JP5325571B2 - Radiation detection apparatus, radiographic imaging system, and radiographic imaging method - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To acquire highly accurate radiation image information by preventing a retake and improving the efficiency in photography. <P>SOLUTION: In the radiation image photographing system 10, it is determined whether the remaining quantity in a battery 44 for driving a radiation detector 40 is at least a prescribed threshold (step S3) when a photographing apparatus 22 outputs a radiography requesting signal to announce the start of irradiation of a subject 14 with radiation X (step S2: Yes). When the remaining quantity in the battery is less than the threshold (step S3: No), irradiation with radiation X by the photographing apparatus 22 is prohibited (step S4). <P>COPYRIGHT: (C)2010,JPO&amp;INPIT

Description

  The present invention relates to a radiation detection apparatus including a radiation detector that detects radiation transmitted through a subject and converts the radiation into radiation image information, a radiation image capturing system including the radiation detection apparatus, and a radiation image capturing method.

  2. Description of the Related Art In the medical field, radiation image capturing apparatuses that irradiate a subject with radiation and guide the radiation transmitted through the subject to a radiation conversion panel to capture a radiation image are widely used. As the radiation conversion panel, a conventional radiation film in which a radiation image is exposed and recorded, or radiation energy as a radiation image is accumulated in a phosphor, and the radiation image is irradiated as excitation light by irradiating excitation light. A storage phosphor panel that can be removed is known. These radiation conversion panels supply a radiation film on which a radiographic image is recorded to a developing device to perform development processing, or supply a stimulable phosphor panel to a reading device to perform reading processing so that a visible image can be obtained. A radiographic image can be obtained.

  On the other hand, in an operating room or the like, it is necessary to immediately read out and display a radiation image from a radiation conversion panel after imaging in order to perform a quick and accurate treatment on a patient. Similarly, rapid imaging is also required for imaging of infants, children, elderly people, and patients who cannot stand for a long time due to illness or injury. 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 to read out as a radiation conversion panel that can meet such demands A vessel has been developed.

  For example, in Patent Document 1, when the remaining battery level of a battery that drives the radiation detector has reached an amount that can be imaged, the imaging standby state is switched to the imageable state, while the remaining battery level is When the amount that can be photographed has not reached the amount that can be photographed, a radiation detection device (electronic cassette) and a radiation image photographing system that maintain a photographing standby state have been proposed.

International Publication No. 2006/080377 Pamphlet

  As described above, the technique disclosed in Patent Document 1 determines whether to allow photographing (capturing enabled state) or prohibition (capturing standby state) according to the remaining battery level. There is no proposal regarding the relationship between the prohibition and the charging operation from the charging device to the battery.

  For example, if imaging is performed while a battery that is charged to the remaining battery level necessary for imaging is being further charged, noise due to the charging is mixed into the radiographic image obtained by the imaging Therefore, the radiographic image becomes an image that is not suitable for interpretation interpretation by a doctor, and re-imaging is necessary.

  Further, when the remaining battery level has not reached the amount required for shooting, charging from the charging device to the battery is not always started promptly even if the shooting enabled state is switched to the shooting standby state. Therefore, if the imaging is performed in a state where the remaining battery level has not reached the amount required for imaging, the radiation detection device malfunctions due to insufficient battery power, so that a desired radiographic image cannot be obtained and imaging is performed again. Is required.

  In particular, in a non-contact charging method in which a battery is charged in a non-contact manner from a charging device, charging to the battery is rarely completed in a short time, and it is desirable to charge until just before the start of photographing. In addition, in a radiation detection apparatus equipped with a battery charged by the non-contact charging method, a relatively small battery is mounted in order to reduce the weight of the entire apparatus, so a large battery is mounted and charged with a margin. I can't do it. Therefore, in the said radiation detection apparatus, it is easy to raise | generate the subject mentioned above.

  The present invention has been made in consideration of the above-described problems. A radiation detection apparatus and a radiation image that can prevent the occurrence of re-imaging and improve the imaging efficiency to acquire highly accurate radiation image information. An object is to provide an imaging system and a radiographic imaging method.

The radiation detection apparatus according to the present invention includes:
A radiation detector that detects radiation that has been irradiated from an external imaging device and transmitted through the subject and converts the radiation into radiation image information, a battery that drives the radiation detector, and a remaining battery level of the battery is greater than or equal to a predetermined threshold value A remaining battery level determination unit that determines whether or not there is an imaging control unit that controls irradiation of the radiation by the imaging device;
The battery remaining amount determination unit determines whether or not the battery remaining amount is equal to or greater than the threshold when the imaging apparatus outputs an imaging request signal for notifying the irradiation start of the radiation to the subject;
The imaging control unit is characterized by prohibiting the irradiation of the radiation by the imaging device when the remaining battery level determining unit determines that the remaining battery level is less than the threshold value.

Moreover, the radiographic imaging system according to the present invention includes:
An imaging device for irradiating a subject with radiation;
A radiation detector comprising: a radiation detector that detects the radiation transmitted through the subject and converts it into radiation image information; and a battery that drives the radiation detector;
A control device for controlling the imaging device and the radiation detection device;
A battery remaining capacity determining unit that determines whether or not the battery remaining capacity of the battery is equal to or greater than a predetermined threshold;
An imaging control unit that controls irradiation of the radiation by the imaging device;
Have
The battery remaining amount determination unit determines whether or not the battery remaining amount is equal to or greater than the threshold when the imaging apparatus outputs an imaging request signal for notifying the irradiation start of the radiation to the subject;
The imaging control unit is characterized by prohibiting the irradiation of the radiation by the imaging device when the remaining battery level determining unit determines that the remaining battery level is less than the threshold value.

Furthermore, the radiographic image capturing method according to the present invention includes:
A radiation image capturing method for irradiating a subject with radiation from an imaging device, detecting the radiation with a radiation detector mounted on the radiation detection device, and converting the radiation into radiation image information,
When the imaging apparatus outputs an imaging request signal for notifying the start of irradiation of the radiation to the subject, it is determined whether or not a remaining battery level of a battery that drives the radiation detector is equal to or greater than a predetermined threshold;
When the battery remaining amount is less than the threshold value, irradiation of the radiation by the imaging device is prohibited.

  According to the present invention, when the imaging apparatus outputs an imaging request signal for notifying the start of radiation irradiation on the subject, it is determined whether or not the remaining battery level of the battery is greater than or equal to a threshold value, and the remaining battery level is When the value is less than the threshold value, irradiation of the radiation by the imaging apparatus is prohibited.

  Thereby, the malfunction of the radiation detection apparatus due to the shortage of the remaining battery capacity can be avoided, and the occurrence of reimaging can be prevented. In addition, the prohibition of radiation irradiation enables charging of the battery that has insufficient battery power, so that imaging efficiency is improved and highly accurate radiation image information can be acquired.

  DESCRIPTION OF THE PREFERRED EMBODIMENTS Hereinafter, a radiographic imaging system and a radiographic imaging method according to the present invention will be described in detail with reference to the accompanying drawings by giving preferred embodiments in relation to a radiation detection apparatus used in the system.

  As shown in FIG. 1, the operating room 12 in which the radiographic image capturing system 10 (hereinafter also referred to as “imaging system 10”) according to the first embodiment of the present invention is installed is a bed on which a patient 14 lies. A certain operating table 16 and an instrument table 20 on which various instruments used by the doctor 18 for surgery are placed. Around the operating table 16, various devices necessary for the operation such as an anesthesia machine, an aspirator, an electrocardiograph, and a blood pressure monitor (not shown) are arranged.

