JP2010051477A - Portable radiographic imaging apparatus and radiation photographing system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To enable an electronic cassette to directly receive data from a photographing apparatus by a simple constitution. <P>SOLUTION: In the photographing apparatus 32, a transmission signal showing tube voltage, an mAs value of radiation and the quality of radiation is modulated to a sonic wave signal by a signa modulating part 138 and a sonic wave is outputted from a speaker 142 according to the modulated sonic wave signal. In the electronic cassette 32, the sonic wave outputted from the photographing apparatus 32 is inputted by a sonic wave inputting part 95 and the inputted sonic wave is demodulated to the transmission signal from the photographing apparatus 32 by a signal demodulating part 99. The gain of a signal processing part 82 is set according to the tube voltage, mAs value of radiation and quality of radiation shown by the demodulated transmission signal by a cassette control part 92. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a portable radiation image forming apparatus and a radiation imaging system.

  In recent years, an FPD (Flat Panel Detector) has been put into practical use in which a radiation sensitive layer is arranged on a TFT (Thin Film Transistor) active matrix substrate and radiation can be directly converted into digital data. 2. Description of the Related Art A portable radiographic imaging device (hereinafter also referred to as “electronic cassette”) that generates image information indicating a radiographic image represented by radiation and stores the generated image information has been put into practical use.

  Because this electronic cassette has portability, it is possible to take a picture of a patient while it is placed on a stretcher or bed, and the position of the electronic cassette can be changed to adjust the shooting location. It is possible to deal with it flexibly.

In addition, a method for notifying the operator of the operation state of the electronic cassette is known so that the operator can operate in cooperation (for example, Patent Documents 1 to 4). The electronic cassette receives control information related to radiography from the console when radiographing is performed.
JP-A-8-238234 JP 2004-105518 A JP 2005-13272 A JP 2008-67935 A

  However, in the method in which the electronic cassette receives information from the console, there is a problem in that the electronic cassette cannot directly receive data from an imaging apparatus that emits radiation.

  The present invention has been made to solve the above-described problems, and an object thereof is to provide a portable radiographic image forming apparatus and a radiographic imaging system capable of receiving data directly from an imaging apparatus with a simple configuration. To do.

  In order to achieve the above object, a portable radiographic image forming apparatus according to a first aspect of the present invention has a charge corresponding to the amount of radiation irradiated from the radiation irradiation source of an imaging apparatus having a radiation irradiation source for irradiating radiation. An electronic circuit that generates image information indicating a radiation image by accumulating, a sound input unit that receives sound waves output from the imaging device, and a sound wave input by the sound input unit from the imaging device Demodulation means for demodulating the transmission information, and control means for controlling the electronic circuit so as to generate the image information in accordance with the transmission information demodulated by the demodulation means.

  According to the portable radiographic image forming apparatus according to the first invention, the sound wave output from the imaging apparatus is input by the sound input means, and the sound wave input by the sound input means is input from the imaging apparatus by the demodulation means. Demodulate transmission information. Then, the control means controls the electronic circuit so as to generate image information according to the transmission information demodulated by the demodulation means, and the electronic circuit responds to the radiation dose irradiated from the radiation irradiation source of the imaging apparatus. By accumulating electric charges, image information indicating a radiation image is generated.

  In this way, by demodulating the sound wave output from the imaging device into transmission information from the imaging device, it is possible to receive data directly from the imaging device with a simple configuration and to respond to transmission information from the imaging device. Thus, the electronic circuit can be controlled to generate appropriate image information.

  According to a second aspect of the present invention, there is provided a portable radiographic image forming apparatus that stores a radiographic image by accumulating charges according to a radiation dose emitted from the radiation irradiation source of an imaging apparatus having a radiation irradiation source for irradiating radiation. An electronic circuit for generating image information to be shown; sound input means for inputting sound waves output from the imaging apparatus; and demodulation means for demodulating the sound waves input by the sound input means into transmission information from the imaging apparatus And output means for outputting the transmission information demodulated by the demodulation means together with the image information generated by the electronic circuit.

  According to the portable radiographic image forming apparatus of the second invention, the sound wave output from the imaging apparatus is input by the sound input means, and the sound wave input by the sound input means is input from the imaging apparatus by the demodulation means. Demodulate transmission information. In addition, the electronic circuit generates image information indicating a radiographic image by accumulating charges corresponding to the radiation dose emitted from the radiation irradiation source of the imaging apparatus. Then, the output means outputs the transmission information demodulated by the demodulation means together with the image information generated by the electronic circuit.

  In this way, by demodulating the sound wave output from the imaging device into transmission information from the imaging device, data can be received directly from the imaging device with a simple configuration, and transmission information from the imaging device can be converted into an image. Can be output together with information.

  A radiation imaging system according to a third invention is a portable radiographic image forming apparatus according to the first invention or the second invention, a radiation irradiation source for irradiating radiation, transmission of the irradiated radiation or irradiation of the radiation. The imaging device includes a modulation unit that modulates information into a sound wave signal, and a sound output unit that outputs a sound wave according to the sound wave signal modulated by the modulation unit.

  According to the radiation imaging system according to the third aspect of the present invention, in the imaging apparatus, the modulation means modulates the radiation to be emitted or the transmission information related to the irradiation of the radiation into a sound wave signal, and the sound output means modulates it by the modulation means A sound wave is output according to the sound wave signal. In the imaging apparatus, radiation is irradiated by a radiation irradiation source.

  In the portable radiation image forming apparatus, the sound wave output from the imaging apparatus is input by the sound input unit, and the sound wave input by the sound input unit is demodulated into transmission information from the imaging apparatus by the demodulation unit.

  As described above, in the portable radiographic image forming apparatus, by demodulating the sound wave output from the imaging apparatus into transmission information from the imaging apparatus, the portable radiographic image forming apparatus can be directly connected from the imaging apparatus with a simple configuration. Can receive data.

