the first embodiment, when the conditions for performing radiation imaging are in a given state, the state control unit 110 controls the transition of the state of the radiation imaging apparatus 100 from a standby state to a state capable of imaging.

[0097] In the second embodiment, similarly to the first embodiment, appropriate radiation imaging can be performed while saving power, thereby enabling radiation imaging to be performed without impairing the convenience of the operator.

[0098] (Third embodiment) Next, a third embodiment will be described. In the following description of the third embodiment, the description of the matters common to the first and second embodiments will be omitted, and only the matters different from the first and second embodiments will be described.

[0099] Fig. 11 is a diagram showing an example of a schematic configuration of a radiation imaging system 10-3 according to a third embodiment of the present disclosure. In Fig. 11, the same components as those shown in Fig. 1 and Fig. 7 are denoted by the same reference numerals, and detailed description thereof will be omitted. The radiation imaging system 10-3 according to the third embodiment shown in Fig. 11 is a radiation imaging system including the radiation imaging system 10-1 according to the first embodiment shown in Fig. 1 and the radiation imaging system 10-2 according to the second embodiment shown in Fig. 7.

[0100] In this embodiment, the radiation imaging apparatus 100 included in the radiation imaging system 10-1 and the radiation imaging apparatuses 100-1 and 100-2 included in the radiation imaging system 10-2 can be used in other radiation imaging systems. However, it is necessary to clarify which radiation imaging apparatus is connected to which radiation imaging system. For example, when communication is performed using a wired cable such as Ethernet, the connection destination is clear, but in the case of wireless communication such as wireless LAN, it is not necessarily known whether the radiation imaging apparatus is connected to the intended network just by moving the radiation imaging apparatus. Therefore, when moving the radiation imaging apparatus to use it in another radiation imaging system, it is first necessary to perform an operation of disconnecting the radiation imaging system before moving and entering the radiation imaging system at the destination (hereinafter referred to as "check-in"). Specifically, the operator may check in by intentionally taking an action using a dedicated communication module (not shown) provided in the radiation imaging system at the destination, for example, infrared, Bluetooth, short-distance wireless communication, etc. If a wired cable is available, the check-in may be performed by connecting the wired cable once. In addition, it is possible to automatically check in by detecting the approach of the destination radiation imaging system without requiring any intentional action, but it is necessary to avoid checking in to the wrong radiation imaging system.

[0101] When the check-in is performed, information for joining the network is transmitted from the destination radiation imaging system to the radiation imaging apparatus and set. Here, the information for joining the network is, for example, an IP address, an SSID or a password of a wireless access point, etc. In addition, information for identifying the radiation imaging apparatus, for example, a MAC address, etc. is transmitted to the destination radiation imaging system. Furthermore, the check-in transmits and sets an imaging mode that can be used in the radiation imaging system. For example, since the radiation imaging room S has a generator IF unit 510 with the radiation generating apparatus 200, the radiation imaging apparatus can receive a press of the preparation request switch 221 from the radiation generating apparatus 200. Furthermore, since the mobile cart K does not have a generator IF unit 510, the radiation imaging apparatus cannot receive a press of the preparation request switch 221. The internal configuration of the radiation imaging apparatus in this embodiment is the configuration shown by the radiation imaging apparatus 100 (100-1 and 100-2) shown in FIG. 8. The state transition mode determination unit 113 determines a state transition mode from the system configuration information obtained by the check-in, the irradiation preparation time Tg, and the imaging preparation time Tp.

[0102] Fig. 12 is a flowchart showing an example of a processing procedure in a control method for the radiation imaging apparatus 100 according to the third embodiment of the present disclosure. In the flowchart shown in Fig. 12, the same processing steps as those in the flowchart shown in Fig. 10 are assigned the same step numbers, and detailed description thereof will be omitted.

[0103] When the processing of the flowchart shown in FIG. 12 starts, first, in step S301, the state transition mode determination unit 113 determines whether or not the system configuration of the currently participating network is capable of receiving a press of the preparation request switch 221.