  The imaging system 10 includes an imaging device (radiation irradiation device) 22 that irradiates a patient 14 as a subject with a dose of radiation X according to imaging conditions, and a radiation detector 40 that detects the radiation X transmitted through the patient 14 (FIG. 2). The electronic cassette 24, which is a radiation detection device with a built-in reference), and a power feeding device (charging device, wireless power feeding device) that wirelessly (contactlessly) supplies power to the battery 44 (see FIG. 2) built in the electronic cassette 24 ) 25, a display device 26 that displays a radiation image based on the radiation X detected by the radiation detector 40, and a console (control device) 28 that comprehensively controls the imaging system 10. In the imaging system 10, signals can be transmitted and received between the imaging device 22, the electronic cassette 24, the power feeding device 25, the display device 26, and the console 28 by wireless communication using, for example, UWB (Ultra Wide Band).

  The imaging device 22 is connected to a free arm 30 extending from the ceiling, can be moved to a desired position according 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 power feeding device 25 is connected to the universal arm 31 and can be moved to a desired position according to the arrangement of the electronic cassette 24. 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 displayed radiation image. The free arms 30 to 32 may be provided on a wall, a floor, a movable wagon, or the like, and the power feeding device 25 or the display device 26 may be fixed to a ceiling, a wall, a floor, or the like without using a free arm. Good. Note that the power supply device 25 is arranged so that the magnetic field M applied to the radiation detection device (such as the electronic cassette 24) avoids the patient 14, for example, in the horizontal direction of the radiation detection device (see FIGS. 1 and 11) or below the bottom surface. (See FIG. 12).

  FIG. 2 is a partially cut perspective explanatory view of the electronic cassette 24 of FIG. The electronic cassette 24 includes a box-shaped casing 34 made of a material that transmits the radiation X. In the casing 34, a grid 38 for removing scattered radiation of the radiation X by the patient 14 and a radiation detector (radiation for detecting the radiation X transmitted through the patient 14) in order from the irradiation surface 36 side where the radiation X is irradiated. Conversion panel) 40 and a lead plate 42 that absorbs backscattered radiation X are arranged in layers. The irradiation surface 36 of the casing 34 can also be configured as a grid 38.

  The electronic cassette 24 includes a battery 44 that functions as a power supply unit, a cassette control unit 46 that performs drive control of the radiation detector 40 using power from the battery 44, and information on the radiation X detected by the radiation detector 40. A transceiver 48 that wirelessly transmits and receives a signal including (radiation image information) to and from the console 28 is provided. The battery 44, the cassette control unit 46, and the transmitter / receiver 48 are preferably provided with a lead plate or the like on the irradiation surface 36 side in order to avoid damage caused by irradiation with the radiation X. Further, the electronic cassette 24 includes a wireless power receiving unit 49 that receives a magnetic field (magnetic field, magnetic flux) M that is converted from electrical energy by the power supply device 25 and applied wirelessly, and reconverts the magnetic field M into electrical energy. Provided.

  FIG. 3 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 (storage unit) 53, the TFT 52 is sequentially turned on for each row, and the charge is read as an image signal. In FIG. 3, only the connection relationship between one pixel 50 including the photoelectric conversion layer 51 and the storage capacitor 53 and one TFT 52 is shown, and the configuration of the other pixels 50 is omitted. Amorphous selenium must be used within a predetermined temperature range because its structure changes and its function decreases at high temperatures. Therefore, it is preferable to provide means for cooling the radiation detector 40 in the electronic 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 for switching the gate lines 54 and an address decoder 60 for outputting 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.

  Further, 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. 4 is a block explanatory diagram of the photographing system 10 including the photographing device 22, the electronic cassette 24, the power feeding device 25, the display device 26, and the console 28.

  The console 28 stores radiographic image information and other information handled by the radiology department in the hospital, for example, order information (ordering information) such as the number of imaging (number of imaging, number of exposure) for each patient 14, A radiology information system (RIS, information management system) 29 for comprehensively managing these pieces of information is connected. Further, a medical information system (HIS) 33 that manages medical information in the hospital in an integrated manner is connected to the RIS 29. It can also be configured as a comprehensive system in which the functions of the RIS 29 are added to the HIS 33 in an integrated manner.

  The imaging device 22 includes an imaging switch 72, a radiation source 74, a transceiver 76, and a radiation source controller 78. The transceiver 76 receives imaging conditions from the console 28 by wireless communication, and transmits an imaging completion signal, an imaging start signal, and the like to the console 28. The radiation source controller 78 drives and controls the radiation source 74 based on the imaging start signal (imaging request signal) supplied from the imaging switch 72 and the imaging conditions supplied from the console 28. The radiation source 74 outputs the radiation X based on the control from the radiation source control unit 78.

  The power supply device 25 receives a power supply permission signal (power supply start signal, charge permission signal) and the like from the console 28 through wireless communication with a power source 80 connected to an external power source (not shown). A transmitter / receiver 82 that transmits 25 ID information (identification data), an LC resonator (power transmission unit) 84 that converts electric energy from the power supply 80 into a magnetic field M and wirelessly transmits the electric cassette 24, and a console And a power supply control unit 86 that drives and controls the LC resonator 84 based on the power supply permission signal supplied from the power supply 28.

  FIG. 5 is a block explanatory diagram of the imaging system 10 more specifically showing the configuration of the electronic cassette 24 as the radiation detection apparatus according to the present embodiment.

  As shown in FIGS. 4 and 5, the electronic cassette 24 includes a radiation detector 40, a battery 44, a wireless power receiver 49, a cassette controller 46, and a transceiver (transmission / reception means, wireless transceiver) 48. Prepare.

  The battery 44 is configured by a rechargeable secondary battery such as a lithium ion battery, and is a power source that supplies power to each part of the electronic cassette 24 such as the radiation detector 40, the cassette control unit 46, and the transceiver 48. In addition to the secondary battery, for example, a storage element such as an electric double layer capacitor can be used as the battery 44. In short, the battery 44 can be charged and functions appropriately as a power source for the electronic cassette 24. That's fine.

  The wireless power receiving unit 49 has a function of receiving power supplied wirelessly from the power supply device 25 and supplying (charging) the battery 44. The wireless power receiving unit 49 receives a magnetic field M applied from the LC resonator 84 of the power feeding device 25 and reconverts it into electric energy, and the electric energy reconverted by the LC resonator 88 in a desired manner. And a charging circuit 90 that converts the electric power to supply to the battery 44. The charging circuit 90 rectifies the current generated by the LC resonator 88 and charges the battery 44 with a predetermined constant current, for example.

  Further, the wireless power receiving unit 49 is arranged in parallel with the LC resonator 88 and detects the detection LC resonator 94 smaller than the LC resonator 88 and the electric energy reconverted by the detection LC resonator 94. An energy detection unit 96 is provided. The energy detection unit 96 detects the electric energy to detect that the electronic cassette 24 is within the power supplyable area of the power supply device 25, and transmits a power supply area detection signal to the cassette control unit 46.

  As described above, for the electronic cassette 24 from the power supply device 25, a known method using the resonance of the magnetic field M from the LC resonator 84 configured by an LC resonance circuit having a coil and a capacitor to the LC resonator 88. Using power transmission technology, wireless power feeding (charging) can be performed.

  As shown in FIG. 5, the cassette control unit 46 includes an address signal generation unit 98, an image memory 100, an operation management unit 102, a cassette ID memory 104, and a data management unit 106. The address signal generator 98 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 100 stores radiation image information detected by the radiation detector 40. That is, the image memory 100 stores radiation image information that is irradiated to the radiation detector 40 and accumulated as signal charges, and then read and converted into digital signals.

