JP2012208337A - Portable radiation image detection device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To resume photographing relatively in a short time when a cable or a connector is damaged.SOLUTION: A type B socket 32 of USB 2.0 or 3.0 specification having a power supply function is provided to a housing 29 of an electronic cassette 21. A type B connector 33 of USB cable 26 is inserted in the type B socket 32. A type A connector 34 of the other end of the USB cable 26 is inserted in a type A socket 35 of photographing control equipment 23. Electric power fed through the USB cable 26 is used for charging of a built-in battery 31 in the electronic cassette 21. Electric power is supplied to each section of the electronic cassette 21 from the battery 31. The order in the breakage takes time in the exclusive cable, but the general-purpose USB cable 26 is available immediately and relatively inexpensive at a nearby electric appliance shop, so the convenience of the user is high.

Description

  The present invention relates to a portable radiographic image detection apparatus that receives radiation and detects a radiographic image.

  A radiation imaging system, for example, an X-ray imaging system includes an X-ray generation apparatus that generates X-rays and an X-ray imaging apparatus that receives an X-ray and captures an X-ray image. The X-ray generator has an X-ray source that irradiates X-rays toward a subject, a radiation source control device that controls driving of the X-ray source, and an irradiation switch for inputting an X-ray irradiation start instruction. ing. The X-ray imaging apparatus has an X-ray image detection apparatus that receives an X-ray transmitted through a subject and detects an X-ray image, and an imaging control apparatus that controls driving of the X-ray image detection apparatus.

  Recently, an X-ray image detection apparatus using a flat panel detector (FPD) as a detector instead of an X-ray film or an imaging plate (IP) has become widespread. In the FPD, pixels that accumulate signal charges corresponding to the amount of incident X-rays are arranged in a matrix. The FPD accumulates signal charge for each pixel, converts the accumulated signal charge into a voltage signal by a signal processing circuit, detects an X-ray image representing the image information of the subject, and uses this as digital image data Output.

  A portable X-ray image detection apparatus (hereinafter referred to as an electronic cassette) in which an FPD is built in a rectangular parallelepiped housing has also been put into practical use. The electronic cassette is used by attaching it to an existing imaging table for film cassettes and IP cassettes or a dedicated imaging table. In addition, the electronic cassette is placed on the bed or held by the subject itself to image areas that are difficult to capture with the stationary type. Used. In addition, in order to take pictures of elderly people who are being treated at home or those who are suddenly ill due to accidents, disasters, etc., they may be taken out of hospitals where there is no equipment for taking pictures.

  The electronic cassette is connected to a cable for exchanging signals with the imaging control device and receiving power (see Patent Documents 1 and 2). Some types have built-in batteries in the electronic cassette to cover the drive power and exchange signals with the imaging control device via wireless communication. Standard equipment.

JP 2010-107202 A JP 2009-237230 A

  As described above, the electronic cassette is used not only by being set on an imaging stand having a fixed layout but also used in various ways. In some cases, the subject may take an image on the electronic cassette. For this reason, when connecting and using a cable to an electronic cassette, there exists a possibility that a cable and the connector of the edge part may be damaged. If a cable or connector is damaged, the imaging must be interrupted until a new one is ordered from the manufacturer, causing serious damage to the hospital and inconvenience to the patient.

  It is possible to use a general-purpose cable that can be obtained relatively easily, such as a USB cable or a cable that conforms to IEEE 1394, instead of a dedicated cable that takes time to order, such as a USB cable or a cable that conforms to IEEE 1394. A general-purpose cable has limited power that can be supplied, and cannot supply power for operating an electronic cassette that requires relatively high power during shooting.

  The present invention has been made in view of the above-described problems, and an object of the present invention is to make it possible to resume photographing in a relatively short time even when a cable or a connector is damaged.

