JP2010137058A - Radiation detecting cassette and radiation image capturing system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a radiation detecting cassette effectively utilizing a low remaining power level and acquiring radiation image data even when the remaining power level of a power supply becomes low, and a radiation image capturing system provided with the radiation detecting cassette. <P>SOLUTION: The radiation detecting cassette 24 includes: a radiation detector 40 for detecting a radiation X having passed through a patient 14 and converting it into radiation image data; a transceiver 48 for wirelessly transmitting the radiation image data; a data transmission and reception control part 84 of a cassette control part 46 for controlling the radiation detector 40 and the transceiver 48; a power supply 43 for energizing the radiation detector 40 and the transceiver 48; and a remaining power supply level detector 44 for detecting the remaining power level RC[%] of the power supply 43. The cassette control part 46 stops wireless communication of the radiation image data and prioritizes the capturing of a radiation image when the remaining power level RC of the power supply 43 gets smaller than a predetermined threshold T1. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a radiation detection cassette having a radiation conversion panel for detecting radiation that has passed through a subject and converting it into radiation image data, and a radiation image capturing system having the radiation detection cassette. More specifically, the present invention relates to a radiation detection cassette that transmits the radiation image data to the outside by wireless communication, and a radiation image capturing system having the radiation detection cassette.

  2. Description of the Related Art In the medical field, a radiation image capturing apparatus that irradiates a subject with radiation and guides the radiation transmitted through the subject to a radiation conversion panel to capture a radiation image is widely used. As a radiation conversion panel used in this radiographic imaging apparatus, a conventional radiation film in which a radiographic image is exposed and recorded, or radiation energy as a radiographic image is accumulated in a phosphor and irradiated with excitation light to generate a radiographic image. A stimulable phosphor panel that can be extracted as stimulated emission light is known. These radiation conversion panels supply a radiation film on which a radiographic image is recorded to a developing device to perform development processing, or supply a stimulable phosphor panel to a reading device to perform reading processing so that a visible image can be obtained. A radiographic image is obtained.

  On the other hand, in a place such as an examination room, it is preferable that a radiation image can be read and displayed immediately from the radiation conversion panel after imaging in order to perform a quick and accurate treatment on the patient. Radiation detection using a solid-state detector that converts radiation directly into electrical signals, or converts radiation into visible light with a scintillator and then converts it into electrical signals and reads it as a radiation conversion panel that can meet such demands A vessel has been developed. Such a radiation conversion panel is separated from a console as a control device and a radiation source because it is necessary to photograph various parts (Patent Documents 1 to 3).

  Patent Document 1 discloses a technique in which a radiation image signal is transmitted as a radio signal from a radiation detection cassette having a radiation conversion panel (hereinafter also referred to as “cassette”) to an external signal processing device. (Patent Document 1, paragraph [0043], FIG. 5). Patent Document 2 discloses a technique for detecting the remaining battery level and calculating the number of images that can be shot (paragraph [0033] of Patent Document 2). Further, Patent Document 3 discloses a technique for detecting the remaining amount of a battery and controlling so that X-ray irradiation is not performed when the remaining amount is smaller than a predetermined value (paragraph [0017] of Patent Document 3). ] To [0022]).

Japanese Patent No. 3494683 JP 2005-007086 A JP-A-2005-208269

  In Patent Document 1, the radiation detector (solid state detection element, scan pulse generator, and transfer register) and the transmission processing circuit are driven by one power source (paragraphs [0033] and [0041] in Patent Document 1). In such a configuration, since the power of the power source is used for both radiation detection and data wireless transmission, the power is consumed faster than the configuration in which the power of the power source is used only for radiation detection. As a result, there is a high possibility that the power of the power source for acquiring the necessary number of radiation images will be insufficient.

  In Patent Documents 2 and 3, as described above, the remaining amount of the power source is detected and X-ray imaging is controlled according to the result, but the radiation image data is acquired by effectively utilizing the small remaining amount. Has not been considered.

  The present invention has been made in view of the problems as described above, and a radiation detection cassette capable of acquiring radiation image data by effectively utilizing a small remaining amount even when the remaining amount of a power source is reduced, and this It aims at providing the radiographic imaging system which has a radiation detection cassette.

  A radiation detection cassette according to the present invention includes a radiation conversion panel that detects radiation that has passed through a subject and converts the radiation into radiation image data, wireless communication means that wirelessly transmits the radiation image data, the radiation conversion panel, and the wireless communication Control means for controlling the means, a power source for driving the radiation conversion panel and the wireless communication means, and a remaining amount detecting means for detecting the remaining amount of the power source, wherein the control means comprises a remaining amount of the power source. Is less than a predetermined threshold value, the radio communication of the radiographic image data is stopped, and radiographing of the radiographic image is prioritized.

  According to the present invention, when the remaining amount of the power source falls below the predetermined threshold, radio communication of the radiographic image data is stopped, and radiographing is given priority. Therefore, when the remaining amount of power is low, power is preferentially supplied to radiographic image capturing, and radiation image data can be acquired by effectively utilizing the small remaining amount.

  Here, the predetermined threshold is preferably variable. The power required for radiographic image capture and radiographic data wireless transmission varies depending on the situation such as the planned number of radiographs. By making the predetermined threshold variable, it is possible to set the threshold according to the required power.

  The radiation detection cassette further includes a nonvolatile memory for recording the radiation image data, and the control means records the radiation image data in the nonvolatile memory when the wireless transmission is stopped. It is preferable to do. Thereby, even when the power of the radiation detection cassette is turned off, the radiation image data can be kept in the nonvolatile memory, and the timing for transmitting the radiation image data to the outside can be arbitrarily determined. For this reason, the convenience of a radiation detection cassette can be improved.

  The radiation detection cassette further includes a volatile memory for temporarily recording the radiation image data, and the control means temporarily stores the radiation image data in the volatile memory before the wireless transmission. It is preferable to record them automatically.

  The radiation detection cassette further includes a wired communication unit that wire-transmits the radiation image data, and the control unit is a second unit in which a remaining amount of the power source is lower than the predetermined threshold and lower than the predetermined threshold. When the threshold value is exceeded, the radiation image data may be transmitted to the outside via the wired communication means. In general, wired communication consumes less power than wireless communication. Therefore, even if the power for transmitting radiation image data by wireless communication does not remain in the power source, radiation image data can be transmitted by wired communication. it can. For this reason, the radiographic image data can be externally transmitted earlier than the case where the transmission of the radiographic image data is always stopped when wireless communication is not possible, so that the convenience of the radiation detection cassette can be improved.