  The modulation means can modulate the transmission information into a sound wave signal by frequency modulation or pulse modulation.

  The transmission information described above can be information indicating the irradiation timing of radiation. As a result, the portable radiographic image forming apparatus can receive information indicating the radiation irradiation timing directly from the imaging apparatus, so that the operations can be synchronized.

  The transmission information may be information indicating at least one of the tube voltage of the radiation source, the amount of radiation to be irradiated, and the quality of the irradiated radiation. Accordingly, the imaging apparatus can receive information indicating the tube voltage, the amount of radiation, or the quality of radiation directly from the portable radiographic image forming apparatus.

  In addition, the electronic circuit according to the invention in which the transmission information described above is information indicating at least one of the tube voltage of the radiation irradiation source, the amount of radiation to be irradiated, and the quality of the radiation to be irradiated. An amplifying circuit for amplifying with a predetermined gain is provided, and image information corresponding to the charge amplified by the amplifying circuit is generated, and the control means can set the gain of the amplifying circuit according to the transmission information. Thereby, the gain of the amplifier circuit can be appropriately set according to the tube voltage, the amount of radiation, or the quality of radiation.

  The sound output means can output a sound wave according to the sound wave signal modulated by the modulation means before the radiation irradiation by the radiation irradiation source is started.

  The portable radiographic image forming apparatus may further include wireless communication means for transmitting / receiving control information to / from the outside. In this case, even if control information cannot be transmitted and received by wireless communication, the portable radiographic image forming apparatus can receive data directly from the imaging apparatus.

  According to the portable radiographic image forming apparatus and the radiographic imaging system according to the present invention, it is possible to obtain an effect that the portable radiographic image forming apparatus can directly receive data from the imaging apparatus with a simple configuration.

  The best mode for carrying out the present invention will be described below in detail with reference to the drawings.

  First, the configuration of the radiation information system 10 according to the first embodiment will be described. FIG. 1 is a block diagram showing each component of a radiation information system 10 (hereinafter also referred to as “RIS10” (Radiology Information System)) according to the first embodiment.

  The RIS 10 is a system for managing information such as medical appointment reservations and diagnostic records in the radiology department, and constitutes a part of a hospital information system (HIS).

  The RIS 10 includes a plurality of imaging request input terminals 12 (hereinafter also referred to as “input terminals 12”), a RIS server 14, and a plurality of radiographic imaging systems 18 (hereinafter also referred to as “imaging systems 18”). It is comprised including.

  The RIS server 14 manages the entire RIS 10 and is configured to be capable of mutual communication with each input terminal 12 and the imaging system 18 via a LAN (Local Area Network) cable 20 or a wireless LAN 22. The RIS server 14 is connected to a HIS server 24 that manages the entire HIS.

  The input terminal 12 is used by a doctor 26 (see FIG. 2) and a radiographer to input and view diagnostic information and facility reservations. A radiographic imaging request (imaging reservation) is also received from the input terminal 12. Made. Each input terminal 12 is composed of a personal computer with a display device, and is connected to the RIS server 14 via a LAN to enable mutual communication.

  The RIS server 14 receives an imaging request from each input terminal 12 and manages a radiographic imaging schedule in the imaging system 18 and includes a database 28.

  The database 28 includes information on the patient 30 such as attribute information (name, sex, date of birth, age, blood, patient ID, etc.), medical history, medical history, radiation images taken in the past, and the like of the patient 30 (see FIG. 2). And information relating to the electronic cassette 32 such as the identification number, model, size, sensitivity, usable imaging part (content of imaging request that can be supported), start date of use, number of uses, etc. It is comprised including.

  The imaging system 18 captures a radiographic image by an operation of a doctor 26 or a radiographer in response to an instruction from the RIS server 14. The imaging system 18 includes an imaging device 34 that irradiates a subject with radiation X having a radiation dose according to imaging conditions, and a radiation detector 60 that detects the radiation X transmitted through the patient 30 and converts the radiation X into radiation image information (FIG. 3). 2), a display device 36 for displaying a radiation image based on the radiation X detected by the radiation detector 60, a cradle 40 for charging a battery built in the electronic cassette 32, and the electronic cassette. 32, an imaging device 34, a display device 36, and a console 42 for controlling the cradle 40.

  FIG. 2 shows a state in which the imaging system 18 is installed in an operating room 44 as an imaging room as an example of a state in which the imaging system 18 according to the present embodiment is arranged. In the imaging system 18 according to the present embodiment, signals are transmitted and received by wireless communication between the electronic cassette 32 and the console 42. Each of the imaging device 34 and the display device 36 and the console 42 are connected by a cable and various types of information are transmitted / received by wired communication. However, in FIG. 2, the cables for connecting the devices are omitted.

  In the operating room 44 of FIG. 2, in addition to the imaging system 18, an operating table 46 on which the patient 30 lies is disposed, and an instrument table 48 on which various instruments used by the doctor 26 for surgery are placed. It is arranged on the side. Various devices necessary for the operation such as an anesthesia machine, an aspirator, an electrocardiograph, a sphygmomanometer, and the like are arranged around the operating table 46 (these devices are omitted in FIG. 2). .

  The imaging device 34 is connected to the free arm 52 and can be moved to a desired position according to the imaging region of the patient 30 and can be retracted to a position that does not interfere with the operation by the doctor 26. Similarly, the display device 36 is connected to the free arm 52 and can be moved to a position where the doctor 26 can easily check the captured radiographic image.

  The cradle 40 is formed with a housing portion 40 </ b> A capable of housing the electronic cassette 32.

  The electronic cassette 32 is accommodated in the accommodating portion 40A of the cradle 40 during standby, and the built-in battery is charged. When the radiographic image is captured, the electronic cassette 32 is removed from the cradle 40 and placed at the imaging region of the patient 30.