  The operation management unit 102 controls driving of the wireless power receiving unit 49 and the battery 44, and also controls driving of the entire electronic cassette 24. Further, the operation management unit 102 is provided with a remaining battery level determination unit 107, a charging control unit 108, and an imaging control unit 109.

  The battery remaining amount determination unit 107 determines whether or not the remaining amount (battery remaining amount) of the battery 44 is equal to or greater than a predetermined threshold value. Specifically, if the remaining battery level is equal to or greater than the threshold, the remaining battery level determination unit 107 has reached the amount necessary for radiographic image capture, and the battery 44 is sufficiently charged. It is determined that Further, if the remaining battery level is less than the threshold value, the remaining battery level determining unit 107 determines that the remaining battery level has not reached the amount necessary for radiographic image capturing and the battery 44 is insufficiently charged. To do. The determination process described above is performed when the transmitter / receiver 48 receives from the imaging device 22 via the console 28 an imaging start signal that notifies the patient 14 of the start of radiation X irradiation (imaging start). Note that the determination process is not limited to when the imaging start signal is received by the transmitter / receiver 48, and may be appropriately performed before or after radiographic imaging.

  The image capturing control unit 109 receives the image capturing start signal by the transceiver 48, and the image capturing apparatus 22 when the remaining battery level determining unit 107 performs the above determination process and determines that the remaining battery level is equal to or greater than the threshold value. A control signal (imaging permission signal) for permitting imaging (irradiation of radiation X) is generated. In addition, when the transmitter / receiver 48 receives the shooting start signal and the remaining battery level determination unit 107 performs the above determination process and determines that the remaining battery level is less than the threshold value, the shooting control unit 109 receives the shooting start signal. 22 generates a control signal (photographing prohibition signal) for prohibiting the photographing by 22.

  When the remaining battery level determination unit 107 determines that the remaining battery level is equal to or greater than the threshold value and the shooting control unit 109 generates a shooting permission signal, the charging control unit 108 transfers from the power supply device 25 to the electronic cassette 24. A signal for prohibiting power supply (charging) is generated (power supply prohibition signal, charge prohibition signal). In addition, when the remaining battery level determination unit 107 determines that the remaining battery level is less than the threshold value and the shooting control unit 109 generates a shooting inhibition signal, the charging control unit 108 receives the electronic cassette from the power supply device 25. Signals (power supply permission signal, power supply start signal, charge permission signal) permitting power supply (charging) to 24 are generated. As described above, the charge control unit 108 that generates the power supply prohibition signal and the power supply permission signal in response to the determination result of the battery remaining amount determination unit 107 and the signal from the imaging control unit 109 is configured to supply the power supply prohibition signal and the power supply permission signal. It is also possible to configure as a plurality of control units (signal generation units) respectively corresponding to.

  The power supply prohibition signal and the power supply permission signal issued by the charge control unit 108 and the image capture permission signal and the image capture prohibition signal issued by the imaging control unit 109 are transmitted to the console 28 via the transceiver 48. When the console 28 receives these signals, the wireless power supply prohibition (stop) control and start (restart) control from the power supply device 25 and the photographing permission (start) control and prohibition (stop) from the image capturing device 22 are received. Implement control. Note that a power supply prohibition (permission) signal or a photographing permission (prohibition) signal is directly transmitted from the electronic cassette 24 to the power supply device 25 without going through the console 28, for example, by the power supply control unit 86 or the radiation source control unit 78. You may comprise so that electric power feeding prohibition (start) control and imaging | photography start (prohibition) control may be performed.

  The cassette ID memory 104 stores cassette ID information for specifying the electronic cassette 24. The data management unit 106 manages ID information (identification data) for specifying the power supply device 25 corresponding to the power supply of the electronic cassette 24, a power supply area detection signal from the energy detection unit 96, and the like.

  The transceiver 48 receives the transmission request signal, the imaging start signal, and the ID information of the power supply device 25 from the console 28 by wireless communication, while the radiographic image information, cassette ID information, wireless power supply enable signal, power supply to the console 28. A prohibition signal, a power supply permission signal, a photographing permission signal, a photographing prohibition signal, and the like are transmitted.

  As shown in FIG. 4, the display device 26 includes a receiver 110 that receives radiation image information from the console 28, a display control unit 112 that processes the received radiation image information, and a radiation processed by the display control unit 112. And a display unit 114 that displays image information.

  The console 28 includes a transceiver 116, an imaging condition management unit 118, an image processing unit 120, an image memory 122, a patient information management unit 124, a cassette information management unit 126, and a power supply information management unit 128. Note that the console 28 may be installed outside the operating room 12 as long as signals can be reliably transmitted to and received from the imaging device 22, the electronic cassette 24, the power supply device 25, and the display device 26.

  The transmitter / receiver 116 needs to include radiation image information, a power supply prohibition (permission) signal, and an imaging permission (prohibition) signal between the console 28 and the imaging device 22, the electronic cassette 24, the power supply device 25, and the display device 26. Such information is transmitted and received by wireless communication. The shooting condition management unit 118 manages shooting conditions necessary for shooting by the shooting device 22, and further, shooting start control and shooting prohibition control of the shooting device 22 based on a shooting permission signal and a shooting prohibition signal from the shooting control unit 109. I do. The image processing unit 120 performs predetermined image processing on the radiation image information received from the electronic cassette 24. The image memory 122 stores the radiation image information processed by the image processing unit 120. The patient information management unit 124 manages patient information of the patient 14 to be imaged. The cassette information management unit 126 manages the cassette information including the wireless power feed enable signal and the cassette ID information received from the electronic cassette 24. The power supply information management unit 128 performs operation control of the power supply device 25, management of ID information transmitted from the power supply device 25, and the like, and also a power supply device based on a power supply prohibition signal and a power supply permission signal from the charge control unit 108. 25, power supply prohibition control and power supply start control (power supply resumption control) are performed.

  The imaging conditions are conditions for determining a tube voltage, a tube current, an irradiation time, and the like for irradiating a radiation X having an appropriate dose to an imaging region of the patient 14. The conditions such as the site and the imaging method can be listed. Furthermore, as imaging conditions, conditions, such as the frequency | count of imaging | photography, are mentioned as order information from RIS29, for example. 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 order 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. Further, the cassette information includes a wireless power feedable signal from the data management unit 106 in addition to the cassette ID information for specifying the electronic cassette 24.

  The imaging system 10 according to the first embodiment is basically configured as described above. Next, the operation thereof will be described with reference to the flowchart of FIG.

  Here, the operation of the imaging system 10 when the number of shots is one will be described.

  The imaging system 10 is installed in the operating room 12, and is used when, for example, it is necessary to capture a radiographic image during surgery. Therefore, the patient information, the number of shots, and the like of the patient 14 to be imaged are registered in advance in the patient information management unit 124 of the console 28 prior to imaging. If the imaging region and the imaging method are determined in advance, these imaging conditions are registered in the imaging condition management unit 118 in advance. These registrations can be performed by obtaining information from the RIS 29. The operation on the patient 14 is performed in the state where the above preparation work is completed.

  First, in step S1 of FIG. 6, when taking a radiographic image during an operation, the doctor 18 or a radiographer in charge takes the patient 14 and the operating table 16 with the irradiation surface 36 facing the imaging device 22 side. The electronic cassette 24 is installed at a desired position between the two.