  The radiation detection cassette further includes a remaining amount display means for displaying the remaining amount of the power supply, and the remaining amount display means can acquire the radiation image data with at least one remaining amount of the power supply. When the temporary empty value indicating the correct amount is reduced, the remaining power display means may display that the remaining power of the power source is zero.

  Accordingly, it is possible to prompt the photographer to stop the acquisition of the radiation image data when the fact that the remaining amount of the power source is zero is displayed on the remaining amount display means. It can be expected that the power supply is maintained in a state where it can be acquired. As a result, it becomes easy to cope with the case of urgently acquiring radiation image data. Further, it is possible to notify the photographer that the remaining amount of the power source is low, and it is possible to suppress the deterioration of the power source as much as possible by prompting the charging of the power source.

  Here, the control means prohibits the power supply from the power source to the radiation conversion panel when the remaining amount of the power source falls to the temporary empty value, and when receiving a power supply permission command from the outside, It is also possible to permit power supply from the power source to the radiation conversion panel. As a result, the amount of electric power that enables acquisition of at least one radiation image data can be ensured, and it becomes easier to deal with an emergency.

  A radiographic imaging system according to the present invention includes the above-described radiation detection cassette, and a console capable of wireless communication with the radiation detection cassette and controlling the radiation detection cassette, wherein the radiation detection cassette is provided. Notifies the console of the remaining amount of power detected by the remaining amount detecting means, and when the remaining amount of power falls below the predetermined threshold, the console sends the radiation image data to the radiation detection cassette. The radio transmission cassette is instructed to give priority to radiographic image capturing, and the control means of the radiation detection cassette stops radio transmission of the radiographic image data in accordance with an instruction from the console to capture radiographic images. Is given priority.

  According to the above configuration, the radio transmission of radiation image data is stopped on the console side, not on the radiation detection cassette side. Thereby, the processing in the radiation detection cassette can be reduced, and the circuit configuration of the radiation detection cassette can be made simpler. Since the position of the radiation detection cassette is often changed according to the imaging region of the subject, demands for weight reduction and durability are high compared to the console. Therefore, since the circuit configuration of the radiation detection cassette can be made simpler, the performance of the entire radiographic imaging system can be improved.

  The console further includes a remaining amount display means for displaying the remaining amount of the power supply, and the remaining amount display means is an amount by which the remaining amount of the power supply can acquire the radiation image data at least once. May be displayed on the remaining amount display means that the remaining amount of the power source is zero. Thereby, in addition to the effect obtained when the remaining amount display means is provided in the radiation detection cassette, it is not necessary to provide the remaining amount display means in the radiation detection cassette, so that the radiation detection cassette can be reduced in size and weight.

  The console transmits a power supply prohibition command for prohibiting power supply from the power supply to the radiation conversion panel to the control means when the remaining amount of the power supply falls to the temporary empty value, and the control means includes: In response to the power supply prohibition instruction, power supply from the power source to the radiation conversion panel is prohibited, and when the power supply from the power source to the radiation conversion panel is commanded to the console from the outside, the console A power supply command for requesting power supply from the power source to the radiation conversion panel is transmitted to the control unit, and the control unit permits the power supply from the power source to the radiation conversion panel according to the power supply command. You can also. Also in this case, since the processing can be transferred from the radiation detection cassette to the console, the radiation detection cassette can be reduced in size and weight.

  According to the present invention, when the remaining amount of the power source falls below the predetermined threshold, radio communication of the radiographic image data is stopped, and radiographing is given priority. Therefore, when the remaining amount of power is low, power is preferentially supplied to radiographic image capturing, and radiation image data can be acquired by effectively utilizing the small remaining amount.

FIG. 1 is a view showing an examination room in which a radiographic imaging system according to the first embodiment of the present invention is installed. FIG. 2 is an internal configuration diagram of the radiation detection cassette. FIG. 3 is a circuit configuration block diagram of the radiation detector. FIG. 4 is a configuration block diagram of the radiographic image capturing system according to the first embodiment. FIG. 5 is a flowchart showing the operation of the radiographic image capturing system according to the first embodiment. FIG. 6 is a flowchart showing in detail a part of the processing shown in FIG. FIG. 7 is a configuration block diagram of a radiographic image capturing system according to the second embodiment. FIG. 8 is a configuration block diagram of a radiographic image capturing system according to the third embodiment. FIG. 9 is a configuration block diagram of a modified example of the radiographic image capturing system according to the third embodiment. FIG. 10 is another configuration diagram of the radiation detection cassette. FIG. 11 is a configuration diagram of a cradle that charges the radiation detection cassette.

[A. First Embodiment]
1. Configuration of Radiographic Imaging System 10 (1) Overall Configuration FIG. 1 shows an examination room 12 in which a radiographic imaging system 10 (hereinafter also referred to as “imaging system 10”) according to the first embodiment of the present invention is installed. It is explanatory drawing. In the examination room 12, in addition to the imaging system 10, an examination table 16 on which the patient 14 lies is arranged.

  The imaging system 10 includes a mobile radiographic imaging apparatus 20 (hereinafter also referred to as “imaging apparatus 20”) capable of processing such as irradiation of radiation X and display of a radiographic image, and radiation X transmitted through a patient 14. A radiation detection cassette 24 (hereinafter also referred to as “cassette 24”) having a built-in radiation detector (described later) for detection is provided.

  The imaging device 20 includes a radiation irradiation device 22 (hereinafter also referred to as “irradiation device 22”) for irradiating the patient 14 with radiation X having a dose according to the radiation detection imaging conditions, and radiation image data based on the radiation X. Is received from the cassette 24 via the console 28, and a display device 26 that displays a radiation image based on the radiation image data, and a console 28 that controls the irradiation device 22, the cassette 24, and the display device 26 are provided. Signals are transmitted and received by wireless communication between the cassette 24 and the console 28. Further, by connecting the cassette 24 and the console 28 with a cable 49 (FIG. 2), it is possible to transmit and receive signals between them by wired communication.

  The radiation irradiation device 22 is connected to the universal arm 30 and can be moved to a desired position corresponding to the imaging region of the patient 14 and can be retracted to a position that does not interfere with the medical examination by the doctor 18 or the imaging technician. Similarly, the display device 26 is connected to the free arm 32 and can be moved to a position where the doctor 18 can easily confirm the captured radiographic image.

