JP2010271198A - Radiation detection device - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a radiation detection device having each performance of a continuous using time, a communication property and load resistance of an electronic cassette together compatibly, and having excellent convenience for usability, storage or the like. <P>SOLUTION: The electronic cassette has: a cassette body 30 including a radiation detector 44 for converting into transmission radiation image information, and an image memory 122 for storing the transmission radiation image information; and a casing 32 capable of storing the cassette body 30, and connected electrically to the cassette body 30 with the cassette body 30 stored. The cassette body 30 has a cassette body transceiver 52 transmitting the radiation image information stored in the image memory 122 by radio communication, and a built-in battery 48 supplying the power to the cassette body 30, The casing 32 has a casing transmission part 130 for transmitting the radiation image information stored in the image memory 122 by radio communication, and an external battery 68 for supplying the power to the cassette body 30. <P>COPYRIGHT: (C)2011,JPO&INPIT

Description

  The present invention relates to a radiation detection apparatus including a radiation detector that detects radiation transmitted through a subject and converts the detected radiation into 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 radiographic image information from a radiation detector after imaging in order to quickly and accurately perform treatment on a patient (subject). 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.

  The radiation detection apparatus incorporating the radiation detector is classified into a stationary type installed at a predetermined position as a part of the radiographic imaging system and a portable type (cassette type) that is portable. The latter cassette-type radiation detection device (hereinafter simply referred to as an electronic cassette) is highly convenient for imaging, but must have extremely high requirements from the viewpoint of continuous use time (power supply specification), communication, and load resistance. There is. In order to solve such a problem, various apparatuses have been proposed (see Patent Documents 1 to 3).

  Patent Document 1 includes an internal power supply for storing a battery and a connection terminal connected to an external power supply, and switches between a photographing enable mode and a photographing standby mode depending on whether the connection terminal is connected to the external power supply. An apparatus capable of performing the above is disclosed. According to the invention of Patent Document 1, it is possible to efficiently take an image after the battery is charged or replaced.

  In Patent Document 2, a casing that can be attached to and detached from the cassette body has signal transmission means for wirelessly transferring data, and when the casing is attached to the cassette body, the casing is attached wirelessly. If not, a device is disclosed that can transfer data by wire. According to the invention of Patent Document 2, the portable type and the stationary type can be used in combination.

  Further, Patent Document 3 discloses an apparatus in which a radiation detector is made rigid by including a casing having at least one opening for receiving a cassette body.

JP 2006-208305 A Japanese Patent No. 4078096 JP 2008-90304 A

  By the way, in an imaging mode using an electronic cassette, a doctor or the like may perform imaging several times at a location physically separated from the console. From the viewpoint of the load on the electronic cassette, this imaging mode is used when imaging without applying a load to the electronic cassette (hereinafter referred to as imaging type 1) and when the electronic cassette is directly placed on a patient (hereinafter referred to as imaging). Type 2)). The photographing type 1 requires a relatively short photographing time and does not need to consider load resistance, but a lightweight and compact cassette is desired. On the other hand, the shooting type 2 requires a longer shooting time than the shooting type 1, and it is necessary to consider the continuous use time (battery capacity) and the load resistance of the cassette.

  The devices disclosed in Patent Documents 1 and 2 described above do not take load resistance into consideration in the imaging type 2, and unevenness or the like is locally generated in the radiation detector due to the patient's load, resulting in complicated distortion. However, image distortion corresponding to the distortion may occur in the radiation image information. Moreover, there is a risk of damage or disconnection of electronic components mounted on the electronic cassette.

  In addition, although the apparatus disclosed in Patent Document 3 considers the load resistance of the photographing type 2, it is not always easy to attach and detach the casing from the cassette body, and it is not a lightweight and compact configuration. This is not necessarily suitable for shooting type 1.

  The present invention has been made in consideration of such problems, and in particular, when the electronic cassette is directly placed on a patient for imaging, the electronic cassette is compatible with continuous use time, communication performance, and load bearing performance. It is an object of the present invention to provide a radiation detection apparatus that is excellent in convenience of use and storage of a main body and a casing.

  A radiation detection apparatus according to claim 1 of the present invention includes a radiation detector that detects radiation transmitted through a subject and converts the radiation into radiation image information, and an image memory that stores the converted radiation image information. A radiation detection apparatus comprising: a main body; and a casing that is capable of accommodating the cassette main body and is electrically connected to the cassette main body in a accommodated state of the cassette main body, wherein the cassette main body includes the image memory The first radio means for transmitting the radiological image information stored in the radio communication by wireless communication, and a first battery for supplying power to the cassette body, the casing is the radiation stored in the image memory It has the 2nd wireless means which transmits image information by radio | wireless communication, and the 2nd battery which supplies electric power to the said cassette body, It is characterized by the above-mentioned.

  According to the first aspect of the present invention, the cassette body and the casing are electrically connected to each other in the accommodated state of the cassette body, and the wireless means and the battery are provided to the cassette body and the casing, respectively. Power supply to the cassette body and transmission of radiographic image information via the casing become possible, and the performance of continuous use, communication, and load resistance as the entire electronic cassette can be improved by complementing the casing function. This makes it possible to improve the convenience of use and storage of the cassette body and casing, while maintaining both the continuous use time, communication performance, and load-bearing performance of the electronic cassette, especially when photographing with the electronic cassette placed directly on the patient. .

  The radiation detection device according to claim 2 is the radiation detection device according to claim 1, wherein the first wireless unit converts the radiation image information into a radio frequency signal, and the first signal. It is set as a 1st radio | wireless communication apparatus provided with the at least 1 antenna which transmits the said radio frequency signal supplied from the conversion part outside.

  The radiation detection apparatus according to claim 3 is the radiation detection apparatus according to claim 2, wherein the second radio unit transmits the radio frequency signal supplied from the first signal conversion unit to the outside. It is an antenna.

  According to the invention described in claim 3, since at least one antenna is provided in the casing, radiation image information can be transmitted via the casing with a very simple configuration, and the communication performance of the entire electronic cassette can be achieved by complementing the function of the casing. Can be improved.

  The radiation detection apparatus according to claim 4 is the radiation detection apparatus according to claim 1 or 2, wherein the second wireless unit converts the radiation image information into a radio frequency signal; A second radio communication device comprising: at least one antenna that transmits the radio frequency signal converted by the second signal conversion unit to the outside.

  The radiation detection apparatus according to claim 5 is the radiation detection apparatus according to any one of claims 1 to 4, wherein the cassette body converts the radiation image information into first radiation image information and second radiation. And the second radiographic image information is supplied to the casing, the first radiographic image information is supplied by the first radio means, and the second radiographic image information is supplied by the second radio means. It has the control means to transmit, It is characterized by the above-mentioned.

  According to the fifth aspect of the present invention, since the cassette body and the casing can transmit the radiation image information independently, when transmitting the radiation image information, the load (data amount) of wireless communication for each channel is reduced. Therefore, the communication performance of the entire electronic cassette can be improved by complementing the casing function.

  The radiation detection apparatus according to claim 6 is the radiation detection apparatus according to any one of claims 1 to 5, wherein the first wireless unit uses a radio channel different from the channel of the second wireless unit. It is characterized by transmitting information.

  According to the sixth aspect of the present invention, since the cassette body and the casing can transmit radiation image information from different channels, it is possible to prevent a reduction in communication speed due to cross-links at the time of transmission. Communication performance of the entire electronic cassette can be improved.

  The radiation detection device according to claim 7 is the radiation detection device according to any one of claims 2 to 4, wherein the casing amplifies the power of the radio frequency signal converted from the radiation image information. It has the means.

  According to the seventh aspect of the present invention, since the amplifying means for amplifying the power of the radio frequency signal is provided in the casing, it is possible to maintain the communication quality of the casing because the radiant intensity of the radio wave is increased. Communication performance of the entire electronic cassette can be improved.