  To achieve the above object, a portable radiographic image detection apparatus of the present invention includes a radiographic image detector having a plurality of pixels that receive radiation irradiated from a radiation source and accumulate signal charges, and the radiographic image detection. A housing for housing the device, a socket provided in the housing, a general-purpose standard cable having a power feeding function connected to the socket and a socket provided in the external control device, and power to each part of the device A battery to be supplied, performs signal communication with an external control device via the cable, and charges the battery with electric power supplied by the cable.

  The cable is a USB standard cable.

  The power supplied by the cable is dedicated to the charging of the battery, and all the power supply to each part of the apparatus is provided by the battery.

  A part of each part of the apparatus may be operated with electric power supplied by the cable. When a sleep mode for supplying power to only a part of each part of the apparatus is provided, the part is operated with power supplied by the cable. A part of each part of the apparatus that is operated by the power supplied by the cable is a part that bears a communication function that mediates signal communication with the external control apparatus.

  The battery is not removable.

  The radiation source, the holder for holding the radiation source, and the external control device are preferably used in a portable radiography system.

  The portable radiological image detection apparatus of the present invention includes a radiographic image detector having a plurality of pixels that receive radiation irradiated from a radiation source and accumulates signal charges, and a housing that houses the radiographic image detector. A general-purpose standard socket provided in the housing and connected to a cable for connecting to an external control device, and a battery for supplying power to each part of the device, and the external control device via the cable In addition, the battery is charged with electric power fed by the cable.

  According to the present invention, since signal communication with the external control device and charging of the built-in battery are performed using a general-purpose cable, it is possible to resume shooting in a relatively short time even when the cable or the connector is damaged. it can.

It is the schematic which shows the structure of a X-ray imaging system. It is a figure which shows the state by which the electronic cassette was set to the imaging stand. It is a perspective view which shows the structure of an electronic cassette. It is a figure which shows the electrical structure of an electronic cassette and FPD. It is the schematic which shows the structure of a portable X-ray imaging system.

  In FIG. 1, the X-ray imaging system 10 includes an X-ray generation device 11 and an X-ray imaging device 12. The X-ray generator 11 includes an X-ray source 13, a radiation source controller 14 that controls driving of the X-ray source 13, and an irradiation switch 15. The X-ray source 13 includes an X-ray tube 13a that emits X-rays, and an irradiation field limiter (collimator) 13b that limits an X-ray irradiation field emitted by the X-ray tube 13a.

  The X-ray tube 13a includes a cathode made of a filament that emits thermoelectrons, and an anode (target) that emits X-rays when the thermoelectrons emitted from the cathode collide. The target has a disk shape, and is a rotating anode in which the focal point moves on a circular orbit by rotation, and the heat generated at the focal point where thermal electrons collide is dispersed. The irradiation field limiter 13b has a plurality of lead plates that shield X-rays arranged in a cross-beam shape, and an irradiation opening that transmits X-rays is formed in the center. By moving the position of the lead plate, The irradiation field is limited by changing the size of the irradiation opening.

  The radiation source control device 14 determines a high voltage generator that supplies a high voltage to the X-ray source 13, a tube voltage that determines the energy spectrum of the X-rays that the X-ray source 13 irradiates, and an irradiation amount per unit time. It consists of a controller that controls the tube current and the X-ray irradiation time. The high voltage generator boosts the input voltage with a transformer to generate a high voltage tube voltage, and supplies driving power to the X-ray source 13 through the high voltage cable 16. The X-ray generation apparatus 11 of this example does not have a communication function with the X-ray imaging apparatus 12, and radiographers can set imaging conditions such as tube voltage, tube current, and irradiation time through the operation panel of the radiation source control apparatus 14. Set manually.

  The irradiation switch 15 is operated by a radiologist and is connected to the radiation source control device 14 by a signal cable 17. The irradiation switch 15 is a two-stage push switch, which generates a warm-up start signal for starting the warm-up of the X-ray source 13 by pressing the single stage, and for starting the irradiation of the X-ray source 13 by pressing the two-stage. The irradiation start signal is generated. These signals are input to the radiation source controller 14 through the signal cable 17.

