JP2010154897A - Radiation image photographing system and method of charging radiation detecting cassette - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To efficiently photograph radiation images by actively and preferentially charging a radiation detecting cassette to be used when order information requesting a plurality of times of photography of radiation image information on a subject is given. <P>SOLUTION: In the radiation image photographing system 10A, the charging quantity in a plurality of radiation detecting cassettes 24a-24c is controlled based on the order information requesting a plurality of times of photography of radiation image information on the subject, so that the total power supply capacity necessary for the photography of the radiation image information in the plurality of radiation detecting cassettes 24a-24c is secured. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a radiation detection cassette that detects radiation transmitted through a subject and converts it into radiation image information, a radiation image capturing system including a charging device that charges the radiation detection cassette, and a method of charging the radiation detection cassette. About.

  2. Description of the Related Art In the medical field, a radiation image capturing system is widely used that irradiates a subject with radiation and guides the radiation transmitted through the subject to a radiation conversion panel to capture radiation image information. As the radiation conversion panel, the radiation image information is obtained by storing radiation energy as the radiation image information on a conventional radiation film in which the radiation image information is exposed and recorded, and irradiating excitation light. A stimulable phosphor panel that can be extracted as stimulated emission light is known. These radiation conversion panels supply the radiation film on which the radiation image information is recorded to a developing device for development processing, or supply the storage phosphor panel to a reading device for reading processing. A visible image is obtained.

  Further, in an operating room or the like, it is necessary to be able to immediately read out and display radiation image information from a radiation conversion panel after imaging in order to perform a quick and accurate treatment on a 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.

  By the way, the radiation detection cassette provided with such a radiation conversion panel is configured to be electrically driven partially or entirely so that it can be used in connection with a console or the like. For this reason, when the radiation detection cassette does not reach the charge amount necessary for the radiographing when radiographic image information is captured for the subject, it is necessary to perform charging from the outside.

  Patent Document 1 proposes to perform non-contact charging from the charging device to the radiation detection cassette.

  Further, in Patent Document 2, a radiation conversion cassette that is most suitable for photographing predetermined radiographic image information is displayed on a display device among a plurality of radiation detection cassettes stored in a cassette storage box, and a doctor or a radiographer It has been proposed to take out one corresponding radiation conversion cassette from the cassette storage box based on the display content of the display device.

JP 2008-170315 A Japanese Patent Laid-Open No. 2002-248095

  However, the technique of Patent Document 1 simply performs non-contact charging from the charging device to the radiation detection cassette. On the other hand, the technique of Patent Document 2 detects a plurality of radiation detected in a cassette storage box. From the cassette, a doctor or a radiographer can select (take out) one radiation conversion cassette that is most suitable for capturing predetermined radiation image information. Therefore, in a radiographic imaging system having a plurality of radiation detection cassettes, when order information that requests imaging of radiographic information multiple times for a subject is given, the number of imaging times all the radiation detection cassettes indicate in the order information No measures have been proposed for measures to be taken when the amount of charge corresponding to has not been reached.

  The present invention has been made in view of the above-described problems, and actively and preferentially charges a radiation detection cassette to be used when order information for requesting imaging of radiographic image information for a subject is given. Thus, an object of the present invention is to provide a radiographic imaging system that can efficiently perform the imaging and a method for charging the radiation detection cassette.

  The present invention controls the amount of charge for a plurality of radiation detection cassettes based on order information that requires imaging of a plurality of radiographic image information for a subject, thereby providing a total amount necessary for the imaging in the plurality of radiation detection cassettes. It is characterized by securing power supply capacity.

  According to the present invention, it is necessary for the imaging in the plurality of radiation detection cassettes by controlling the charging amount for the plurality of radiation detection cassettes for the order information requesting the imaging of the radiographic image information for the subject multiple times. Secure the total power capacity.

  This makes it possible to actively and preferentially charge the radiation detection cassette desired to be used for the imaging when performing the imaging a plurality of times, and initially all the radiation detection cassettes are used for the imaging a plurality of times. Even if the necessary amount of charge has not been reached, it is possible to efficiently perform the photographing.

  A preferred embodiment of a radiographic imaging system according to the present invention will be described with reference to the drawings in connection with a method for charging a radiation detection cassette.

  First, a radiographic imaging system 10A according to the first embodiment will be described with reference to FIGS.

  FIG. 1 is an explanatory diagram of an operating room 12 in which a radiographic imaging system 10A is installed.

  An operating table (bed) 16 on which a patient (subject) 14 lies is disposed in the operating room 12, and an instrument table 20 on which various instruments used by the doctor 18 for surgery are placed is a side portion of the operating table 16. Placed in. In addition, around the operating table 16, various devices necessary for an operation, such as an anesthesia machine, an aspirator, an electrocardiograph, and a blood pressure monitor, are arranged.

  The radiographic imaging system 10A includes an imaging device 22 for irradiating a patient 14 with radiation X having a dose according to imaging conditions, and a radiation detector 40 for detecting the radiation X transmitted through the patient 14 (FIGS. 2 to 5). The radiation detection cassette 24 (24a to 24c) having a built-in reference), a display device 26 for displaying radiation image information based on the radiation X detected by the radiation detector 40, and the radiation detection cassette 24 loaded with the radiation. A cradle (charging device) 30 that can charge the detection cassette 24 and a console (control device) 28 that controls the imaging device 22, the radiation detection cassette 24, the display device 26, and the cradle 30 are provided.

  Note that signals are transmitted and received between the imaging device 22, the radiation detection cassette 24, the display device 26, the console 28, and the cradle 30 by wireless communication using UWB (Ultra Wide Band).

  The imaging device 22 is connected to the free arm 33 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 obstruct the operation by the doctor 18. 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.

  A plurality of loading sections 37 for loading the radiation detection cassette 24 are provided on the upper surface of the cradle 30 and a display section (for displaying information of the radiation detection cassette 24 loaded in the cradle 30 on the side surface ( (Cassette notification unit, information display unit) 35 is arranged.

  Note that FIG. 1 shows that among the three radiation detection cassettes 24 (24a to 24c) in the operating room 12, one charged radiation detection cassette 24a is used for photographing the radiation image information of the patient 14, and the rest The two radiation detection cassettes 24b and 24c are loaded in the two loading sections 37, respectively, and a state in which charging by the cradle 30 is possible is illustrated. The cradle 30 is a charging device for the radiation detection cassettes 24a to 24c, and also functions as a storage box for the radiation detection cassettes 24a to 24c.

  FIG. 2 is a perspective view of the radiation detection cassette 24.

  The radiation detection cassette 24 includes a casing (housing) 34 made of a material that transmits the radiation X. Inside the casing 34 are a grid 38 that removes 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 that detects the radiation X transmitted through the patient 14 ( Radiation conversion panel) 40 and lead plate 42 that absorbs backscattered rays of radiation X are arranged in this order. Note that the irradiation surface 36 of the casing 34 may be configured as a grid 38.

  The casing 34 includes information on the power supply unit 44, a cassette control unit 46 that drives and controls the radiation detector 40 with power supplied from the power supply unit 44, and information on the radiation X detected by the radiation detector 40. A transmitter / receiver (charge notification unit, charge amount transmission unit) 48 that transmits and receives signals to and from the console 28 is housed. 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.

  FIG. 3 is a plan view of the radiation detection cassette 24.

  On the irradiation surface 36 of the casing 34, information such as a charge amount of the power supply unit 44 as a battery of the radiation detection cassette 24 is provided on the power supply unit 44, cassette control unit 46, and transmitter / receiver 48 side as non-irradiated portions of the radiation X A display unit (charging notification unit, charge amount display unit) 49 for displaying is arranged.

  The power supply unit 44 (battery) can be a rechargeable secondary battery such as a lithium ion battery, or a storage element such as an electric double layer capacitor. The point is that the battery can be charged and can function properly as a power source of the radiation detection cassette 24.

  FIG. 4 is a circuit configuration block diagram of the radiation detector 40.

  The radiation detector 40 has a photoelectric conversion layer 51 made of a material such as amorphous selenium (a-Se) that senses the radiation X and generates charges on an array of thin film transistor (TFT) 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. 4, 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 radiation detection 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 information converted into a digital signal by the A / D converter 70 is supplied to the cassette control unit 46.

  Note that the TFT 52 functioning as a switching element may be realized in combination with another imaging element such as a CMOS (Complementary Metal-Oxide Semiconductor) image sensor. Furthermore, it can be replaced with a CCD (Charge-Coupled Device) image sensor that transfers charges while shifting them with a shift pulse corresponding to a gate signal referred to as a TFT.

  FIG. 5 is a partial configuration block diagram of a radiographic image capturing system 10 </ b> A including the imaging device 22, the radiation detection cassette 24, the display device 26, and the console 28. FIG. 6 is a configuration block diagram of the console 28 and the cradle 30.