  The electronic cassette 32 is not limited to being used in the operating room 44, and can be applied to, for example, medical examinations and rounds in hospitals.

  FIG. 3 shows an internal configuration of the electronic cassette 32 according to the first exemplary embodiment. The electronic cassette 32 includes a housing 54 made of a material that transmits the radiation X, and has a waterproof and airtight structure. When the electronic cassette 32 is used in the operating room 44 or the like, there is a risk that blood or other germs may adhere. Therefore, one electronic cassette 32 can be used repeatedly by making the electronic cassette 32 have a waterproof and airtight structure and sterilizing and cleaning as necessary. Inside the housing 54, a grid 58 for removing scattered radiation of the radiation X by the patient 30 from the irradiation surface 56 side of the housing 54 irradiated with the radiation X, and radiation detection for detecting the radiation X transmitted through the patient 30. A vessel 60 and a lead plate 62 that absorbs backscattered radiation X are disposed in sequence. Note that the irradiation surface 56 of the housing 54 may be configured as a grid 58.

  A case 31 that houses various circuits including a microcomputer and a rechargeable secondary battery is disposed at one end of the housing 54. The radiation detector 60 and various circuits are operated by electric power supplied from a secondary battery disposed in the case 31. In order to avoid various circuits housed in the case 31 from being damaged by the radiation X irradiation, it is desirable to arrange a lead plate or the like on the irradiation surface 56 side of the case 31.

  FIG. 4 is a block diagram showing a detailed configuration of the radiation image capturing system 18 according to the present embodiment.

  The imaging device 34 is provided with a connection terminal 34 </ b> A for communicating with the console 42. The console 42 is provided with a connection terminal 42 </ b> A for communicating with the photographing device 34 and a connection terminal 42 </ b> B for outputting an image signal to the display device 36.

  The photographing device 34 is connected to the console 42 via the communication cable 35, and the display device 36 is connected to the console 42 via the display cable 37.

  The electronic cassette 32 is provided with a transceiver 32A for performing wireless communication. The console 42 is provided with a transceiver 42C for performing wireless communication. Data is transferred between the electronic cassette 32 and the console 42 by wireless communication.

  The radiation detector 60 built in the electronic cassette 32 is configured by laminating a photoelectric conversion layer that absorbs the radiation X and converts it into charges on a TFT active matrix substrate 66. The photoelectric conversion layer is made of amorphous a-Se (amorphous selenium) containing, for example, selenium as a main component (for example, a content rate of 50% or more), and when irradiated with radiation X, a charge corresponding to the amount of irradiated radiation. By generating a certain amount of charge (electron-hole pairs) internally, the irradiated radiation X is converted into a charge. The radiation detector 60 uses a phosphor material and a photoelectric conversion element (photodiode) instead of the radiation-charge conversion material that directly converts the radiation X such as amorphous selenium into electric charges. You may convert into an electric charge indirectly. As phosphor materials, gadolinium sulfate (GOS) and cesium iodide (CsI) are well known. In this case, radiation X-light conversion is performed by a fluorescent material, and light-charge conversion is performed by a photodiode of a photoelectric conversion element.

  Further, on the TFT active matrix substrate 66, a pixel portion 74 (FIG. 4) provided with a storage capacitor 68 for storing the charge generated in the photoelectric conversion layer and a TFT 70 for reading out the charge stored in the storage capacitor 68. Here, a large number of photoelectric conversion layers corresponding to the individual pixel portions 74 are schematically shown as photoelectric conversion portions 72) in a matrix. Charges generated in the photoelectric conversion layer as the electronic cassette 32 is irradiated with the radiation X are stored in the storage capacitors 68 of the individual pixel portions 74. As a result, the image information carried on the radiation X irradiated to the electronic cassette 32 is converted into charge information and held in the radiation detector 60.

  The TFT active matrix substrate 66 extends in a certain direction (row direction), and has a plurality of gate lines 76 for turning on and off the TFTs 70 of the individual pixel portions 74, and a direction orthogonal to the gate lines 76. A plurality of data wirings 78 extending in the (column direction) and for reading out stored charges from the storage capacitor 68 via the turned-on TFTs 70 are provided. Individual gate lines 76 are connected to a gate line driver 80, and individual data lines 78 are connected to a signal processing unit 82. When charges are accumulated in the storage capacitors 68 of the individual pixel portions 74, the TFTs 70 of the individual pixel portions 74 are sequentially turned on in units of rows by a signal supplied from the gate line driver 80 via the gate wiring 76. The charge stored in the storage capacitor 68 of the pixel unit 74 for which is turned on is transmitted as a charge signal through the data wiring 78 and input to the signal processing unit 82. Accordingly, the charges accumulated in the storage capacitors 68 of the individual pixel portions 74 are sequentially read out in units of rows.

  FIG. 5 shows an equivalent circuit diagram focusing on one pixel portion of the radiation detector 60 according to the present exemplary embodiment.

  As shown in the figure, the source of the TFT 70 is connected to a data line 78, and the data line 78 is connected to a signal processing unit 82. The drain of the TFT 70 is connected to the storage capacitor 68 and the photoelectric conversion unit 72, and the gate of the TFT 70 is connected to the gate wiring 76.

  The signal processing unit 82 includes a sample hold circuit 84 for each individual data wiring 78. The charge signal transmitted through each data wiring 78 is held in the sample hold circuit 84. The sample hold circuit 84 includes an operational amplifier 84A and a capacitor 84B, and converts the charge signal into an analog voltage. The operational amplifier 84A has a gain set by the cassette control unit 92, and amplifies and outputs the charge signal with the set gain. Further, the sample hold circuit 84 is provided with a switch 84C as a reset circuit that, when turned on, causes both electrodes of the capacitor 84B to be short-circuited to discharge the charge accumulated in the capacitor 84B.