  The radiation source control device 14 controls the operation of the X-ray source 13 based on a control signal from the irradiation switch 15. When the warm-up start signal is received, the radiation source control device 14 activates the heater to preheat the filament, and also starts the rotation of the target to reach the target rotational speed. The time required for warm-up is about 200 msec to 1500 msec. The radiologist inputs a warm-up start instruction by pressing the irradiation switch 15 in one stage, and then inputs the irradiation start instruction by pressing in two stages after a necessary interval for warm-up.

  When receiving the irradiation start signal, the radiation source control device 14 starts supplying power to the X-ray source 13 and activates a timer to start measuring the X-ray irradiation time. Then, when the irradiation time set in the imaging conditions has elapsed, X-ray irradiation is stopped. Although the X-ray irradiation time varies depending on the imaging conditions, in the case of still image shooting, the maximum X-ray irradiation time is often set to a range of about 500 msec to about 2 s, and the irradiation time Is set with this maximum irradiation time as the upper limit.

  The X-ray imaging apparatus 12 includes an electronic cassette 21, an imaging table 22, an imaging control apparatus 23, and a console 24. The electronic cassette 21 includes an irradiation detection sensor 25, an FPD 54 (see FIGS. 3 and 4), and a portable housing 29 (see FIG. 3) that houses the FPD 54, and is irradiated from the X-ray source 13 and covered. Receiving X-rays transmitted through the specimen H, an X-ray image is output. The electronic cassette 21 has a substantially rectangular shape and a flat shape, and the plane size is substantially the same size as the film cassette and the IP cassette.

  The irradiation detection sensor 25 is disposed in the vicinity of the imaging region 56 (see FIG. 4) of the FPD 54. The irradiation detection sensor 25 receives the X-ray irradiation and outputs an irradiation detection signal corresponding to the incident amount of the X-ray. The irradiation detection signal is input to the imaging control device 23 via the USB cable 26. The imaging control device 23 monitors the signal level of the irradiation detection signal and detects that X-ray irradiation by the X-ray source 13 has started.

  As shown in FIG. 2, the imaging table 22 includes a holder 27 to which the electronic cassette 21 can be detachably attached, and the electronic cassette 21 is placed in a posture in which an incident surface on which X-rays are incident faces the X-ray source 13. Hold. Since the size of the housing 29 is substantially the same as that of the film cassette or the IP cassette, the electronic cassette 21 can be attached to an existing photographing stand for the film cassette or the IP cassette. In addition, although the standing position imaging stand which image | photographs the subject H with a standing posture is illustrated as the imaging stand 22, the supine position imaging stand which image | photographs the subject H with a standing posture may be sufficient. Further, the electronic cassette 21 may be placed on a bed on which the subject H lies, or the subject itself may be used instead of being set on a dedicated imaging stand.

  3 and 4, a battery 31 is incorporated in the electronic cassette 21 so as not to be removed. The battery 31 supplies power for operating each part of the electronic cassette 21. The battery 31 is a relatively small battery that can be accommodated in the thin electronic cassette 21. The battery 31 can be charged by USB power feeding.

  The electronic cassette 21 is provided with a B-type socket 32 of USB (Universal Serial Bus) standard having a power feeding function, for example, USB 2.0 or USB 3.0 standard. The B-type socket 32 is arranged close to one side of one side surface of the electronic cassette 21 opposite to the battery 31. A B-type socket 32 is provided for wired connection with the imaging control device 23. The B-type socket 32 has a B-type USB cable 26 of USB 2.0 or 3.0 standard (see also FIGS. 1 and 2). The connector 33 is inserted. An A-type connector 34 is provided at the other end of the USB cable 26, and the A-type connector 34 is inserted into an A-type socket 35 provided in the photographing control device 23.

  When the B-type connector 33 is inserted into the B-type socket 32 and the A-type connector 34 is inserted into the A-type socket 35 and the USB cable 26 is used, wired communication with the imaging control device 23 becomes possible, and the imaging control device 23 sends an electronic signal. It is possible to supply power to the cassette 21 (5V, 500 mA for USB 2.0, 5 V, 900 mA for 3.0). All the power supplied via the USB cable 26 is always used for charging the battery 31. All the electric power for operating each part of the electronic cassette 21 is provided by the battery 31.