  Since the configurations of the console 28 and the radiation detection cassettes 24 (24a to 24c) are illustrated in detail in FIG. 5, in FIG. 6, only the transceiver 96 for the console 28 includes only the radiation detection cassettes 24 (24a to 24c). Only the power supply unit 44 (44a to 44c), the display unit 49 (49a to 49c), and the power supply management unit 86 (86a to 86c) are illustrated.

  The console 28 is connected to a radiology information system (RIS) 29 for comprehensively managing radiographic image information and other information handled in the radiology department in the hospital, and the RIS 29 stores medical information in the hospital. A medical information system (HIS) 31 that is comprehensively managed is connected.

  The imaging apparatus 22 includes an imaging switch 72, a radiation source 74, a transceiver 76, and a radiation source control unit 78.

  The transceiver 76 receives imaging conditions and the like from the console 28 by wireless communication, and transmits an imaging completion signal and the like by wireless communication to the console 28.

  The radiation source control unit 78 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. The radiation source 74 outputs the radiation X based on the control from the radiation source control unit 78.

  The cassette control unit 46 of the radiation detection cassette 24 includes an address signal generation unit 80, an image memory 82, a cassette ID memory 84, and a power management unit 86.

  The address signal generator 80 supplies an address signal to the address decoder 60 of the line scan driver 58 and the address decoder 68 of the multiplexer 66 that constitute the radiation detector 40. The image memory 82 stores the radiation image information detected by the radiation detector 40. The cassette ID memory 84 stores cassette ID information for specifying the radiation detection cassette 24.

  The power management unit 86 detects the charge amount of the power supply unit 44, displays the detected charge amount on the display unit 49 (notifies the outside), and outputs it to the transceiver 48. Further, the power management unit 86 determines that the charge amount of the power supply unit 44 is a predetermined charge amount (a charge amount necessary for one shooting or a predetermined number of times) based on ordering information (order information) from the console 28. If the charging amount of the power supply unit 44 has not reached the predetermined charging amount, charging by the cradle 30 is necessary. Is displayed on the display unit 49, and the information is output to the transceiver 48. Further, the power management unit 86 detects the stop of charging from the cradle 30 to the power supply unit 44 and the charge amount of the power supply unit 44 when the charge is stopped, and the charge amount of the power supply unit 44 reaches the predetermined charge amount. When it is determined that charging has been completed, information indicating that charging by the cradle 30 has been completed is displayed on the display unit 49 and output to the transceiver 48.

  The transceiver 48 receives a transmission request signal and ordering information from the console 28 by radio communication, while the console ID information stored in the cassette ID memory 84 and the radiation image information stored in the image memory 82 are received from the console 28. Various information (information related to the charge amount of the power supply unit 44) from the power management unit 86 is transmitted by wireless communication.

  In addition, the information regarding the charge amount of the power supply unit 44 (44a to 44c) transmitted from the transceiver 48 (48a to 48c) of the radiation detection cassette 24 (24a to 24c) to the transceiver 96 of the console 28 is a power source. In addition to the amount of charge of the unit 44, information indicating that charging by the cradle 30 is necessary, and information indicating that charging has been completed, the cassette ID information for specifying the radiation detection cassette 24 including the power source unit 44 is also included. included.

  The console 28 includes a transceiver 96, an imaging condition management unit 98, an image processing unit 100, an image memory 101, a patient information management unit 102, a cassette information management unit 104, and a power supply information management unit 105.

  The transmitter / receiver 96 transmits / receives necessary information including radiographic image information to / from the imaging device 22, the radiation detection cassette 24, the display device 26, and the cradle 30 by wireless communication. The shooting condition management unit 98 manages shooting conditions necessary for shooting by the shooting device 22. The image processing unit 100 performs image processing on the radiation image information transmitted from the radiation detection cassette 24. An image memory 101 stores the radiation image information subjected to the image processing. The patient information management unit 102 manages patient information of the patient 14 to be imaged. The cassette information management unit 104 manages the cassette ID information transmitted from the radiation detection cassette 24. The power supply information management unit 105 manages information related to the number of times radiographic image information is captured for the patient 14 and the amount of charge of the power supply unit 44 included in the ordering information.

  The console 28 may be installed outside the operating room 12 as long as it can transmit and receive signals to and from the imaging device 22, the radiation detection cassette 24, the display device 26, and the cradle 30 by wireless communication. .

  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. The conditions such as the photographing method and the number of photographing can be listed. 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 cradle 30 includes a transceiver (cassette notification unit, information transmission unit) 120, a control unit (charge control unit) 122, a charge processing unit 124, a power supply 126, a changeover switch 128, and a display unit (cassette notification unit, information display unit) 35. Is provided.

  The transceiver 120 receives ordering information from the transceiver 96 of the console 28 by wireless communication, and transmits information related to the charge amount of each power supply unit 44a to 44c from the control unit 122 to the transceiver 96 by wireless communication.

  The control unit 122 controls the charge processing unit 124 and the changeover switch 128, and the power supply unit 44 (44a to 44c) of the radiation detection cassette 24 (24a to 24c) loaded in the loading unit 37 (see FIG. 1) of the cradle 30. ). The changeover switch 128 switches the connection between the input port 128d and the output ports 128a to 128c based on the control from the control unit 122. Based on the control from the control unit 122, the charging processing unit 124 supplies DC power supplied from a power source 126 connected to an external power source (not shown) to any of the power source units 44 a to 44 c via the changeover switch 128. The power supply unit is charged by supplying the power supply unit (power supply unit 44a in FIG. 6). In addition, the charge processing unit 124 detects the charge amount of the power supply unit connected via the changeover switch 128, and outputs the detected charge amount to the control unit 122.

  As described above, since the radiation detection cassettes 24a to 24c, the console 28, and the cradle 30 can be wirelessly communicated, the transceiver 96 of the console 28 can charge the power supply units 44a to 44c from the power management units 86a to 86c. When information on the quantity is received, the information is output to the power supply information management unit 105 and transferred to the transceiver 120 of the cradle 30.

  Therefore, the control unit 122 compares the amount of charge detected by the charge processing unit 124 with the information on the amount of charge of the power supply units 44a to 44c transferred from the console 28, and the cassette in the information whose charge amount substantially matches. ID information and the charge amount detected by the charge processing unit 124 are associated with each other, and the associated cassette ID information and the charge amount are associated with the charge amount of the power supply unit that is currently being charged by the charge processing unit 124. To the display unit 35 and the transceiver 120. That is, the control unit 122 performs a process of associating the radiation detection cassette currently being charged in the cradle 30 (the cassette ID information thereof) with the current charge amount of the radiation detection cassette. The display unit 35 displays the associated information (notifies outside), and the transceiver 120 transmits the information to the console 28.

  By the way, when the ordering information for requesting the patient 14 to capture radiographic image information a plurality of times is transmitted (given) from the transceiver 96 of the console 28 to the transceiver 120 via wireless communication, the control unit First, the control unit 122 controls the charge processing unit 124 and the changeover switch 128 to determine whether or not the charge amount of each of the power supply units 44a to 44c has reached the charge amount necessary for multiple times of photographing.

  In this case, it is controlled that the charge amount of each of the power supply units 44a to 44c has not reached the charge amount necessary for the plurality of times of photographing or the charge amount necessary for one photographing. When the unit 122 determines that the cradle 30 is active and prioritized only in the radiation detection cassette that is desired to be used for imaging in order to avoid delays in imaging radiographic image information due to insufficient charging of the radiation detection cassettes 24a to 24c. Charge the battery. That is, the cradle 30 weights the charging process for the power supply units 44a to 44c based on the ordering information, and performs the following charging process for the weighted power supply units 44a to 44c.

  Specifically, in FIG. 6, the control unit 122 of the cradle 30 first controls the changeover switch 128 so as to connect the input port 128d and the output port 128a based on the ordering information, and one radiation detection cassette. The charging processing unit 124 is controlled so that the power supply unit 44a of 24a is charged up to at least one charge amount for photographing. That is, the cradle 30 charges the single radiation detection cassette 24a up to a charge amount necessary for at least one imaging regardless of the remaining capacity of the single radiation detection cassette 24a.

  When the charge amount of the power supply unit 44a reaches the charge amount for the one shooting while the power supply unit 44a is being charged, the control unit 122 establishes the connection between the input port 128d and the output port 128a and the output of the input port 128d. The selector switch 128 is controlled so as to switch to the connection with the port 128b or the connection between the input port 128d and the output port 128c, and the power supply unit 44b of the other radiation detection cassette 24b or the power supply unit of the other radiation detection cassette 24c. The charging processing unit 124 is controlled so as to charge up to the charging amount corresponding to the remaining number of times of shooting for 44c.

  In this case, the control unit 122 outputs to the display unit 35 and the transceiver 120 information indicating that the amount of charge of the power supply unit 44a has been charged to the amount of charge necessary for one shooting. Further, during one imaging using the charged radiation detection cassette 24a, the cradle 30 is charged up to the amount of charge necessary for imaging for the remaining number of times for the power supply unit 44b or the power supply unit 44c.