  A multiplexer 86 and an A / D converter 88 are sequentially connected to the output side of the sample and hold circuit 84, and the charge signals held in the individual sample and hold circuits 84 are converted into analog voltages and sequentially supplied to the multiplexer 86. It is input (serially) and converted into digital image information by an A / D converter 88.

  A frame memory 90 is connected to the signal processing unit 82 (see FIG. 4), and image information output from the A / D converter 88 of the signal processing unit 82 is sequentially stored in the frame memory 90. The frame memory 90 has a storage capacity capable of storing image information indicating a radiation image for one frame, and the read image information for one line is framed each time the charge is read line by line. The data are sequentially stored in the memory 90.

  The radiation detector 60, the gate line driver 80, the signal processing unit 82, and the frame memory 90 according to the present embodiment correspond to the electronic circuit of the present invention.

  The frame memory 90 is connected to a cassette control unit 92 that controls the operation of the entire electronic cassette 32. The cassette control unit 92 is realized by a microcomputer, and a communication control unit 94 is connected thereto. The communication control unit 94 is connected to the transmitter / receiver 32A, and controls transmission of various types of information to / from external devices by wireless communication via the transmitter / receiver 32A. The cassette control unit 92 can transmit and receive various types of information to and from external devices via the communication control unit 94. The cassette control unit 92 stores later-described shooting control information received from the console 42, accumulates charges based on the information, and starts reading the charges.

  Note that the transceiver 32A and the communication control unit 94 according to the present embodiment correspond to the output unit of the present invention.

  The electronic cassette 32 includes, for example, a microphone and includes a sound input unit 95 to which an external sound wave is input. The sound input unit 95 is connected to a synchronization sound detection unit 97 that detects sound waves in a specific frequency band for synchronizing with the operation of the imaging device 34 from the sound waves input from the sound input unit 95. The synchronization sound detection unit 97 detects sound waves for synchronization using, for example, a filter that passes only a specific frequency band.

  The synchronization sound detection unit 97 is connected to a signal demodulation unit 99 that demodulates a sound wave signal indicating a sound wave in a specific frequency band detected by the synchronization sound detection unit 97 into a reception signal indicating reception information. In the present embodiment, OFDM (Orthogonal Frequency Division Multiplexing) modulation, which is one of frequency modulation, is used as a signal modulation method, and a sound wave signal is received by a demodulation method corresponding to OFDM modulation. Demodulate.

  Further, the synchronization sound detection unit 97 and the signal demodulation unit 99 are connected to the cassette control unit 92. The cassette control unit 92 controls the operation of the radiation detector 60 based on the sound wave for synchronization detected by the synchronization sound detection unit 97 and the reception information indicated by the reception signal demodulated by the signal demodulation unit 99. To do.

  In addition, the electronic cassette 32 is provided with a power supply unit 96, and the various circuits and elements described above (gate line driver 80, signal processing unit 82, frame memory 90, sound input unit 95, communication control unit 94, The synchronization sound detecting unit 97, the signal demodulating unit 99, and the microcomputer functioning as the cassette control unit 92) are operated by the power supplied from the power supply unit 96. The power supply unit 96 incorporates a battery (a rechargeable secondary battery) so as not to impair the portability of the electronic cassette 32, and supplies power from the charged battery to various circuits and elements.

  On the other hand, the console 42 is configured as a server computer, and includes a display 100 that displays an operation menu, captured radiographic images, and the like, and a plurality of keys, and inputs various information and operation instructions. An operation panel 102.

  The console 42 according to the present embodiment includes a CPU 104 that controls the operation of the entire apparatus, a ROM 106 that stores various programs including a control program in advance, a RAM 108 that temporarily stores various data, and various data. HDD 110 that stores and holds, display driver 112 that controls display of various types of information on display 100, operation input detection unit 114 that detects an operation state of operation panel 102, and connection terminal 42A, and is connected to connection terminal 42A. And a communication interface (I / F) unit 116 for transmitting and receiving various types of information such as exposure conditions, which will be described later, and state information of the imaging device 34, and the transceiver 42C via the communication cable 35. Shooting control information, image information, etc. with the electronic cassette 32 via the transceiver 42C A communication control unit 118 that transmits and receives various types of information; and an image signal output unit 120 that is connected to the connection terminal 42B and outputs an image signal to the display device 36 via the connection terminal 42B and the display cable 37. Yes.

  The CPU 104, ROM 106, RAM 108, HDD 110, display driver 112, operation input detection unit 114, communication I / F unit 116, communication control unit 118, and image signal output unit 120 are connected to each other via a system bus BUS. . Therefore, the CPU 104 can access the ROM 106, RAM 108, and HDD 110, controls the display of various types of information on the display 100 via the display driver 112, and the imaging device 34 via the communication I / F unit 116. Control of transmission / reception of various types of information, control of transmission / reception of various types of information to / from the electronic cassette 32 via the communication control unit 118, and control of images displayed on the display device 36 via the image signal output unit 120. Can do. Further, the CPU 104 can grasp the operation state of the user with respect to the operation panel 102 via the operation input detection unit 114.

  On the other hand, the imaging device 34 has received the communication I / F unit 132 that transmits and receives various types of information such as the exposure conditions and the status information of the imaging device 34 between the radiation source 130 that outputs the radiation X and the console 42. A radiation source controller 134 for controlling the radiation source 130 based on the exposure conditions, the quality of the radiation X output from the radiation source 130, the mAs value corresponding to the energy amount of the radiation X output from the radiation source 130, and A transmission signal generator 136 that generates a transmission signal indicating transmission information including a tube voltage (voltage between the cathode and the positive electrode of the radiation source 130) when the radiation X is output from the radiation source 130, and the generated transmission signal Is modulated into a sound wave signal by OFDM modulation, a speaker 140, and a sound output control unit 142 that outputs sound waves from the speaker 140 according to the modulated sound wave signal It is equipped with a.