  A B-type socket 32 is connected to the communication unit 51. The communication unit 51 mediates transmission / reception of various information and signals including image data between the B-type socket 32, the control circuit 52, and the memory 53.

  The FPD 54 has a TFT active matrix substrate, and an imaging region 56 in which a plurality of pixels 55 for accumulating signal charges corresponding to the amount of incident X-rays is arranged on the substrate, and the signal charges by driving the pixels 55. And a signal processing circuit 58 that converts the signal charge read from the pixel 55 into digital data and outputs the digital data. The operation of the gate driver 57 and the signal processing circuit 58 is controlled by the control circuit 52. The plurality of pixels 55 are two-dimensionally arranged in a matrix of n rows (x direction) × m columns (y direction) at a predetermined pitch.

  The FPD 54 has a scintillator (phosphor) that converts X-rays into visible light, and is an indirect conversion type in which visible light converted by the scintillator is photoelectrically converted by the pixels 55. The scintillator is disposed so as to face the entire surface of the imaging region 56 in which the pixels 55 are arranged. Note that a direct conversion type FPD using a conversion layer (such as amorphous selenium) that directly converts X-rays into electric charges may be used.

  The pixel 55 includes a photodiode 59 that is a photoelectric conversion element that generates charges (electron-hole pairs) upon incidence of visible light, a capacitor (not shown) that accumulates charges generated by the photodiode 59, and a switching element. A thin film transistor (TFT) 60 is provided.

  The photodiode 59 has a structure in which a semiconductor layer (for example, PIN type) that generates electric charges and an upper electrode and a lower electrode are arranged above and below the semiconductor layer. In the photodiode 59, the TFT 60 is connected to the lower electrode, and the bias line 61 is connected to the upper electrode. The bias line 61 is provided by the number of rows (n rows) of the pixels 55 in the imaging region 56 and connected. 62 is bound. The connection 62 is connected to the bias power source 63. A bias voltage Vb is applied from the bias power source 63 to the upper electrode of the photodiode 59 through the connection 62 and the bias line 61. An electric field is generated in the semiconductor layer by application of the bias voltage Vb, and charges (electron-hole pairs) generated in the semiconductor layer by photoelectric conversion are applied to the upper and lower electrodes, one having a positive polarity and the other having a negative polarity. The electric charge is accumulated in the capacitor.

  The TFT 60 has a gate electrode connected to the scanning line 64, a source electrode connected to the signal line 65, and a drain electrode connected to the photodiode 59. The scanning lines 64 and the signal lines 65 are arranged in a grid pattern. The scanning lines 64 are the number of rows of the pixels 55 in the imaging region 56 (n rows), and the signal lines 65 are the number of columns of the pixels 55 (m columns). Min) each is provided. The scanning line 64 is connected to the gate driver 57, and the signal line 65 is connected to the signal processing circuit 58.

  The gate driver 57 drives the TFT 60 to accumulate a signal charge corresponding to the amount of incident X-rays in the pixel 55, a read (main reading) operation for reading the signal charge from the pixel 55, and a reset (empty reading). ) Make an action. The control circuit 52 controls the start timing of each operation performed by the gate driver 57.

  In the accumulation operation, the TFT 60 is turned off, and signal charges are accumulated in the pixel 55 during that time. In the read operation, gate pulses G1 to Gn for simultaneously driving the TFTs 60 in the same row are generated sequentially from the gate driver 57, the scanning lines 64 are sequentially activated one by one, and the TFTs 60 connected to the scanning lines 64 are one row at a time. Turn on. The charge accumulated in the capacitor of the pixel 55 is read out to the signal line 65 and input to the signal processing circuit 58 when the TFT 60 is turned on.