(2) Radiation detection cassette 24
FIG. 2 is an internal configuration diagram of the radiation detection cassette 24. The cassette 24 includes a casing 34 made of a material that transmits the radiation X. Inside the casing 34, a grid 38 for removing scattered radiation of the radiation X by the patient 14 from the irradiation surface 36 side of the casing 34 to which the radiation X is irradiated, and a radiation detector 40 for detecting the radiation X transmitted through the patient 14. (Radiation conversion panel) and a lead plate 42 that absorbs backscattered rays of radiation X are sequentially disposed. Note that the irradiation surface 36 of the casing 34 may be configured as a grid 38.

  Further, inside the casing 34, a power source 43 of the radiation detection cassette 24, a cassette control unit 46 that drives and controls the radiation detector 40 with power supplied from the power source 43, and the radiation X detected by the radiation detector 40. A transceiver 48 that receives and transmits radiographic image data including information to and from the console 28 by radio communication is accommodated. Further, a cable 49 for wired communication can be connected to the transmitter / receiver 48 to perform wired communication with the console 28. Further, on the surface opposite to the irradiation surface 36, a touch panel 45 for performing various settings and displaying messages is provided. The cassette controller 46 and the transmitter / receiver 48 are preferably provided with a lead plate or the like on the irradiation surface 36 side of the casing 34 in order to avoid damage due to irradiation with the radiation X.

  When the cassette 24 is used in the examination room 12 or the like, there is a risk that blood or other germs may adhere. Therefore, one cassette 24 can be repeatedly used by making the cassette 24 have a waterproof and airtight structure and sterilizing and cleaning as necessary.

  The cassette 24 is not limited to being used in the examination room 12, and can be applied to, for example, operating rooms, examinations, and rounds in hospitals.

  Further, the wireless communication between the cassette 24 and the external device may be performed by optical wireless communication using infrared rays or the like instead of normal communication using radio waves.

(3) Radiation Detector FIG. 3 is a block diagram of the circuit configuration of the radiation detector 40. The radiation detector 40 has a photoelectric conversion layer 51 made of a substance such as amorphous selenium (a-Se) that senses the radiation X and generates a charge on an array of matrix thin film transistors (TFTs) 52. After the generated charge is stored in the storage capacitor 53, the TFT 52 is sequentially turned on for each row, and the charge is read as an image signal. In FIG. 3, only the connection relationship between one pixel 50 including the photoelectric conversion layer 51 and the storage capacitor 53 and one TFT 52 is shown, and the configuration of the other pixels 50 is omitted. Amorphous selenium must be used within a predetermined temperature range because its structure changes and its function decreases at high temperatures. Therefore, it is preferable to provide means for cooling the radiation detector 40 in the cassette 24.

  A gate line 54 extending parallel to the row direction and a signal line 56 extending parallel to the column direction are connected to the TFT 52 connected to each pixel 50. Each gate line 54 is connected to a line scanning drive unit 58, and each signal line 56 is connected to a multiplexer 66 constituting a reading circuit.

  Control signals Von and Voff for controlling on / off of the TFTs 52 arranged in the row direction are supplied from the line scanning drive unit 58 to the gate line 54. In this case, the line scan driving unit 58 includes a plurality of switches SW1 that switches the gate lines 54, and an address decoder 60 that outputs a selection signal for selecting one of the switches SW1. An address signal is supplied from the cassette control unit 46 to the address decoder 60.

  In addition, the charge held in the storage capacitor 53 of each pixel 50 flows out to the signal line 56 through the TFTs 52 arranged in the column direction. This charge is amplified by the amplifier 62. A multiplexer 66 is connected to the amplifier 62 via a sample and hold circuit 64. The multiplexer 66 includes a plurality of switches SW2 for switching the signal line 56, and an address decoder 68 for outputting a selection signal for selecting one of the switches SW2. An address signal is supplied from the cassette control unit 46 to the address decoder 68. An A / D converter 70 is connected to the multiplexer 66, and radiation image data converted into a digital signal by the A / D converter 70 is supplied to the cassette control unit 46.

(4) Details of Each Component FIG. 4 is a configuration block diagram of the radiation image capturing system 10 including the radiation irradiation device 22, the radiation detection cassette 24, the display device 26, and the console 28. The console 28 is connected to a radiology information system (RIS) 29 for comprehensively managing radiographic image data and other information handled in the radiology department in the hospital. A medical information system (HIS) 31 for comprehensively managing information is connected.

(A) Radiation irradiation device 22
The radiation irradiation apparatus 22 receives imaging conditions from the imaging switch 72, the radiation source 74 that outputs the radiation X, and the console 28 through wireless communication, and transmits a signal such as an imaging completion signal through wireless communication to the console 28. And a radiation source controller 78 that controls the radiation source 74 based on the imaging start signal supplied from the imaging switch 72 and the imaging conditions supplied from the transceiver 76.

(B) Radiation detection cassette 24
The cassette 24 accommodates a radiation detector 40, a power source 43, a remaining power source detection unit 44, a cassette control unit 46, a transceiver 48 and a touch panel 45. The power source 43 drives the radiation detector 40, the remaining power source detection unit 44, the cassette control unit 46, the transceiver 48 and the touch panel 45.

  The cassette controller 46 includes an address signal generator 80 that supplies an address signal to the address decoder 60 of the line scan driver 58 (FIG. 3) and the address decoder 68 of the multiplexer 66 that constitute the radiation detector 40, and radiation detection. In the memory 82 for storing the radiation image data detected by the device 40 and the cassette ID data for specifying the radiation detection cassette 24, and the remaining amount RC [%] of the power source 43 detected by the remaining power source detection unit 44. Accordingly, a data transmission / reception control unit 84 that controls transmission of radiation image data is provided.

  The memory 82 includes a volatile memory 86 that temporarily stores radiation image data and a non-volatile memory 88 that permanently stores radiation image data and cassette ID data. The volatile memory 86 is, for example, a DRAM, and each data is lost when the power supply from the power source 43 is stopped. The non-volatile memory 88 is, for example, a flash memory, and continues to hold radiation image data and cassette ID data even when power supply from the power supply 43 is stopped.

  The transmitter / receiver 48 receives the cassette ID data and the radiographic image data transmission request signal from the console 28 by wireless communication or wired communication, while the cassette ID data stored in the nonvolatile memory 88 and the volatile data are transmitted to the console 28. The radiographic image data stored in the volatile memory 86 or the nonvolatile memory 88 is transmitted by wireless communication or wired communication.

