JP2010075605A - Radiation detector - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a radiation detector having good flexibility. <P>SOLUTION: The radiation detector is structured so as to arrange a radiation detection circuit portion 10 having an array of switching elements of a matrix arrangement which detects radiation having penetrated a subject and converts it to signal electric charge and where pixels are to be formed in a flexible portion 30 and a control circuit portion 62 having a driving circuit driving the switching elements and a signal reading circuit reading the signal electric charge from the pixels in a stiff portion 34. That structure prevents so-called discrete parts from being arranged in the flexible portion 30 brought into contact with the subject 14 and provides good flexibility. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a radiation detection apparatus that detects radiation transmitted through a subject and converts the detected radiation into signal charges having radiation image information.

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

  On the other hand, in an operating room or the like, it is necessary to be able to immediately read out and display radiation image information from a radiation detector after imaging in order to perform a quick and accurate treatment on a patient. Radiation detection using a solid state detector that converts radiation directly into an electrical signal, or converts radiation into visible light with a scintillator, and then converts it into an electrical signal and reads it out A vessel has been developed.

  Patent Document 1 proposes a cassette type radiation detection apparatus using this solid state detection element.

  However, since it is a cassette type, since it is a rigid body as a whole, it cannot be matched with the surface shape of the patient.

  Patent Document 2 proposes a radiation detection apparatus having flexibility that can be matched with the surface shape of a patient.

JP 2003-172783 A JP 2003-70776 A

  However, in the radiation detection apparatus disclosed in Patent Document 2, since the drive circuit is arranged in a direction having flexibility, sufficient flexibility cannot be obtained.

  The present invention has been made in consideration of such a problem, and an object thereof is to provide a radiation detection apparatus capable of obtaining good flexibility.

  The radiation detection apparatus according to the present invention is a radiation detection apparatus divided into a flexible part and a rigid part, wherein a signal line is connected to one signal electrode of the flexible part, and a gate line is connected to the gate electrode. Is connected to the other signal electrode, and a radiation detection circuit unit having an array of switching elements in a matrix arrangement in which each pixel for detecting radiation that has passed through the subject and converting it to signal charge is formed, and the rigid unit A control circuit having a gate driving circuit for driving the switching element through the gate line, and a signal readout circuit for reading out signal charges from the pixels supplied from the driven switching element through the signal line. It has a configuration to be arranged.

  In this case, it is preferable that the flexible portion has a quadrangular shape, and the rigid portion is provided on one side of the square shape or on opposite sides.

  The signal readout circuit includes an A / D converter that converts the signal charge into a digital signal, and the control circuit unit includes the digital signal in addition to the gate drive circuit and the signal readout circuit. An image memory for storing a signal, and at least one of a transmitter / receiver for transmitting a digital signal read from the image memory as a radio signal or a battery for supplying electricity to the entire radiation detection apparatus are disposed. Is preferred.

  According to this invention, the radiation detection circuit unit is arranged in the flexible part, and the gate drive circuit for driving the switching element of the radiation detection circuit unit in the rigid part and the pixel of the radiation detection circuit part are supplied through the switching element. Since the signal readout circuit for reading out the signal charge is arranged, a so-called discrete component is not arranged in the radiation detection circuit unit, that is, the flexible unit, and good flexibility is obtained. Can be arranged along the surface shape of the subject.

  FIG. 1 is a configuration block diagram of a radiographic imaging system 12 to which a wireless radiation detection apparatus 11 according to this embodiment is applied.

  The radiographic imaging system 12 is disposed, for example, in an operating room, and basically includes a radiation source 16 for irradiating a subject 14 such as a patient with a radiation R having a dose according to imaging conditions, and a subject 14. The radiation detection device 11 that detects the transmitted radiation R, the display device 18 that displays radiation image information based on the radiation R detected by the radiation detection device 11, the radiation detection device 11, the radiation source 16, and the display device 18 are controlled. And a console (control device) 20 that performs the operation.

  Signals are transmitted and received by radio communication between the console 20 and the radiation detection device 11, the radiation source 16, and the display device 18.

  The console 20 is connected to a radiology information system (RIS) 22 that centrally manages radiographic image information and other information handled in the radiology department in the hospital via an in-hospital communication network. A medical information system (HIS) 24 that comprehensively manages medical information in the hospital is connected via the in-hospital communication network.