  When the console 28 receives information on the charge amount of the power supply unit 44 from the power management unit 86 and / or the control unit 122, the console 28 registers the information in the power supply information management unit 105 and also displays the information from the transceiver 96. 26 transfers the information.

  The display device 26 includes a receiver 90 that receives radiation image information from the console 28, a display control unit 92 that performs display control of the received radiation image information, and a display that displays the radiation image information processed by the display control unit 92. Part 94. Further, when the display device 26 receives information related to the charge amount of the power supply unit 44 from the console 28, the display device 26 displays the information on the display unit 94.

  The radiographic imaging system 10A according to the first embodiment is basically configured as described above. Next, the operation (a method of charging the radiation detection cassette) will be described.

  Here, as described above, the ordering information is information requesting the patient 14 to capture radiographic image information a plurality of times, and the amount of charge of each of the power supply units 44a to 44c is necessary for one imaging. A case where the two radiation detection cassettes 24a and 24b are charged when the charge amount has not been reached will be described.

  The radiographic image capturing system 10A is installed in the operating room 12, and is used, for example, when radiographic image information needs to be captured during surgery 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. If the imaging region, the imaging method, and the number of imaging (number of imaging) are determined in advance, these imaging conditions are registered in advance in the imaging condition management unit 98 and the power supply information management unit 105. In addition, all the radiation detection cassettes 24a to 24c are loaded into the loading unit 37 of the cradle 30 so that they can be charged. In the state where the above preparatory work (setting of ordering information) is completed, the operation on the patient 14 is performed.

  When the ordering information is set, the console 28 transmits the set ordering information to the control unit 122 of the cradle 30 via the transceivers 96 and 120, and each radiation detection cassette via the transceivers 96 and 48. The data is transmitted to the power management units 86a to 86c of 24a to 24c (see FIGS. 5 and 6).

  The power management units 86a to 86c detect the charge amounts of the power supply units 44a to 44c based on the received ordering information, and the detected charge amount has not reached the charge amount necessary for one shooting. It is determined that the radiation detection cassettes 24a to 24c are not in a state that can be used for photographing at present. Then, the power management units 86a to 86c output information (charge amount, cassette ID information, etc.) indicating that charging is necessary to the display unit 49 and the transceiver 48, respectively. Each display unit 49 displays the information, respectively, while each transceiver 48 transmits the information to the transceiver 96, respectively. The console 28 registers each piece of information received by the transceiver 96 in the power supply information management unit 105 and also transfers it to the cradle 30.

  Based on the received ordering information, the control unit 122 of the cradle 30 first controls the changeover switch 128 so as to sequentially switch the connection between the input port 128d and the output ports 128a to 128c, and when the connection is switched. The charge processing unit 124 is controlled so as to detect the charge amount of the power supply units 44a to 44c. Thereby, the charging processing unit 124 detects the charging amount of each of the power supply units 44 a to 44 c and outputs each detected charging amount to the control unit 122.

  The control unit 122 determines whether or not the charge amount of each of the power supply units 44a to 44c has reached a charge amount necessary for a plurality of times of photographing in the ordering information, and each detected charge amount is photographed for one time. Therefore, it is determined that all the radiation detection cassettes 24a to 24c loaded in the loading sections 37 are not in a state that can be used for imaging at present. Then, the control unit 122 compares the detected charge amounts of the power supply units 44a to 44c with the information from the power management units 86a to 86c received from the console 28, and cassette ID information in the information with the same charge amount. And the detected charge amounts of the power supply units 44 a to 44 c are associated with each other, and the associated information is output to the display unit 35 and also transmitted to the console 28 via the transceivers 120 and 96.

  The display unit 35 displays the associated information. The console 28 registers the information received by the transmitter / receiver 96 in the power supply information management unit 105 and transfers the information from the transmitter / receiver 96 to the receiver 90 of the display device 26. The display device 26 causes the display unit 94 to display the transferred information.

  As a result, the doctor 18 or the radiologist visually recognizes the display contents of the display units 35, 49a to 49c, 94, so that all the radiation detection cassettes 24a to 24c loaded in the cradle 30 are insufficiently charged. It can be understood that it is not possible.

  Next, the control unit 122 controls the changeover switch 128 so as to connect the input port 128d and the output port 128a based on the ordering information and the charge amounts of the power supply units 44a to 44c that have already been detected. Regardless of the remaining capacity of one radiation detection cassette 24a, the charge processing unit 124 is controlled so that the power supply unit 44a of the one radiation detection cassette 24a is charged to a charge amount necessary for at least one imaging.

  Thereby, the charging processing unit 124 supplies the DC power from the power source 126 to the power source unit 44a via the input port 128d and the output port 128a, while the charge amount of the power source unit 44a being charged is supplied to the control unit 122. Output.

  On the other hand, the power management unit 86a also detects the charge amount of the power supply unit 44a, and outputs information indicating the detected charge amount to the display unit 49a and the transceiver 48. The display unit 49a displays the information, and the transceiver 48 transmits the information to the transceiver 96. The console 28 registers the information received by the transceiver 96 in the power supply information management unit 105 and transfers the information to the control unit 122 via the transceivers 96 and 120.

  The control unit 122 compares the charge amount of the power supply unit 44a detected by the charge processing unit 124 with the information transferred from the control unit 122, and when the charge amounts match, the cassette ID information in the information The detected charge amount of the power supply unit 44a is associated, and the associated information (cassette ID information, the detected charge amount) is output to the display unit 35 and the transceiver 120. The display unit 35 displays the information, while the transceiver 120 transmits the information to the transceiver 96 via wireless communication. The console 28 registers the information received by the transceiver 96 in the power supply information management unit 105 and transfers the information to the receiver 90 of the display device 26. The display device 26 causes the display unit 94 to display the transferred information.

  Thereby, the doctor 18 or the radiographer can recognize that the radiation detection cassette 24a loaded in the cradle 30 is being charged by visually recognizing the display contents of the display units 35, 49a, and 94.

  Next, when the charge amount of the power supply unit 44a reaches the charge amount necessary for one shooting, the control unit 122 connects the input port 128d and the output port 128a, and connects the input port 128d and the output port 128b. And the charge processing unit 124 is controlled so that the power supply unit 44b of the other radiation detection cassette 24b is charged up to the charge amount necessary for imaging for the remaining number of times. To do.

  On the other hand, the power management unit 86a detects the stop of charging from the cradle 30 to the power supply unit 44a and the charge amount of the power supply unit 44a when the charge is stopped, and the charge amount reaches the charge amount necessary for one shooting. If it is determined that the charging amount of the power supply unit 44a includes the cassette ID information, the information indicating that the charging amount required for one shooting has been reached is output to the display unit 49a and the transceiver 48. As a result, the display unit 49 a displays the information, and the transceiver 48 transmits the information to the transceiver 96. The console 28 registers the information received by the transceiver 96 in the power supply information management unit 105 and transfers the information to the control unit 122 via the transceivers 96 and 120.

  The control unit 122 is based on the cassette ID information of the radiation detection cassette 24a in the information received from the console 28 and the charge amount of the power supply unit 44a detected by the charge processing unit 124 (charge amount necessary for one imaging). Then, the information indicating that the power supply unit 44a is charged is associated, and the associated information is output to the display unit 35 and the transceiver 120. Thereby, the display unit 35 displays the information, while the transmitter / receiver 120 transmits the information to the transmitter / receiver 96. The console 28 registers the information received by the transceiver 96 in the power supply information management unit 105 and transfers the information to the receiver 90 of the display device 26. The display device 26 causes the display unit 94 to display the transferred information.

  Thereby, the doctor 18 or the radiographer grasps that the radiation detection cassette 24a has been charged to the charge amount necessary for one imaging by visually recognizing the display contents of the display units 35, 49a, and 94. Can do.

  When one radiographic image information is taken during the operation, the doctor 18 or a radiographer in charge pulls out the charged radiation detection cassette 24a from the cradle 30 and sets the predetermined distance between the patient 14 and the operating table 16. The radiation detection cassette 24a is installed at the position with the irradiation surface 36 facing the imaging device 22 (see FIG. 1).

  Next, after appropriately moving the imaging device 22 to a position facing the radiation detection cassette 24a, the imaging switch 72 is operated to perform imaging.

  In this case, when the doctor 18 or the radiographer operates the imaging switch 72, the radiation source controller 78 of the imaging apparatus 22 requests the console 28 to transmit imaging conditions via the transceivers 76 and 96.

  The console 28 receives the request, and then transmits the imaging conditions related to the imaging region of the patient 14 registered in the imaging condition management unit 98 to the imaging apparatus 22 via the transceivers 96 and 76. When receiving the imaging conditions, the radiation source control unit 78 controls the radiation source 74 in accordance with the imaging conditions and irradiates the patient 14 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 radiation detection cassette 24 (24 a), and the photoelectric conversion layer of each pixel 50 constituting the radiation detector 40. It is converted into an electric signal by 51 and held as a charge in the storage capacitor 53 (see FIG. 4). Next, the charge information, which is the radiographic image information 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 information, which is charge information held in the storage capacitor 53 of each pixel 50, is sequentially read out via the signal line 56.