  Dark charges are generated in the semiconductor layer of the photodiode 59 regardless of whether X-rays are incident. This dark charge is accumulated in the capacitor because the bias voltage Vb is applied. Since the dark charge generated in the pixel 55 becomes a noise component for the image data, a reset operation is performed to remove this. The reset operation is an operation of sweeping out dark charges generated in the pixels 55 through the signal line 65.

  For example, the reset operation is performed by a sequential reset method in which the pixels 55 are reset row by row. In the sequential reset method, similarly to the signal charge reading operation, gate pulses G1 to Gn are sequentially generated from the gate driver 57 to the scanning line 64, and the TFTs 60 of the pixels 55 are turned on line by line. While the TFT 60 is in the ON state, dark charge flows from the pixel 55 to the integrating amplifier 66 through the signal line 65. In the reset operation, unlike the read operation, the charge accumulated in the integrating amplifier 66 by the multiplexer (MUX) 67 is not read, and the reset pulse RST is generated from the control circuit 52 in synchronization with the generation of the gate pulses G1 to Gn. Is output, and the integrating amplifier 66 is reset.

  Instead of the sequential reset method, multiple rows of array pixels are grouped as a group, and the reset is performed sequentially within the group, and the dark charge of the number of rows in the group is simultaneously discharged. An all-pixel reset method that simultaneously sweeps out the dark charges may be used. The reset operation can be speeded up by a parallel reset method or an all-pixel reset method.

  The signal processing circuit 58 includes an integration amplifier 66, a MUX 67, an A / D converter 68, and the like, and is supplied with driving power from a power source 69. The integrating amplifier 66 is individually connected to each signal line 65. The integrating amplifier 66 includes an operational amplifier and a capacitor connected between the input and output terminals of the operational amplifier, and the signal line 65 is connected to one input terminal of the operational amplifier. The other input terminal of the integrating amplifier 66 is connected to the ground (GND). The integrating amplifier 66 integrates charges input from the signal line 65, converts them into voltage signals D1 to Dm, and outputs them. The MUX 67 is connected to the output terminal of the integration amplifier 66 in each column via an amplifier 70 and a sample hold (S / H) unit 71. An A / D converter 68 is connected to the output side of the MUX 67.

  The MUX 67 selects one integration amplifier 66 in order from a plurality of integration amplifiers 66 connected in parallel, and serially inputs voltage signals D1 to Dm output from the selected integration amplifier 66 to the A / D converter 68. . The A / D converter 68 converts the input voltage signals D1 to Dm into digital data and outputs the digital data to the memory 53 built in the housing 29 of the electronic cassette 21. An amplifier may be connected between the MUX 67 and the A / D converter 68.

  When the voltage signal D1 to Dm for one row is read from the integrating amplifier 66 by the MUX 67, the control circuit 52 outputs a reset pulse RST to the integrating amplifier 66 and turns on the reset switch 66a of the integrating amplifier 66. As a result, the signal charge for one row accumulated in the integrating amplifier 66 is reset. When the integration amplifier 66 is reset, the gate pulse of the next row is output from the gate driver 57, and reading of the signal charge of the pixel 55 of the next row is started. These operations are sequentially repeated to read the signal charges of the pixels 55 in all rows.

  When the reading of all rows is completed, image data representing an X-ray image for one screen is recorded in the memory 53. This image data is read from the memory 53 and output to the imaging control device 23 through the communication unit 51. Thus, an X-ray image of the subject H is detected.

  In the FPD 54, the irradiation detection sensor 25 detects the start of X-ray irradiation while repeatedly performing the reset operation. When the irradiation detection sensor 25 detects the start of X-ray irradiation, the control circuit 52 shifts the operation of the FPD 54 from the reset operation to the accumulation operation. The control circuit 52 counts the elapsed time from the start of the accumulation operation with a timer. When the elapsed time reaches the time set in the shooting conditions, the FPD 54 is shifted from the accumulation operation to the read operation.