  The radiation detection device according to claim 8 is the radiation detection device according to claim 4, wherein the first wireless communication device has lower power consumption and smaller size than the second wireless communication device. To do.

  According to the eighth aspect of the present invention, since the wireless communication device of the cassette body has a lower power consumption and a smaller size compared to the wireless communication device of the casing, the amount of power used by the cassette body can be reduced, so the weight of the cassette body can be reduced. This makes it possible to improve the usability of the cassette body when taking a picture only with the cassette body removed.

  The radiation detection device according to claim 9 is the radiation detection device according to any one of claims 1 to 5, wherein the first battery has a smaller power capacity and a smaller size than the second battery. It is characterized by that.

  According to the ninth aspect of the present invention, since the battery of the cassette body has a lower power consumption and a smaller size than the battery of the casing, it is possible to reduce the weight and space of the cassette body. It is possible to improve the usability of the cassette body when shooting only with the body.

  The radiation detection device according to claim 10 is the radiation detection device according to any one of claims 1 to 5, wherein the casing uses the electric power supplied from the second battery to supply the first battery. It has a charging means for charging.

  According to the invention described in claim 10, since the charging means for charging the first battery is provided in the casing, the cassette body can be charged by accommodating the cassette body in the casing, and the cassette body can be easily charged. .

  The radiation detection device according to claim 11 is the radiation detection device according to any one of claims 1 to 5, wherein the casing has a grip portion, and the radiation incident direction of the cassette body. The cassette body is accommodated so as to be detachable in the vertical direction.

  According to the eleventh aspect of the invention, since the casing detachable in the direction parallel to the radiation incident direction of the cassette body is provided, the surface of the radiation detector is scratched when being detached from the cassette body. Injury caused by doctors and the like touching the scratches, and adverse effects on image diagnosis due to imprints of scratch marks are eliminated. Thereby, the convenience of a cassette main body and a casing, storage, etc. can be improved.

  The radiation detection device according to claim 12 is the radiation detection device according to any one of claims 1 to 5, wherein the casing includes a grip portion and is directed to a radiation incident direction of the cassette body. The cassette body is accommodated so as to be detachable in a horizontal direction.

  According to the twelfth aspect of the present invention, since the casing that can be attached / detached in the horizontal direction with respect to the radiation incident direction of the cassette body is provided, it is easily attached / detached if a doctor or the like holds the casing with the gripping part and slides the cassette body This makes it possible to improve the convenience of the cassette body and the casing and the convenience of storage.

  According to a thirteenth aspect of the present invention, in the radiation detection device according to any one of the first to fifth aspects, the casing is configured such that the cassette body is accommodated on the inner wall of the casing. A rib having a shape straddling a plurality of circuit boards included in the main body is provided.

  According to the thirteenth aspect of the present invention, since the casing is provided with ribs shaped so as to straddle the plurality of circuit boards included in the cassette body, the casing is lightweight while the rigidity of the cassette body is supported and the casing is secured. Therefore, the convenience of the cassette body and the casing and the convenience of storage can be improved.

  The radiation detection device according to claim 14 is the radiation detection device according to any one of claims 1 to 5, wherein the casing has a rectangular shape, and at least one antenna is provided at a corner of the casing. It is characterized by having.

  According to the fourteenth aspect of the present invention, since at least one antenna is provided at the corner of the casing, a reduction in communication speed due to a physical obstacle between the transmitter and the receiver is prevented during transmission and reception of radiation image information. It becomes possible, and the communication performance of the entire electronic cassette can be improved by complementing the function of the casing.

  The radiation detection apparatus according to claim 15 is the radiation detection apparatus according to claim 11 or 12, wherein the casing includes at least one antenna in the grip portion.

  According to the fifteenth aspect of the present invention, since at least one antenna is provided in the grip portion of the casing, it is possible to prevent a reduction in communication speed due to a physical obstacle between the transmitter and the receiver when transmitting and receiving radiation image information. It becomes possible, and the communication performance of the entire electronic cassette can be improved by complementing the function of the casing.

  According to the radiation detection apparatus of the present invention, a cassette body comprising: a radiation detector that detects radiation that has passed through a subject and converts the radiation into radiation image information; and an image memory that stores the converted radiation image information; A radiation detecting device capable of accommodating the cassette body and having a casing electrically connected to the cassette body in a accommodated state of the cassette body, wherein the cassette body is stored in the image memory First radio means for transmitting the radiographic image information by radio communication, and a first battery for supplying power to the cassette body, wherein the casing stores the radiographic image information stored in the image memory. Since there is provided a second wireless means for transmitting by wireless communication and a second battery for supplying power to the cassette body, particularly electronic Providing a radiation detection device that is easy to use and store in the cassette body and casing, as well as the continuous use time, communication performance, and load-bearing performance of the electronic cassette when shooting with the cassette placed directly on the patient can do.

It is explanatory drawing of the operating room where the radiographic imaging system in which the radiation detection apparatus which concerns on this embodiment is integrated is installed. It is a perspective view of the radiation detector concerning this embodiment. It is a perspective view of the radiation detection device concerning this embodiment. It is a circuit block diagram of a radiation detector. 1 is a configuration block diagram of a radiographic imaging system in which a radiation detection apparatus according to the present embodiment is incorporated. It is a block diagram of the cassette transmission / reception system which the radiation detection apparatus concerning this embodiment comprises. It is a block diagram of the electric power supply system which the radiation detection apparatus concerning this embodiment comprises. The imaging | photography workflow using the radiation detection apparatus which concerns on this embodiment is shown. The imaging | photography workflow using the radiation detection apparatus which concerns on this embodiment is shown. It is a block diagram of the configuration of a radiographic image capturing system according to a first modification. It is a block diagram of the cassette transmission / reception system which the radiation detection apparatus concerning a 1st modification comprises. It is a block diagram of the electric power supply system which the radiation detection apparatus which concerns on a 1st modification comprises. It is a perspective view of the radiation detection apparatus which concerns on a 2nd modification. FIG. 14A is a front view of a radiation detection apparatus according to a second modification. 14B is a cross-sectional view of the radiation detection apparatus shown in FIG. 14A along the line XIVB-XIVB. It is a perspective view of the radiation detection apparatus which concerns on a 3rd modification. It is XVI-XVI sectional view taken on the line of the radiation detection apparatus in FIG. FIG. 16 is a partially omitted plan view of the radiation detection apparatus of FIG. 15.

  FIG. 1 is an explanatory view of an operating room 12 in which a radiographic imaging system 10 in which a radiation detection apparatus according to the present invention is incorporated is installed. In the operating room 12, in addition to the radiographic imaging system 10, an operating table 16 on which the patient 14 lies is disposed, and an operating table 20 on which various instruments used by the doctor 18 for surgery are placed. It is arranged on the side. In addition, around the operating table 16, various devices necessary for an operation, such as an anesthesia machine, an aspirator, an electrocardiograph, and a blood pressure monitor, are arranged.

  The radiographic imaging system 10 includes an imaging device 22 for irradiating a patient 14 with radiation X having a dose according to imaging conditions, and a radiation detector (see FIG. 2) for detecting the radiation X transmitted through the patient 14. An electronic cassette (radiation detection device) 24, a display device 26 that displays a radiation image based on the radiation X detected by the radiation detector, and a console (electronic cassette) that controls the imaging device 22, the electronic cassette 24, and the display device 26. 24 external control devices) 28. The electronic cassette 24 includes a cassette body 30 containing a radiation detector and a casing 32 that houses the cassette body 30 and is detachable from the cassette body 30. Between the console 28 and the imaging device 22, the electronic cassette 24, and the display device 26, signals are transmitted and received by wireless communication indicated by broken lines.