[0104] If it is determined in step S301 that the system configuration of the currently participating network is not capable of receiving a press of the preparation request switch 221 (S301 / N), the process proceeds to step S302. For example, in the case of a system configuration that cannot receive a press of the preparation request switch 221, such as the radiation imaging system 10-1 (radiography system on the side of the medical cart K), the process proceeds to step S302. In step S302, the state transition mode determination unit 113 selects the imaging preparation completion trigger mode as in step S207. Thereafter, in step S303, the radiation imaging apparatus 100 performs radiation imaging in the imaging preparation completion trigger mode selected in step S302.

[0105] On the other hand, if the result of the determination in step S301 is that the system configuration of the currently participating network is capable of receiving a press of the preparation request switch 221 (S301 / Y), the process proceeds to step S201. For example, if the system configuration is capable of receiving a press of the preparation request switch 221, such as the radiation imaging system 10-2 (radiography system on the side of the radiation imaging room S), the process proceeds to step S201. The process from step S201 onwards is the same as the process in the flowchart shown in FIG. 10, and therefore a description thereof will be omitted.

[0106] In the third embodiment, similarly to the first embodiment, appropriate radiation imaging can be performed while saving power, thereby enabling radiation imaging to be performed without impairing the convenience of the operator.

[0107] In the above embodiment, the camera 231 has been described as being attached to the tube 230 of the radiation generating device 200, but the present disclosure is not limited to this form. For example, a camera attached to the ceiling of the radiography room S may be used, or a network camera attached to the room may be used when visiting hospital beds in a medical cart K. The type of camera 231 is not particularly limited, and the type, number of pixels, frame rate, recording method, etc. are not limited as long as the camera can obtain information sufficient to perform the processing intended in the present disclosure.

[0108] (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) that implements one or more functions. This program and a computer-readable storage medium having the program stored thereon are included in the present disclosure.

[0109] It should be noted that the above-described embodiments of the present disclosure are merely illustrative examples of the implementation of the present disclosure, and the technical scope of the present disclosure should not be interpreted as being limited by these. In other words, the present disclosure can be implemented in various forms without departing from its technical concept or main features.