  The radiation image information read from the storage capacitor 53 of each pixel 50 connected to the selected gate line 54 of the radiation detector 40 is amplified by each amplifier 62 and then sampled by each sample and hold circuit 64. The signal is supplied to the A / D converter 70 via the multiplexer 66 and converted into a digital signal. The radiographic image information converted into the digital signal is temporarily stored in the image memory 82 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 information, which is charge information, is read through the signal line 56 and stored in the image memory 82 of the cassette control unit 46 through the multiplexer 66 and the A / D converter 70.

  The radiation image information stored in the image memory 82 is transmitted to the console 28 by wireless communication via the transceiver 48.

  The radiographic image information transmitted to the console 28 is received by the transmitter / receiver 96, subjected to predetermined image processing in the image processing unit 100, and then associated with the patient information of the patient 14 registered in the patient information management unit 102. Stored in the image memory 101.

  The radiographic image information subjected to the image processing is transmitted from the transceiver 96 to the display device 26. The display device 26 that has received the radiation image information by the receiver 90 controls the display unit 94 by the display control unit 92 to display the radiation image information. The doctor 18 performs the operation while confirming the radiation image information displayed on the display unit 94.

  The above is the operation of the radiographic image capturing system 10 </ b> A in one capturing.

  When the amount of charge of the power supply unit 44b reaches the amount of charge necessary for the remaining number of times during the shooting for one time, the control unit 122 connects the input port 128d and the output port 128b to the input port. The changeover switch 128 is controlled so as to switch to the connection between the 128d and the output port 128c, and the charging processing unit 124 is controlled so as to charge the power supply unit 44c of the other radiation detection cassette 24c.

  On the other hand, the power management unit 86b detects the stop of the charging from the cradle 30 to the power supply unit 44b and the charge amount of the power supply unit 44b when the charge is stopped, and the charge amount is a charge amount necessary for photographing for the remaining number of times. If it is determined that the charging amount of the power supply unit 44b includes the cassette ID information, the display unit 49b and the transmitter / receiver 48 indicate information indicating that the charging amount necessary for photographing for the remaining number of times has been reached. Output. Thereby, the display unit 49b displays the information, and the transceiver 48 transmits the information to the transceiver 96. The console 28 registers the information received by the transceiver 96 in the power supply information management unit 105 and transfers the information to the control unit 122 via the transceivers 96 and 120.

  The control unit 122 includes the cassette ID information of the radiation detection cassette 24b in the information received from the console 28, and the charge amount of the power supply unit 44b detected by the charge processing unit 124 (the charge amount necessary for imaging for the remaining number of times). Is associated with information indicating that the power supply unit 44b is charged, and the associated information is output to the display unit 35 and the transceiver 120. Thereby, the display unit 35 displays the information, while the transmitter / receiver 120 transmits the information to the transmitter / receiver 96. The console 28 registers the information received by the transceiver 96 in the power supply information management unit 105 and transfers the information to the receiver 90 of the display device 26. The display device 26 causes the display unit 94 to display the transferred information.

  Thereby, the doctor 18 or the radiographer grasps that the radiation detection cassette 24b has been charged to the charge amount necessary for the remaining number of times by visually recognizing the display contents of the display units 35, 49b, and 94. can do.

  Therefore, the doctor 18 or a radiographer reloads the charged radiation detection cassette 24b from the cradle 30 and reloads the radiation detection cassette 24a used for the one shot after the completion of one shot. The remaining number of times can be taken.

  As described above, according to the radiographic image capturing system 10A according to the first embodiment, the cradle 30 captures the radiographing information indicated in the ordering information with respect to the ordering information for requesting the radiography of the patient 14 a plurality of times. One radiation detection cassette 24a is selected from all the radiation detection cassettes 24a to 24c that have not reached the charge amount corresponding to the number of times and the charge amount is insufficient, and the selected radiation detection cassette 24a is selected. Thus, charging is performed until the amount of charge necessary for at least one shooting is reached. That is, the cradle 30 charges the single radiation detection cassette 24a up to a charge amount necessary for at least one imaging regardless of the remaining capacity of the single radiation detection cassette 24a.

  Next, during one imaging using the radiation detection cassette 24a after charging, the cradle 30 selects another radiation detection cassette 24b, and at least the remaining number of times for the selected other radiation detection cassette 24b. Charge until you reach the amount of charge required to shoot minutes.

  Thereby, when imaging is performed a plurality of times, the radiation detection cassettes 24a and 24b that are desired to be used for the imaging can be positively and preferentially charged. Therefore, initially, all the radiation detection cassettes 24a to 24c are provided in a plurality. Even if the amount of charge necessary for one shooting is not reached, the shooting can be performed efficiently.

  In the cradle 30, the control unit 122 controls the display unit 35, the transceiver 120, and the charging processing unit 124 based on the ordering information, so that the charging processing unit 124 can charge the single radiation detection cassette 24a, and The other radiation detection cassettes 24 b and 24 c are charged, and the display unit 35 displays information on the radiation detection cassette currently being charged, while the transceiver 120 transmits the information to the console 28. The console 28 transfers the received information to the display device 26, and the display device 26 displays the transferred information. Thereby, the doctor 18 or the radiologist can easily grasp the radiation detection cassette currently charged by the cradle 30 by visually recognizing the display contents of the display unit 35 and the display device 26.

  Further, when the charging processing unit 124 completes charging for one radiation detection cassette 24a or charging for the other radiation detection cassettes 24b and 24c, the control unit 122 displays information on the radiation detection cassette that has been charged. The data is output to the display unit 35 and the transceiver 120. Thereby, the display unit 35 displays the information of the radiation detection cassette after the completion of charging, while the transceiver 120 transmits the information to the console 28. The console 28 transfers the received information to the display device 26, and the display device 26 displays the transferred information. Thereby, the doctor 18 or the radiographer can easily grasp the charged radiation detection cassette by visually recognizing the display contents of the display unit 35 and the display device 26.

  Further, the control unit 122 controls the changeover switch 128 so as to connect one radiation detection cassette 24 a and the charging processing unit 124 based on the ordering information, and the radiation from the charging processing unit 124 via the changeover switch 128. By controlling the charging processing unit 124 so as to charge the detection cassette 24a, the one radiation detection cassette 24a is selected. On the other hand, when charging of the one radiation detection cassette 24a is completed, another radiation detection is performed. The charge processing unit controls the changeover switch 128 to connect the cassettes 24b, 24c and the charge processing unit 124, and charges the other radiation detection cassettes 24b, 24c from the charge processing unit 124 via the changeover switch 128. By controlling 124, the other radiation detection cassettes 24b, 24c To choose. Thereby, it is possible to reliably and efficiently charge one radiation detection cassette 24a and the other radiation detection cassettes 24b and 24c.

  On the other hand, in each radiation detection cassette 24 (24a to 24c), the power management unit 86 (86a to 86c) detects the charge amount of the power supply unit 44 (44a to 44c), and includes the detected charge amount and cassette ID information. Then, information regarding the charge amount of the power supply unit 44 is output to the display unit 49 (49a to 49c) and the transceiver 48. The display unit 49 displays the information, and the transceiver 48 transmits the information to the transceiver 96 of the console 28.

  As a result, the console 28 registers the information received by the transceiver 96 in the power supply information management unit 105 and transmits the information to the control unit 122 via the transceivers 96 and 120. The cassette ID information in the information can be associated with information such as the charge amount detected by the charge processing unit 124. Further, the associated information is displayed on the display unit 35, and further transferred from the cradle 30 to the display device 26 via the console 28 and displayed on the display unit 94 of the display device 26, whereby the doctor 18 or the radiologist. Can visually recognize the display contents of the respective display units 35, 49, and 94, and can reliably grasp the information regarding the charge amount of the power supply unit 44.

  Further, the power management unit 86 detects the stop of charging from the cradle 30 to the power supply unit 44 and the charge amount of the power supply unit 44 when the charge is stopped, and the charge amount is a predetermined number of times of photographing (one photographing, or When it is determined that the required amount of charge has been reached (remaining number of times of photographing), information indicating that the required amount of charge has been reached for the predetermined number of times of photographing (information indicating that charging has been completed) is displayed. 49 and the transceiver 48. The display unit 49 displays the information, and the transceiver 48 transmits the information to the transceiver 96.

  Accordingly, the console 28 registers the information received by the transceiver 96 in the power supply information management unit 105 and transfers the information to the control unit 122 via the transceivers 96 and 120. Therefore, the control unit 122 receives the received information The cassette ID information in the information can be associated with the information indicating that the charging is completed. Further, the associated information is displayed on the display unit 35, and further transferred from the cradle 30 to the display device 26 via the console 28 and displayed on the display unit 94 of the display device 26, whereby the doctor 18 or the radiologist. Can easily recognize that the radiation detection cassette 24 has been charged by visually recognizing the display contents of the display units 35, 49, and 94.