  The imaging control device 23 is communicably connected to the electronic cassette 21 by a wired method using a USB cable 26, and controls the electronic cassette 21. Specifically, the imaging conditions are transmitted to the electronic cassette 21 to set the signal processing conditions (such as the gain of the amplifier 70) of the FPD 54, and each operation of the FPD 54 is indirectly controlled. The image data from the electronic cassette 21 is transmitted to the console 24.

  In FIG. 1, the imaging control device 23 communicates with a CPU 23 a that controls the device centrally, a communication unit 23 b that communicates with the console 24 via the communication cable 28, and communicates with the electronic cassette 21 and the USB cable 26. And a memory 23c. The communication unit 23b and the memory 23c are connected to the CPU 23a. The memory 23c stores a control program executed by the CPU 23a.

  The console 24 transmits imaging conditions to the imaging control device 23 and performs various image processing such as offset correction and gain correction on the X-ray image data transmitted from the imaging control device 23. In addition to being displayed on the display of the console 24, the processed X-ray image is stored in a data storage device such as a hard disk or memory in the console 24 or an image storage server connected to the console 24 via a network.

  The console 24 receives an input of an examination order including information such as the patient's sex, age, imaging region, and imaging purpose, and displays the examination order on the display. The examination order is input from an external system that manages patient information such as HIS (Hospital Information System) and RIS (Radiation Information System) and examination information related to radiation examination, or is manually input by a radiographer. The radiologist confirms the contents of the examination order on the display, and inputs imaging conditions corresponding to the contents through the operation screen of the console 24.

  Hereinafter, the operation of the above configuration will be described. When imaging with the X-ray imaging system 10, first, the height of the electronic cassette 21 set on the imaging table 22 is adjusted to align the imaging site of the subject H with the position. Further, the height of the X-ray source 13 and the size of the irradiation field are adjusted according to the height of the electronic cassette 21 and the size of the imaging region. Next, the power of the electronic cassette 21 is turned on. Subsequently, shooting conditions are input from the console 24, and shooting conditions are set in the electronic cassette 21 via the shooting control device 23. The imaging conditions are also set in the radiation source control device 14.

  When the above preparation for photographing is completed, the radiation switch 15 is pushed one step by the radiologist. As a result, a warm-up start signal is transmitted to the radiation source control device 14 and the warm-up of the X-ray source 13 is started. After a predetermined time has elapsed, the irradiation switch 15 is pushed in two steps, an irradiation start signal is transmitted to the radiation source control device 14, and X-ray irradiation is started.

  The FPD 54 detects whether or not X-ray irradiation has been started by the irradiation detection sensor 25 while performing a reset operation. When the start of X-ray irradiation is detected, the control circuit 52 turns off all the TFTs 60 and shifts to the accumulation operation. The radiation source control device 14 stops the X-ray irradiation when the irradiation time set in the imaging conditions has elapsed. The FPD 54 also ends the accumulation operation after a predetermined time corresponding to the irradiation time set in the imaging conditions, and shifts to a reading operation. In the read operation, the signal charges accumulated in the pixels 55 are read one by one in order from the first row, and this is recorded in the memory 53 as X-ray image data for one screen. After the read operation, the FPD 54 restarts the reset operation.

  The image data in the memory 53 is transmitted to the photographing control device 23 via the USB cable 26 and further transmitted from the photographing control device 23 to the console 24. The image data is subjected to various image processing such as offset correction and gain correction at the console 24, and then displayed on the display of the console 24 or stored in a data storage device.

  Power is supplied from the battery 31 to each part of the electronic cassette 21. The battery 31 is charged with power supplied by the USB cable 26. Further, signal communication between the electronic cassette 21 and the imaging control device 23 is performed by the USB cable 26. When a dedicated cable is used, if the cable or connector is damaged, it will be time to order the manufacturer and it will take time, and it will not be possible to shoot until a new cable arrives. However, the general-purpose USB cable 26 is available immediately at the nearest electronics store. Can be obtained, and since it is relatively inexpensive, convenience for the user can be improved.