  The imaging device 22 is connected to the free arm 34 and can be moved to a desired position according to the imaging region of the patient 14 and can be retracted to a position that does not obstruct the operation by the doctor 18. Similarly, the display device 26 is connected to the free arm 36 and can be moved to a position where the doctor 18 can easily confirm the captured radiographic image.

  FIG. 2 is a perspective view of the cassette body 30 according to the present embodiment. The cassette body 30 includes a protective cover 38 made of a material that transmits the radiation X. Inside the protective cover 38, a radiation detector 44 that detects the radiation X that has passed through the patient 14 from the irradiation surface 40 side of the protective cover 38 that is irradiated with the radiation X, and lead that absorbs backscattered rays of the radiation X Plates 46 are arranged in order. In addition, you may comprise the irradiation surface 40 of the protective cover 38 as a grid which removes the scattered ray of the radiation X. FIG.

  The protective cover 38 includes a built-in battery 48 that is a power source for the cassette body 30 and supplies the voltage Vcc, a cassette control unit 50 that drives and controls the radiation detector 44 by the power supplied from the built-in battery 48, A cassette body transceiver (first wireless means) 52 for receiving and transmitting a signal including information on the radiation X detected by the radiation detector 44 to and from the console 28 is accommodated. The cassette control unit 50 and the cassette body transmitter / receiver 52 are preferably provided with a lead plate or the like on the irradiation surface 40 side of the protective cover 38 in order to avoid damage due to irradiation with the radiation X. .

  FIG. 3 is a perspective view of the electronic cassette 24 according to the present embodiment. The cassette body 30 includes a substantially rectangular protective cover 38. The power switch 54 disposed on one short side of the protective cover 38 can manually switch on / off the built-in battery (first battery) 48 (see FIG. 2). The switch knob does not switch easily during such operations. A lamp 56 disposed at the short side end (in the vicinity of the power switch 54) of the upper surface of the protective cover 38 displays the remaining power of the built-in battery 48. The lamp 56 is configured such that, for example, the doctor 18 can visually grasp the remaining battery level by indicating the remaining capacity based on the display color difference (green is full, red is insufficient) and the number of lamps lit. .

  A connector 58a disposed on the other short side of the protective cover 38 can be fitted to a connector 58b provided in the casing 32 described later, and the cassette body 30 and the casing 32 can be electrically connected.

  The hollow rectangular casing 32 has a main body 60, and grips (gripping portions) 62a and 62b are provided on both side portions on the long side. Since the grips 62a and 62b are arranged so as to be bilaterally symmetric with respect to the opposing side surface portions of the main body 60, the doctor 18 is configured to easily carry the casing 32 (or the electronic cassette 24). The ring-shaped antennas 64a and 64b disposed on a part of the grips 62a and 62b enable wireless signals to be transmitted and received between the casing 32 and the console 28 (see FIG. 1). The antennas 64a and 64b are rotatable with respect to the axes of the handles 62a and 62b, and the doctor 18 can adjust the directivity of the antennas.

  An opening 66 provided on one short side of the main body 60 is configured to accommodate the cassette main body 30. A connector 58 b is provided on the inner wall of the other short side surface of the main body 60. As described above, the connector 58b can be fitted to the connector 58a included in the cassette body 30.

  An external battery (second battery) 68 disposed on the other short side of the main body 60 is detachable from the casing 32. The power switch 70 disposed on the side of the long side of the main body 60 can manually switch on / off the external battery 68, and the switch knob is not easily switched during operations such as photographing by the doctor 18. It has a structure. A lamp 72 provided at the short side end (near the power switch 70) of the upper surface of the main body 60 displays the remaining power of the external battery 68. Similarly to the lamp 56, the lamp 72 is configured so that the doctor 18 can visually grasp the remaining battery level by indicating the remaining amount by the display color difference (green is full, red is insufficient) and the number of lamps lit. It has become.

  Therefore, the cassette body 30 is inserted into the casing 32 by inserting it in the arrow direction (perpendicular to the incident direction of the radiation X of the cassette body 30) from the opening 66 with the short side surface provided with the connector 58a as the head. Is housed in. Further, the cassette body 30 and the casing 32 are electrically connected by fitting the connectors 58a and 58b.

  FIG. 4 is a block diagram of the circuit configuration of the radiation detector 44. The radiation detector 44 has a photoelectric conversion layer 81 made of a substance such as amorphous selenium (a-Se) that senses the radiation X and generates a charge on an array of thin film transistors (TFTs) 82. After the generated charge is stored in the storage capacitor 83, the TFT 82 is sequentially turned on for each row, and the charge is read as an image signal. In FIG. 4, only the connection relationship between one pixel 80 including the photoelectric conversion layer 81 and the storage capacitor 83 and one TFT 82 is shown, and the configuration of the other pixels 80 is omitted. Amorphous selenium must be used within a predetermined temperature range because its structure changes and its function decreases at high temperatures. Therefore, it is preferable to provide means for cooling the radiation detector 44 in the cassette body 30.

  A gate line 84 extending in parallel with the row direction and a signal line 86 extending in parallel with the column direction are connected to the TFT 82 connected to each pixel 80. Each gate line 84 is connected to a line scanning drive unit 88, and each signal line 86 is connected to a multiplexer 96 constituting a reading circuit.

  Control signals Von and Voff for turning on / off the TFTs 82 arranged in the row direction are supplied from the line scanning drive unit 88 to the gate line 84. In this case, the line scan driving unit 88 includes a plurality of switches SW1 for switching the gate lines 84 and an address decoder 90 for outputting a selection signal for selecting one of the switches SW1. An address signal is supplied to the address decoder 90 from the cassette control unit 50.

  Further, the charge held in the storage capacitor 83 of each pixel 80 flows out to the signal line 86 through the TFTs 82 arranged in the column direction. This charge is amplified by the amplifier 92. A multiplexer 96 is connected to the amplifier 92 via a sample and hold circuit 94. The multiplexer 96 includes a plurality of switches SW2 for switching the signal line 86 and an address decoder 98 for outputting a selection signal for selecting one of the switches SW2. An address signal is supplied from the cassette control unit 50 to the address decoder 98. The A / D converter 100 is connected to the multiplexer 96, and radiation image information converted into a digital signal by the A / D converter 100 is supplied to the cassette control unit 50.

  Thereafter, when wireless transmission from the cassette body transceiver 52 is performed, part or all of the radiation image information from the cassette controller 50 is supplied to the cassette body transceiver 52. In addition, when performing wireless transmission from a casing transmission unit to be described later, a part or all of the radiation image information is supplied to a communication / power supply I / F 102 that is electrically connected to the casing 32 via a connector 58a. Is done.

  FIG. 5 is a configuration block diagram of the radiographic image capturing system 10 in which the electronic cassette 24 according to the present embodiment is incorporated. The console 28 is connected to a radiology information system (RIS) 29 for comprehensively managing radiographic image information and other information handled in the radiology department in the hospital. A medical information system (HIS) 31 for comprehensively managing information is connected.

  The radiographic image acquisition system 141 incorporated in the radiographic image capturing system 10 receives radiography from the radiation source 112 that outputs the radiation X by the operation of the radiographing switch 110 and the console transceiver 133 of the console 28 by radio communication. On the other hand, the radiation source 112 is controlled based on the transmitter / receiver 114 that transmits an imaging completion signal or the like by wireless communication to the console 28, the imaging start signal supplied from the imaging switch 110, and the imaging conditions supplied from the transceiver 114. The radiation source controller 116 that detects the radiation X transmitted through the patient 14, the address decoder 90 (see FIG. 4) of the line scan driver 88 that constitutes the radiation detector 44, and the address of the multiplexer 96. Supply address signal to decoder 98 (see FIG. 4) The address signal generator 118, the image memory 122 for storing the radiation image information detected by the radiation detector 44, the cassette ID memory 124 for storing the cassette ID information for specifying the cassette body 30, and the image memory 122. And a memory 120 having a cassette ID memory 124. The imaging conditions are conditions for determining a tube voltage, a tube current, an irradiation time, and the like for irradiating radiation X having an appropriate dose to an imaging region of the patient 14. And conditions such as a photographing method.