  On the touch panel 45, various settings of the cassette 24 can be performed by an operator's operation, and a message is displayed to the operator.

(C) Display device 26
The display device 26 includes a receiver 90 that receives radiation image data from the console 28, a display control unit 92 that performs display control of the received radiation image data, and a display that displays the radiation image data processed by the display control unit 92. Part 94.

(D) Console 28
The console 28 is necessary for imaging with the radiation device 22 and a transmitter / receiver 96 that transmits / receives necessary information including radiation image data to / from the radiation irradiation device 22, the radiation detection cassette 24, and the display device 26 by wireless communication or wired communication. An imaging condition management unit 98 that manages various imaging conditions, an image processing unit 100 that performs image processing on radiation image data transmitted from the cassette 24, an image memory 101 that stores the processed radiation image data, and an imaging target. A patient information management unit 102 that manages patient information of the patient 14 and a cassette information management unit 104 that manages cassette information are provided.

  The imaging conditions are conditions for determining a tube voltage, a tube current, an irradiation time, and the like for irradiating radiation X having an appropriate dose to an imaging region of the patient 14. And conditions such as a photographing method. Further, the scheduled number of shots is also included in the shooting conditions. The patient information is information for identifying the patient 14 such as the name, sex, and patient ID number of the patient 14. The imaging ordering information including these imaging conditions and patient information can be set directly on the console 28 or supplied to the console 28 from the outside via the RIS 29.

  The cassette information is cassette ID data for specifying the cassette 24.

2. Operation of the First Embodiment The radiographic image capturing system 10 of the first embodiment is basically configured as described above. Next, the operation will be described with reference to FIGS. 5 and 6. .

  The imaging system 10 is installed in the examination room 12 and is used, for example, when a radiographic image needs to be taken during the examination of the patient 14 by the doctor 18. Therefore, the patient information of the patient 14 to be imaged is registered in advance in the patient information management unit 102 of the console 28 prior to imaging. In addition, when the imaging region, the imaging method, and the scheduled number of imaging are determined in advance, these imaging conditions are registered in the imaging condition management unit 98 in advance. In the state where the above preparatory work is completed, the patient 14 is examined.

  When radiographing is performed during the examination, the console 28 transmits a reception confirmation request signal for requesting confirmation of reception to a predetermined range in response to an input of an imaging start command from the doctor 18 or a radiographer in charge. The doctor 18 or a radiographer in charge installs the cassette 24 at a predetermined position between the patient 14 and the examination table 16 with the irradiation surface 36 facing the radiation irradiation apparatus 22. At this time, when receiving the reception confirmation request signal from the console 28, the cassette 24 transmits a reception confirmation notification signal for notifying the reception confirmation to the console 28. Thereby, communication is established between the cassette 24 and the console 28 (step S1).

  In step S <b> 2, the cassette 24 detects the remaining amount RC of the power source 43 by the power remaining amount detection unit 44, triggered by reception of the reception confirmation request signal from the console 28. In step S3, the cassette control unit 46 selects a method of handling radiation image data based on the detected remaining amount RC. Options for handling include wireless transmission, wired transmission, and storage in non-volatile memory 88.

  FIG. 6 is a flowchart showing in detail the process of step S3. In step S31, the cassette control unit 46 confirms the scheduled number of radiographic image data. That is, the data transmission / reception control unit 84 of the cassette control unit 46 transmits a scheduled shooting number inquiry signal for inquiring the scheduled shooting number to the shooting condition management unit 98 of the console 28. In response to the scheduled shooting number inquiry signal, the shooting condition management unit 98 returns a scheduled shooting number notification signal for notifying the scheduled shooting number. The cassette control unit 46 confirms the scheduled number of shots from the scheduled number of shots notification signal.

  In step S32, the data transmission / reception control unit 84 of the cassette control unit 46 sets threshold values T1, T2, and T3 [%] (T1> T2> T3) of the remaining amount RC of the power supply 43 according to the planned number of shots. The threshold values T1, T2, and T3 are ratio values when the maximum value of the remaining amount RC of the power supply 43 is 100%. The threshold value T1 is a minimum value of the remaining amount RC that can wirelessly transmit all of the radiation image data corresponding to the planned number of shots. The threshold value T2 is a minimum value of the remaining amount RC that is capable of wirelessly transmitting a part of the radiation image data corresponding to the planned number of radiographs, but capable of transmitting all of the radiation image data by wire in the case of wired communication. is there. The threshold value T3 is a minimum value of the remaining amount RC that can be stored in the nonvolatile memory 88, although wireless communication and wired communication are not possible. If the threshold value T3 is not reached, shooting is not possible. For the threshold values T1, T2, and T3, for example, the value of the remaining amount RC required for wireless transmission, wired transmission, and storage in the non-volatile memory 88 when the planned number of shots is one is obtained in advance, and this value is scheduled. It can be calculated by multiplying the number of shots. Alternatively, the value of the remaining amount RC necessary for wireless transmission, wired transmission, and storage in the nonvolatile memory 88 may be calculated in advance for each scheduled number of shots.

  In step S33, the data transmission / reception control unit 84 determines whether or not the remaining amount RC detected by the power remaining amount detection unit 44 is equal to or greater than a threshold value T1. When the remaining amount RC is equal to or greater than the threshold value T1, in step S34, the cassette control unit 46 selects “wireless transmission” as the method of handling radiation image data. If the remaining amount RC is less than the threshold value T1, the process proceeds to step S35.

  In step S <b> 35, the data transmission / reception control unit 84 determines whether or not the remaining amount RC detected by the power remaining amount detection unit 44 is equal to or greater than the threshold T <b> 2. If the remaining amount RC is greater than or equal to the threshold value T2, in step S36, the cassette control unit 46 sends a message to the touch panel 45 notifying that the remaining amount RC is insufficient and data transmission cannot be performed by wireless communication. indicate. In a succeeding step S37, a message asking whether to select data transmission by wire communication or storage in the nonvolatile memory 88 is displayed on the touch panel 45.

  If wired data communication is selected in step S37, in step S38, the data transmission / reception control unit 84 displays a message prompting the connection of the cable 49 on the touch panel 45, and the cable 49 is connected in step S39. Until the cable 49 is connected. When the cable 49 is connected, in step S3A, the cassette control unit 46 selects “wired transmission” as the radiation image data handling method.