  Here, in conjunction with the start of operation of the console 28 or by operation of an operation start switch (not shown), the power feeding device 25 is driven under a predetermined operation condition (low output operation). Therefore, the electronic cassette 24 can detect that the electronic cassette 24 is disposed in the power supplyable area of the power supply device 25 by the detection LC resonator 94 and the energy detection unit 96 of the wireless power receiving unit 49. That is, the energy detection unit 96 functions as a power reception availability detection unit that detects whether or not the electronic cassette 24 is in an area where power can be received from the power supply device 25. At this time, the power supply control unit 86 of the power supply device 25 applies a weak magnetic field M that allows the detection LC resonator 94 and the energy detection unit 96 of the electronic cassette 24 to detect the presence or absence of the magnetic field M from the LC resonator 84. Low power operation is performed to effectively reduce power consumption.

  On the other hand, in the electronic cassette 24, a power feeding area detection signal is supplied from the energy detection unit 96 to the data management unit 106. Upon receiving the power supply area detection signal, the data management unit 106 receives the ID information of the power supply device 25 stored in the power supply information management unit 128 from the console 28, while transmitting the wireless power supply enable signal to the cassette information management unit 126 of the console 28. And send.

  Further, the power supply area detection signal is also transmitted from the energy detection unit 96 to the operation management unit 102. Upon receiving the power feeding area detection signal, the operation management unit 102 turns on the electronic cassette 24 so that the electronic cassette 24 can be used, thereby completing the preparation for photographing. Of course, a power switch (not shown) operated by the doctor 18 or the like can be provided on the side surface of the electronic cassette 24 or the like.

  Next, when the doctor 18 or the radiographer operates the imaging switch 72, the radiation source control unit 78 of the imaging apparatus 22 transmits an imaging start signal from the imaging switch 72 to the imaging condition management unit 118 of the console 28, and the console 28 is requested to transmit the imaging conditions, and the radiation source 74 is activated with a predetermined tube current or the like to prepare for irradiation, and the imaging apparatus 22 is set in the imaging start standby state. The imaging condition management unit 118 transfers the received imaging start signal to the transceiver 48 of the electronic cassette 24.

  The operation management unit 102 monitors whether or not the transmitter / receiver 48 has received a shooting start signal (step S2), and when the transmitter / receiver 48 has received a shooting start signal (YES in step S2), the remaining battery level is determined. The amount determination unit 107 determines whether or not the remaining battery level of the battery 44 is equal to or greater than a threshold value (step S3). When the transceiver 48 does not receive the shooting start signal (NO in step S2), the operation management unit 102 continues to monitor whether or not the shooting start signal is received by the transmitter / receiver 48.

  In step S3, if the remaining battery level is less than the threshold value (NO in step S3), the remaining battery level determining unit 107 does not reach the amount necessary for radiographic image capture and the battery level is not reached. 44 determines that charging is insufficient. In this case, the photographing control unit 109 generates a photographing prohibition signal for prohibiting photographing by the photographing device 22 based on the determination result in the battery remaining amount determining unit 107, while the charging control unit 108 Based on the determination result in the amount determination unit 107 and the generation of the photographing prohibition signal, a power supply permission signal for permitting power supply from the power supply device 25 to the electronic cassette 24 is generated (step S4).

  The transceiver 48 transmits an imaging prohibition signal to the imaging condition management unit 118 of the console 28, and transmits ID information of the power supply device 25 and a power supply permission signal to the power supply information management unit 128 of the console 28.

  The photographing condition management unit 118 transfers the received photographing prohibition signal to the photographing device 22, and the photographing device 22 maintains a photographing start standby state based on the received photographing prohibition signal.

  On the other hand, the power supply information management unit 128 transfers the received ID information and power supply permission signal of the power supply device 25 to the power supply device 25, and the power supply control unit 86 of the power supply device 25 performs a desired operation based on the received power supply permission signal. Power is supplied (charged) to the electronic cassette 24 at the power amount and timing (step S5). In addition, when the remaining amount of the battery 44 is insufficient during the operation, the electronic cassette 24 can be appropriately charged while being placed in a predetermined photographing position. Of course, if the remaining amount of the battery 44 is insufficient even during preparation for imaging (during installation of the electronic cassette 24) or before the start of imaging, wireless charging immediately before the start of surgery or after the start of surgery. Can complete the preparation for shooting quickly.

  In step S5, when the electric power is supplied to the electronic cassette 24, the magnetic field M applied from the LC resonator 84 to the electronic cassette 24 is changed to a magnetic field sufficiently stronger than the low-power operation. The power feeding device 25 may be driven and controlled by output operation and power feeding operation). Further, in the electronic cassette 24, the power received by the LC resonator 94 for detection together with the LC resonator 88 can be used for charging the battery 44 from the charging circuit 90, so that the battery 44 can be charged more rapidly. .

  In the imaging system 10, the ID information of the corresponding power supply device 25 can be confirmed between the electronic cassette 24 and the power supply device 25 via the console 28 as described above. For this reason, for example, even when a plurality of power supply apparatuses are installed, it is possible to appropriately and selectively perform a power supply operation from the corresponding desired power supply apparatus to the electronic cassette 24, and wasteful power consumption, malfunction, etc. It can be avoided.

  In step S <b> 3, when the remaining battery level becomes equal to or greater than the threshold value due to power feeding from the power feeding device 25 to the electronic cassette 24, the remaining battery level determining unit 107 sets the remaining battery level to an amount necessary for radiographic image capturing. Therefore, it is determined that the battery 44 is fully charged (YES in step S3). As a result, the photographing control unit 109 generates a photographing permission signal for permitting photographing by the photographing device 22 based on the determination result in the battery remaining amount determining unit 107 (step S6). Generates a power supply prohibition signal for prohibiting power supply from the power supply device 25 to the electronic cassette 24 based on the determination result in the battery remaining amount determination unit 107 and the generation of the photographing permission signal (step S7).

  The transceiver 48 transmits the photographing permission signal to the photographing condition management unit 118 and transmits the ID information of the power feeding device 25 and the power feeding prohibition signal to the power feeding information management unit 128 of the console 28.

  The power supply information management unit 128 transfers the received ID information of the power supply device 25 and the power supply prohibition signal to the power supply device 25, and the power supply control unit 86 of the power supply device 25 receives the power supply prohibition signal from the power supply device 25 based on the received power supply prohibition signal. Power supply to the electronic cassette 24 is stopped, and the power supply device 25 is set in a power supply prohibition state.

  On the other hand, based on the received imaging permission signal, the imaging condition management unit 118 captures the imaging conditions and the number of images related to the imaging region of the patient 14 registered in the imaging condition management unit 118 and the imaging permission signal. Transmit to device 22. The imaging device 22 shifts from the imaging start standby state to an imaging state in which radiation X can be irradiated based on the received imaging permission signal, and then controls the radiation source 74 based on the received imaging conditions and the like. The patient 14 is irradiated (exposed) with radiation X having a predetermined dose (step S8). Of course, the imaging conditions may be transmitted in advance from the console 28 to a memory (not shown) of the radiation source controller 78.

  This prohibits wireless power feeding during radiographic imaging, so that it is possible to effectively avoid, for example, the voltage supplied from the battery 44 to the radiation detector 40 becoming unstable and greatly fluctuating. it can. In addition, noise caused by the magnetic field M applied from the power supply device 25 affects the radiation detector 40 side, so that noise is mixed into the captured radiographic image and the quality of the radiographic image is degraded. It can be effectively avoided.

  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 electronic cassette 24, and an electric signal is transmitted by the photoelectric conversion layer 51 of each pixel 50 constituting the radiation detector 40. Then, the charge is held as a charge in the storage capacitor 53 (see FIG. 3). Next, the charge information (signal charge) that is the radiographic image information of the patient 14 held in each storage capacitor 53 is supplied from the address signal generation unit 98 that constitutes the cassette control unit 46 to the line scanning drive unit 58 and the multiplexer 66. Read according to the address signal.