  As described above, the display unit 49 of the radiation detection cassette 24 displays various types of information related to the charge amount of the power supply unit 44, and the transmitter / receiver 48 transmits the various types of information to the console 28, thereby obtaining the following effects. That is, even when the cradle 30 is appropriately performing the charging process based on the ordering information, wireless communication cannot be performed between the cradle 30 and the console 28, and display by the display unit 35 is not possible. Instead of the cradle 30, the radiation detection cassette 24 detects the charge amount of the power supply unit 44, the display unit 49 displays various information such as the charge amount, and the transceiver 48 transmits the various information to the console 28. By doing so, the console 28 can reliably receive the various types of information. Further, since the console 28 transfers the various information to the display device 26 and the display device 26 displays the various information, the doctor or the radiologist can display the display device 26 or the display unit 49 based on the display contents. The various types of information can be reliably grasped.

  The cassette control unit 46 and the transmitter / receiver 48 including the radiation detector 40, the power supply unit 44, and the power supply management unit 86 are accommodated in a casing 34 made of a material that transmits the radiation X, and the display unit 49 is connected to the casing 34. The irradiation surface 36 is disposed at a non-irradiated portion of the radiation X. Therefore, the display unit 49 can display information such as the amount of charge of the power supply unit 44 without preventing the radiation detector 40 from being irradiated with the radiation X (imaging radiographic image information).

  Further, signals are transmitted and received among the imaging device 22, the radiation detection cassette 24, the display device 26, the console 28, and the cradle 30 by UWB wireless communication. That is, the cables for transmitting and receiving the signals are not connected between the imaging device 22, the radiation detection cassette 24, the display device 26, and the console 28. For example, these cables are arranged on the floor surface of the operating room 12. Therefore, there is no possibility that the work of the doctor 18 or the like will be hindered. Therefore, the doctor 18 can perform his / her work efficiently. In addition, by using UWB as the wireless communication, it is possible to reduce power consumption, improve fading resistance, and improve high-speed communication compared to conventional wireless communication.

  The radiographic imaging system 10A according to the first embodiment is not limited to the above-described embodiment, and can be changed to the following configuration.

  The cradle 30 may control the amount of charge for each of the radiation detection cassettes 24a to 24c based on the ordering information so that the plurality of radiation detection cassettes 24a to 24c have a total power supply capacity necessary for imaging.

  In this case, the cradle 30 selects one radiation detection cassette 24a having the maximum charge amount from among the plurality of radiation detection cassettes 24a to 24c that match the ordering information. For the radiation detection cassette 24a, it is detected how many times of imaging based on the ordering information the charging amount necessary for imaging is provided.

  Specifically, when the cradle 30 detects that the charge amount of one selected radiation detection cassette 24a is less than one imaging, it is necessary for at least one imaging with respect to the radiation detection cassette 24a. The remaining radiation detection conforming to the ordering information is performed during the one-time imaging using the one radiation detection cassette 24a after the completion of charging for the one radiation detection cassette 24a. The other radiation detection cassette with the next largest charge amount is selected from the cassettes 24b and 24c, and the charge amount necessary for imaging at least for the remaining number of times is reached with respect to the selected other radiation detection cassette. Charge the battery.

  At that time, the cradle 30 is further charged when the other radiation detection cassette is used for imaging while the other radiation detection cassette having the next highest charge amount is being charged, even though the charging is not completed. Next to the other radiation detection cassettes, the remaining radiation detection cassettes including the one radiation detection cassette 24a that conforms to the ordering information so as to reach the charge amount necessary for at least the remaining number of times of imaging. It is desirable to select a radiation detection cassette with the largest amount of charge and charge the radiation detection cassette with the next highest charge amount.

  Even if it changes to such a structure, it is possible to acquire the effect mentioned above.

  In the radiographic imaging system 10A according to the first embodiment, as an example, the case where a plurality of radiation detection cassettes 24a to 24c are loaded and charged in one cradle 30 is described, but the present invention is not limited thereto. Instead, for example, as shown in FIG. 7, signals can be transmitted and received by wireless communication between the consoles 28 and a plurality of cradles 30 a to 30 c each having display units 35 a to 35 c, and each cradle 30 a The radiation detection cassettes 24a to 24c may be loaded in the ˜30c so as to be chargeable.

  In this case, the changeover switch 128 (see FIG. 6) does not exist in each cradle 30a-30c, and the charging processing unit 124 of each cradle 30a-30c is directly connected to the power supply unit 44a-44c. Therefore, the charging processing unit 124 of one cradle 30a among the cradles 30a to 30c charges one radiation detection cassette 24a loaded in the one cradle 30a based on the ordering information, and one cradle 30a. When the charging of one radiation detection cassette 24a is completed, the control unit 122 notifies the console 28 of the completion of the charging, and the control units 122 of the other cradles 30b and 30c transfer from the ordering information and the console 28. Based on the notification of the completion of charging, the charging processing unit 124 of the other cradle 30b, 30c is controlled to charge the other radiation detection cassette 24b, 24c loaded in the other cradle 30b, 30c. .

  Accordingly, in each cradle 30a to 30c, only one radiation detection cassette 24a to 24c is loaded and charging processing is performed. However, by adjusting the cradle to be selected on the console 28 side, each effect described above can be easily performed. Is obtained.

  Further, in the above description, one radiation detection cassette is charged to a charge amount necessary for at least one imaging, and then the other radiation detection cassette is charged for at least the remaining number of imaging. The amount of charge for one radiation detection cassette and the amount of charge for other radiation detection cassettes are set as appropriate so long as the number of times indicated in the ordering information can be reliably photographed. Also good.

  In the radiographic imaging system 10A according to the first embodiment, radiographic image information is captured due to the operation of the imaging switch 72 of the doctor 18 or the radiographer. The radiographic image information may be captured due to the operation.

  In addition, when the radiation detection cassette 24 is used in the operating room 12 or the like, there is a possibility that blood or other germs may adhere. Therefore, the radiation detection cassette 24 has a waterproof and airtight structure and is sterilized and washed as necessary, so that one radiation detection cassette 24 can be used repeatedly.

  Further, the radiation detection cassette 24 is not limited to the case where it is used in the operating room 12, and can be applied to, for example, a medical examination or a round in a hospital.

  Furthermore, the above-described charging method may be used for the wireless communication between the radiation detection cassette 24 and the external device as an optical wireless communication using infrared rays or a wired communication using a cable instead of a communication using a normal radio wave. Of course, it is possible to easily obtain the effect.

  Further, it is more preferable to configure the radiation detection cassette 24 as shown in FIG.

  That is, the radiation detection cassette 24 is provided with a guide line 140 serving as a reference for an imaging region and an imaging position on the irradiation surface 36 side of the casing 34. Using this guide line 140, the patient 14 is positioned with respect to the radiation detection cassette 24, and the radiation image information can be recorded in an appropriate imaging region by setting the radiation X irradiation range.

  In addition to the amount of charge of the power supply unit 44 described above, the display unit 49 includes the ID information of the patient 14 recorded in the radiation detection cassette 24, the number of times the radiation detection cassette 24 is used, the cumulative exposure dose, and radiation image information. Imaging conditions, a positioning image of the patient 14 with respect to the radiation detection cassette 24, and the like are displayed. In this case, for example, the radiologist confirms the patient 14 according to the ID information displayed on the display unit 49, confirms in advance that the radiation detection cassette 24 is in a usable state, and displays the displayed positioning image. Based on the above, it is possible to position the desired imaging region of the patient 14 in the radiation detection cassette 24 and to perform imaging of optimal radiation image information.

  Further, by forming the handle 142 in the radiation detection cassette 24, the radiation detection cassette 24 can be easily handled and carried.

  Furthermore, it is preferable to arrange a USB (Universal Serial Bus) terminal 146 and a card slot 149 for loading a memory card 148 on the side of the radiation detection cassette 24.

  The USB terminal 146 or the card slot 149 can be used when the radiation detection cassette 24 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 146, 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 148 into the card slot 149, recording necessary information on the memory card 148, and then removing the memory card 148 and loading it into an external device.

  Further, the cradle 30 is not limited to the operating room 12 and may be disposed at a necessary location in the hospital. In this case, the cradle 30 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 unit 44 but also the wireless communication function of the cradle 30. Also good. The information to be transmitted and received can include radiation image information recorded in the radiation detection cassette 24 loaded in the cradle 30.

  In addition, the display unit 35 of the cradle 30 may display not only the charged amount of the loaded radiation detection cassette 24 but also necessary information including radiation image information acquired from the radiation detection cassette 24.

  Further, the plurality of cradles 30 and 30a to 30c are connected to the network, and the charge amount of the radiation detection cassette 24 loaded in each cradle 30 and 30a to 30c is collected via the network, and is in a usable charge amount. It can also be configured so that the location of the radiation detection cassette 24 can be confirmed.