  Note that the speaker 140 and the sound output control unit 142 in the present embodiment correspond to the sound output means of the present invention.

  As shown in FIG. 6, the signal modulator 138 modulates the generated transmission signal into a sound wave signal in a specific frequency band by OFDM modulation. The mAs value is a value obtained by multiplying the tube current (mA) when the radiation X is output from the radiation source 130 and the irradiation time (sec). Further, the transmission information including the quality of the radiation X, the mAs value of the radiation X, and the tube voltage in the present embodiment corresponds to the transmission information related to the irradiated radiation of the present invention.

  The sound output control unit 142 is connected to the radiation source control unit 134, and before the radiation control by the radiation source control unit 134 is started, the sound source control unit 142 has a specific frequency band according to the modulated sound wave signal. The speaker 140 is controlled to output a sound wave as a warning sound, and when the radiation control by the radiation source control unit 134 is started, the speaker outputs a sound wave in a specific frequency band as an exposure sound. 140 is controlled.

  The radiation source control unit 134 is realized by a microcomputer, stores the received exposure conditions, and irradiates the radiation X from the radiation source 130 based on the stored exposure conditions.

  The display device 36 includes a display unit 36A that displays an image indicated by the received image signal.

  Next, the overall operation of the RIS 10 according to the first embodiment will be briefly described.

  The input terminal 12 (see FIG. 1) accepts an imaging request from the doctor 26 or a radiologist. In the imaging request, the date and time of imaging by the electronic cassette 32 and the imaging conditions (imaging site, angle and number, tube voltage for irradiating the radiation X, tube current, irradiation time, size and sensitivity of the electronic cassette 32, etc. ) Is specified.

  The input terminal 12 notifies the RIS server 14 of the contents of the accepted imaging request. The RIS server 14 stores the contents of the imaging request notified from the input terminal 12 in the database 28.

  The console 42 accesses the RIS server 14 to acquire the content of the imaging request from the RIS server 14 and displays the content of the imaging request on the display 100 (see FIGS. 2 and 4).

  Based on the content of the imaging request displayed on the display 100 by the doctor 26 or the radiographer, imaging of the radiographic image is started.

  For example, as shown in FIG. 2, when taking a radiographic image of the affected part of the patient 30 lying on the operating table 46, the doctor 26 and the radiographer can use the operating table 46 and the patient 30 according to the part and angle of the imaging. The electronic cassette 32 is disposed between the affected area and the imaging device 34 is disposed above the affected area. Further, the doctor 26 and the radiographer set exposure conditions such as a tube voltage, a tube current, and an irradiation time when the operation panel 102 of the console 42 is irradiated with the radiation X according to the imaging region and imaging conditions of the patient 30. Perform the specified exposure condition specification operation. When the preparation of exposure of the imaging apparatus 34 is completed, the doctor 26 and the radiographer perform an imaging instruction operation for instructing imaging on the operation panel 102 of the console 42.

  Next, the operation of the imaging system 18 according to the first embodiment will be described in detail. FIG. 7 shows a timing chart showing the flow of operations when radiographic images are captured by the imaging system 18.

  The electronic cassette 32 is in a non-operating state (NOP state) in which the operation mode is the initial state when the power is turned on (started up), and an instruction received from the console 42 via the transceiver 32A. Operates based on information.

  By the way, the radiation detector 60 (see FIG. 4) in which the electronic cassette 32 is built-up is stored by dark current or the like even when the electronic cassette 32 is turned on even when the radiation X is not irradiated. Charge is accumulated in the capacitor 68. Therefore, the cassette control unit 92 outputs an instruction signal for instructing the signal processing unit 82 to reset when the operation mode is a non-operation state. When an instruction signal for instructing reset is input, the signal processing unit 82 turns on the switch 84C (see FIG. 5) to short-circuit both electrodes of the capacitor 84B. In this way, by short-circuiting both electrodes of the capacitor 84B, the charge unnecessarily accumulated in the capacitor 84B is released.

  The console 42 first transmits instruction information C1 for instructing an operation in the reset mode to the electronic cassette 32 via the transceiver 42C.

  When the cassette control unit 92 receives the instruction information C1 instructing the operation in the reset mode, the cassette control unit 92 shifts the operation mode to the reset mode, controls the gate line driver 80, and sequentially controls each gate wiring line by line from the gate line driver 80. An ON signal is output to 76, and the TFTs 36 connected to the gate wirings 76 are sequentially turned on line by line. As a result, the charges accumulated in each storage capacitor 68 in order line by line flow out to each data wiring 78 as a charge signal. While the operation mode is the reset mode, the cassette control unit 92 repeats the reset operation for outputting the ON signal to each gate line 76 in order line by line and resetting the charge accumulated in each storage capacitor 68 for one frame.

  When an exposure condition designation operation is performed on the operation panel 102, the console 42 transmits the exposure condition information C2 such as the tube voltage, the tube current, and the irradiation time designated by the exposure condition designation operation, and the communication cable 35. To the imaging device 34. Further, the console 42 transmits imaging control information C3 such as an accumulation time during which charges are accumulated in the respective accumulation capacitors 68 of the radiation detector 60 to the electronic cassette 32 via the transceiver 42C when radiographing is performed.

  When the power is turned on and a predetermined initial activation operation is completed, the photographing device 34 is in a sleep state and stands by. When receiving the exposure condition information C2, the imaging device 34 stores the received exposure condition information and shifts the operation state to the drive state. When the operation state returns to the driving state, the imaging device 34 transmits information C4 indicating completion of imaging preparation to the console 42 via the communication cable 35.

  When receiving the shooting control information C3, the cassette control unit 92 of the electronic cassette 32 stores the received shooting control information.