  The cassette body transmission / reception system 142 incorporated in the radiographic image capturing system 10 includes an image compression processing unit (not shown) that reduces the amount of information by performing compression processing on the radiation image information stored in the image memory 122, and a compression. A transmission / reception control unit that performs control for dividing the processed radiographic image information into first radiographic image information and second radiographic image information, and transmitting the first radiographic image information and cassette ID information ( Control means) 126 and a cassette body transceiver 52 for transmitting a radiation image signal or the like to the console 28 by wireless communication.

  Further, the casing transmission system 143 incorporated in the radiographic image capturing system 10 includes the above-described image compression processing unit (not shown), the radiographic image information subjected to the compression processing, the first radiographic image information and the second radiographic image information. A transmission / reception control unit 126 that performs control for transmitting the second radiation image information and cassette ID information, and the connector 56a that electrically connects the cassette body 30 and the casing 32 so that they can communicate with each other. 56b, a communication / power supply I / F 102 on the cassette body 30 side, a communication / power supply I / F 128 on the casing 32 side, and a casing transmission unit for transmitting a radiation image signal or the like by wireless communication to the console 28 (second Wireless means) 130.

  Furthermore, the power supply system 144 incorporated in the radiographic imaging system 10 is configured so that the radiation detector 44, the cassette control unit 50, the cassette body transceiver 52, the communication / power I / F 102, and the memory 120 are manually operated by the power switch 54. A built-in battery 48 that switches power supply, an external battery 68 that switches power supply to the communication / power I / F 128 and power auxiliary circuit 132 on the casing 32 side by manual operation of the power switch 70, and communication on the casing 32 side The power supply auxiliary circuit 132 that supplies power to the power supply I / F 128 and the casing transmission unit 130 or charges the built-in battery 48 is electrically connected to the cassette body 30 and the casing 32. Connectors 56a and 5 that enable power supply to 30 Comprising b and a communication, power supply I / F102 of the cassette body 30, and a communication of the casing 32 side, the power I / F 128.

  Furthermore, the radiographic image display system 146 incorporated in the radiographic imaging system 10 includes a console transceiver 133 that receives a transmission radio wave (radiological image information) from the cassette body transceiver 52 or the casing transmission unit 130, and a console transceiver 133. A control unit 134 that controls radio communication, a receiver 136 that receives radiographic image information from the console 28, a display control unit 138 that performs display control of the received radiographic image information, and a radiographic image processed by the display control unit 138 And a display unit 140 for displaying information.

  FIG. 6 is a block diagram of a cassette transmission / reception system 148 configured by the electronic cassette 24 according to the present embodiment. Here, the cassette transmission / reception system 148 includes the cassette body transmission / reception system 142 and the casing transmission system 143 described above.

  The cassette body transmission / reception system 142 is basically composed of a CPU 150 and a cassette body transmission / reception device 52 that transmits and receives radiation image information by radio signals. The cassette body transceiver 52 includes an antenna 152 that transmits radio waves (RF signals) and an RF circuit (first signal conversion unit) 154 that modulates / demodulates signals.

  The RF circuit 154 obtains data (radiation image information) read from the image memory 122 (see FIG. 5), modulates the data into an intermediate frequency signal (IF signal), and the baseband. A transmission circuit 158 that converts the IF signal supplied from the processing circuit 156 into an RF signal, and a switch 160 that switches a transmission destination of the RF signal supplied from the transmission circuit 158 based on an instruction from the baseband processing circuit 156. And an antenna duplexer 161 for supplying the RF signal to the antenna 152 as a transmission signal.

  Further, the RF circuit 154 obtains an RF signal from the console 28 (see FIG. 5) via the antenna 152, and converts the RF signal supplied from the antenna duplexer 161 into an IF signal. A receiving circuit 162 and a baseband processing circuit 156 that demodulates the IF signal and acquires data (radiation image information) are provided.

  The casing transmission system 143 basically includes a CPU 150 and a casing transmission unit 130. The casing transmission unit 130 amplifies the RF signals supplied from the antennas 64a and 64b and the cassette body transceiver 52. An AMP circuit 164.

  The AMP circuit 164 includes an amplifier 166 that amplifies the RF signal supplied by switching the switch 160, and a destination of the RF signal supplied from the cassette body transceiver 52 based on an instruction from the CPU 150 (either of the antennas 64a and 64b). And a switch 168 for switching.

  Further, the cassette body transceiver 52 and the casing transmission unit 130 can be set to have different channels. For example, in IEEE802.11g, 6 ch (2427 to 2452 Hz) can be assigned to the cassette body transceiver 52 and 11 ch (2452 to 2472 Hz) can be assigned to the casing transmitter 130 so that the carrier frequency bands do not overlap each other. .

  Further, as a method of setting different channels between the cassette body transceiver 52 and the casing transmission unit 130, it is needless to say that not only frequency division as described above but also time division can be set.

  As described above, the cassette transmission / reception system 148 of the electronic cassette 24 is configured.

  FIG. 7 is a block diagram of the power supply system 144 configured by the electronic cassette 24 according to the present embodiment. In FIG. 7, power is supplied in the direction of the arrow.

  The built-in battery 48 supplies power to the CPU 150 and the RF circuit 154 on the cassette body side. The external battery 68 supplies power to the power auxiliary circuit (charging means) 132, the CPU 150, and the RF circuit 154 on the cassette body 30 side. The power auxiliary circuit 132 supplies power to the CPU 150 and the AMP circuit 164 on the casing 32 side.

  The built-in battery 48 is supplied with power from the power auxiliary circuit 132 of the casing 32 and can be charged (thick arrow). Furthermore, the external battery 68 can be removed from the casing 32 and charged using a charger (not shown).

  As described above, the power supply system 144 of the electronic cassette 24 is configured.

  The built-in battery 48 is preferably a small capacity and small size battery. For example, a small lithium ion battery can be used.

  The external battery 68 is preferably a detachable large capacity battery. For example, a large-capacity lithium battery, a fast-charging capacitor type, or a battery having both functions can be used.

  Furthermore, the external battery 68 can be charged without being detached from the casing 32. In such a case, the casing 32 can be rapidly charged by providing an electronic circuit capable of managing the charging voltage, current, and temperature inside the casing 32. Furthermore, in order to operate the casing 32 stably, it is preferable to design the apparatus in consideration of heat dissipation. Furthermore, when using a capacitor suitable for rapid charging, a voltage converter can be provided in the casing 32 in order to prevent voltage fluctuations that occur during charging.

  The radiographic imaging system 10 according to this embodiment is basically configured as described above. Next, the operation is performed using the electronic cassette 24 according to this embodiment shown in FIGS. 8 and 9. This will be described with reference to a diagram (flow chart) showing a photographing workflow.

  The doctor 18 selects an imaging type using the electronic cassette 24. Here, from the viewpoint of the load received by the electronic cassette 24, the shooting mode using the portable electronic cassette 24 is taken without applying a load to the electronic cassette 24 (hereinafter referred to as shooting type 1). This is roughly divided into a case where the electronic cassette 24 is directly laid on the patient 14 for imaging (hereinafter referred to as imaging type 2).

  FIG. 8 shows a flowchart when the photographing type is 1. Here, the shooting type 1 is a shooting mode in which shooting is performed only with the cassette body 30 without using the casing 32.

  First, the doctor 18 checks the remaining battery level of the cassette body 30 used for imaging (step S11). When the lighting state of the lamp 56 provided in the cassette body 30 is confirmed and it is determined that the remaining power of the built-in battery 48 is insufficient, the casing 32 is attached to the cassette body 30 to charge the cassette body 30. Is performed (step S12).