  Furthermore, in the radiographic imaging system 10 </ b> A according to the first embodiment, for example, the radiation detector 40 housed in the radiation detection cassette 24 directly converts the dose of incident radiation X into an electrical signal by the photoelectric conversion layer 51. Although it is a direct conversion type radiation detector, instead of this, incident radiation X is once converted into visible light by a scintillator, and then this visible light is converted into a solid detection element such as amorphous silicon (a-Si). You may use the radiation detector of the indirect conversion system comprised so that it might convert into an electric signal (refer patent 3494683).

  Further, radiation image information can be acquired by using a light readout type radiation detector. In this optical readout type radiation detector, when radiation is incident on the solid detection elements arranged in a matrix, an electrostatic latent image corresponding to the dose is accumulated and recorded on the solid detection elements. 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 information. The radiation detector can erase and reuse the radiation image information that is the remaining electrostatic latent image by irradiating the radiation detector with erasing light (refer to Japanese Patent Laid-Open No. 2000-105297). .

  Next, a radiographic image capturing system 10B according to the second embodiment will be described with reference to FIGS. 9 to 13C. In the radiographic image capturing system 10B, the same components as those in the radiographic image capturing system 10A according to the first embodiment (see FIGS. 1 to 8) are denoted by the same reference numerals and detailed description thereof is omitted. The same shall apply hereinafter.

  The radiation imaging system 10B according to the second embodiment is that the power supply device (wireless power supply device) 150 charges the radiation detection cassette 24 (24a to 24c) wirelessly (non-contact), in the first embodiment. This is different from the radiographic image capturing system 10A according to FIG.

  That is, as illustrated in FIG. 9, signals are transmitted and received by radio communication using UWB between the imaging device 22, the radiation detection cassette 24, the display device 26, the console 28, and the power supply device 150. It is connected to a free arm 152 extending from the ceiling, and can be moved to a desired position according to the arrangement of the radiation detection cassette 24. The power feeding device 150 converts electric energy into a magnetic field M, and can charge the radiation detection cassette 24 in an area where power can be fed by the converted magnetic field M (a range indicated by M in FIG. 9).

  FIG. 10 is a perspective view of the radiation detection cassette 24 of FIG. 9, and the power supply unit 44 of the radiation detection cassette 24 is an energy conversion unit (re-converting the magnetic field M into electric energy when in the power supplyable area). 2nd energy conversion part) 154. In this case, as shown in the plan view of FIG. 11, the display unit 49 is disposed at a location that is not irradiated with the radiation X on the irradiation surface 36 of the casing 34 and that does not overlap the energy conversion unit 154.

  FIG. 12 is a block diagram of a part of the configuration of the radiographic image capturing system 10 </ b> B including the radiation detection cassette 24, the console 28, and the power supply device 150. In the radiographic imaging system 10B, the configuration of the imaging device 22 and the display device 26 is the same as that of the radiographic imaging system 10A (see FIGS. 1 to 8). Illustration of the display device 26 and the like is omitted.

  The power supply device 25 includes a power source 160, a transceiver (cassette notification unit, information transmission unit) 162, an LC resonator (first energy conversion unit, charge processing unit) 164, a display unit (cassette notification unit, information display unit) 165, and A power supply control unit (charge control unit) 166 is included.

  The transceiver 162 receives ordering information and a power supply area detection signal of the radiation detection cassette 24 described later from the transceiver 96 of the console 28 by wireless communication, and transmits information from the power supply control unit 166 to the transceiver 96 by wireless communication. To do.

  The power feeding control unit 166 controls the LC resonator 164 based on the received ordering information and the power feeding area detection signal, and supplies the DC power supplied from the power source 160 connected to an external power source (not shown) to the LC resonator 164. Thus, the DC power (electric energy) is converted into the magnetic field M. The radiation conversion cassette 154 having the power supply unit 44 and outputting the power supply area detection signal by the energy conversion unit 154 of the power supply unit 44 in the power supplyable area of the magnetic field M reconverting the magnetic field M into electric energy. Is charged.

  In this case, the power management unit 86 of the radiation detection cassette 24 detects the charge amount of the power supply unit 44, and consoles the information regarding the detected charge amount and the charge amount of the power supply unit 44 including the cassette ID information from the transceiver 48. The console 28 registers this information in the power supply information management unit 105 and transfers it to the transceiver 162. By receiving the information via the transceiver 162, the power supply control unit 166 can grasp the currently-detected radiation detection cassette 24 and its charge amount.

  Further, the power supply control unit 166 causes the display unit 165 to display the information (cassette ID information and charge amount) received via the transceiver 162.

  Furthermore, the power supply control unit 166 determines that the charge amount of the power supply unit 44 is a predetermined charge amount (a charge amount necessary for one shooting or a predetermined number of shootings) based on the information received via the transceiver 162. If it is determined that the required amount of charge has been reached, it is determined that charging has been completed, and the supply of electrical energy to the LC resonator 164 is stopped or reduced, and information indicating that charging has been completed is displayed. Output to the unit 165 and the transceiver 162. The display unit 165 displays the information, while the transmitter / receiver 162 transmits the information to the transmitter / receiver 96.

  The power feeding control unit 166 can also move the power feeding device 150 to a desired position by controlling the power feeding device movement control unit 153 and moving the universal arm 152. Thereby, the power supplyable area of the magnetic field M can be changed, and the power supplyable area can have directivity.

  On the other hand, the power supply unit 44 of the radiation detection cassette 24 includes an energy conversion unit 154 including an LC resonator 168 and a power supply 170, a battery 172, a detection LC resonator 174, and an energy detection unit 176. The power management unit 86 includes an operation management unit 180 and a data management unit 182.

  The LC resonator 168 reconverts the magnetic field M from the LC resonator 164 of the power feeding device 150 into electric energy. That is, in the second embodiment, wireless power feeding is performed using a known power transmission technique using resonance of the magnetic field M from the LC resonator 164 configured by an LC resonant circuit having a coil and a capacitor to the LC resonator 168. . The power supply 170 supplies (charges) the reconverted electrical energy to the battery 172 as desired power. In addition, the power supply 170 supplies the power charged in the battery 172 to the radiation detector 40, the cassette control unit 46, and the transceiver 48 after the charging of the radiation detection cassette 24 is completed. The detection LC resonator 174 reconverts the magnetic field M into electric energy when the magnetic field M is relatively low. When the detection LC resonator 174 detects the electric energy, the energy detection unit 176 detects that the radiation detection cassette 24 (the power supply unit 44 thereof) is within the power supplyable area, and the detection result is displayed in the power supply area. The detection signal is output to the power management unit 86.

  On the other hand, the operation management unit 180 of the power management unit 86 controls the driving of the radiation detection cassette 24 by performing drive control of the power supply unit 44. In this case, the operation management unit 180 manages (detects) the charge amount of the battery 172 of the power supply unit 44. In addition, the data management unit 182 manages ID information for specifying the power supply device 150 corresponding to the power supply of the radiation detection cassette 24, a power supply area detection signal from the energy detection unit 176, and the like. Therefore, the power supply management unit 86 charges the power supply unit 44 (battery 172) including the power feeding area detection signal managed by the data management unit 182 and the charge amount of the battery 172 managed by the operation management unit 108. Information about the quantity is transmitted to the console 28 via the transceiver 48.

  The radiographic image capturing system 10B according to the second embodiment is basically configured as described above. Next, the operation (a method of charging the radiation detection cassette) will be described.

  Also in this case, the ordering information is information for requesting the patient 14 to capture a plurality of times of radiographic image information, and the amount of charge of each of the power supply units 44a to 44c reaches the amount of charge required for one imaging. A case where the two radiation detection cassettes 24a and 24b are charged when not performed will be described.

  When the ordering information is transmitted to the power supply control unit 166 via the transceivers 96 and 162, and the ordering information is transmitted to the power management unit 86 of each of the radiation detection cassettes 24a to 24c via the transceivers 96 and 48. Each power management unit 86 detects the amount of charge of the battery 172 based on the received ordering information, and since the detected amount of charge has not reached the amount of charge required for one imaging, radiation detection is performed. It is determined that the cassettes 24a to 24c are not in a state that can be used for photographing at present. Then, the power management unit 86 outputs information (charge amount, cassette ID information, etc.) indicating that charging is necessary to the display unit 49 and the transceiver 48, respectively. Each display unit 49 displays the information, respectively, while each transceiver 48 transmits the information to the transceiver 96, respectively. The console 28 registers each piece of information received by the transceiver 96 in the power supply information management unit 105 and also transfers it to the power supply apparatus 150.