  When the console 42 receives the information C4 indicating that shooting preparation is complete, the console 42 displays on the display 100 that shooting preparation has been completed, and enables the shooting instruction operation to instruct shooting on the operation panel 102. In the photographing system 18 according to the present embodiment, the photographing instruction operation on the operation panel 102 is a two-stage operation, and the second-stage photographing instruction operation is performed on the operation panel 102 after the first-stage photographing instruction operation. Radiographic images are taken. This two-stage shooting instruction operation may be, for example, pressing two buttons on the operation panel 102 in order, or may be half-pressing or fully-pressing one button, for example.

  When the first-step photographing instruction operation is performed on the operation panel 102, the console 42 transmits instruction information C5 instructing preparation for exposure to the photographing apparatus 34 via the communication cable 35.

  When receiving the instruction information C5 instructing preparation for exposure, the imaging apparatus 34 is in a standby state of the radiation source 130 so that exposure is performed with the tube voltage and tube current indicated by the exposure condition information stored immediately before. I do. When the standby of the radiation source 130 is completed, the imaging apparatus 34 transmits information C6 indicating the completion of standby to the console 42 via the communication cable 35. At this time, in the imaging apparatus 34, the transmission signal generation unit 136 uses the tube voltage indicated by the exposure condition information stored immediately before, the mAs value based on the tube current and the irradiation time, and the radiation source 130 stored in advance. A transmission signal of transmission information indicating the quality of the radiation X is generated, and the signal modulation unit 138 performs OFDM modulation on the transmission signal into a sound wave signal.

  When the console 42 receives the information C6 indicating the completion of standby, the second-stage shooting instruction operation can be performed. When a second-stage shooting instruction operation is performed on the operation panel 102, the console 42 transmits instruction information C7 requesting shooting to the shooting device 34 via the communication cable 35.

  Upon receiving the instruction information C7 requesting shooting, the imaging device 34 outputs sound waves in a specific frequency band from the speaker 140 as the warning sound C8 in accordance with the OFDM-modulated sound wave signal. Then, after a lapse of a predetermined time from the output of the warning sound C8, the imaging device 34 outputs a sound wave having the same specific frequency band as the warning sound as the exposure sound C9 from the speaker 140, and the exposure stored immediately before. The radiation X is irradiated from the radiation source 130 for the irradiation time indicated by the condition information.

  The predetermined time is set in advance to a time longer than the time required to complete the reset operation for one frame in the electronic cassette 32.

  When the cassette control unit 92 of the electronic cassette 32 receives the above-described shooting control information C3, the cassette control unit 92 executes a program that realizes the shooting control processing routine shown in FIG.

  First, in step 150, it is determined whether or not a warning sound has been detected. When the warning sound C8 (see FIG. 7) composed of sound waves in a specific frequency band is detected via the sound input unit 95 and the synchronization sound detection unit 97, the process proceeds to step 152.

  In step 152, the sound wave signal indicating the sound wave of the warning sound detected in step 150 is demodulated into a transmission signal indicating transmission information from the imaging device 34. In step 154, the transmission information obtained in step 152 is converted into the transmission information. An appropriate gain is set in the operational amplifier 84A of the signal processing unit 82 in accordance with the included tube current, mAs value, and quality of the radiation X.

  For example, a lower gain is set so that the charge signal is not saturated as the mAs value is larger, and a higher gain is set so that the charge signal is not buried in noise as the mAs value is smaller. In addition, even with the same mAs value, the sensitivity of the electronic cassette changes with the tube voltage (because the apparent gain changes), so a lower gain is set so that the charge signal does not saturate as the tube voltage increases. A lower gain is set so that the charge signal is not buried in noise.

  In step 156, the reset operation is performed until the reset operation for one frame is completed. After the reset operation for one frame is completed, the process proceeds to step 158.

  In step 158, it is determined whether an exposure sound is detected. The system waits until an exposure sound C9 (see FIG. 7) composed of ultrasonic waves in a specific frequency band is detected via the sound input unit 95 and the synchronization sound detection unit 97. When the exposure sound C9 is detected, the radiation source 130 It is determined that the irradiation of the radiation X is started, and the process proceeds to step 160.

  In the next step 160, the operation mode is changed to the imaging mode, and the radiation is so stored in the storage capacitor 68 of each pixel unit 74 of the radiation detector 60 that the charge corresponding to the dose of the irradiated radiation X is accumulated. The detector 60 is controlled.

  At this time, the radiation X irradiated from the radiation source 130 reaches the electronic cassette 32 after passing through the patient 30. Thereby, charges corresponding to the dose of the irradiated radiation X are stored in the storage capacitors 68 of the respective pixel portions 74 of the radiation detector 60 built in the electronic cassette 32. Further, the cassette control unit 92 ends the charge accumulation when the charge accumulation in the accumulation capacitor 68 of each pixel unit 74 of the radiation detector 60 is continued for the accumulation time determined by the imaging control information stored immediately before. Then, the process proceeds to step 162.

  In step 162, the charge stored in the storage capacitor 68 of each pixel unit 74 of the radiation detector 60 is read as follows. The gate line driver 80 is controlled to output an ON signal to each gate line 76 sequentially from the gate line driver 80 line by line, and each TFT 36 connected to each gate line 76 is turned on line by line. As a result, the charges accumulated in each storage capacitor 68 in order line by line flow out to each data wiring 78 as a charge signal. The charge signal that has flowed out to each data line 78 is input to each sample and hold circuit 84 and amplified with the gain set in step 154 and converted into an analog voltage signal, and the converted analog voltage signal is converted into a multiplexer. 86 are sequentially input (serially) to 86, converted into digital image information by the A / D converter 88, and stored in the frame memory 90.

  In step 164, the operation mode is shifted to the reset mode. In the next step 166, the image information for one frame stored in the frame memory 90 is converted into serial data, and the console 42 is connected via the transceiver 32A. To end the shooting control processing routine.

  In the present embodiment, the cassette control unit 92 shifts the operation mode to the reset mode on the assumption that the continuous shooting is not performed when the reading of the charge for one frame is completed by the above-described shooting control processing routine. However, continuous shooting may be performed.