  If saving to the nonvolatile memory 88 is selected in step S37, the process proceeds to step S3C described later.

  In step S35, when the remaining amount RC is less than the threshold value T2, in step S3B, the data transmission / reception control unit 84 determines whether or not the remaining amount RC detected by the power remaining amount detection unit 44 is equal to or greater than the threshold value T3. To do. When the remaining amount RC is equal to or greater than the threshold value T3, in step S3C, the data transmission / reception control unit 84 selects “save in the nonvolatile memory 88” as the handling method of the radiation image data, and the selection is performed in step S3D. That is, a message indicating that the radiation image data is stored in the cassette 24 is displayed on the touch panel 45. In addition, the message can be displayed on the display device 26 via the console 28. In addition, the cassette 24 notifies the console 28 that “save in the non-volatile memory 88” has been selected as the method of handling the radiation image data. Thereby, the console 28 can know that no radiation image data is transmitted from the cassette 24 at the present time.

  In step S3B, when the remaining amount RC is less than the threshold value T3, in step S3E, the cassette control unit 46 displays a message on the touch panel 45 that the radiation image data cannot be acquired.

  Returning to FIG. 5, when the radiation image data handling method is selected in step S <b> 3, the doctor 18 moves the radiation irradiation device 22 to a position facing the cassette 24 in step S <b> 4, and then operates the imaging switch 72. Shooting is performed.

  At the time of imaging, the radiation source control unit 78 of the radiation irradiation apparatus 22 acquires imaging conditions related to the imaging region of the patient 14 from the imaging condition management unit 98 of the console 28 via the transceivers 96 and 76, and acquires the acquired imaging. By controlling the radiation source 74 according to the conditions, the patient 14 is irradiated with the radiation X having a predetermined dose.

  The radiation X transmitted through the patient 14 is irradiated with the radiation detector 40 after the scattered radiation is removed by the grid 38 of the cassette 24, and is converted into an electric signal by the photoelectric conversion layer 51 of each pixel 50 constituting the radiation detector 40. It is converted and held as a charge in the storage capacitor 53 (see FIG. 3). Next, the charge information, which is the radiation image data of the patient 14 held in each storage capacitor 53, is in accordance with the address signal supplied from the address signal generator 80 constituting the cassette controller 46 to the line scan driver 58 and the multiplexer 66. Read out.

  That is, the address decoder 60 of the line scan driver 58 outputs a selection signal according to the address signal supplied from the address signal generator 80, selects one of the switches SW1, and the TFT 52 connected to the corresponding gate line 54. A control signal Von is supplied to the gates of the first and second gates. On the other hand, the address decoder 68 of the multiplexer 66 outputs a selection signal in accordance with the address signal supplied from the address signal generation unit 80, sequentially switches the switch SW2, and is connected to the gate line 54 selected by the line scan driving unit 58. Radiation image data as charge information held in the storage capacitor 53 of each pixel 50 is sequentially read out via the signal line 56.

  In step S <b> 5, the cassette control unit 46 temporarily records the radiation image data in the volatile memory 86. That is, the radiation image data read from the storage capacitor 53 of each pixel 50 connected to the selected gate line 54 of each radiation detector 40 is amplified by each amplifier 62 and then each sample and hold circuit 64. The sampled signal is supplied to the A / D converter 70 through the multiplexer 66 and converted into a digital signal. The radiographic image data converted into the digital signal is temporarily recorded in the volatile memory 86 of the cassette control unit 46.

  Similarly, the address decoder 60 of the line scan driving unit 58 sequentially switches the switch SW1 in accordance with the address signal supplied from the address signal generating unit 80, and the storage capacitor 53 of each pixel 50 connected to each gate line 54. The stored radiation image data as charge information is read out via the signal line 56 and recorded in the volatile memory 86 of the cassette control unit 46 via the multiplexer 66 and the A / D converter 70.

  In step S6, the cassette control unit 46 confirms the handling method selected in step S3. If wireless transmission is selected in step S3, in step S7, the cassette control unit 46 transmits the radiation image data to the console 28 by wireless communication. If wired transmission is selected in step S3, in step S8, the cassette control unit 46 transmits the radiation image data to the console 28 by wired communication.

  When the wireless transmission in step S7 or the wired transmission in step S8 is performed, the radiation image data is displayed on the display device 26 in step S9. That is, the radiographic image data transmitted from the cassette 24 to the console 28 is received by the transmitter / receiver 96, subjected to predetermined image processing in the image processing unit 100, and then registered in the patient information management unit 102. Is stored in the image memory 101 in a state associated with the patient information. The radiographic image data subjected to image processing is transmitted from the transceiver 96 to the display device 26. The display device 26 that has received the radiation image data by the receiver 90 controls the display unit 94 by the display control unit 92 to display the radiation image. The doctor 18 performs a diagnosis while confirming the radiographic image displayed on the display unit 94.

  When wireless communication is performed between the cassette 24 and the console 28, a cable 49 for transmitting and receiving signals is not connected between the two, and therefore, for example, the cable 49 is arranged on the floor surface of the examination room 12. There is no possibility that it will interfere with the work of the doctor 18 or the like.

  If saving to the non-volatile memory 88 is selected in step S <b> 3, in step S <b> 10, the cassette control unit 46 saves the radiation image data in the non-volatile memory 88 without transmitting it to the console 28. The radiation image data stored in the non-volatile memory 88 increases the remaining amount RC of the power source 43 by charging or replacing the power source 43 of the cassette 24 or connecting a power cable (not shown) to the cassette 24. Can be sent to the console 28.

3. Effects of First Embodiment As described above, in the first embodiment, the data transmission / reception control unit 84 of the cassette control unit 46 wirelessly transmits radiographic image data when the remaining amount RC of the power supply 43 becomes less than the threshold value T1. Stop communication and give priority to radiographic imaging. As a result, when the remaining amount RC of the power source 43 is reduced, power is preferentially supplied to radiographic image capturing, and radiation image data can be acquired by effectively utilizing the small remaining amount RC.

  In the first embodiment, the threshold value T1 is variable. The power required for radiographic image capture and radiographic data wireless transmission varies depending on the situation such as the planned number of radiographs. By making the threshold value T1 variable, it is possible to set the threshold value T1 according to the required power.