  Since the power supplied by the USB cable 26 is used for charging the battery 31, it is not necessary to prepare a charging terminal or an AC adapter in the electronic cassette 21. In addition, since the power supplied by the USB cable 26 is exclusively used for charging the battery 31, and all the power supply to each part of the electronic cassette 21 is provided by the battery 31, a photographing operation requiring a relatively large power can be performed without any trouble. .

  In the above embodiment, the power supplied by the USB cable 26 is dedicated to charging the battery 31, but the power supplied by the USB cable 26 may be supplied to each part of the electronic cassette 21. However, since the power supplied by the USB cable 26 is relatively small, it is limited to a portion that operates reliably with the power.

  For example, when the electronic cassette 21 is not used, power is supplied only to the communication function (communication unit 51, control circuit 52), and power supply to other units is stopped to operate in a sleep mode that reduces power consumption. The power is supplied by the power supplied by the USB cable 26 instead of the battery 31. Then, when the shooting condition is input from the shooting control device 23, the power supply source is switched from the USB cable 26 to the battery 31 and power is supplied from the battery 31 to other parts other than the communication function to operate the fpd 54 and the like. Then, the mode shifts from the sleep mode to an imaging preparation mode in which an X-ray image can be immediately output. In the shooting preparation mode, the power supplied by the USB cable 26 is used to charge the battery 31 as in the above embodiment. Since the battery 31 is not used in the sleep mode, the power consumption of the battery 31 can be saved.

  In addition to supplying power with the USB cable 26, the housing 31 of the electronic cassette 21 may be set in a cradle having a B-type connector inserted into the B-type socket 32, and the battery 31 may be charged via the cradle. Alternatively, a lid may be provided on the electronic cassette 21 so that the battery 31 can be removed to the outside, and the battery 31 may be charged with a charger. In this way, if the battery 31 other than the power supplied by the USB cable 26 is provided, and the electronic cassette 21 or some of the batteries 31 are prepared, the X-ray imaging is performed several times in succession to obtain the battery 31. Even if the remaining amount of the battery is drastically reduced and cannot be caught by charging with the USB cable 26, it is possible to continue the photographing by exchanging with the fully charged electronic cassette 21 or the battery 31.

  When the remaining amount of the battery 31 is detected and the remaining amount of the battery 31 is equal to or less than a first predetermined value close to the use limit value, the battery 31 is charged with the power supplied by the USB cable 26, and the remaining amount of the battery 31 is When the second predetermined value close to full charge is exceeded, the power supplied by the USB cable 26 may be distributed to power supply to each part of the apparatus.

  In addition to the connection function of the USB cable 26, a connection function of a dedicated cable provided by a manufacturer may be provided. Usually, the battery 31 is not used, but a dedicated cable is used, power is supplied from an external commercial power source and signal communication is performed, and the USB cable 26 may be used for emergency evacuation when the dedicated cable is damaged. In this case, a mechanism for detecting whether a dedicated cable or the USB cable 26 is connected is provided, and whether to use power from the external commercial power source or to use the battery 31 is switched according to the detection result.

  It should be noted that the X-ray imaging system according to the present invention is not limited to the above-described embodiment, and various configurations can be adopted without departing from the gist of the present invention.

  The X-ray imaging system is not limited to the type installed in the imaging room of the hospital, but the type installed in the round-trip car, the functions of the X-ray source 82, the radiation source controller 83, the electronic cassette 84, the imaging controller 23, and the console 24. It can be applied to the portable system 81 shown in FIG. 5 where X-rays can be taken by taking the laptop PC 85, etc., responsible for medical care, to the site where emergency medical treatment is required, such as an accident or disaster, or to the home of a patient receiving home medical care. May be.

  In this case, the A-type connector of the USB cable 86 is inserted into the USB-A socket provided as standard on the notebook computer 85, and the B-type connector of the USB cable 86 is inserted into the B-type socket of the electronic cassette 84, respectively. Connect the PC 85. Reference numeral 87 is an irradiation switch, and reference numeral 88 is a holder for holding the X-ray source 82 suspended.