  The radiation detection apparatus 11 is interposed between a mattress 28 disposed on a bed 26, for example, an operating table, and the subject 14. Since the radiation detection apparatus 11 has flexibility in the length direction y, the radiation detection apparatus 11 is curved along the surface shape of the subject 14 by the weight of the subject 14 on the mattress 28. Thus, since the radiation detection apparatus 11 has flexibility, it is suitable for bed imaging without causing pain to the subject 14.

  As shown in FIG. 2, the radiation detection apparatus 11 has a main surface of a rectangular shape, and includes a resin substrate 40 having flexibility (flexibility) having a size of the square. A configuration in which a thin and flexible flexible portion 30 at the center of y and thick and rigid rigid portions 32 and 34 on both sides (both ends) in the length direction y are provided. It is said that. The rigid portions 32 and 34 are made of hard resin.

  A handle 33 is provided in one rigid portion 32 of the solid that is not hollow by an opening. The other rigid portion 34 has a rectangular tube-like structure having a hollow portion in which circuit components of the control circuit portion 62 described later are mounted. Openings at both ends in the lengthwise direction of the rectangular tube are closed by lids 36, and the rigid portion The hollow part 34 is sealed. Most of the surface of the rigid portion 34 in contact with the substrate 40 is an opening 37, and the circuit component is mounted in the hollow portion through the opening 37.

  Thus, since the radiation detection apparatus 11 is provided with the rigid portions 32 and 34 on both sides in the length direction y having flexibility, it is possible in the length direction (also referred to as the flexibility direction) y. It has flexibility and has rigidity in the width direction (rigid direction) x orthogonal to the length direction y.

  FIG. 3 shows a partially omitted sectional view taken along line III-III in FIG. As can be seen from FIG. 3, a thick sheet-like radiation detection circuit unit 10 is bridged over the rigid part 32 and the rigid part 34 not shown in FIG.

  The radiation detection circuit unit 10 includes a substrate 40 having a size corresponding to the size of the entire surface of the radiation detection device 11, and rigid portions 32 and 34 are attached to both end portions (opposite sides) of the substrate 40. It has been.

  A scintillator 52 that converts the radiation R transmitted through the subject 14 (see FIG. 1) into visible light and a signal line 66 (see FIG. 6) are connected to one of the signal electrodes formed in a matrix on the front side of the substrate 40. A TFT layer 48 including an array of thin film transistors (TFTs) 68 (see FIG. 6), to which a gate line 64 (see FIG. 6) is connected to the gate electrode, and capable of transmitting radiation R and visible light, and the TFT 68 ( The visible light is signaled using a solid state detection element (hereinafter referred to as a pixel) 50 (see FIG. 6) formed on the other signal electrode of each of the other signal electrodes of FIG. 6 and made of a material such as amorphous silicon (a-Si). A photoelectric conversion layer 46 that converts an electric signal that is an electric charge, a grid 42 that removes scattered rays of radiation R from the subject 14, and a protective film layer 41 made of resin. It is provided in order. The visible light irradiated with the radiation R from the protective film layer 41 side and converted into the radiation R by the scintillator 52 is converted into a signal charge (electric signal) by the pixel 50 and accumulated in the pixel 50.

  The scintillator 52 may be interposed between the grid 42 and the photoelectric conversion layer 46 as shown in FIG.

  Further, as the pixel 50, instead of a-Si, a photoelectric conversion layer made of a material such as amorphous selenium (a-Se), which has a temperature tolerance range narrower than that of a-Si, is arranged on an array of TFTs 68. It is possible to substitute for the configuration. In this case, the scintillator 52 is not necessary.

  Further, the TFT 68 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.

  In FIG. 3, the surface of the protective film layer 41 of the radiation detection circuit unit 10 is a radiation R irradiation surface 56.

  The substrate 40 is preferably configured by mixing a material having a high radiation absorption rate, for example, tungsten powder. More specifically, with this configuration, the substrate 40 mixed with the tungsten powder covers the entire back surface of the radiation detection device 11, thereby preventing back scattering from the radiation detection device 11. Further, damage due to radiation R of circuit components mounted on the control circuit unit 62 (see FIG. 2) disposed in the hollow portion of the rigid portion 34 is prevented. It should be noted that damage to the circuit components mounted on the control circuit 62 due to radiation R can be further prevented by sticking a lead plate covering the surface of the rigid portion 34 to the surface of the rigid portion 34.