  As shown in FIG. 3, the doctor 18 holds the cassette body 30 and inserts the casing 32 into the cassette body 30 when the doctor 18 is inserted in the direction of the arrow from the opening 66 with the short side surface provided with the connector 58a as the head. Can do. At this time, since the connector 58a of the cassette body and the connector 58b of the casing 32 are fitted, the cassette body 30 and the casing 32 are electrically connected.

  Further, it is checked whether or not there is a spare cassette body 30 having a sufficient remaining power of the built-in battery 48 (step S13). If there is no spare cassette body 30, the charging of the cassette body 30 with the casing 32 attached is completed. It waits until it does (step S14).

  As shown in FIG. 7, since power is supplied to the built-in battery 48 from the power auxiliary circuit 132 of the casing 32 via the power / communication I / Fs 128 and 108 (see FIG. 5), the built-in battery of the cassette body 30 is provided. 48 can be charged (thick arrows). After the charging of the cassette body 30 is completed, the doctor 18 grasps the cassette body 30 and pulls it out from the opening 66 in the direction opposite to the arrow direction, as shown in FIG. 3, and removes the casing 32 from the cassette body 30. Can do.

  On the other hand, when the lighting state of the lamp 56 provided in the cassette body 30 is confirmed and it is determined that the remaining power of the built-in battery 48 is sufficient, or when there is a reserve of the cassette body 30, type 1 shooting is performed. Start (step S15).

  As shown in FIG. 5, after moving the photographing device 22 to a position facing the electronic cassette 24, the photographing switch 110 is operated to perform photographing.

  The radiation source control unit 116 of the imaging apparatus 22 acquires the imaging conditions relating to the imaging region of the patient 14 from the console 28 via the console transceiver 133 and the transceiver 114 by wireless communication, and the radiation source according to the acquired imaging conditions. By controlling 112, the patient 14 is irradiated with radiation X having a predetermined dose.

  As shown in FIG. 4, the radiation X transmitted through the patient 14 is irradiated to the radiation detector 44, converted into an electric signal by the photoelectric conversion layer 81 of each pixel 80 constituting the radiation detector 44, and stored in the storage capacitor 83. It is held as a charge (see FIG. 4). Next, the charge information, which is the radiation image information of the patient 14 held in each storage capacitor 83, is in accordance with the address signal supplied from the address signal generator 118 constituting the cassette controller 50 to the line scan driver 88 and the multiplexer 96. Read out.

  That is, the address decoder 90 of the line scan driver 88 outputs a selection signal according to the address signal supplied from the address signal generator 118 to select one of the switches SW1, and the TFT 82 connected to the corresponding gate line 84. A control signal Von is supplied to the gates of the two. On the other hand, the address decoder 98 of the multiplexer 96 outputs a selection signal in accordance with the address signal supplied from the address signal generation unit 118, sequentially switches the switch SW2, and is connected to the gate line 84 selected by the line scan driving unit 88. Radiation image information that is charge information held in the storage capacitor 83 of each pixel 80 is sequentially read out via the signal line 86.

  The radiation image information read from the storage capacitor 83 of each pixel 80 connected to the selected gate line 84 of the radiation detector 44 is amplified by each amplifier 92 and then sampled by each sample and hold circuit 94. The signal is supplied to the A / D converter 100 via the multiplexer 96 and converted into a digital signal. The radiographic image information converted into the digital signal is temporarily stored in the image memory 122 of the cassette control unit 50.

  Similarly, the address decoder 90 of the line scan driving unit 88 sequentially switches the switch SW 1 in accordance with the address signal supplied from the address signal generating unit 118, and the storage capacitor 83 of each pixel 80 connected to each gate line 84. The stored radiation image information, which is charge information, is read out via the signal line 86 and stored in the image memory 122 via the multiplexer 96 and the A / D converter 100.

  As shown in FIGS. 5 and 6, the stored radiation image information is read from the image memory 122 and supplied to the RF circuit 154 of the cassette body transceiver 52 by transmission control of the transmission / reception controller 126. The radiographic image information supplied to the RF circuit 154 is modulated into an IF signal via the baseband processing circuit 156 and converted from the IF signal to an RF signal via the transmission circuit 158. Since the switch 160 can be switched to the antenna 152 side based on an instruction from the CPU 150, the RF signal is supplied to the antenna 152 via the antenna duplexer 161, and a radio signal having the console 28 as a transmission destination is transmitted.

  The radiographic image information transmitted to the console 28 is received by the console transceiver 133, subjected to predetermined image processing by the control unit 134, and associated with the patient information of the patient 14, and then displayed from the console transceiver 133. Transmitted to the device 26. The display device 26 that has received the radiation image information by the receiver 136 controls the display unit 140 by the display control unit 138 and displays the radiation image on the display unit 140.

  When there is a next imaging request, the doctor 18 repeats the imaging preparation (step S17) and the imaging operation (step S15). When shooting is finished, the cassette body 30 is charged, the casing 32 is charged, or the power is turned off, and the work is finished.

  Since the charging of the built-in battery 48 of the cassette body 30 is started when the casing 32 is attached to the cassette body 30 as described above, detailed description thereof is omitted here. Alternatively, when the remaining power of the external battery 68 is insufficient due to the charging operation of the cassette body (step S14) or the like, the doctor 18 removes the external battery 68 from the casing 32 and charges it using a charger (not shown). May be. Alternatively, the power switch 54 of the cassette body 30 may be manually switched off.

  FIG. 9 shows a flowchart when the photographing type is 2. Here, the shooting type 2 is a shooting mode in which shooting is performed with the casing 32 attached to the cassette body 30.

  The radiographic image capturing system 10 is installed in the operating room 12 and is used, for example, when a radiographic image needs to be captured during surgery of the patient 14 by the doctor 18. Therefore, the patient information of the patient 14 to be imaged is registered in advance in a patient information management unit (not shown) of the console 28 before imaging. Further, when the imaging region and the imaging method are determined in advance, these imaging conditions are registered in advance in an imaging condition management unit (not shown). In the state where the above preparatory work is completed, an operation on the patient 14 is performed.

  When radiographing is performed during surgery, the doctor 18 or the radiologist 18 in charge of the electronic cassette 24 at a predetermined position between the patient 14 and the operating table 16 with the irradiation surface 40 facing the imaging apparatus 22 side. And the power switch 70 of the casing 32 is turned on.

  First, the doctor 18 checks the remaining battery level of the casing 32 used for imaging (step S21). When the lighting state of the lamp 72 provided in the casing 32 is confirmed and it is determined that the remaining power of the external battery 68 is insufficient, the external battery 68 of the casing 32 is attached to a charger (not shown). Then, the casing 32 is rapidly charged (step S22).

  After confirming that the remaining power of the external battery 68 of the casing 32 is sufficient, the casing 32 is attached to the cassette body 30 used for photographing (step S23), and type 2 photographing is started (step S24).

  It is determined whether or not there is a next imaging request (step S25). If there is a next imaging request, the radiographic image information acquired by the imaged image memory 122 and the cassette ID memory 124 is wirelessly multiplexed and transmitted (step S26). . Until imaging is completed, the doctor 18 repeats the next imaging preparation (step S27) and imaging operation (step S24).

  The method of attaching and detaching the casing 32 to and from the cassette body 30 and the operating principle of charging the cassette body 30 and the operating principle until the radiation image signal is stored in the image memory 122 after the radiation X is applied to the patient 14 are described above. The description is omitted for convenience.

  The multiplex transmission described above (step S26) means simultaneous transmission by the cassette body transceiver 52 and the casing transmission unit 130. The radiation image information stored in the image memory 122 is read from the image memory 122 and divided into first radiation image information and second radiation image information by the transmission / reception control unit 126. The transmission / reception control unit 126 determines the division ratio of the radiation image information of the cassette body transceiver 52 and the casing transmission unit 130. Although this distribution ratio may be set to a fixed value in advance, it is preferable to determine the optimum value in consideration of the theoretical value, estimated value, actual measurement value, etc. of the current communication speed.