  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 98, 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 two. 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 98, 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 A / D converted into a digital signal. The radiographic image information converted into the digital signal is temporarily stored in the image memory 100 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 98, 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 out through the signal line 56, A / D converted through the multiplexer 66 and the A / D converter 70, and stored in the image memory 100 of the cassette control unit 46.

  The radiation image information stored in the image memory 100 is transmitted to the console 28 by wireless communication. The radiation image information transmitted to the console 28 is subjected to predetermined image processing in the image processing unit 120 and then associated with the patient information of the patient 14 registered in the patient information management unit 124. Is remembered.

  The radiographic image information subjected to the image processing is transmitted from the console 28 to the display device 26. The display device 26 that has received the radiation image information performs image display processing while displaying the radiation image while controlling the display unit 114 by the display control unit 112. For this reason, the doctor 18 can perform the operation while confirming the radiation image displayed on the display unit 114.

  When the A / D conversion in the A / D converter 70 is completed, that is, when the digitalization of the radiation image information obtained by the current imaging is completed, the charging control is performed in the next step S9. A power supply permission signal is issued from the unit 108.

  The ID information and the power supply permission signal of the power supply device 25 are transmitted from the electronic cassette 24 to the console 28. For example, under the management of the power supply information management unit 128, control for starting power supply by the power supply device 25, or power supply immediately The power supply device 25 is controlled to be in a power supply start standby state (power supply restart standby state) so that the power supply device 25 can be started (step S11). Thereby, after A / D conversion of the acquired radiation image information is completed after imaging, wireless power feeding to the battery 44 can be performed quickly (step S12). When the power supply start standby control is performed, for example, in the state where the console 28 receives the power supply permission signal, the battery 44 by the cassette control unit 46 or the cassette information management unit 126 is shown in step S10. In consideration of the remaining amount of power, it is preferable to perform power supply start control. Further, the power supply permission signal is directly transmitted from the electronic cassette 24 to the power supply device 25 without the console 28, and power supply start control is performed by the power supply control unit 86 of the power supply device 25 or the cassette control unit 46 of the electronic cassette 24. Alternatively, power supply start standby control may be executed.

  In addition, if the end point of the storage of the radiation image information after A / D conversion in the image memory 100 is regarded as the end point of the A / D conversion, it is not as much as the A / D conversion, but is somewhat affected by noise. It is possible to effectively avoid the influence of noise caused by wireless power supply during data transfer to the possible image memory 100, and to prevent data corruption or the like. Of course, by controlling the completion of data transmission from the image memory 100 to the console 28 by the transceivers 48 and 116 as the end point of A / D conversion, control is performed so as to more reliably avoid the influence of noise caused by wireless power feeding. You can also.

  In addition, the generation of the power supply permission signal in step S9 is performed at a predetermined timing, for example, after transmission of the digital signal from the electronic cassette 24 to the console 28 is completed, after the A / D conversion is completed. It goes without saying that it is possible.

  As described above, in the photographing system 10, even when the power feeding prohibition control is performed before photographing (step S <b> 7), the power is quickly fed to the battery 44 after the A / D conversion with relatively little influence of noise. Can be started (resumed) (step S9). For this reason, for example, it is particularly effective when the remaining amount of the battery 44 used in shooting is greatly reduced and it is desired to charge the battery quickly before the next shooting. In addition, after imaging | photography and electric power supply by above-mentioned step S1-S12 are complete | finished, when it is due to image | photograph again, etc., it should just return to each procedure, such as step S1, after completion | finish of step S12 (step S10). .

  In such a photographing system 10, it goes without saying that charging of the battery 44 may be appropriately performed under the control of the console 28 other than during photographing.

  In the above description of the operation, the operation of the photographing system 10 when the number of shots is one has been described. However, when there are a plurality of shots, all shooting (step S8) and A / D conversion are completed. Then, a power supply permission signal is issued from the charging control unit 108 (step S9).

  As described above, in the imaging system 10 according to the first embodiment, when the imaging device 22 outputs an imaging start signal that notifies the patient 14 of the start of irradiation of the radiation X, the battery remaining amount of the battery 44 is equal to or greater than the threshold value. When the remaining battery level is equal to or greater than the threshold value, charging of the battery 44 in the electronic cassette 24 from the power supply device 25 is prohibited. Alternatively, when the remaining amount of the battery is less than the threshold, charging of the battery 44 from the power supply device 25 is permitted, and irradiation of the radiation X by the imaging device 22 is prohibited.

  Thereby, when the remaining battery level is equal to or greater than the threshold value, charging to the battery 44 is prohibited. Therefore, even if the patient 14 is irradiated with the radiation X from the imaging device 22, the radiation image of noise caused by the charging As a result, it is possible to prevent re-imaging from occurring and to acquire highly accurate radiation image information.

  Further, when the remaining battery level is less than the threshold value, charging from the power supply device 25 to the battery 44 is permitted, and irradiation of the radiation X by the imaging device 22 is prohibited, resulting in insufficient battery level. The malfunction of the electronic cassette 24 thus performed can be avoided, and re-shooting can be prevented.

  In this case, the imaging control unit 109 generates an imaging permission signal that permits irradiation of the radiation X by the imaging device 22 when the remaining battery level determination unit 107 determines that the remaining battery level is equal to or greater than the threshold value, or When the remaining battery level determination unit 107 determines that the remaining battery level is less than the threshold value, an imaging prohibition signal that prohibits irradiation of the radiation X by the imaging apparatus 22 is generated.

  In addition, when the battery remaining amount determination unit 107 determines that the remaining battery level is equal to or greater than the threshold value and the shooting control unit 109 generates a shooting permission signal, the charging control unit 108 receives the electronic cassette 24 from the power supply device 25. A power supply prohibition signal for prohibiting power supply to the battery, or when the remaining battery level determination unit 107 determines that the remaining battery level is less than the threshold and the imaging control unit 109 generates an imaging prohibition signal, A power supply permission signal for permitting power supply from the power supply device 25 to the electronic cassette 24 is generated.

  Further, the transceiver 48 of the electronic cassette 24 receives the imaging start signal from the console 28, while transmitting the imaging permission signal and the power supply prohibition signal or the imaging prohibition signal and the power supply permission signal to the console 28.

  Accordingly, the electronic cassette 24 can reliably notify the console 28 of information on prohibition of charging the battery 44 and permission of photographing of the photographing device 22, and permission of charging of the battery 44 and photographing prohibition of the photographing device 22. The imaging device 22, the power feeding device 25, and the display device 26 can be notified via the console 28. As a result, it is possible to surely prevent the noise from being mixed into the radiographic image information and the occurrence of re-imaging, and to reliably avoid the malfunction of the electronic cassette 24 and the occurrence of re-imaging due to insufficient battery power. be able to.

  As described in steps S3 to S5, in the imaging system 10 according to the first embodiment, when the remaining battery level is not sufficient, the electronic cassette 24 notifies the console 28 of imaging prohibition and power supply permission. Instead of this, a request for charging the battery 44 may be notified by appropriately transmitting a power supply permission signal from the electronic cassette 24 to the console 28 regardless of whether or not the remaining battery level is sufficient.

  In the above description, when the remaining battery level is insufficient, the electronic cassette 24 notifies the console 28 of photographing prohibition and power supply permission. Instead, the electronic cassette 24 notifies the console 28 only of the photographing prohibition signal. You may send it. As a result, the console 28 or the like can determine that the battery 44 can be charged when receiving the photographing prohibition signal.