  FIG. 5 shows a substantial wiring configuration diagram of the radiation detection apparatus 11.

  FIG. 6 shows a circuit diagram of the radiation detection apparatus 11.

  As can be seen from FIG. 5, the radiation detection apparatus 11 has a rectangular shape as a whole, and both ends in the flexible direction y are rigid portions 32 and 34, and a rectangular plate-shaped portion between the rigid portions 32 and 34. Is the flexible portion 30.

  The radiation detection circuit unit 10 is disposed in the flexible part 30, and the control circuit unit 62 is disposed in one of the rigid parts 32 and 34.

  As described above, the radiation detection circuit unit 10 disposed in the flexible unit 30 includes the pixels 50 arranged in a matrix. Further, as illustrated in FIGS. 5 and 6, one of the signal electrodes is provided in each pixel 50. And a TFT 68 which is a gate element in which the signal line 66 is connected to the other signal electrode and the gate line 64 is connected to the gate electrode. In FIG. 5, the TFT 68 is drawn with a circle.

  As shown in FIGS. 5 and 6, the control circuit unit 62 includes a gate drive circuit 73 that drives the TFT 68 through the gate line 64, and a signal readout circuit 93 that reads out signal charges supplied through the driven TFT 68 and the signal line 66. And a drive circuit 110 including a bias circuit 74 that applies a bias voltage to the pixel 50 through a bias line 72, a battery 92 that is a power source of the radiation detection apparatus 11, and the radiation detection apparatus 11 as a whole by power supplied from the battery 92. A control unit 100 that controls driving, and a transceiver that transmits and receives a signal including information on the radiation R detected by the radiation detection circuit unit 10 and read by the signal reading circuit 93 and stored in the image memory 96 to and from the console 20 ( Wireless communication means) 102 is arranged.

  A part of the control circuit part 62 may be divided and arranged on the other rigid part 32 side. For example, the signal readout circuit 93 may be arranged in the control circuit section 62 in the other rigid section 32.

  As shown in FIG. 6, the signal readout circuit 93 is connected in series to each signal line 66, each of which is an integral amplifier 82 composed of an integrated circuit, a sample hold circuit 84, and an FET ( A field effect transistor) switch 78, and an A / D converter 90 connected to the output side of the FET switch 78 through a signal line 88.

  The multiplexer driving circuit 79 sequentially drives (turns on) each FET switch 78 constituting the multiplexer 76 for each signal line 66 {for each row direction (width direction x)}.

  The gate drive circuit 73 includes a gate IC 69 including an FET switch 71 having one end connected to the gate line 64 and the other end connected in common and connected to the voltage Vcc through a resistor, and each FET switch 71 ( And a gate IC drive circuit 70 for driving the gate electrode). A pull-down resistor is connected between the signal electrode on the TFT 68 side of the FET switch 71 of the gate IC 69, that is, the gate line 64, and the ground.

  When the FET switch 71 is turned on by the gate IC drive circuit 70, the TFTs 68 arranged in the column direction (length direction y) connected to the gate line 64 are driven and turned on.

  The control unit 100 stores an address signal generation circuit 94 that supplies an address signal to the gate IC drive circuit 70 and the multiplexer drive circuit 79, and a digital signal for each pixel 50 that has been A / D converted by the A / D converter 90. And an ID memory 98 that stores detection device ID information that is an identification code for specifying the radiation detection device 11.

  As described above, in each pixel 50, signal charges generated by converting visible light into electrical signals are accumulated, and the TFTs 68 are sequentially turned on for each column in the width direction x, while the FFT switch 78 of the multiplexer 76. Are sequentially turned on for each row, whereby the signal charge can be read out as an image signal.

  The transceiver 102 connected to the control unit 100 collectively transmits the detection apparatus ID information stored in the ID memory 98 and the radiation image information stored in the image memory 96 to the console 20 by wireless communication.

  The radiation detection apparatus 11 and the radiographic imaging system 12 according to this embodiment are configured as described above, and the operation thereof will be described next.

  The radiographic image capturing system 12 is installed in an operating room or the like, and is used, for example, when a radiographic image needs to be captured during the operation of the subject 14 (patient) by a doctor. Therefore, the patient information of the subject 14 that is an imaging target is registered in advance in the console 20 prior to imaging. If the imaging region and the imaging method are determined in advance, these imaging conditions are also registered in the console 20 in advance. In the state where the above preparatory work is completed, the treatment for the subject 14 is performed.