  The data transmission / reception control unit 84 records radiation image data in the nonvolatile memory 88 when wireless transmission and wired transmission are stopped. Thereby, even when the power of the cassette 24 is turned off, the radiation image data can be kept in the nonvolatile memory 88, and the timing for transmitting the radiation image data to the console 28 can be arbitrarily determined. For this reason, the convenience of the radiation detection cassette 24 can be improved.

  When the remaining amount RC of the power supply 43 is less than the threshold value T1 and greater than or equal to the threshold value T2, the data transmission / reception control unit 84 transmits the radiation image data to the console 28 by wired communication. In general, wired communication consumes less power than wireless communication. Therefore, even if the power for transmitting radiation image data by wireless communication does not remain in the power supply 43, the radiation image data is transmitted by wired communication. Can do. For this reason, since radiographic image data can be externally transmitted earlier than when transmission of radiographic image data is always stopped when wireless communication is not possible, the convenience of the cassette 24 can be improved.

[B. Second Embodiment]
1. Configuration of radiation image capturing system 10A (difference from the first embodiment)
FIG. 7 is a configuration block diagram of a radiographic imaging system 10A (hereinafter also referred to as “imaging system 10A”) according to the second embodiment. The imaging system 10A of the second embodiment is basically the same as the imaging system 10 of the first embodiment. However, the radiographing image data handling method (wireless transmission, wired transmission, or storage in the nonvolatile memory 88) is selected not on the cassette 24 side but on the console 28 side. Different. That is, the imaging system 10 </ b> A has a data transmission / reception control unit 106 in the console 28. The selection of the radiation image data handling method (step S3 in FIG. 5 and steps S31 to S3E in FIG. 6) is performed by the data transmission / reception control unit 106 of the console 28, not the data transmission / reception control unit 84 of the cassette 24. The message display (steps S36, S38, and S3D in FIG. 6) is performed using the display unit 94 of the display device 26 instead of the touch panel 45 of the cassette 24. The data transmission / reception control unit 84 of the cassette 24 transmits the remaining amount RC detected by the power remaining amount detection unit 44 to the console 28, receives the method of handling the radiation image data selected by the console 28, and uses this method. Perform later processing. In addition, about the component similar to the imaging | photography system 10, the same referential mark is attached | subjected and the description is abbreviate | omitted.

2. Effects of Second Embodiment As described above, in the second embodiment, the method for handling radiographic image data is selected not on the cassette 24 side but on the console 28 side. As a result, the processing in the cassette 24 can be reduced, and the circuit configuration of the cassette 24 can be simplified. Since the cassette 24 is often changed in position according to the imaging region of the patient 14, demands for weight reduction and durability are higher than those of the console 28. Accordingly, since the circuit configuration of the cassette 24 can be made simpler, the performance of the entire photographing system 10A can be improved.

[C. Third Embodiment]
1. Configuration of Radiation Image Capturing System 10B (Difference from First Embodiment)
FIG. 8 is a configuration block diagram of a radiographic image capturing system 10B (hereinafter also referred to as “imaging system 10B”) according to the third embodiment. The imaging system 10B of the third embodiment is basically the same as the imaging system 10 of the first embodiment. However, the imaging system 10B is different from the imaging system 10 in that it has a configuration that ensures a certain amount of the remaining amount RC of the power supply 43 for emergency imaging. In other words, in the photographing system 10B, the cassette 24 has a remaining power level display unit 108, and the remaining power level RC detected by the remaining power level detection unit 44 is displayed on the remaining power level display unit 108. Here, the remaining power amount display unit 108 displays that the remaining amount RC is zero when the remaining amount RC of the power source 43 falls to the temporary empty value Ep. As the temporary empty value Ep, a remaining amount RC capable of acquiring at least one radiation image data can be set. In this embodiment, for example, a remaining amount RC capable of acquiring ten times of radiation image data is set. The temporary empty value Ep is set.

  In addition, the data transmission / reception control unit 84 of the cassette control unit 46 instructs the power supply 43 to prohibit power supply to the radiation detector 40 when the remaining amount RC of the power supply 43 falls to the temporary empty value Ep. The power supply 43 that has received this command stops the power supply to the radiation detector 40 by a process such as turning off a switch (not shown).

  The cassette 24 is provided with an emergency shooting button 110, and when the photographer presses the emergency shooting button 110 even when the remaining amount RC drops to the temporary empty value Ep (in other words, the power supply permission from the photographer). When receiving the command), the data transmission / reception control unit 84 commands the power supply 43 to supply power to the radiation detector 40. The power supply 43 that has received this command restarts the power supply to the radiation detector 40 by a process such as turning on the switch, and continues the power supply until the remaining amount RC of the power supply 43 becomes zero.

2. Advantages of the Third Embodiment As described above, in the third embodiment, the remaining power amount display unit 108 in accordance with the fact that the actual remaining amount RC of the power source 43 has decreased to the temporary empty value Ep even if it is not zero. Displays that the remaining amount RC is zero. As a result, the photographer can be prompted to stop the acquisition of the radiation image data, and as a result, it can be expected that the power supply 43 is maintained in a state where at least one acquisition of the radiation image data is possible. As a result, it becomes easy to cope with the case of urgently acquiring radiation image data. In addition, it is possible to notify the photographer that the remaining amount RC of the power source 43 is low, and it is possible to suppress deterioration of the power source 43 as much as possible by prompting the power source 43 to be charged.

  Further, the data transmission / reception control unit 84 prohibits power supply from the power supply 43 to the radiation detector 40 when the remaining amount RC of the power supply 43 falls to the temporary empty value Ep, and when the emergency imaging button 110 is pressed, The power supply from the power supply 43 to the radiation detector 40 is permitted. As a result, the amount of electric power that enables at least one acquisition of radiation image data can be ensured, and it becomes easier to deal with an emergency.

[D. Modified example]
The present invention is not limited to the above-described embodiments, and it is needless to say that various configurations can be adopted based on the contents described in this specification. For example, the following configurations 1 to 5 can be adopted.

1. Radiation imaging system 10, 10A, 10B
In each of the above embodiments, the imaging systems 10, 10A, and 10B are arranged in the examination room 12, but the place to arrange is not limited to this. For example, the imaging systems 10, 10 </ b> A, and 10 </ b> B can be brought into each hospital room for use in rounds. Further, the photographing systems 10, 10A, and 10B may be mounted instead of movable.

  In each of the above embodiments, the imaging system 10 is connected to the RIS 29. However, the imaging system 10 may be used alone. In this case, the cassette ID and patient ID can be input to the console 28 directly on the console 28 itself.