  Furthermore, since the power feeding device 25 feeds power to the battery 44 of the electronic cassette 24 wirelessly (contactlessly), even when the electronic cassette 24 is installed at a desired imaging position with respect to the patient 14, the power feeding device 25. Thus, power supply to the electronic cassette 24 can be easily performed. For this reason, even when it is necessary to charge the battery 44 of the electronic cassette 24 during the operation, the electronic cassette 24 can be charged without moving the electronic cassette 24, and the electronic cassette 24 and the imaging system. The handleability of the entire 10 can be improved. Further, it is possible to effectively avoid interruption and extension of imaging and surgery due to a shortage of the battery 44 of the electronic cassette 24.

  In the photographing system 10 (electronic cassette 24), when a photographing permission signal is issued, a power feeding prohibition signal is issued, and when A / D conversion ends, a power feeding permission signal is issued. Therefore, at least in the time period from the start of imaging until the conversion of the radiographic image information detected by the radiation detector 40 into a digital signal is completed, wireless power feeding is prohibited, so analogs that are particularly susceptible to noise. It is possible to prevent the noise caused by the wireless power transmission from the power supply device 25 from affecting the radiation image information in the signal, and to acquire a high quality radiation image.

  Further, after the end of A / D conversion, which is relatively less susceptible to the influence of noise, power supply can be started (restarted) quickly by the generation of a power supply permission signal from the charge control unit 108. Even if the remaining amount of 44 is greatly reduced, the battery can be charged quickly after the shooting is completed to prepare for the next shooting.

  In the imaging system 10, when the electronic cassette 24 is arranged in the power supplyable area of the corresponding power supply device 25, information is automatically transmitted and received between the electronic cassette 24 and the power supply device 25 via the console 28. The electronic cassette 24 is driven and controlled so that it can be photographed. Therefore, it is possible to omit providing a manual power switch or the like in the electronic cassette 24, and it is possible to prevent a shooting mistake caused by forgetting to operate the operation switch. For this reason, the handleability of the electronic cassette 24 and the imaging system 10 can be further improved. In this case, when the desired magnetic field M is not detected by the energy detection unit 96 of the electronic cassette 24, for example, a wireless power supply impossible signal is transmitted from the data management unit 106 to the cassette information management unit 126, and further, the wireless power supply is performed. By transmitting the disabled signal to the display device 26, the display unit 114 can notify the doctor or the like to that effect.

  FIG. 7 is an explanatory block diagram of the radiographic image capturing system 10a according to the second embodiment of the present invention.

  The imaging system 10a according to the present embodiment is basically the same as the imaging system 10 according to the first embodiment (see FIGS. 4 and 5) except that the RIS 29 and the HIS 33 are not connected to the console 28. It is suitably used for a system to which the RIS 29 and the HIS 33 are not connected, for example, a hospital that does not have the RIS 29 or the like, an imaging system for round trips, and the like.

  In this photographing system 10a, the same components as those in the photographing system 10 according to the first embodiment are denoted by the same reference numerals, detailed description thereof is omitted, and the same applies hereinafter.

  Also in this photographing system 10a, since the electronic cassette 24 includes the operation management unit 102, the same effect as that of the photographing system 10 according to the first embodiment can be obtained.

  FIG. 8 is a block explanatory diagram of a radiographic image capturing system 10b according to a first modification of the radiographic image capturing system 10 shown in FIG.

  The imaging system 10b is different from the above-described imaging systems 10 and 10a (see FIGS. 4, 5, and 7) in that the battery remaining amount determination unit 107a, the charging control unit 108a, and the imaging control unit 109a are provided on the console 28. Different.

  In the photographing system 10b, the remaining battery level determination unit 107a performs a determination process on the remaining battery level, for example, when the remaining battery level is transmitted from the electronic cassette 24 to the console 28, and the determination result is displayed on the charging control unit 108a. By notifying the shooting control unit 109a, an operation based on the shooting procedure shown in FIG. 6 and the like is performed. Note that the battery remaining amount determination unit 107, the charging control unit 108, and the imaging control unit 109 provided in the electronic cassette 24 may be set so as not to use the functions under the control of the console 28. Of course, in the photographing system 10b, a simple electronic cassette in which the battery remaining amount determining unit 107, the charging control unit 108, and the photographing control unit 109 are omitted can be used.

  Further, as shown in FIG. 8, in the photographing system 10b, in addition to or instead of the battery remaining amount determining unit 107a, the charging control unit 108a, and the photographing control unit 109a, the battery remaining amount determining unit 107b, charging The control unit 108b and the imaging control unit 109b may be provided, and the battery remaining amount determination unit 107c, the charging control unit 108c, and the imaging control unit 109c may be provided in the power feeding device 25. That is, if the battery remaining amount determination unit, the charging control unit, and the imaging control unit are provided in at least one of the console 28, the imaging device 22, the power feeding device 25, and the electronic cassette 24, the same as the imaging systems 10 and 10a. Naturally, a dedicated console or the like may be installed separately. When a plurality of devices are provided with a remaining battery level determination unit, a charging control unit, and a photographing control unit, for example, a remaining battery level determination unit and a charging control unit mounted on an arbitrary device under the control of the console 28 The photographing control unit is set to be selectively used, and the functions of the remaining battery level determination unit, the charging control unit, and the photographing control unit of other devices are not used.

  Since the electronic cassette 24 includes the remaining battery level determination unit 107, the charging control unit 108, and the imaging control unit 109 as described above, for example, the console 28 can be used for an existing radiographic imaging system. There is an advantage that a control function such as the above-described determination process can be easily added only by slightly changing the control program or the like.

  In the radiographic imaging systems 10, 10 a, and 10 b described above, the radiographic image used during the operation is displayed on the display device 26. However, the present invention is also applicable to the case where only normal radiographic imaging is performed except during the operation. It goes without saying that it is possible. Similarly, the electronic cassette 24 is not limited to being used in the operating room 12 and can be applied to, for example, a medical examination or a round in a hospital.

  The power supply device 25 only needs to be able to supply power to the electronic cassette 24 wirelessly (contactlessly). For example, instead of the LC resonators 84 and 88 and the detection LC resonator 94, each of them is a dielectric. And an electric field may be used instead of the magnetic field M, and a device other than the so-called resonance-type wireless power feeding device as described above may be used. That is, as the supply energy obtained by converting the electric energy supplied from the power supply device 25 to the electronic cassette 24, for example, light energy, heat energy, or the like can be applied.

  Furthermore, in the radiographic imaging systems 10, 10 a, and 10 b, for example, the radiation detector 40 accommodated in the electronic cassette 24 is a direct conversion type that converts the dose of incident radiation X directly into an electrical signal by the photoelectric conversion layer 51. Although it is a 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 an electrical signal using a solid detection element such as amorphous silicon (a-Si). An indirect conversion type radiation detector configured as described above may be used (see Japanese Patent No. 3494683).

  Furthermore, radiation image information can also be acquired 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 (see Japanese Patent Laid-Open No. 2000-105297). .

  Further, for example, transmission / reception of signals among the photographing device 22, the power feeding device 25, the display device 26, the console 28, and the like can be performed by wired communication. The wireless communication between the electronic cassette 24 and the external device may be performed by optical wireless communication using infrared rays or the like instead of normal communication using radio waves.

  FIG. 9 is a configuration diagram of an electronic cassette 500 according to a modification of the electronic cassette 24. In the electronic cassette 500, a guide line 504 serving as a reference for an imaging region and an imaging position is formed on the radiation irradiation surface side of the casing 502. By using the guide line 504 to position the subject (patient 14) with respect to the electronic cassette 500 and setting the radiation X irradiation range, the radiographic image information can be recorded in an appropriate imaging region.