  When radiographing is performed during treatment, a doctor or a radiographer in charge takes the irradiation surface 56 (FIGS. 3 and 4) of the radiation detection device 11 at a predetermined position between the subject 14 and the mattress 28 on the bed 26. The radiation detection apparatus 11 is installed in a state where the reference) is on the radiation source 16 side.

  Next, after moving the radiation source 16 to a position facing the radiation detection circuit unit 10, an imaging switch (not shown) is operated to perform imaging.

  In this case, the radiation source 16 acquires an imaging condition related to the imaging region of the subject 14 from the console 20 by wireless communication, and controls a dose adjustment unit in the radiation source 16 according to the acquired imaging condition, thereby obtaining a predetermined dose. The subject 14 is irradiated with the radiation R consisting of

  The radiation R that has passed through the subject 14 is applied to the radiation detection circuit unit 10, and after the scattered radiation is removed by the grid 42 of the radiation detection circuit unit 10, the radiation R is converted into an electric signal by each pixel 50 constituting the radiation detection circuit unit 10. It is converted and held as a charge (signal charge). Next, the signal charge, which is the radiographic image information of the subject 14 held in each pixel 50, is supplied to the gate IC drive circuit 70 and the multiplexer drive circuit 79 from the address signal generation circuit 94 constituting the control unit 100. Is read according to

  That is, the gate IC drive circuit 70 outputs a selection signal according to the address signal supplied from the address signal generation circuit 94, turns on the corresponding FET switch 71, selects the gate line 64, and is connected to the gate line 64. An ON signal is supplied to the gate electrode of the TFT 68. On the other hand, the multiplexer drive circuit 79 outputs a selection signal in accordance with the address signal supplied from the address signal generation circuit 94 to sequentially switch the FET switches 78 constituting the multiplexer 76, and the gate line 64 selected by the gate IC drive circuit 70. The signal charges as the radiation image information held in the respective pixels 50 connected to are sequentially read out via the signal line 66.

  The signal charges as radiation image information read out from each pixel 50 are amplified by each integrating amplifier 82, then sampled by each sample and hold circuit 84, and A through the signal line 88 via the multiplexer 76 (FET switch 78). The signal is supplied to the / D converter 90 and converted into a digital signal by the A / D converter 90. The radiation image information converted into the digital signal is temporarily stored in the image memory 96 of the control unit 100.

  Similarly, the gate IC drive circuit 70 sequentially switches the TFTs 68 connected to the gate lines 64 in accordance with the address signal supplied from the address signal generation circuit 94, and as radiation image information that is charge information held in each pixel 50. The signal charges are read out via the signal line 66 and stored in the image memory 96 of the control unit 100 via the integrating amplifier 82, the sample hold circuit 84, the multiplexer 76, the signal line 88, and the A / D converter 90.

  The radiation image information stored in the image memory 96 is transmitted to the console 20 by wireless communication via the transceiver 102. The radiographic image information transmitted to the console 20 is received by a transceiver (not shown) of the console 20, subjected to predetermined image processing in an image processing unit (not shown), and then a patient of the subject 14 registered in the console 20. The information is stored in the image memory of the console 20 in a state associated with the information.

  The radiographic image information subjected to predetermined image processing in the console 20 is transmitted from the console 20 to the display device 18, and the display device 18 that has received the radiographic image information displays the radiographic image.

  A doctor (not shown) performs the procedure while confirming the radiation image displayed on the display device 18.

  In this case, in the radiographic imaging system 12, wireless communication is performed between the radiation detection device 11 and the console 20, between the radiation source 16 and the console 20, and between the console 20 and the display device 18. Since cables for transmitting and receiving signals are not connected, for example, these cables are not disposed on the floor surface of an operating room or the like, and there is no possibility of hindering the work of a doctor or the like.

  As described above, the radiation detection apparatus 11 according to the above-described embodiment is divided into the flexible portion 30 and the rigid portion 34, the signal line 66 is connected to one signal electrode of the flexible portion 30, and the gate A radiation detection circuit unit having an array of TFTs 68 in a matrix arrangement in which the gate line 64 is connected to the electrode, and the other signal electrode is formed with each pixel 50 for detecting the radiation R transmitted through the subject 14 and converting it into signal charges. 10 is disposed, and a gate driving circuit 73 that drives the TFT 68 through the gate line 64 and a signal readout circuit 93 that reads out the signal charges supplied through the driven TFT 68 and the signal line 66 are disposed in the rigid portion 34. It has a configuration.