  Upon receiving image information for one frame, the console 42 performs predetermined image processing on the image information for one frame, and stores the image information after image processing in the HDD 110 in a state associated with the patient information of the patient 30. Remember me. Further, the console 42 outputs an image signal indicating a radiographic image after image processing to the display device 36 and causes the display unit 36A of the display device 36 to display the image signal. The doctor 26 performs the operation while confirming the radiation image displayed on the display unit 36A.

  As described above, according to the first embodiment, in the electronic cassette, by demodulating the sound wave output from the imaging device into transmission information from the imaging device, the electronic cassette can be configured with a simple configuration. Data can be received directly from the imaging device. Also, in the electronic cassette, appropriate image information can be generated by optimizing the gain in accordance with the tube voltage, the radiation mAs value, and the radiation quality included in the transmission information from the imaging apparatus. it can.

  Further, by transmitting data using sound waves, data can be sent from the photographing apparatus to the electronic cassette even when the electronic cassette is hidden behind the human body.

  In addition, the use of sound waves as a synchronization signal frees you from delay care in wireless communications and eliminates the need for care for directivity required by other wireless systems. Even if it is hidden, the electronic cassette can be operated in synchronization with the operation of the photographing apparatus.

  In the above embodiment, the case where sound waves in a specific frequency band are output as the warning sound or the exposure sound has been described as an example. However, for example, an ultrasonic wave is output as the warning sound or the exposure sound. Alternatively, a sound in a frequency band different from the frequency band of the real voice may be output. Further, a sound having a frequency band different from the audible band may be output. As a result, it is possible to prevent erroneous detection of other sounds such as a voice of a patient or the like as a sound for synchronization.

  Moreover, sound waves in different frequency bands may be output as the warning sound and the exposure sound.

  Next, a second embodiment will be described. In addition, since the structure of the radiation information system which concerns on 2nd Embodiment is the structure similar to 1st Embodiment, it attaches | subjects the same code | symbol and abbreviate | omits description.

  In the second embodiment, in the electronic cassette, the transmission information from the imaging device demodulated from the sound wave is transmitted to the console together with the image information, and the transmission information transmitted together with the image information is used in the console. Thus, the image processing is mainly different from the first embodiment.

  The cassette control unit 92 of the electronic cassette 32 includes information indicating the tube voltage out of the reception information indicated by the reception signal demodulated by the signal demodulation unit 99 together with the image information stored in the frame memory 90 and the communication control unit 94 and The data is transmitted to the console 42 via the transceiver 32A.

  When the console 42 receives information indicating the tube voltage together with the image information, the console 42 executes an image processing program stored in the HDD 110 and performs predetermined image processing on the image information using the information indicating the tube voltage. . For example, the console 42 uses a plurality of pairs of image information and information indicating the tube voltage, and calculates a difference by weighting image information obtained by imaging at each tube voltage, thereby calculating the bone in the image. An image in which one of an image portion corresponding to a hard tissue such as a portion and an image portion corresponding to a soft tissue is emphasized and the other is removed is generated as an energy subtraction image. At this time, the image information paired with the information indicating the high tube voltage is image information photographed using high-energy radiation with high transparency, and therefore an image portion corresponding to a thick tissue such as a chest is not included. Image information used to emphasize or remove and paired with information indicating low tube voltage is image information taken using low-energy radiation with low transparency, so bones such as breasts It is used to enhance or remove an image portion corresponding to a soft tissue having no image.

  Next, a shooting control processing routine according to the second embodiment will be described with reference to FIG. In addition, about the process similar to 1st Embodiment, the same code | symbol is attached | subjected and detailed description is abbreviate | omitted.

  First, in step 150, it is determined whether or not a warning sound is detected. If a warning sound composed of sound waves in a specific frequency band is detected, the process proceeds to step 152. In step 152, the sound wave signal indicating the sound wave of the warning sound detected in step 150 is demodulated into a transmission signal indicating transmission information from the imaging device 34. In step 154, the tube current and mAs value included in the transmission information are demodulated. In accordance with the quality of the radiation X, an appropriate gain is set in the operational amplifier 84A of the signal processing unit 82.

  In step 156, the reset operation is performed until the reset operation for one frame is completed. After the reset operation for one frame is completed, the process proceeds to step 158 to determine whether an exposure sound is detected. When an exposure sound composed of ultrasonic waves of a specific frequency band is detected, the process proceeds to step 160, the operation mode is shifted to the imaging mode, and the irradiated radiation X is stored in the storage capacitors 68 of the pixel units 74 of the radiation detector 60. The radiation detector 60 is controlled so as to accumulate electric charges according to the dose.

  In the next step 162, the charges accumulated in the storage capacitors 68 of the respective pixel units 74 of the radiation detector 60 are read. In step 164, the operation mode is shifted to the reset mode. In the next step 200, the frame memory is read. The image information for one frame stored in 90 is converted into serial data together with the information indicating the tube voltage obtained in step 152, and is transmitted to the console 42 via the transceiver 32A. Exit.

  When the above-described imaging control processing routine is performed for each imaging, a plurality of pairs of image information and information indicating tube voltage are received by the console 42 via the transceiver 42C. Then, the console 42 uses the information indicating the paired tube voltage to perform predetermined image processing on a plurality of pieces of image information to generate an energy subtraction image, and the generated image is displayed on the patient. The information is stored in the HDD 110 in a state associated with 30 patient information. Further, the console 42 outputs an image signal indicating the generated energy subtraction image to the display device 36 and causes the display unit 36A of the display device 36 to display the image signal.

  In addition, about the other structure and effect | action of the radiation information system which concern on 2nd Embodiment, since it is the same as that of 1st Embodiment, description is abbreviate | omitted.