[0110] Embodiments of the present disclosure include the following configurations, methods, and programs. [Configuration 1] A radiation imaging apparatus for performing radiation imaging of a subject, comprising: an image generating means for generating a radiographic image based on incident radiation; When at least one of the conditions of the positional relationship between a radiation generating device that generates the radiation and the radiation imaging device, the positional relationship between the subject and the radiation imaging device, and the posture of the subject is in a given state for the radiation imaging, a control means for controlling a transition from a standby state, which consumes less power than a radiographing-enabled state in which the radiation can be detected by the image generating means, to the radiographing-enabled state; A radiation imaging apparatus comprising: [Configuration 2] the subject is located between a radiation irradiation unit of the radiation generating device and the radiation imaging device, The positional relationship between the radiation generating device and the radiation imaging device is the positional relationship between the radiation irradiation unit of the radiation generating device and the radiation imaging device. 2. The radiation imaging apparatus according to claim 1, [Configuration 3] The control means performs control to transition from the standby state to the image capturing enabled state using a determination result that the at least one condition determined based on a camera image captured by a camera has reached the given state. 3. The radiation imaging apparatus according to configuration 1 or 2. [Configuration 4] The control means performs control to transition from the standby state to the image capturing enabled state using a determination result that the at least one condition determined based on output data of a detection sensor that detects at least one of a position and a movement has reached the given state. 3. The radiation imaging apparatus according to configuration 1 or 2. [Configuration 5] The control means Using a result of a determination that the at least one condition has become the given state, the result being determined based on a camera image captured by a camera and output data of a detection sensor that detects at least one of a position and a movement, Controlling a transition from the standby state to the image capturing enabled state 3. The radiation imaging apparatus according to configuration 1 or 2. [Configuration 6] The camera is provided in a radiation irradiation unit of the radiation generating device. 6. The radiation imaging apparatus according to configuration 3 or 5, [Configuration 7] The detection sensor includes at least one of an acceleration sensor, a gyro sensor, and a geomagnetic sensor. 6. The radiation imaging apparatus according to configuration 4 or 5, [Configuration 8] The control means performs control to transition from the photographing possible state to the standby state when the at least one condition is not in the given state. 8. The radiation imaging apparatus according to any one of configurations 1 to 7, [Configuration 9] The control means controls the notification means to notify a state where the at least one condition is no longer in the given state after the transition to the photographing possible state. 9. The radiation imaging apparatus according to any one of configurations 1 to 8. [Configuration 10] The notification means performs the notification using at least one of a display and an audio output. 10. The radiation imaging apparatus according to claim 9, [Configuration 11] The notification means is provided in at least one of a control device that controls the radiation imaging device, the radiation imaging device, and the radiation generating device. 11. The radiation imaging apparatus according to configuration 9 or 10. [Configuration 12] The control means performs control to transition to the standby state when the radiographic image is transmitted to a control device that controls the radiographic apparatus after transitioning to the radiography-enabled state. 12. The radiation imaging apparatus according to any one of configurations 1 to 11. [Configuration 13] The control means performs control to transition to the standby state when the image generating means reads out an electrical signal related to the radiation image after transition to the imaging possible state. 13. The radiation imaging apparatus according to any one of configurations 1 to 12. [Configuration 14] The control means when an imaging preparation time of the radiation imaging device is equal to or shorter than a radiation irradiation preparation time of the radiation generating device, when a radiation irradiation preparation request is made to the radiation generating device, performing control to transition the radiation imaging device from the standby state to the imaging enabled state; When the imaging preparation time of the radiation imaging device is longer than the radiation irradiation preparation time of the radiation generating device, when the at least one condition becomes the given state, control is performed to transition from the standby state to the imaging possible state. 14. The radiation imaging apparatus according to any one of configurations 1 to 13. [Configuration 15] The given state is determined based on an imaging order. 15. The radiation imaging apparatus according to any one of configurations 1 to 14. [Configuration 16] The radiation imaging apparatus according to any one of configurations 1 to 15, The radiation generating device; A radiation imaging system comprising: [Method 1] 1. A method for controlling a radiographic imaging apparatus that is provided with an image generating means for generating a radiographic image based on incident radiation and that performs radiographic imaging of a subject, comprising the steps of: When at least one of the conditions of the positional relationship between the radiation generating device that generates the radiation and the radiation imaging device, the positional relationship between the subject and the radiation imaging device, and the posture of the subject is in a given state in the radiation imaging, A control step of controlling the image generating means to transition from a standby state in which power consumption is smaller than a radiographing-enabled state in which radiation can be detected by the image generating means to the radiographing-enabled state. 13. A method for controlling a radiation imaging apparatus comprising: [Program 1] A program for causing a computer to execute the steps of the control method for a radiation imaging apparatus according to the first method. [Explanation of symbols]

[0111] 10: Radiography system, 100: Radiography device, 110: Status control unit, 120: Image generation unit, 130: Battery, 200: Radiation generator, 210: Radiation generator body, 211: Irradiation permission receiving unit, 220: Radiation switch, 221: Preparation request switch, 222: Irradiation request switch, 230: Tube, 231: Camera, 300: Console, 310: Data processing unit, 320: Determination unit, 330: Display unit, 400: Wireless access point, H: Subject, K: Medical cart, R: Radiation, S: Radiography room

Claims

1. A radiation imaging apparatus for performing radiation imaging of a subject, comprising: an image generating means for generating a radiographic image based on incident radiation; a control means for performing control to transition from a standby state, which consumes less power than an imaging ready state in which the image generating means is capable of detecting the radiation, to the imaging ready state, when at least one of conditions among a positional relationship between a radiation generating device that generates the radiation and the radiation imaging device, a positional relationship between the subject and the radiation imaging device, and a posture of the subject becomes a given state for the radiation imaging; A radiation imaging apparatus comprising:

2. the subject is located between a radiation irradiation unit of the radiation generating device and the radiation imaging device, The positional relationship between the radiation generating device and the radiation imaging device is the positional relationship between the radiation irradiation unit of the radiation generating device and the radiation imaging device.