  As described above, the radiation detection circuit unit 10 is arranged in the flexible part 30, and the rigid part 34 is supplied from the pixel 50 of the radiation detection circuit unit 10 through the gate drive circuit 73 and the TFT 68 that drives the TFT 68 of the radiation detection circuit unit 10. Since the control circuit unit 62 including the signal readout circuit 93 for reading out the signal charge is arranged, so-called discrete components are arranged in the sheet-like radiation detection circuit unit 10, that is, the flexible unit 30 that contacts the subject 14. The radiation detecting device 11 can be arranged so that the flexible portion 30 can be obtained and the flexible portion 30 follows the surface shape of the subject 14.

  In this case, the signal readout circuit 93 includes an A / D converter 90 that converts the signal charge supplied from each pixel 50 through the signal lines 66 and 88 into a digital signal, and the rigid portion 34 includes a gate drive. In addition to the circuit 73 and the signal reading circuit 93, the image memory 96 for storing the digital signal, the transceiver 102 for sending the digital signal read from the image memory 96 as a radio signal, and the radiation detection apparatus 11 as a whole. And a battery 92 for supplying electricity. Thereby, the portable radio | wireless type radiation detection apparatus 11 which has flexibility in the length direction y which is one direction can be provided. However, the signal reading circuit 93 is not provided with both the transmitter / receiver 102 and the battery 92, but is provided with at least one of the transmitter / receiver 102 (which is wired instead of wireless) or the battery 92. The configuration may be changed. For example, by disposing the battery 92, it is possible to provide a radiation detection apparatus that is flexible in one direction and portable and battery-driven. By disposing the transmitter / receiver 102, it is possible to provide a lighter-weight wireless radiation detection apparatus that is flexible in one direction, portable, and operable by an external power source.

  7 and 8 show a substantial wiring configuration diagram and a circuit diagram, respectively, of a radiation detection apparatus 11A according to still another embodiment.

  Also in this radiation detection apparatus 11A, the whole is formed in a quadrangular shape, both end portions in the direction y having flexibility are rigid portions 32 and 34, and a rectangular plate-shaped portion between the rigid portions 32 and 34 is a flexible portion 30. It is said that.

  The radiation detection circuit unit 10 </ b> A is disposed in the flexible part 30, and the control circuit part 62 is disposed in one rigid part 34 among the rigid parts 32 and 34. The configuration of the control circuit unit 62 of the radiation detection apparatus 11A of FIGS. 7 and 8 arranged in the rigid portion 34 is the same as the configuration of the control circuit unit 62 of the radiation detection apparatus 11 of FIGS. 5 and 6 described above. Therefore, the description thereof is omitted.

  On the other hand, in the radiation detection circuit unit 10A arranged in the flexible part 30, the pixels 50 are arranged in a matrix, and one of the signal electrodes is connected to each pixel 50, and the signal line 66 is connected to the other signal electrode. However, in the radiation detection circuit unit 10A, in particular, all of the signal lines 66 are connected to the TFT 68 which is a gate element in which the gate line 64 is connected to the gate electrode. The difference is that they are arranged in parallel along the length direction y having flexibility.

  Since the signal charge of the analog signal flows from the pixel 50 to the signal line 66, the signal line 66 is formed to be short, wide and thick, in other words, to be routed with a low impedance so as not to distort the analog signal. Yes.

  In practice, it is preferable that each signal line 66 has a wiring pattern on the substrate 40 so that the length to the input port of the A / D converter 90 including the signal line 88 is the shortest.

  Also in this radiation detection apparatus 11A, a part of the control circuit unit 62 may be divided and disposed on the other rigid portion 32 side. For example, the signal readout circuit 93 may be arranged in the control circuit section 62 in the other rigid section 32.

  As described above, the radiation detection apparatus 11A according to the other embodiment described above is divided into the flexible portion 30 and the rigid portion 34, and the signal line 66 is connected to one signal electrode of the flexible portion 30. Radiation detection having an array of TFTs 68 in a matrix arrangement in which the gate line 64 is connected to the gate electrode, and the other signal electrode is formed with each pixel 50 for detecting the radiation R transmitted through the subject 14 and converting it into signal charges. The circuit unit 10A is arranged, and a gate driving circuit 73 that drives the TFT 68 through the gate line 64 and a signal readout circuit 93 that reads out the signal charges supplied through the driven TFT 68 and the signal line 66 are arranged in the rigid unit 34. It has the composition which is done.