2. Radiation conversion panel (radiation detector 40)
In each of the above embodiments, the radiation detector 40 accommodated in the radiation detection cassette 24 converts the dose of the incident radiation X directly into an electric signal by the photoelectric conversion layer 51. A radiation detector configured to convert the visible light once into visible light by a scintillator and then convert the visible light into an electrical signal using a solid-state detection element such as amorphous silicon (a-Si) may be used. (See Japanese Patent No. 3494683).

  Also, radiation image data can be obtained using a light conversion type radiation detector. In this light conversion type radiation detector, when radiation is incident on each solid detection element arranged in a matrix, an electrostatic latent image corresponding to the dose is accumulated and recorded in the solid detection element. When reading the electrostatic latent image, the radiation detector is irradiated with reading light, and the value of the generated current is acquired as radiation image data. The radiation detector can erase and reuse the radiation image data, which is a remaining electrostatic latent image, by irradiating the radiation detector with erasing light (see Japanese Patent Laid-Open No. 2000-105297). .

3. Power supply 43 and remaining power detection unit 44
In each of the above embodiments, the radiation detector 40, the remaining power detection unit 44, the touch panel 45, the cassette control unit 46, and the transceiver 48 are driven by one power source 43, but these devices are driven using a plurality of power sources. May be. In this case, one or a plurality of remaining power level detectors 44 may be provided to detect the remaining power RC of the power source that drives the radiation detector 40 and the power source that drives the transceiver 48.

4). Threshold values T1, T2, T3
In each of the above-described embodiments, the thresholds T1, T2, and T3 are set according to the scheduled number of shots. However, resolution, sensitivity, and the like can be used as elements for setting the thresholds T1, T2, and T3. Further, a configuration that does not use any of the threshold values T1, T2, and T3 is also possible.

5). Others In each of the above embodiments, the console 28 is disposed in the examination room 12. However, as long as it can transmit and receive signals to and from the radiation irradiation device 22, the radiation detection cassette 24, and the display device 26 by wireless communication, The console 28 may be installed outside the examination room 12.

  In each of the embodiments described above, the cassette control unit 46 records the radiation image data in the nonvolatile memory 88 when the wireless transmission and the wired transmission of the radiation image data are stopped. There is no. For example, a configuration in which radiation image data is temporarily recorded in the volatile memory 86, power is supplied from the outside to the cassette 24, and wireless transmission is performed using the power is also possible.

  In each of the above embodiments, the radiation image data is temporarily recorded in the volatile memory 86. However, when the wireless transmission through the transceiver 48 is performed at high speed, or the radiation image data of the nonvolatile memory 88 is stored. When recording is performed at high speed, a configuration in which the volatile memory 86 is not used is also possible.

  In each of the above embodiments, radiation image data is transmitted using wired transmission in addition to wireless transmission, but a configuration not using wireless transmission or wired transmission is also possible.

  In each of the embodiments described above, when wireless transmission and wired transmission are stopped and radiation image data is recorded in the nonvolatile memory 88 of the cassette 24, a message notifying the fact is displayed on the touch panel 45 of the cassette 24. Instead, an LED indicating that wireless transmission or wired transmission is being performed or an LED indicating that data is stored in the nonvolatile memory 88 is provided in the cassette 24, and the lighting state or color change of these LEDs is changed. A method for handling radiation image data can also be shown.

  In the third embodiment, the power supply from the power source 43 to the radiation detector 40 is stopped when the temporary empty value Ep is lowered, but only the fact that the remaining amount RC is zero is displayed on the remaining power amount display unit 108. Thus, the power supply can be continued.

  In the third embodiment, the configuration that secures the remaining amount RC of the power source 43 to a certain extent for emergency shooting is realized only in the cassette 24, but is not limited thereto. For example, in the radiographic image capturing system 10C shown in FIG. 9 (hereinafter, also referred to as “imaging system 10C”), the cassette 24 and the console 28 are used to secure a certain amount of remaining RC of the power source 43 for emergency imaging. The configuration is realized. That is, the remaining amount RC detected by the power remaining amount detection unit 44 of the cassette 24 is notified to the imaging condition management unit 98 of the console 28 via the data transmission / reception control unit 84, the transceiver 48 and the transceiver 96, and the imaging condition The management unit 98 displays the remaining amount RC on the power remaining amount display unit 112. Here, the remaining power amount display unit 112 displays that the remaining amount RC is zero when the remaining amount RC of the power source 43 falls to the temporary empty value Ep.

  Further, the imaging condition management unit 98 instructs the data transmission / reception control unit 84 to prohibit the power supply from the power supply 43 to the radiation detector 40 when the remaining amount RC of the power supply 43 falls to the temporary empty value Ep. . Upon receiving this command, the data transmission / reception control unit 84 controls the power supply 43 to stop the power supply to the radiation detector 40.

  Further, on the console 28, an emergency shooting command Ce can be input from a keyboard (not shown), and when the emergency shooting command Ce is input by a photographer, the remaining amount is sent from the shooting condition management unit 98 to the data transmission / reception control unit 84. Even if RC is equal to or less than the temporary empty value Ep, the power supply 43 is instructed to supply power to the radiation detector 40. Upon receiving this command, the data transmission / reception control unit 84 controls the power supply 43 to restart the power supply to the radiation detector 40 and continues to supply the power until the remaining amount RC of the power supply 43 becomes zero.

  This eliminates the need to provide the power remaining amount display unit 108 and the emergency photographing button 110 in the cassette 24. In addition to the effects described in the third embodiment, the cassette 24 can be reduced in size and weight.

  As shown in FIG. 10, it is more preferable to configure a radiation detection cassette 500 (hereinafter referred to as “cassette 500”).

  That is, the guide line 504 serving as a reference for the imaging region and the imaging position is formed on the cassette 500 on the radiation irradiation surface side of the casing 502. By using this guide line 504 to position the subject (patient 14) with respect to the cassette 500 and setting the radiation X irradiation range, the radiographic image information can be recorded in an appropriate imaging region.

  A display unit 506 that displays various types of information related to the cassette 500 is disposed outside the imaging region of the cassette 500. In the display unit 506, the ID information of the patient 14 recorded in the cassette 500, the number of times the cassette 500 is used, the cumulative exposure dose, the state of charge (remaining capacity) of the power source 43 built in the cassette 500, radiation image information Imaging conditions, a positioning image of the patient 14 with respect to the cassette 500, and the like are displayed. In this case, for example, the engineer confirms the patient 14 according to the ID information displayed on the display unit 506, confirms in advance that the cassette 500 is in a usable state, and based on the displayed positioning image. A desired imaging region of the patient 14 can be positioned on the cassette 500, and optimal radiographic image information can be captured.