  The power supply control unit 166 of the power supply device 150 first controls the power supply device movement control unit 153 based on the ordering information and the information received via the transmitter / receiver 162 to move the universal arm 152 to thereby move the power supply device. While moving 150, low electric energy is supplied to the LC resonator 164 to form a power supplyable area by a relatively weak magnetic field M. In other words, by moving the power feeding device 150 while generating a power feedable area by a relatively weak magnetic field M, the power feedable area can be provided with directivity.

  In this case, the detection LC resonator 174 of the power supply unit 44 in the power supplyable area reconverts the magnetic field M into low electric energy, and the energy detection unit 176 uses the reconverted electric energy to generate a power supply unit. It detects that the radiation detection cassette 24a having 44 is in the power supplyable area, and outputs the detection result to the power management unit 86 as a power supply area detection signal. The data management unit 182 of the power management unit 86 transmits information including the power feeding area detection signal and the cassette ID information to the console 28 via the transceiver 48, and the console 28 feeds the information received by the transceiver 96. The information is registered in the information management unit 105 and transferred to the power supply control unit 166 via the transceivers 96 and 162.

  The power supply control unit 166 grasps from the received information that the power supply unit 44a of the radiation detection cassette 24a is in the power supplyable area, stops control of the power supply device movement control unit 153, and supplies it to the LC resonator 164. The electrical energy to be changed is changed from low energy to high energy. As a result, the power supply area is fixed, and a strong magnetic field M is supplied from the LC resonator 164 toward the LC resonator 168 of the energy conversion unit 154 (154a). As a result, the LC resonator 168 is strong. The magnetic field M is converted back into high electrical energy and supplied to the battery 172 via the power source 170 (see FIG. 13A).

  During charging from the power supply device 150 to the radiation detection cassette 24a, the operation management unit 180 detects the charge amount of the battery 172, and charges the power supply unit 44 (44a) including the detected charge amount of the battery 172 and the cassette ID information. Information about the quantity is transmitted to the console 28 via the transceiver 48. The console 28 registers the information received by the transceiver 96 in the power feeding information management unit 105 and transfers the information to the power feeding control unit 166 via the transceivers 96 and 162. The power supply control unit 166 can grasp the charge amount of the battery 172 of the radiation detection cassette 24 a from the information received from the console 28.

  When the power supply control unit 166 determines that the charge amount of the battery 172 included in the information received from the console 28 has reached the charge amount necessary for one imaging of the radiation detection cassette 24a, the LC resonator By changing the electrical energy supplied to 164 from high energy to low energy, the magnetic field M is changed from a strong magnetic field for charging to a weak magnetic field, and the feeder arm movement control unit 153 is controlled to move the free arm 152. The power supply device 150 is moved to start the charging process for the radiation detection cassette 24b. That is, the charging process for the radiation detection cassette 24b is performed while the radiation image information for the patient 14 is captured once using the charged radiation detection cassette 24a (see FIG. 13B).

  The flow of the charging process for the radiation detection cassette 24b is substantially the same as the charging process for the radiation detection cassette 24a described above, and is simply the amount of charge to be charged (in the case of the radiation detection cassette 24b, the remaining number of times). Since only the charge amount required for shooting is different, detailed description thereof is omitted.

  In addition, when the magnetic field M is changed from a strong magnetic field for charging to a weak magnetic field, and the reconversion from the magnetic field M to the electric energy by the LC resonator 168 becomes impossible, the power management unit 86 includes the battery 172. The charge amount reaches the charge amount necessary for the predetermined number of times of photographing (the amount of charge necessary for one or the remaining number of times of photographing), and it is determined that the charging to the battery 172 is completed, and includes cassette ID information. Information indicating that the amount of charge of the battery 172 has reached the amount of charge required for a predetermined number of times of imaging may be output to the display unit 49 and the transceiver 48.

  As described above, in the second embodiment, the radiation detection cassettes 24a to 24c, the console 28, and the power supply device 150 can each have information on the charge amount of the battery 172 via wireless communication. Similarly to the above, the information can be displayed on the display units 49, 94, 165.

  As described above, according to the radiographic image capturing system 10B according to the second embodiment, each of the radiation detection cassettes 24a to 24c can be charged from the power supply apparatus 150 via wireless (magnetic field M). The handling of not only the cassettes 24a to 24c but the entire system can be improved.

  In addition, the power supplyable area of the magnetic field M has directivity with respect to the one radiation detection cassette 24a when charging with respect to one radiation detection cassette 24a. Since it has directivity with respect to the other radiation detection cassettes 24b, the radiation detection cassettes 24a and 24b can be charged accurately.

  Further, the LC resonator 164 converts the electric energy into the magnetic field M, and the LC resonator 168 reconverts the magnetic field M into the electric energy only when it is within the power supplyable area. It can be performed with high accuracy.

  Furthermore, since the power feeding device movement control unit 153 moves the universal arm 152 and moves the power feeding device 150 based on the control from the power feeding control unit 166, the power supply possible area of the magnetic field M can be easily changed.

  In addition, the radiographic imaging system 10B which concerns on 2nd Embodiment is not limited to the description mentioned above, As shown to FIG. 13C, you may perform a charging process with respect to the radiation detection cassette 24c.

  Next, a radiographic imaging system 10C according to the third embodiment will be described with reference to FIG.

  The radiographic imaging system 10C according to the third embodiment is the radiographic imaging system 10B according to the second embodiment in that the power supply apparatus 150 includes the transmitter 190 and the power supply unit 44 includes the receiver 192. (See FIGS. 9 to 13C).

  That is, in the second embodiment, the detection LC resonator 174 detects a relatively weak magnetic field M, but in FIG. 14, the transmitter 190 has a directional antenna and the receiver 192 has a transmitter 190. By connecting with the transmitter 190 via radio waves (wireless) from the power reception, the power reception availability detection unit 194 can detect that the power supply unit 44 is within the power supplyable area.

  As described above, according to the radiographic imaging system 10C according to the third embodiment, it is determined whether or not the power supply unit 44 is within the power supplyable area using the transmitter 190 and the receiver 192 having directional antennas. Since it detects, it becomes possible to perform this detection more correctly.

  Further, compared with the second embodiment, it is not necessary to change the intensity of the magnetic field M (electric energy supplied to the LC resonator 164), and thus the control of the power feeding control unit 166 with respect to the LC resonator 164 is simplified. can do.

  Next, a radiographic image capturing system 10D according to the fourth embodiment will be described with reference to FIG.

  The radiographic imaging system 10D according to the fourth embodiment is charged with a transmitter 190 and a receiver 192 instead of the LC resonators 164 and 168, and thus the radiographic imaging system 10C according to the third embodiment. (See FIG. 14).

  Here, when a weak radio wave (radio wave corresponding to low electrical energy) is transmitted from the transmitter 190 to the receiver 192, the changeover switch 199 connects the receiver 192 and the power reception availability detection unit 194. When the receiver 192 detects the weak radio wave and outputs low electrical energy, the power reception availability detection unit 194 detects that the power supply unit 44 is within the power supplyable area (communication range of the transmitter 190). . On the other hand, when a strong radio wave (a radio wave corresponding to high electrical energy) is transmitted from the transmitter 190 to the receiver 192, the changeover switch 199 connects the receiver 192 and the power source 170, and the power source 170 is When the receiver 192 receives the strong radio wave and outputs high electric energy, the electric energy is supplied (charged) to the battery 172.

  As described above, also in the radiographic imaging system 10D according to the fourth embodiment, charging is performed using the transmitter 190 and the receiver 192 having directional antennas, so that the charging operation can be performed accurately.

  Next, a radiographic image capturing system 10E according to the fifth embodiment will be described with reference to FIGS.

  The radiation image capturing system 10E according to the fifth embodiment is that the radiation detection cassettes 24a to 24c are charged from the power supply device 200 including the display unit 202 via the cable 204, according to the first to fourth embodiments. It is different from the image capturing systems 10A to 10D (see FIGS. 1 to 15).

  In this case, charging is started by inserting the connector 206 of the cable 204 into the terminals 208a to 208c provided in the radiation detection cassettes 24a to 24c. When charging is completed, information indicating that is displayed on the display unit 202. Therefore, the doctor 18 or the radiologist can take radiographic image information on the patient 14 by using the charged radiation detection cassette by visually recognizing the display content of the display unit 202 and pulling out the connector 206.

  As described above, in the radiographic image capturing system 10E according to the fifth embodiment, the doctor 18 or the radiographer must perform the work when connecting the power supply apparatus 200 and the radiation detection cassettes 24a to 24c with the cable 204. In this embodiment, the above-described effects related to the charging process can be obtained.

  Note that the present invention is not limited to the above-described embodiment, and it is needless to say that various configurations can be adopted without departing from the gist of the present invention.