  In the case of a portable system, when a conventional dedicated cable or connector is damaged, it gets stuck at the destination. In portable systems, there are more opportunities to use an electronic cassette placed on a bed or the subject itself, so there is a higher probability that cables and connectors will be damaged compared to a stationary system. Therefore, by applying power supply and signal communication using a USB cable to a portable system, a more excellent effect can be exhibited.

  Some X-ray sources do not require warm-up, such as a fixed anode type in which the anode does not rotate and a cold cathode type source that does not require preheating. For this reason, the irradiation switch may have only a function of generating an irradiation start signal. Even in the case of an X-ray source that requires warm-up, an irradiation start signal is input from the irradiation switch to the radiation source controller, and the radiation source controller starts warm-up based on the irradiation start signal. If irradiation is started after completion, it is not necessary to provide a function for generating a warm-up start signal in the irradiation switch.

  In the above-described embodiment, the electronic cassette and the imaging control device are described as separate components. Good. In addition, although image processing is performed by the console, it may be performed by a photographing control device. Furthermore, although an electronic cassette having only one wired connection method has been illustrated, an antenna may be provided on the electronic cassette to enable wireless communication with the imaging control apparatus.

  In the above-described embodiment, an example of a USB cable is described as a general-purpose cable. However, other than that, for example, a cable that is compliant with IEEE1394 and used for an audio device may be used. In short, any cable can be used as a general-purpose cable, not limited to a USB cable, as long as it is a cable that can be obtained without effort at a general consumer electronics retailer and has a power supply function.

  The present invention can be applied not only to X-rays but also to imaging systems that use other radiation such as gamma rays.

DESCRIPTION OF SYMBOLS 10, 81 X-ray imaging system 11 X-ray generator 12 X-ray imaging device 21, 84 Electronic cassette 23 Imaging control device 24 Console 26, 86 USB cable 29 Case 31 Battery 32, 33 B type socket, B type connector 34, 35 A-type connector, A-type socket 51 Communication unit 52 Control circuit 54 FPD
55 pixels 58 signal processing circuit 85 notebook computer

Claims (9)

A radiological image detector having a plurality of pixels that receive radiation emitted from a radiation source and accumulate signal charges;
A housing for housing the radiation image detector;
A socket provided in the housing;
A universal standard cable having a power feeding function, connected to the socket and a socket provided in the external control device,
A battery for supplying power to each part of the device,
A portable radiographic image detection apparatus that performs signal communication with an external control device via the cable and charges the battery with electric power fed by the cable.   The portable radiographic image detection apparatus according to claim 1, wherein the cable is a USB standard cable.   The portable radiographic image detection apparatus according to claim 1 or 2, wherein power supplied by the cable is dedicated to charging the battery, and supply of power to each part of the apparatus is all covered by the battery.   The portable radiographic image detection apparatus according to claim 1, wherein a part of each part of the apparatus is operated with electric power supplied by the cable. It has a sleep mode that supplies power to only a part of each part of the device,
The portable radiation image detection apparatus according to claim 4, wherein the part is operated by electric power supplied by the cable.   The part of each part of the apparatus operated by the power supplied by the cable is a part that bears a communication function that mediates signal communication with an external control apparatus. Portable radiological image detection device.   The portable radiographic image detection apparatus according to any one of claims 1 to 6, wherein the battery is not removable.   The portable radiation image detection according to any one of claims 1 to 7, wherein the radiation source is a portable radiation imaging system including a radiation source, a holder for holding the radiation source, and an external control device. apparatus. A radiological image detector having a plurality of pixels that receive radiation emitted from a radiation source and accumulate signal charges;
A housing for housing the radiation image detector;
A general-purpose standard socket that is provided in the housing and to which a cable for connecting to an external control device is connected;
A battery for supplying power to each part of the device,
A portable radiographic image detection apparatus that performs signal communication with an external control device via the cable and charges the battery with electric power fed by the cable.

Images