  The signal lines 66 arranged in the radiation detection circuit unit 10A of the flexible part 30 are configured to be patterned in parallel (in a straight line) along the flexible length direction y and to the rigid part 34. Therefore, the signal readout circuit 93 from the flexible portion 30 to the rigid portion 34 can be achieved by patterning the signal line 66 with a low impedance (short, thick, and thick patterning. In particular, it is important to make the signal line 66 short). Can be routed up to. With this configuration, it is possible to minimize the waveform distortion of signal charges, which are analog signals transmitted from the respective pixels 50 to the signal readout circuit 93 through the signal line 66, and the mixing of noise. Obtaining a signal (radiation image information) with good S / N in a radiographic image is extremely preferable for diagnostic interpretation.

  In the radiation detection apparatus 11A of FIGS. 6 and 7 as well, a so-called discrete component is not disposed in the radiation detection circuit unit 10A formed in a sheet shape, that is, the flexible unit 30 that is in contact with the subject 14. The radiation detection device 11A can be arranged so that the flexible portion 30 follows the surface shape of the subject 14.

  In addition, this invention is not limited to embodiment mentioned above, Of course, it can change freely in the range which does not deviate from the main point of this invention.

  For example, in the above-described embodiment, the radiographic image capturing system 12 is used during the operation, and the radiographic image is displayed on the display device 18. However, the radiographic image capturing system 12 captures a normal radiographic image other than during the operation. Needless to say, the present invention can also be applied to the case of performing only. For example, it can also be applied to medical examinations and rounds in hospitals.

  When the radiation detectors 11 and 11A are used in an operating room or the like, there is a risk that blood or other germs may adhere. Therefore, the radiation detection device 11 can have a waterproof and hermetic structure, and can be used repeatedly and continuously by sterilizing and cleaning as necessary.

  Further, wireless communication between the radiation detection apparatuses 11 and 11A and the console 20 that is an external device may be performed by optical wireless communication using infrared rays or the like instead of normal communication using radio waves.

1 is a configuration block diagram of a radiographic imaging system including a radiation detection apparatus in this embodiment. It is a perspective view of a radiation detection apparatus. FIG. 3 is a cross-sectional view of the radiation detection apparatus shown in FIG. FIG. 6 is a partially omitted cross-sectional view of a radiation detection apparatus according to another embodiment. It is a substantial wiring block diagram of a radiation detection apparatus. It is a circuit diagram of a radiation detection apparatus. It is a substantial wiring block diagram of the radiation detection apparatus which concerns on other embodiment. It is a circuit diagram of the radiation detector concerning other embodiments.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10, 10A ... Radiation detection circuit part 11, 11A ... Radiation detection apparatus 14 ... Subject 30 ... Flexible part 34 ... Rigid part 40 ... Substrate 50 ... Pixel 62 ... Control circuit part 64 ... Gate line 66 ... Signal line 68 ... TFT 73 ... Gate drive circuit 90 ... A / D converter 92 ... Battery 93 ... Signal readout circuit 96 ... Image memory 102 ... Transceiver

Claims (3)

A radiation detection apparatus divided into a flexible part and a rigid part,
A signal line is connected to one signal electrode, a gate line is connected to the gate electrode, and each pixel that detects radiation transmitted through the subject and converts it into a signal charge is formed in the flexible portion. A radiation detection circuit unit having an array of switching elements arranged in a matrix,
A control having a gate driving circuit for driving the switching element through the gate line and a signal readout circuit for reading out signal charges from the pixels supplied from the driven switching element through the signal line in the rigid portion. A radiation detection apparatus comprising a circuit unit. The radiation detection apparatus according to claim 1,
The radiation detecting apparatus according to claim 1, wherein the flexible portion has a quadrangular shape, and the rigid portion is provided on one side of the square shape or on opposite sides. The radiation detection apparatus according to claim 1 or 2,
The signal readout circuit includes an A / D converter that converts the signal charge into a digital signal,
In addition to the gate drive circuit and the signal reading circuit, the control circuit unit further includes an image memory for storing the digital signal, and a transmission / reception for transmitting the digital signal read from the image memory as a radio signal. And at least one of a battery for supplying electricity to the whole radiation detection apparatus and the radiation detection apparatus.

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