It is explanatory drawing of the operating room where the radiographic imaging system which concerns on 1st Embodiment was installed. It is a perspective view of the radiation detection cassette of FIG. It is a top view of the radiation detection cassette of FIG. It is a circuit block diagram of the radiation detector of FIG. It is a partial block diagram of the radiographic imaging system of FIG. It is a partial block diagram of the radiographic imaging system of FIG. It is explanatory drawing which shows the modification of the radiographic imaging system which concerns on 1st Embodiment. It is another block diagram of a radiation detection cassette. It is explanatory drawing of the operating room where the radiographic imaging system of 2nd Embodiment was installed. FIG. 10 is a perspective view of the radiation detection cassette of FIG. 9. It is a top view of the radiation detection cassette of FIG. It is a partial block diagram of the radiographic imaging system of FIG. 13A to 13C are explanatory diagrams illustrating an example of the charging process. It is a block diagram of the configuration of the radiographic imaging system of the third embodiment. It is a block diagram of the configuration of the radiographic image capturing system of the fourth embodiment. It is explanatory drawing of the radiographic imaging system of 5th Embodiment. FIG. 17 is a partial configuration block diagram of the radiographic image capturing system in FIG. 16.

Explanation of symbols

10A to 10E ... Radiological imaging system 12 ... Operating room 14 ... Patient 16 ... Operating table 22 ... Imaging device 24, 24a-24c ... Radiation detection cassette 26 ... Display device 28 ... Console 30 ... Cradle 35, 49, 49a-49c, 94, 165 ... display unit 40 ... radiation detector 44 ... power supply unit 46 ... cassette control unit 48, 76, 96, 120, 162 ... transceiver 74 ... radiation source 86 ... power source management unit 90, 192 ... receiver 105 ... power supply Information management unit 122 ... Control unit 124 ... Charge processing unit 128 ... Changeover switches 164, 168 ... LC resonator 166 ... Power supply control unit 172 ... Battery 190 ... Transmitter 204 ... Cable

Claims (21)

A plurality of radiation detection cassettes that detect radiation that has passed through the subject and convert it into radiation image information; and a charging device that can charge each of the radiation detection cassettes,
The charging device is:
A charge amount for each of the radiation detection cassettes such that the plurality of radiation detection cassettes secure a total power supply capacity necessary for the imaging based on order information requesting the radiographic image information to be captured a plurality of times for the subject. A radiographic imaging system characterized by controlling the above. The system of claim 1, wherein
The charging device is:
Among the plurality of radiation detection cassettes, one radiation detection cassette having the maximum charge amount is selected from among the radiation detection cassettes suitable for the order information,
A radiographic imaging system for detecting, for the selected one radiation detection cassette, a charge amount necessary for imaging among the imaging based on the order information. The system of claim 2, wherein
The charging device is:
When it is detected that the amount of charge of the selected one radiation detection cassette is less than one imaging, the radiation detection cassette is charged until the amount of charge necessary for at least one imaging is reached. Do,
After the completion of charging for the one radiation detection cassette, during the one-time imaging using the one radiation detection cassette, the next largest amount of charge is among the remaining radiation detection cassettes that match the order information. A radiographic imaging system comprising: selecting another radiation detection cassette, and charging the selected other radiation detection cassette so as to reach a charge amount necessary for imaging at least for the remaining number of times. . The system of claim 3, wherein
The charging device is:
When the other radiation detection cassette having the next largest charge amount is being charged, if the other radiation detection cassette is used for imaging even though the charging is not completed, the imaging is performed at least for the remaining number of times. Among the remaining radiation detection cassettes including the one radiation detection cassette that match the order information so as to reach the required charge amount, the radiation having the second largest charge amount after the other radiation detection cassette A radiographic imaging system, wherein a detection cassette is selected, and the selected radiation detection cassette having the next largest charge amount is charged. The system according to claim 3 or 4,
The charging device is:
Charging for the one radiation detection cassette, and charging processing unit for charging the other radiation detection cassette;
A cassette notifying unit for notifying the radiation detection cassette being charged by the charging processing unit;
Based on the order information, a charging control unit that controls the charging processing unit and the cassette notification unit;
A radiographic imaging system comprising: The system of claim 5, wherein
The charging control unit, when the charging processing unit completes charging to the one radiation detection cassette or charging to the other radiation detection cassette, passes the radiation detection cassette that has been charged through the cassette notification unit. A radiographic imaging system characterized by notifying outside. The system according to claim 5 or 6,
The cassette notification unit includes an information display unit that displays information on a radiation detection cassette being charged or information on a radiation detection cassette that has been charged, and / or information on the radiation detection cassette externally via a wireless or wired connection. A radiographic imaging system, characterized in that it is an information transmission unit for transmitting to a radiographic image. The system according to any one of claims 5 to 7,
The charging device is a cradle capable of charging each radiation detection cassette in a state where each radiation detection cassette is loaded, or a power feeding device capable of charging each radiation detection cassette via wireless or wired connection. A featured radiographic imaging system. The system of claim 8, wherein
The cradle further includes a changeover switch that switches connection between the loaded radiation detection cassette and the charging processing unit,
The charge control unit
Based on the order information, the changeover switch is controlled so as to connect the one radiation detection cassette and the charge processing unit, and the one radiation detection cassette is moved from the charge processing unit via the changeover switch. By selecting the one radiation detection cassette by controlling the charging processing unit to charge,
When the charging for the one radiation detection cassette is completed, the changeover switch is controlled so as to connect the other radiation detection cassette and the charging processing unit, and from the charging processing unit via the changeover switch. A radiographic imaging system, wherein the other radiation detection cassette is selected by controlling the charging processing unit to charge the other radiation detection cassette. The system of claim 8, wherein
A plurality of cradles each capable of being loaded with the radiation detection cassette;
Of each of the cradle, a charging processing unit of one cradle charges the one radiation detection cassette loaded in the one cradle based on the order information,
The charging control unit of the one cradle, when the charging of the one radiation detection cassette is completed, notifies the completion of the charging to the outside through the cassette notification unit of the one cradle,
The other cradle charge control unit is configured to charge the other radiation detection cassette loaded in the other cradle based on the order information and the notification of the completion of the charge. A radiographic imaging system characterized by controlling the above. The system of claim 8, wherein
When the power supply device is a wireless power supply device that can charge each of the radiation detection cassettes via the radio,
The charging processing unit of the wireless power feeder has directivity with respect to the one radiation detection cassette when charging the one radiation detection cassette, while the other processing unit is charged with charging the other radiation detection cassette. A radiation image capturing system characterized by having directivity with respect to the radiation detection cassette. The system of claim 11, wherein
The charge processing unit is a first energy conversion unit that converts electric energy into a magnetic field, and can charge each radiation detection cassette in an area that can be fed by the converted magnetic field,
The radiographic imaging system, wherein the first energy conversion unit selects the one radiation detection cassette or the other radiation detection cassette by changing the power supplyable area. The system of claim 12, wherein
Each said radiation detection cassette has a 2nd energy conversion part which reconverts the said magnetic field into the said electrical energy, respectively, when it exists in the said electric power feeding area, The radiographic imaging system characterized by the above-mentioned. The system according to claim 12 or 13,
A power supply device movement control means for moving the wireless power supply device based on the control from the charge control unit;
A radiographic imaging system, wherein the power supply area is changed by moving the wireless power supply device using the power supply device movement control means. The system of claim 11, wherein
The charging processing unit is a transmitter capable of charging each radiation detection cassette via the radio with an antenna having directivity.
Each of the radiation detection cassettes is connected to the transmitter via the radio when the own radiation detection cassette is within a communication range of the transmitter. The system according to any one of claims 1 to 15,
Each of the radiation detection cassettes detects a radiation that has passed through the subject and converts it into the radiation image information, a power supply unit that drives the radiation conversion panel, and a charge amount of the power supply unit A radiographic imaging system, comprising: a power management unit; and a charge notification unit for reporting the charge amount detected by the power management unit to the outside. The system of claim 16, wherein
Each of the power management units detects the amount of charge of the power supply unit based on the order information, and when the charging of the power supply unit by the charging device is completed, the completion of the charging is detected through the charge notification unit. A radiographic imaging system characterized by notifying outside. 18. A system according to claim 16 or 17,
Each of the charge notification units is a charge amount display unit that displays the charge amount, and / or a charge amount transmission unit that transmits the charge amount to the outside via wireless or wired connection. system. The system of claim 18, wherein
The radiation conversion panel, the power supply unit, and the power management unit, or the radiation conversion panel, the power supply unit, the power management unit, and the charge amount transmission unit are inside a casing made of a material that transmits the radiation. Stowed,
The radiographic image capturing system, wherein the charge amount display unit is provided at a non-irradiated portion of the radiation on the surface of the casing. The system according to any one of claims 1 to 19,
A radiation source that outputs the radiation; and a control device that controls the radiation source, the radiation detection cassette, and the charging device;
A radiographic imaging system characterized in that wireless communication or wired communication is possible between the radiation source, the radiation detection cassette, the charging device, and the control device.   The total amount of power necessary for the imaging in the plurality of radiation detection cassettes is secured by controlling the charging amount for the plurality of radiation detection cassettes based on the order information requesting the imaging of the radiation images for the subject multiple times. A method for charging a radiation detection cassette.

Images