  A display unit 506 that displays various types of information related to the electronic cassette 500 is disposed outside the imaging area of the electronic cassette 500. In the display unit 506, the ID information of the patient 14 recorded in the electronic cassette 500, the number of uses of the electronic cassette 500, the cumulative exposure dose, the state of charge (remaining capacity) of the battery 44 built in the electronic cassette 500, The imaging conditions of the radiation image information, the positioning image of the patient 14 with respect to the electronic cassette 500, 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 506, confirms in advance that the electronic cassette 500 is in a usable state, and displays the displayed positioning image. Based on this, it is possible to position the desired imaging region of the patient 14 on the electronic cassette 500 and to perform imaging of optimal radiation image information.

  Further, by forming the handle portion 508 in the electronic cassette 500, the electronic cassette 500 can be easily handled and carried.

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

  The input terminal 510 is connected to the AC adapter from the outside when the charging function of the battery 44 built in the electronic cassette 500 is deteriorated or when sufficient time for charging the battery 44 cannot be secured. By supplying power, the electronic cassette 500 can be immediately used.

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

  As shown in FIG. 10, it is preferable to place a cradle 518 that is loaded with an electronic cassette 24 and charges a built-in battery 44 at a required location in the operating room 12 or hospital. In this case, the cradle 518 uses the wireless communication function or the wired communication function of the cradle 518 as well as charging the battery 44 by a non-contact power supply device (not shown) similar to the power supply device 25 described above, and uses the RIS 29, the HIS 33, the console. Necessary information may be exchanged with an external device such as 28. The information to be transmitted / received can include radiation image information recorded in the electronic cassette 24 loaded in the cradle 518.

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

  Further, a plurality of cradle 518 is connected to the network, and the charging state of the electronic cassette 24 loaded in each cradle 518 is collected via the network so that the location of the electronic cassette 24 in the usable charging state can be confirmed. It can also be configured.

  FIG. 11 is an explanatory diagram of a radiographic image capturing system 10c according to a second modification of the radiographic image capturing system 10 shown in FIG.

  In the imaging system 10 and the like described above, the configuration in which the electronic cassette 24 is used as a radiation detection apparatus that detects the irradiated radiation X and acquires radiation image information has been described. On the other hand, in the imaging system 10c, a configuration in which the supine imaging is performed using the radiation detection device 152 built in the imaging table 150, which is a bed on which the patient 14 lies, instead of the electronic cassette 24 will be described.

  In the imaging system 10c, the radiation detection device 152 has substantially the same configuration and structure as the electronic cassette 24 described above, and includes a radiation detector 40, a battery 44, a wireless power receiving unit 49, a control unit 46a, a transceiver 48, and the like. Each device is housed in a box-shaped casing 154 made of a material that transmits radiation X. The control unit 46a functions in substantially the same manner as the cassette control unit 46 constituting the electronic cassette 24, and includes a battery remaining amount determination unit 107, a charge control unit 108, a photographing control unit 109, and the like.

  Further, a rail (not shown) is provided on the lower surface of the imaging table 150 along the longitudinal direction, and the radiation detection device 152 is moved along the rail by a slider mechanism (not shown) provided in the casing 154. And can be moved to a desired position in the arrow X direction (horizontal direction). Therefore, the radiation detection device 152 can be easily moved to a desired imaging region of the patient 14 lying on the imaging table 150.

  As described above, in the imaging system 10c, while the radiation detection device 152 can be moved, the radiation detection device 152 incorporates the battery 44 and the wireless power receiving unit 49 in substantially the same manner as the electronic cassette 24 described above. A power cable or the like to the detection device 152 is not necessary. Therefore, the radiation detection device 152 can be smoothly moved without being affected by the cables, and the handleability can be improved. Similarly to the imaging system 10 and the like, wireless power feeding from the power supply device 25 to the battery 44 and imaging by the imaging device 22 can be appropriately controlled, and high-quality radiation images can be acquired.

  As shown in FIG. 11, the imaging system 10 c may have a configuration in which wheels 158 are provided on the legs of the imaging table 150. In this case, the imaging table 150 itself can be easily moved to a desired position in the room, and the rail can be eliminated if necessary, and the radiation detection device 152 can be fixed to the imaging table 150.

  FIG. 12 is an explanatory diagram of a radiographic image capturing system 10d according to a third modification of the radiographic image capturing system 10 shown in FIG.

  The imaging system 10d does not use the electronic cassette 24 in the same manner as the imaging system 10c described above, but stands by using a radiation detection device 164 that is detachable from a column 162 that is fixed to a floor surface and a wall surface 160 (not shown). This is a system for shooting.

  The radiation detection device 164 has substantially the same configuration and structure as the electronic cassette 24 and the radiation detection device 152 described above, and includes a radiation detector 40, a battery 44, a wireless power reception unit 49, a control unit 46a, a transceiver 48, and the like. Each of these devices is housed in a box-shaped casing 154 made of a material that transmits the radiation X.

  In this case, a pair of hook members 166 and 168 spaced apart in the vertical direction are provided on the back surface of the radiation detection apparatus 164 functioning as a standing imaging stand. On the other hand, a mounting recess 170 is formed on the side surface of the support column 162 facing the radiation detection device 164. The mounting recess 170 extends in the horizontal direction (the shoulder width direction of the patient 14) and corresponds to the hook members 166 and 168. A pair of shafts 172 and 174 spaced apart in the vertical direction are fixed. Further, the lower hook member 168 can swing upward with a support shaft 176 as a fulcrum by a spring mechanism (not shown) (see a two-dot chain line in FIG. 12).

  Therefore, the hook members 166 and 168 can be easily and reliably attached to and detached from the shafts 172 and 174 by using the swinging motion of the hook member 168, that is, the radiation detection device 164 can be easily attached to the column 162. And can be securely attached and detached. Further, the radiation detection device 164 is movable in the arrow Y direction (vertical direction) by a slide mechanism (not shown) while being attached to the support column 162.

  Note that reference numeral 178 in FIG. 12 is a frame fixed in both width directions of the casing 154, and the imaging posture when the patient 14 takes a desired imaging posture with respect to the radiation detection device 164 which is an imaging table. It is a bar member grasped in order to maintain.

  As described above, in the imaging system 10d, the radiation detection device 164 is detachable and movable with respect to the support column 162, while the radiation detection device 164 includes the battery 44 in substantially the same manner as the electronic cassette 24 and the radiation detection device 152 described above. In addition, since the wireless power receiving unit 49 is built in, a power cable or the like is unnecessary. Therefore, the radiation detection apparatus 164 can be easily moved and detached without being affected by the cables. Similarly to the imaging system 10 and the like, wireless power feeding from the power supply device 25 to the battery 44 and imaging by the imaging device 22 can be appropriately controlled, and high-quality radiation images can be acquired.

  As described above, in the imaging systems 10, 10 a to 10 d according to the present embodiment, the electronic cassette 24 and the radiation detection devices 152 and 164 that are radiation detection devices can be moved, but these are set to desired imaging positions. Even in this case, the power supply device 25 can easily supply power to the electronic cassette 24. In addition, since the battery remaining amount determination unit, the charging control unit, and the imaging control unit are provided, wireless power feeding is not performed until at least the A / D conversion of the detected radiation image information is completed. For this reason, it is possible to capture and acquire a high-quality image while avoiding the influence of noise caused by the wireless power transmission, and it is possible to perform quick charging during non-shooting (end of shooting).