  By the transmission control of the transmission / reception control unit 126, the first radiation image information is transmitted to the console 28 by wireless communication via the cassette body transceiver 52. The operation principle is as described above, and the description is omitted for convenience.

  Further, as shown in FIGS. 5 and 6, the stored second radiation image information is read from the image memory 122 and transmitted to the RF circuit 154 of the cassette body transceiver 52 by the transmission control of the transmission / reception control unit 126. Supplied. The radiographic image information supplied to the RF circuit 154 is modulated into an IF signal via the baseband processing circuit 156 and converted from the IF signal to an RF signal via the transmission circuit 158. Since the switch 160 can be switched to the antennas 64a and 64b based on the instruction of the CPU 150, the RF signal is transmitted to the AMP circuit of the casing 32 via the communication / power I / F 102, the connectors 58a and 58b, and the communication / power I / F 128. 164.

  The RF signal supplied to the AMP circuit 164 is amplified via the amplifier 166. Since the switch 160 can be switched to either the antenna 64a side or the 64b side based on an instruction from the CPU 150, the amplified RF signal is supplied to the antenna 64a (64b), and a radio signal having the console 28 as a transmission destination is transmitted. Sent.

  Here, since the cassette body transceiver 52 and the casing transmission unit 130 are set to have different channels, multiplex transmission is possible, and the load (data amount) of wireless communication per channel is reduced and transmission / reception is performed. Time can be shortened.

  The first and second radiographic image information transmitted to the console 28 is received by the console transmitter / receiver 133, reconstructed into the original radiographic image information by the control unit 134, subjected to predetermined image processing, and the patient 14 After being associated with the patient information, the information is transmitted from the console transceiver 133 to the display device 26. The display device 26 that has received the radiation image information by the receiver 136 controls the display unit 140 by the display control unit 138 and displays the radiation image on the display unit 140.

  It is determined whether or not there is a next imaging request (step S25). If there is no next imaging request, the radiographic image information is transmitted wirelessly (step S28). The doctor 18 selects either single transmission (transmitting in the better communication state of the cassette body 30 or the casing 32) or multiple transmission (simultaneous transmission by the cassette body 30 and the casing 32).

  When wireless transmission is performed by the casing 32 alone, the radiation image information stored in the image memory 122 is read from the image memory 122, and the communication / power I / F 102, the connectors 58a and 58b, the communication / power I / F 128, The data is transmitted to the console 28 by wireless communication via the casing transmission unit 130.

  The doctor 18 performs the final operation of charging the cassette body 30, charging the casing 32, or turning off the power (the cassette body 30 and the casing 32) after the imaging is finished (step S29).

  Note that the charging operation and operation of the cassette body 30 or the casing 32 are the same as those in the photographing type 1, and thus detailed description thereof is omitted.

  The radiographic image capturing system 10 and the electronic cassette 24 according to the present embodiment are not limited to the above description, and can be changed to various configurations. Modifications (first modification to fourth modification) of the present embodiment will be described with reference to FIGS. In the following modifications, the same components as those in the present embodiment are denoted by the same reference numerals, detailed description thereof is omitted, and the same applies hereinafter.

  First, a first modification will be described with reference to FIGS. The first modification differs from the present embodiment in the configurations of the casing 32 shown in FIG. 5, the cassette transmission / reception system 148 shown in FIG. 6, and the power supply system 144 shown in FIG.

  FIG. 10 is a configuration block diagram of the radiographic image capturing system 10 in which the electronic cassette 24 according to the first modification is incorporated.

  The casing transmission / reception system 145 incorporated in the radiographic image capturing system 10 divides the above-described image compression processing unit (not shown) and the radiographic image information subjected to the compression processing into first radiographic image information and second radiographic image information. The transmission / reception control unit 126 that performs control for transmitting the second radiation image information and the cassette ID information, and the connectors 56a and 56b that electrically connect the cassette body 30 and the casing 32 so that they can communicate with each other. A casing transmitter / receiver (second wireless means) for transmitting / receiving a radiographic image signal or the like by wireless communication to / from the console main body 30 side communication / power I / F 102, casing 32 side communication / power I / F 128, and console 28. 170).

  FIG. 11 is a block diagram of a cassette transmission / reception system 148 configured by the electronic cassette 24 according to the first modification. Here, the cassette transmission / reception system 148 includes a cassette body transmission / reception system 142 and a casing transmission / reception system 145.

  First, the cassette body transceiver system 142 is basically composed of a CPU 150 and a cassette body transceiver 52 (see FIG. 5), and the cassette body transceiver 52 transmits and receives RF signals to and from the antenna 152. And an RF circuit 154. Further, the RF circuit 154 includes a baseband processing circuit 156 that controls transmission / reception of radio waves, a transmission circuit 158, an antenna duplexer 161, and a reception circuit 162.

  Secondly, the casing transmission / reception system 145 basically includes a CPU 150 provided in the cassette body 30 and a casing transmission / reception unit 170, and the casing transmission / reception unit 170 transmits and receives RF signals to and from the antennas 64a and 64b. And an RF circuit 172.

  The RF circuit 172 acquires data (radiation image information) read from the image memory 122 (see FIG. 5), modulates the data into an intermediate frequency signal (IF signal), and the baseband. A transmission circuit 176 that converts the IF signal supplied from the processing circuit 174 to an RF signal, an amplifier 178 that amplifies the RF signal converted by the transmission circuit 176, and an amplifier 178 based on an instruction from the CPU 150 And a switch 180 for switching the transmission destination of the RF signal.

  In addition, the RF circuit 172 switches the reception destination to one of the antennas 64a (64b) received from the console 28 (see FIG. 5), and the RF signal received by the antenna 64a (64b). An amplifier 182 to be amplified, a receiving circuit 184 that converts an RF signal amplified by the amplifier 182 into an IF signal, and a baseband processing circuit 174 that demodulates the IF signal and obtains data (radiation image information).

  Since it comprises in this way, the following transmission / reception processes of radiographic image information can be performed.

  First, wireless communication by the cassette body transceiver 52 included in the cassette body 30 is realized as follows.

  As shown in FIGS. 10 and 11, the stored radiation image information is read from the image memory 122 and supplied to the RF circuit 154 of the cassette body transceiver 52 by transmission control of the transmission / reception control unit 126. The radiographic image information supplied to the RF circuit 154 is modulated into an IF signal via the baseband processing circuit 156 and converted from the IF signal to an RF signal via the transmission circuit 158. The RF signal is supplied to the antenna 152 through the antenna duplexer 161, and a radio signal having the console 28 as a transmission destination is transmitted.

  On the other hand, a radio signal from the console 28 is received by the antenna 152 and supplied to the antenna duplexer 161 as an RF signal. The RF signal is supplied to the receiving circuit 162 via the antenna duplexer 161 and converted into an IF signal by the receiving circuit 162. The IF signal is demodulated through a baseband processing circuit 156 and acquired as digital data. Thereafter, the digital data is stored in the memory 120 as required by the reception control of the transmission / reception control unit 126.

  Second, wireless communication by the casing transceiver 170 provided in the casing 32 is realized as follows.

  As shown in FIGS. 10 and 11, the stored radiation image information is read from the image memory 122, and the casing transceiver 170 is connected via the communication / power I / F 102, 128 by transmission control of the transmission / reception control unit 126. Is supplied to the RF circuit 172. The radiographic image information supplied to the RF circuit 172 is modulated into an IF signal via the baseband processing circuit 174 and converted from the IF signal to an RF signal via the transmission circuit 176. The RF signal is power amplified via an amplifier 178. Since the switch 180 can be switched to the antenna 64a side (64b side) based on an instruction from the CPU 150, the RF signal is supplied to the antenna 64a (64b), and a radio signal having the console 28 as a transmission destination is transmitted.