  In this way, in the electronic cassette, by demodulating the sound wave output from the imaging apparatus into transmission information from the imaging apparatus, the electronic cassette can receive data directly from the imaging apparatus with a simple configuration. Also, in the electronic cassette, the information indicating the tube voltage included in the transmission information from the imaging device is transmitted to the console in pairs with the image information, so that the console side can respond to the tube voltage with respect to the image information. Image processing can be performed.

  In the first to second embodiments described above, the case where a sound wave obtained by modulating a transmission signal is output immediately before irradiation with radiation is described as an example. However, the present invention is not limited to this. Alternatively, a sound wave obtained by modulating the transmission signal may be output at other timing.

  In the imaging apparatus, a time signal indicating the irradiation timing may be modulated into a sound wave and output as transmission information related to radiation irradiation. In this case, in the electronic cassette, on the basis of the time signal obtained by demodulating the sound wave, the charge accumulation in the radiation detector is started and the charge is accumulated in synchronization with the radiation irradiation timing. Can do.

  In the imaging apparatus, the target of the radiation source and the type of filter may be modulated into sound waves and output. In this case, in the electronic cassette, the setting of the radiation detector may be changed based on the type of the radiation source target or filter obtained by demodulating the sound wave.

  Also, transmission information indicating at least one of tube voltage, radiation mAs value, and radiation quality may be modulated into a sound wave signal and output.

  In addition, the case where the transmission signal is modulated into the sound wave signal using the OFDM modulation method has been described as an example, but the present invention is not limited to this, and the transmission signal is modulated into the sound wave signal using another frequency modulation method. You may make it do. Further, the transmission signal may be modulated into a sound wave signal using a pulse modulation method.

  In addition, the case where various types of information are transmitted and received between the imaging device and the console via the communication cable has been described as an example, but various types of information are transmitted and received between the imaging device and the console by wireless communication. May be. Moreover, although the case where various information was transmitted / received by radio | wireless communication between an imaging device and an electronic cassette was demonstrated to the example, various information was transmitted / received via a communication cable between an imaging device and an electronic cassette. You may do it.

It is a block diagram which shows the structure of the radiation information system which concerns on the 1st Embodiment of this invention. It is a figure which shows the mode of the operating room where the radiographic imaging system which concerns on the 1st Embodiment of this invention was installed. It is a perspective view which shows the internal structure of the electronic cassette concerning the 1st Embodiment of this invention. It is a block diagram which shows the detailed structure of the radiographic imaging system which concerns on the 1st Embodiment of this invention. It is an equivalent circuit diagram paying attention to one pixel part of the radiation detector concerning a 1st embodiment of the present invention. It is a figure which shows the sound wave signal by which OFDM modulation was carried out. It is a timing chart which shows the flow of operation | movement at the time of imaging | photography of the radiographic image which concerns on the 1st Embodiment of this invention. It is a flowchart which shows the content of the imaging | photography control processing routine in the electronic cassette concerning the 1st Embodiment of this invention. It is a flowchart which shows the content of the imaging | photography control processing routine in the electronic cassette concerning the 2nd Embodiment of this invention.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 Radiation information system 18 Radiographic imaging system 32A Transceiver 32 Electronic cassette 34 Imaging device 42 Console 42C Transceiver 60 Radiation detector 82 Signal processing part 84A Operational amplifier 92 Cassette control part 94 Communication control part 95 Sound input part 97 Synchronous sound detection part 99 Signal demodulator 130 Radiation source 134 Radiation source controller 136 Transmission signal generator 138 Signal modulator 140 Speaker 142 Sound output controller

Claims (9)

An electronic circuit that generates image information indicating a radiological image by accumulating electric charge according to the amount of radiation irradiated from the radiation irradiation source of the imaging apparatus including a radiation irradiation source that irradiates radiation;
Sound input means for inputting sound waves output from the imaging device;
Demodulation means for demodulating the sound wave input by the sound input means into transmission information from the imaging device;
Control means for controlling the electronic circuit to generate the image information in response to the transmission information demodulated by the demodulation means;
A portable radiographic image forming apparatus. An electronic circuit that generates image information indicating a radiological image by accumulating electric charge according to the amount of radiation irradiated from the radiation irradiation source of the imaging apparatus including a radiation irradiation source that irradiates radiation;
Sound input means for inputting sound waves output from the imaging device;
Demodulation means for demodulating the sound wave input by the sound input means into transmission information from the imaging device;
Output means for outputting the transmission information demodulated by the demodulation means together with the image information generated by the electronic circuit;
A portable radiographic image forming apparatus. The portable radiographic image forming apparatus according to claim 1 or 2,
A radiation source that emits radiation,
An imaging device comprising: modulation means for modulating the irradiated radiation or transmission information relating to irradiation of the radiation into a sound wave signal; and sound output means for outputting a sound wave in accordance with the sound wave signal modulated by the modulation means;
Including radiography system.   The radiation imaging system according to claim 3, wherein the modulation unit modulates the transmission information into a sound wave signal by frequency modulation or pulse modulation.   The radiation imaging system according to claim 3 or 4, wherein the transmission information is information indicating an irradiation timing of the radiation.   The radiation imaging system according to claim 3 or 4, wherein the transmission information is information indicating at least one of a tube voltage of the radiation irradiation source, an amount of the irradiated radiation, and a quality of the irradiated radiation. The electronic circuit includes an amplification circuit that amplifies the accumulated charge with a predetermined gain, and generates the image information according to the charge amplified by the amplification circuit,
The radiographic system according to claim 6, wherein the control unit sets a gain of the amplifier circuit according to the transmission information.   8. The sound output means outputs a sound wave according to a sound wave signal modulated by the modulation means before the radiation irradiation by the radiation irradiation source is started. 8. Radiography system.   The radiation imaging system according to any one of claims 3 to 8, wherein the portable radiographic image forming apparatus further includes wireless communication means for transmitting and receiving control information to and from the outside.

Images