2. The radiation imaging apparatus according to claim 1.

3. The control means performs control to transition from the standby state to the image capturing enabled state using a determination result that the at least one condition, determined based on a camera image captured by a camera, has reached the given state.

2. The radiation imaging apparatus according to claim 1.

4. The control means performs control to transition from the standby state to the image capturing enabled state using a determination result that the at least one condition determined based on output data of a detection sensor that detects at least one of a position and a movement has reached the given state.

2. The radiation imaging apparatus according to claim 1.

5. The control means performs control to transition from the standby state to the image capturing enabled state using a result of a determination that the at least one condition determined based on a camera image captured by a camera and output data of a detection sensor that detects at least one of a position and a movement has reached the given state.

2. The radiation imaging apparatus according to claim 1.

6. The camera is provided in a radiation irradiation unit of the radiation generating device.

6. The radiation imaging apparatus according to claim 3, wherein the radiation imaging apparatus is a radiation imaging apparatus.

7. The detection sensor includes at least one of an acceleration sensor, a gyro sensor, and a geomagnetic sensor.

6. The radiographic apparatus according to claim 4, wherein the first and second imaging sections are arranged in a first plane.

8. The control means performs control to transition from the photographing possible state to the standby state when the at least one condition is not in the given state.

2. The radiation imaging apparatus according to claim 1.

9. The control means controls the notification means to notify a state where the at least one condition is no longer in the given state after the transition to the photographing possible state.

2. The radiation imaging apparatus according to claim 1.

10. The notification means performs the notification by using at least one of a display and an audio output.

10. The radiation imaging apparatus according to claim 9.

11. The notification means is provided in at least one of a control device that controls the radiation imaging device, the radiation imaging device, and the radiation generating device.

10. The radiation imaging apparatus according to claim 9.

12. The control means performs control to transition to the standby state when the radiographic image is transmitted to a control device that controls the radiographic apparatus after transitioning to the radiography-enabled state.

2. The radiation imaging apparatus according to claim 1.

13. The control means performs control to transition to the standby state when the image generating means reads out an electrical signal related to the radiation image after transition to the imaging possible state.

2. The radiation imaging apparatus according to claim 1.

14. The control means when an imaging preparation time of the radiation imaging device is equal to or shorter than a radiation irradiation preparation time of the radiation generating device, when a radiation irradiation preparation request is made to the radiation generating device, performing control to transition the radiation imaging device from the standby state to the imaging enabled state; When the imaging preparation time of the radiation imaging device is longer than the radiation irradiation preparation time of the radiation generating device, when the at least one condition becomes the given state, control is performed to transition from the standby state to the imaging possible state.

2. The radiation imaging apparatus according to claim 1.

15. The given state is determined based on an imaging order.

2. The radiation imaging apparatus according to claim 1.

16. The radiation imaging apparatus according to claim 1 , The radiation generating device; A radiation imaging system comprising:

17. 1. A method for controlling a radiographic imaging apparatus that is provided with an image generating means for generating a radiographic image based on incident radiation and that performs radiographic imaging of a subject, comprising the steps of: a control step of performing control to transition from a standby state in which power consumption is smaller than a radiography-enabled state in which the image generating means is capable of detecting the radiation to the radiography-enabled state when at least one of the conditions of the positional relationship between a radiation generating device that generates the radiation and the radiography device, the positional relationship between the subject and the radiography device, and the posture of the subject becomes a given state in the radiography.

13. A method for controlling a radiation imaging apparatus comprising:

18. A program for causing a computer to execute the steps of the method for controlling a radiation imaging apparatus according to claim 17.

Images