  In addition, in order to select one antenna used for transmission of a radio wave among several antennas 64a and 64b, it is possible to take various structures.

  For example, when transmitting radiographic image information from the casing 32, the antenna 64a used for transmitting the RF signal based on a test signal transmitted / received between the casing transceiver 170 and the console transceiver 133 regularly / non-periodically One of 64b can be selected. Specifically, immediately before starting transmission of data stored in the image memory 122, a test signal is transmitted from the casing transmission unit 130 to the console transceiver 133 via the antennas 64a and 64b, and the console The antenna 64a (64b) having a shorter reception completion time of 28 can be selected.

  On the other hand, a radio signal from the console 28 is received by the antenna 64a (64b). Here, in order to select one antenna to be used for receiving radio waves from among the plurality of antennas 64a and 64b, a communication technique (so-called diversity) that preferentially uses an antenna having excellent radio wave conditions for the same radio signal is used. Can do.

  The RF signal received from the antenna 64a (64b) is supplied to the amplifier 182 and is amplified by the amplifier 182. The amplified RF signal is supplied to the reception circuit 184 and converted into an IF signal by the reception circuit 184. The IF signal is demodulated through the baseband processing circuit 174 and acquired as digital data. Thereafter, the digital data is stored in the memory 120 as required by the reception control of the transmission / reception control unit 126.

  FIG. 12 is a block diagram of a power supply system 144 configured by the electronic cassette 24 according to the first modification. In FIG. 12, power is supplied in the direction of the arrow.

  The built-in battery 48 supplies power to the CPU 150 and the RF circuit 154 on the cassette body side. The external battery 68 supplies power to the power auxiliary circuit 132 and the CPU 150. The power auxiliary circuit 132 supplies power to the CPU 150, the RF circuit 154 on the cassette body 30 side, and the RF circuit 172 on the casing 32 side.

  The built-in battery 48 is supplied with power from the power auxiliary circuit 132 of the casing 32 and can be charged (thick arrow). Furthermore, the external battery 68 can be removed from the casing 32 and charged using a charger (not shown).

  Since it comprises in this way, the following electric power supply can be performed.

  When the casing 32 is not attached to the cassette body 30, the built-in battery 48 supplies power to the CPU 150 and the RF circuit 154 on the cassette body side. Thereby, the cassette main body 30 can be operated.

  On the other hand, when the casing 32 is attached to the cassette body 30, the built-in battery 48 or the external battery 68 supplies power to the CPU 150, the RF circuit 154 on the cassette body 30 side, and the RF circuit 172 on the casing 32 side. As a result, the cassette body 30 can be operated if the power of either the internal battery 48 or the external battery 68 remains. When the power switch 70 of the casing 32 is turned on regardless of whether the power switch 54 of the cassette body 30 is turned on or off, the built-in battery 48 can be charged via the power auxiliary circuit 132.

  Furthermore, when the electric power of the external battery 68 is exhausted, it can be removed from the casing 32 and charged using another charger (not shown).

  The cassette main body transceiver 52 is preferably a low power consumption type wireless module having a small size. For example, infrared communication, IrDA, Bluetooth, IEEE802.11V, USB type can be used. Furthermore, power consumption can be suppressed by setting the sleep mode so that the time interval during which no radio wave is transmitted is long.

  The casing transceiver 170 is not limited to the IEEE802.11V, USB type, and various wireless modules such as IEEE802.11g can also be used.

  Next, a second modification will be described with reference to FIGS. 13 and 14. 13 is a perspective view of the electronic cassette 24 according to the second modification, FIG. 14A is a front view of the electronic cassette 24 according to the second modification, and FIG. 14B is a cross-sectional view taken along the line XIVB-XIVB of the electronic cassette 24 shown in FIG. It is. The second modification is different from the present embodiment in the configurations of the cassette body 30 and the casing 32 shown in FIG.

  As shown in FIG. 13, the electronic cassette 24 includes a cassette body 30 and a casing 32. The casing 32 has a rectangular main body 200, and the main body 200 has an opening 202 that opens greatly on one side surface. A support portion 204 is provided above the opening 202, and a movable claw 208 and a slider 210 that displaces the movable claw 208 are provided on the support portion 204. A handle 212 is provided at the top of the main body 200. The cassette body 30 that fits into the opening 202 has two protrusions 206 formed on the bottom surface of the body 200 that forms the opening 202. The cassette body 30 includes two holes 214 on the lower surface portion and two holes 216 on the upper surface portion.

  Here, the main body 200 is made of magnesium, which is lightweight among metals. As an EMC measure, it is preferable to apply an aluminum foil to the inside of the cover of the irradiation surface 40 and apply conductive coating to the inside of the cover on the back of the irradiation surface 40.

  As shown in FIG. 14A, two conical protrusions 206 are provided on the lower inner wall of the casing 32, and fit into holes 214 formed in the bottom surface of the cassette body 30, respectively. Here, it goes without saying that the means for fitting the cassette body 30 and the casing 32 is not limited to the projection 206 and the hole 214, but may be a groove serving as a recess instead of the hole 214, for example.

  As shown in FIG. 14A, two movable claws 208 are provided in the support portion 204 corresponding to the holes 216 and 216 in the upper portion of the cassette body 30, and are moved downward in FIG. 13 by the coil spring 215. The bullet is energized in the direction. A tapered surface is formed on one side of the movable claw 208. The slider 210 is provided in the vicinity of the movable claw 208, and the tip thereof faces the tapered surface of the movable claw 208. That is, when the tip of the slider 210 is pressed toward the taper surface of the movable claw 208, the movable claw 208 can move upward against the elastic force of the coil spring 215 in the drawing.

  The handle 212 is formed integrally with the main body 200 and has a strength that allows the cassette main body 30 and the casing 32 to be gripped.

  As shown in FIG. 14B, the cassette body 30 has a radiation X incident surface side (irradiation surface 40 side of the protective cover 38) directed to the opening 202 and a surface 218 opposite to the irradiation surface 40 and the casing 32. So as not to come into contact with the back surface 220.

  Since it is configured as described above, the cassette body 30 is attached to the casing 32 in a state in which the hole 214 of the cassette body 30 is fitted to the two protrusions 206 while holding the cassette body 30 with the irradiation surface 40 facing forward. The slider 210 is pressed against the taper surface of the movable claw 208 and moved in the lateral direction close to the back surface 220, lifted against the spring force of the coil spring 215, and then released from the slider 210. 214 is engaged at two places, and the casing 32 can be mounted so as to be locked to the cassette body 30. On the other hand, the cassette body 30 can be removed from the casing 32 if the movable claw 208 is lifted by moving it with the cassette 32 accommodated in the casing 32 and the movable claw 208 is detached from the hole 216. In this way, the casing 32 can be attached and detached in the horizontal direction with respect to the incident direction of the radiation X of the cassette body 30.

  Next, a third modification will be described with reference to FIGS. 15 is a perspective view of a cassette body 30 according to a third modification, FIG. 16 is a sectional view taken along line XVI-XVI of the electronic cassette 24 in FIG. 15, and FIG. 17 is a partially omitted plan view of the electronic cassette 24 in FIG. is there. The third modification differs from the present embodiment in the configurations of the cassette body 30 and the casing 32 shown in FIG.

  15 is similar to the electronic cassette 24 shown in FIG. 3. The cassette body 30 is inserted into the casing 32 by inserting the cassette body 30 in the direction of the arrow (FIG. 3) from the opening 66 with the short side surface including the connector 58 a at the head. Shows the housed state. Furthermore, the cassette body 30 and the casing 32 are electrically connected by fitting the connectors 58a and 58b. Since other configurations are substantially the same as those in FIG. 3, detailed description thereof is omitted.