  Note that the present invention is not limited to the above-described embodiments, 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 the 1st Embodiment of this invention was installed. It is a partially cutaway perspective explanatory view of the electronic cassette shown in FIG. It is a circuit block diagram of the radiation detector of FIG. It is block explanatory drawing of the radiographic imaging system shown in FIG. FIG. 5 is a block explanatory diagram showing more specifically the configuration of the electronic cassette shown in FIG. 4. It is a flowchart which shows an example of the imaging | photography procedure of the radiographic imaging system shown in FIG. It is a block explanatory view of the radiographic imaging system concerning a 2nd embodiment of the present invention. It is block explanatory drawing of the radiographic imaging system which concerns on the 1st modification of the radiographic imaging system shown in FIG. It is another block diagram of an electronic cassette. It is a block diagram of the cradle which charges an electronic cassette. It is explanatory drawing of the radiographic imaging system which concerns on the 2nd modification of the radiographic imaging system shown in FIG. It is explanatory drawing of the radiographic imaging system which concerns on the 3rd modification of the radiographic imaging system shown in FIG.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10, 10a-10d ... Radiation imaging system 22 ... Imaging device 24, 500 ... Electronic cassette 25 ... Power feeding device 26 ... Display device 28 ... Console 40 ... Radiation detector 44 ... Battery 46 ... Cassette control part 46a ... Control part 49 ... Wireless power receiving unit 70 ... A / D converter 72 ... Imaging switches 107, 107a to 107c ... Battery remaining amount determining units 108, 108a to 108c ... Charging control units 109, 109a to 109c ... Imaging control units 152, 164 ... Radiation detection devices

Claims (13)

A radiation detector that detects radiation transmitted from an external imaging device and transmitted through the subject and converts the radiation into radiation image information; and
A battery for driving the radiation detector;
A battery remaining capacity determining unit that determines whether or not the battery remaining capacity of the battery is equal to or greater than a predetermined threshold;
An imaging control unit that controls irradiation of the radiation by the imaging device;
A charge control unit for controlling charging of the battery from an external charging device;
Have
The battery remaining amount determination unit determines whether or not the battery remaining amount is equal to or greater than the threshold when the imaging apparatus outputs an imaging request signal for notifying the irradiation start of the radiation to the subject;
The imaging control unit prohibits the irradiation of the radiation by the imaging device when the battery remaining amount determination unit determines that the battery remaining amount is less than the threshold value ,
The charge control unit prohibits charging from the charging device to the battery when the battery remaining amount determining unit determines that the remaining battery amount is equal to or greater than the threshold value, or the remaining battery amount is When the battery remaining amount determination unit determines that it is less than the threshold, charging from the charging device to the battery is permitted . The apparatus of claim 1.
A transmission / reception means for transmitting / receiving signals to / from the outside;
The imaging control unit generates an imaging permission signal that permits irradiation of the radiation by the imaging device when the battery remaining amount determination unit determines that the remaining battery level is equal to or greater than the threshold, or When the remaining battery level determination unit determines that the remaining battery level is less than the threshold value, an imaging prohibition signal for prohibiting the radiation irradiation by the imaging apparatus is generated,
The radiation detection apparatus, wherein the transmission / reception means transmits the imaging permission signal or the imaging prohibition signal to the outside. The apparatus of claim 2.
The radiation detecting apparatus according to claim 1, wherein the transmitting / receiving means is a wireless transmitter / receiver that transmits / receives a signal to / from the outside by wireless communication. The apparatus according to claim 2 or 3 ,
The charging device is a wireless power feeding device,
The radiation detection apparatus further includes a wireless power reception unit that receives electric power supplied wirelessly from the wireless power supply apparatus and supplies the electric power to the battery. The device according to any one of claims 2 to 4 ,
An A / D converter for A / D converting the radiation image information;
In addition, the charging control unit is configured to start from the charging device when irradiation of the radiation from the imaging device based on the imaging permission signal is stopped and A / D conversion by the A / D converter is completed. A radiation detection apparatus that permits charging of the battery. An imaging device for irradiating a subject with radiation;
A radiation detector comprising: a radiation detector that detects the radiation transmitted through the subject and converts it into radiation image information; and a battery that drives the radiation detector;
A control device for controlling the imaging device and the radiation detection device;
A battery remaining capacity determining unit that determines whether or not the battery remaining capacity of the battery is equal to or greater than a predetermined threshold;
An imaging control unit that controls irradiation of the radiation by the imaging device;
A charging device capable of charging the battery;
A charge control unit for controlling charging of the battery from the charging device;
Have
The battery remaining amount determination unit determines whether or not the battery remaining amount is equal to or greater than the threshold when the imaging apparatus outputs an imaging request signal for notifying the irradiation start of the radiation to the subject;
The imaging control unit prohibits the irradiation of the radiation by the imaging device when the battery remaining amount determination unit determines that the battery remaining amount is less than the threshold value ,
The charge control unit prohibits charging from the charging device to the battery when the battery remaining amount determining unit determines that the remaining battery amount is equal to or greater than the threshold value, or the remaining battery amount is A radiographic imaging system characterized by permitting charging of the battery from the charging device when the battery remaining amount determining unit determines that the battery is less than the threshold . The system of claim 6 , wherein
The imaging control unit generates an imaging permission signal that permits irradiation of the radiation by the imaging device when the battery remaining amount determination unit determines that the remaining battery level is equal to or greater than the threshold, or A radiographic imaging system that generates an imaging prohibition signal that prohibits the imaging apparatus from irradiating the radiation when the remaining battery level determination unit determines that the remaining battery level is less than the threshold. The system of claim 7 , wherein
The radiographic imaging system, wherein the battery remaining amount determination unit, the charging control unit, and the imaging control unit are provided in the radiation detection device, the control device, the imaging device, and / or the charging device. . The system of claim 8 , wherein
The radiation request signal is received by the radiation detection device, the control device, the imaging device, and / or the charging device provided with the battery remaining amount determination unit, the charging control unit, and the imaging control unit, On the other hand, a radiographic imaging system, further comprising transmission / reception means for transmitting the imaging permission signal or the imaging prohibition signal to the outside. The system of claim 9 , wherein
The radiographic imaging system according to claim 1, wherein the transmission / reception means is a wireless transmitter / receiver that transmits / receives a signal to / from the outside by wireless communication. The system according to any one of claims 7 to 10 , wherein
The charging device is a wireless power feeding device,
The radiation detection system further includes a wireless power receiving unit that receives power supplied from the wireless power supply device wirelessly and supplies the power to the battery. The system according to any one of claims 7 to 11 ,
The radiation detection apparatus further includes an A / D converter for A / D converting the radiation image information,
In addition, the charging control unit is configured to start from the charging device when irradiation of the radiation from the imaging device based on the imaging permission signal is stopped and A / D conversion by the A / D converter is completed. A radiographic imaging system that permits charging of the battery. A radiation image capturing method for irradiating a subject with radiation from an imaging device, detecting the radiation with a radiation detector mounted on the radiation detection device, and converting the radiation into radiation image information,
When the imaging apparatus outputs an imaging request signal for notifying the start of irradiation of the radiation to the subject, it is determined whether or not a remaining battery level of a battery that drives the radiation detector is equal to or greater than a predetermined threshold;
When the remaining battery level is greater than or equal to the threshold value, charging from the charging device to the battery is prohibited, or when the remaining battery level is less than the threshold value, irradiation of the radiation by the imaging device is prohibited. And the radiographic imaging method characterized by permitting the charge to the said battery from the said charging device .

Images