  Further, by forming the handle portion 508 in the cassette 500, it becomes easy to handle and carry the cassette 500.

  An AC adapter input terminal 510, a USB (Universal Serial Bus) terminal 512, and a card slot 516 for loading a memory card 514 are preferably provided on the side of the cassette 500.

  The input terminal 510 is connected to the AC adapter when the charging function of the power source 43 built in the cassette 500 is deteriorated or when sufficient time for charging the power source 43 cannot be secured. By supplying this, the cassette 500 can be immediately used.

  The USB terminal 512 or the card slot 516 can be used when the cassette 500 cannot transmit and receive information by wireless communication with an external device such as the console 28. That is, by connecting a cable to the USB terminal 512, information can be transmitted / received to / from an external device by wired communication. In addition, information can be transmitted and received by loading a memory card 514 into the card slot 516, recording necessary information on the memory card 514, and then removing the memory card 514 and loading it into an external device.

  As shown in FIG. 11, a cradle 518 for charging the built-in power supply 43 is preferably disposed in the examination room 12 or a necessary place in the hospital. In this case, the cradle 518 transmits and receives necessary information to and from external devices such as the RIS 29, the HIS 31, and the console 28 by using not only the charging of the power supply 43 but also the wireless communication function or the wired communication function of the cradle 518. You may do it. The information to be transmitted and received can include radiation image information recorded in the cassette 24 loaded in the cradle 518.

  In addition, a display unit 520 is provided in the cradle 518, and the display unit 520 displays necessary information including the charged state of the loaded cassette 24 and the radiation image information acquired from the cassette 24. May be.

  In addition, a plurality of cradle 518 is connected to the network, the charging state of the cassette 24 loaded in each cradle 518 is collected via the network, and the location of the cassette 24 in the usable charging state can be confirmed. You can also

10, 10A, 10B, 10C ... Radiation imaging system 14 ... Patient (subject)
24, 500 ... Radiation detection cassette 28 ... Console 40 ... Radiation detector (radiation conversion panel)
43 ... Power supply 44 ... Power supply remaining amount detection unit (remaining amount detection means)
48 ... transceiver (wireless communication means, wired communication means)
84: Data transmission / reception control unit (control means)
86 ... Volatile memory 88 ... Non-volatile memory 108, 112 ... Remaining power display unit (remaining amount display means)
Ep ... Temporary empty value RC ... Remaining power T1, T2, T3 ... Threshold X ... Radiation

Claims (10)

A radiation conversion panel that detects radiation transmitted through the subject and converts it into radiation image data;
Wireless communication means for wirelessly transmitting the radiation image data;
Control means for controlling the radiation conversion panel and the wireless communication means;
A power source for driving the radiation conversion panel and the wireless communication means;
A remaining amount detecting means for detecting the remaining amount of the power source;
With
The radiographic detection cassette according to claim 1, wherein when the remaining amount of the power source falls below a predetermined threshold, the control unit stops radio transmission of the radiographic image data and gives priority to radiographic image capturing. The radiation detection cassette according to claim 1,
The radiation detection cassette, wherein the predetermined threshold is variable. The radiation detection cassette according to claim 1 or 2,
The radiation detection cassette further includes a nonvolatile memory for recording the radiation image data,
The radiation detection cassette, wherein the control means records the radiation image data in the nonvolatile memory when the wireless transmission is stopped. In the radiation detection cassette according to any one of claims 1 to 3,
The radiation detection cassette further includes a volatile memory for temporarily recording the radiation image data,
The radiation detection cassette, wherein the control means temporarily records the radiation image data in the volatile memory before the wireless transmission. In the radiation detection cassette according to any one of claims 1 to 4,
The radiation detection cassette further includes wired communication means for wired transmission of the radiation image data,
The control means transmits the radiation image data to the outside via the wired communication means when the remaining amount of the power source is below the predetermined threshold and exceeds a second threshold lower than the predetermined threshold. Radiation detection cassette characterized by In the radiation detection cassette according to any one of claims 1 to 5,
The radiation detection cassette further includes a remaining amount display means for displaying the remaining amount of the power source,
The remaining amount display means displays the remaining amount of power on the remaining amount display means when the remaining amount of the power source drops to a temporary empty value indicating an amount capable of acquiring at least one radiation image data. Radiation detection cassette characterized by displaying zero. The radiation detection cassette according to claim 6,
The control means includes
When the remaining amount of the power source is reduced to the temporary empty value, the power supply from the power source to the radiation conversion panel is prohibited,
A radiation detection cassette, wherein when a power supply permission command is received from the outside, power supply from the power source to the radiation conversion panel is permitted. The radiation detection cassette according to any one of claims 1 to 5,
A console capable of wireless communication with the radiation detection cassette, and controlling the radiation detection cassette;
A radiographic imaging system comprising:
The radiation detection cassette notifies the console of the remaining amount of power detected by the remaining amount detecting means,
The console instructs the radiation detection cassette to stop wireless transmission of the radiation image data and give priority to radiographic imaging when the remaining amount of power is below the predetermined threshold,
The radiographic imaging system, wherein the control means of the radiation detection cassette stops radio transmission of the radiographic image data and gives priority to radiographic imaging in response to an instruction from the console. The radiographic imaging system according to claim 8, wherein
The console further includes a remaining amount display means for displaying the remaining amount of the power source,
The remaining amount display means displays the remaining amount of power on the remaining amount display means when the remaining amount of the power source drops to a temporary empty value indicating an amount capable of acquiring at least one radiation image data. A radiographic imaging system characterized by displaying that it is zero. The radiographic imaging system according to claim 9, wherein
The console transmits a power supply prohibition command for prohibiting power supply from the power supply to the radiation conversion panel to the control means when the remaining amount of the power supply falls to the temporary empty value, and the control means includes: Prohibiting power supply from the power source to the radiation conversion panel according to the power supply prohibition command,
When power supply from the power supply to the radiation conversion panel is commanded to the console from the outside, the console transmits a power supply command for requesting power supply from the power supply to the radiation conversion panel to the control means, The radiographic imaging system, wherein the control unit permits power supply from the power source to the radiation conversion panel in accordance with the power supply command.

Images