  As shown in FIG. 16, in the cassette body 30, the first member 300 is connected to the second member 306 via the frame member 302, and the radiation detector 44 is disposed in the first chamber 308. Inside the protective cover 38, on the base 309 in the first chamber 308, the radiation X transmitted through the patient 14 is converted into a radiation image, and the converted radiation image is output as an electrical signal (analog signal). The radiation detector 44 is arranged. On the other hand, in the second chamber 310, the lead plate (shielding member) 46 that absorbs the back scattered radiation of the radiation X, and the analog signal output from the radiation detector 44 via the flexible substrate 312 are amplified. A circuit board 316 on which an electronic component 314 for performing the above is mounted is disposed.

  In this case, the circuit board 316 is disposed via the plurality of cylindrical spacers 318 with respect to the lead plate 46 that is in contact with the bottom surface of the base 309, and the circuit board 316, the spacer 318, and the lead plate 46 are interposed therebetween. By fastening the screw 322 to the base 309, the circuit board 316, the spacer 318, and the lead plate 46 can be fixed to the base 309 in the second chamber 310. A hole 320 for communicating the first chamber 308 and the second chamber 310 is formed on the frame member 302 side of the base 309. The flexible substrate 312 passes through the hole 320 and is a radiation detector. 44 and the electronic component 314 are electrically connected.

  FIG. 16 illustrates a configuration of a so-called back-illuminated radiation detector 44 in which a scintillator 324 and a photoelectric conversion layer 326 are stacked in this order on the base 309, but the photoelectric conversion layer 326 is formed on the base 309. Alternatively, the surface irradiation type radiation detector 44 may be configured in the order of the scintillator 324.

  On the other hand, the hollow rectangular casing 32 has a main body 60 and accommodates the cassette main body 30. Two stepped portions 328 are provided on the inner wall of the irradiation surface 40 and the bottom surface 304 of the main body 60. As shown in FIG. 17, the circuit boards 316 are arranged in parallel at approximately equal intervals in 3 rows and 3 columns. A cross-shaped rib 330 is formed so as to straddle the circuit board 316 by the four step portions 328 provided in the main body 60 of the casing 32.

  Since it comprised in this way, the casing 32 can achieve weight reduction of the casing 32 whole, ensuring the rigidity which supports the cassette main body 30. FIG.

  In such a case, the uniformity of the irradiation dose of the radiation X detected by the radiation detector 44 is impaired due to the step difference of the step portion 328 provided on the inner wall of the casing 32 on the irradiation surface 40 side. If it does so, there exists a possibility that the shape of the level | step-difference part 328 of the casing 32 may be reflected in radiation image information.

  Therefore, it is preferable to perform image correction on the radiation image information obtained by the electronic cassette 24 in consideration of the shape of the step portion 328. Since each casing 32 has a unique stepped portion 328 shape, suitable image correction according to each casing 32 can be performed. For example, it is preferable to associate the serial number of the casing 32 with shape information such as the number, position, size, and depth of the stepped portion 328 in advance and perform image correction using the shape information. It is an aspect.

  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.

DESCRIPTION OF SYMBOLS 10 ... Radiographic imaging system 14 ... Patient 22 ... Imaging device 24 ... Electronic cassette 26 ... Display device 28 ... Console 30 ... Cassette main body 32 ... Casing 38 ... Protective cover 44 ... Radiation detector 48 ... Built-in battery 50 ... Cassette control part 52 ... cassette body transceiver 58a, 58b ... connectors 60, 200 ... body 62a, 62b ... handle 64a, 64b, 152 ... antenna 68 ... external battery 122 ... image memory 124 ... cassette ID memory 130 ... casing transmission part 132 ... power supply assistance Circuit 133 ... Console transceiver 142 ... Cassette body transmission / reception system 143 ... Case transmission system 144 ... Power supply system 148 ... Cassette transmission / reception system 150 ... CPU
154, 172 ... RF circuit 156, 174 ... Baseband processing circuit 158, 176 ... Transmission circuit 160, 168, 180 ... Switch 161 ... Antenna duplexer 162, 184 ... Reception circuit 164 ... AMP circuit 166, 178, 182 ... Amplifier 170 ... Case transceiver 330 ... Rib

Claims (15)

A cassette body comprising: a radiation detector that detects radiation that has passed through the subject and converts it into radiation image information; and an image memory that stores the converted radiation image information;
A casing that is capable of accommodating the cassette body and is electrically connected to the cassette body under the accommodated state of the cassette body;
A radiation detection apparatus comprising:
The cassette body has first wireless means for transmitting the radiographic image information stored in the image memory by wireless communication, and a first battery for supplying power to the cassette body,
The casing includes a second wireless unit that transmits the radiographic image information stored in the image memory by wireless communication, and a second battery that supplies electric power to the cassette body. . The radiation detection apparatus according to claim 1,
The first radio means includes a first signal conversion unit that converts the radiographic image information into a radio frequency signal, and at least one antenna that transmits the radio frequency signal supplied from the first signal conversion unit to the outside. A radiation detection apparatus comprising: a first wireless communication device comprising: The radiation detection apparatus according to claim 2.
The radiation detecting apparatus according to claim 2, wherein the second radio unit is at least one antenna that transmits the radio frequency signal supplied from the first signal conversion unit to the outside. The radiation detection apparatus according to claim 1 or 2,
The second radio means includes a second signal conversion unit that converts the radiographic image information into a radio frequency signal, and at least one antenna that transmits the radio frequency signal converted by the second signal conversion unit to the outside. A radiation detection apparatus comprising: a second wireless communication device comprising: The radiation detection apparatus according to any one of claims 1 to 4,
The cassette main body divides the radiographic image information into first radiographic image information and second radiographic image information, supplies the second radiographic image information to the casing, and transmits the first radiographic image information to the casing. A radiation detection apparatus comprising: control means for transmitting the second radiological image information by the second radio means by means of first radio means. The radiation detection apparatus according to any one of claims 1 to 5,
The radiation detecting apparatus, wherein the first wireless unit transmits the radiation image information through a channel different from the channel of the second wireless unit. The radiation detection apparatus according to any one of claims 2 to 4,
The said casing has an amplifying means which amplifies the electric power of the radio frequency signal converted from the said radiographic image information. The radiation detection apparatus characterized by the above-mentioned. The radiation detection apparatus according to claim 4.
The radiation detecting apparatus according to claim 1, wherein the first wireless communication device has lower power consumption and smaller size than the second wireless communication device. The radiation detection apparatus according to any one of claims 1 to 5,
The radiation detection apparatus according to claim 1, wherein the first battery has a smaller power capacity and a smaller size than the second battery. The radiation detection apparatus according to any one of claims 1 to 5,
The casing includes a charging unit that charges the first battery using electric power supplied from the second battery. The radiation detection apparatus according to any one of claims 1 to 5,
The said casing has a holding part, and accommodates the said cassette main body so that it can attach or detach to a perpendicular | vertical direction with respect to the radiation incident direction of the said cassette main body. The radiation detection apparatus characterized by the above-mentioned. The radiation detection apparatus according to any one of claims 1 to 5,
The said casing has a holding part, and accommodates the said cassette main body so that it can attach or detach in a horizontal direction with respect to the radiation incident direction of the said cassette main body. The radiation detection apparatus characterized by the above-mentioned. The radiation detection apparatus according to any one of claims 1 to 5,
The said casing has a rib of the shape which straddles the some circuit board which the said cassette main body has in the state which accommodates the said cassette main body in the inner wall of this casing. The radiation detection apparatus characterized by the above-mentioned. The radiation detection apparatus according to any one of claims 1 to 5,
The casing has a rectangular shape, and has at least one antenna at a corner of the casing. The radiation detection apparatus according to claim 11 or 12,
The casing includes at least one antenna in the grip portion.

Images