JP2009183561A - Radiation image capturing system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To shorten a capturing time, to suppress consumption of a battery when using the battery and to improve work efficiency by shortening the time after specifying a radiation detector and before starting capturing. <P>SOLUTION: In the radiation image capturing system 10 provided with a radiation source and two or more electronic cassettes, a magnetic field generation part is installed to the radiation source, and a three-dimensional magnetic sensor 200 is installed inside the electronic cassette 28. The cassette control part 52 of the electronic cassette 28 is provided with a capturing possibility discrimination part 94 for discriminating whether or not shifting to a capturing-possible mode can be performed, a distance operation part 202 for arithmetically operating distance data Ld to the radiation source on the basis of output data from the three-dimensional magnetic sensor 200, an activation processing part 204 for performing activation processing when specified that it is the suitable electronic cassette 28 from a console 34, and a display control part 206 for controlling display on a display part 62. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates to a radiographic image capturing system using a radiation converter for capturing a radiographic image by irradiating a subject with radiation.

  2. Description of the Related Art In the medical field, a radiation image capturing apparatus that irradiates a subject with radiation and guides the radiation transmitted through the subject to a radiation conversion panel to capture a radiation image is widely used.

  In this case, the radiation conversion panel is a conventional radiation film in which a radiation image is exposed and recorded, or radiation energy as a radiation image is accumulated in a phosphor and irradiated with excitation light, and the radiation image is then emitted as a stimulating light. A storage phosphor panel that can be taken out as is known. These radiation conversion panels supply a radiation film on which a radiographic image is recorded to a developing device to perform development processing, or supply a stimulable phosphor panel to a reading device to perform reading processing so that a visible image can be obtained. A radiographic image is obtained.

  On the other hand, in a medical field such as an operating room, in order to perform a quick and accurate treatment on a patient, it is required that a radiation image can be read and displayed immediately from the radiation conversion panel. Radiation conversion 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 as a radiation conversion panel that can meet such requirements Panels are being developed.

  Such a radiation conversion panel is housed in a housing and used as a radiation detector. When a plurality of radiation detectors are prepared, for example, one selected arbitrarily from the plurality of radiation detectors. It is conceivable to use a radiation detector. As a method for selecting one radiation detector from a plurality of radiation detectors, for example, a method described in Patent Document 1 can be cited.

  In this method, from a cassette ID information given to a plurality of radiation converters stored in a cassette storage box, a radiation converter optimal for photographing a predetermined radiation image is displayed on a display device, and a doctor or a radiologist Based on the display content of the display device, the corresponding radiation converter is taken out from the cassette storage box.

Japanese Patent Laid-Open No. 2002-248095

  However, since the method described in Patent Document 1 specifies a radiation converter selected by a doctor or the like based on the display content of the display device, for example, when a plurality of radiation converters are installed in a distributed manner. It is necessary to find where the specified radiation detector is, and if the found radiation detector happens to be in a position far from the radiation source, it takes time to carry it and put the patient in the imaging room. There is a problem that it takes time to actually start shooting.

  In the case of a radiation detector containing a battery, if it takes time to search for the radiation detector and to carry it, the battery may be consumed and imaging may not be possible.

  The present invention has been made in view of the above problems, and can shorten the time from the identification of the radiation detector to the start of imaging, in the case of shortening the imaging time or using a battery. It is an object of the present invention to provide a radiographic imaging system that can suppress battery consumption and increase work efficiency.

The radiation detection cassette according to the present invention includes a radiation source,
In a radiographic imaging system having a housing and two or more radiation converters having a housing and a radiation conversion panel that detects radiation from a radiation source that has passed through the subject and converts the radiation into radiation image information ,
Distance measuring means for measuring each distance from the radiation source to the two or more radiation converters;
And a notifying unit for notifying distance information about the radiation converter based on a measurement result of the distance measuring unit.

  In this case, the notification unit may select and notify the radiation converter closest to the radiation source among the two or more radiation converters.

  According to the present invention, it is possible to reduce the time from the identification of the radiation detector to the start of imaging, and to shorten the imaging time or to suppress the battery consumption when using a battery. Can improve work efficiency.

  Hereinafter, an embodiment of a radiographic image capturing system according to the present invention will be described with reference to FIGS.

  As shown in FIG. 1, the radiographic imaging system 10 according to the present exemplary embodiment controls a radiation source 24 that irradiates a patient 22 (subject) with radiation X having a dose according to imaging conditions, and the radiation source 24. The radiation source cassette 26, a radiation detection cassette (hereinafter referred to as an electronic cassette 28) having a built-in radiation detector (radiation conversion panel) for detecting the radiation X transmitted through the patient 22, and a charging process for the electronic cassette 28 are performed. The portable information terminal 32 which has an imaging switch of the cradle 30 and the radiation source 24, and is held by an engineer for checking the state including imaging work, the radiation source control device 26, the electronic cassette 28, the cradle 30, and the portable information terminal 32 And a console 34 (control device) that exchanges necessary information.

  The radiation source 24, the radiation source control device 26, and the cradle 30 are disposed in the imaging room 36, and the console 34 is disposed in the operation room 38 outside the imaging room 36. Necessary information is transmitted and received between the radiation source control device 26, the electronic cassette 28, the cradle 30, the portable information terminal 32, and the console 34 by wireless communication.

  As shown in FIG. 2, when there are a plurality of electronic cassettes 28 in the photographing room 36, the electronic cassettes 28 are randomly installed, stored on a shelf, or placed on a desk or the like. There is a case where FIG. 2 shows an example of the installation state of a plurality of electronic cassettes 28 with the display of shelves, desks, etc. omitted.

  When an engineer performs imaging using the electronic cassette 28, the electronic cassette 28 installed closest to the radiation source 24 is used in order to improve work efficiency.

  Therefore, in this radiographic imaging system 10, the magnetic field generator 39 used to detect the positions of the plurality of electronic cassettes 28 placed in the vicinity is installed in the radiation source 24. As the magnetic field generating unit 39, a permanent magnet may be used, but an electromagnet that can be switched between the generation and the stop of the magnetic field by an external operation so as not to be affected by the magnetic field when the radiation is output from the radiation source is used. It is preferable.

  On the other hand, the electronic cassette 28 includes a housing 40 made of a material that transmits the radiation X, as shown in FIG. Inside the housing 40, a grid 42 for removing scattered radiation of the radiation X by the patient 22 from the irradiation surface side irradiated with the radiation X, and a radiation detector 44 for detecting the radiation X transmitted through the patient 22 (solid detection) Instrument) and a lead plate 46 that absorbs backscattered rays of radiation X are disposed in order.

  Further, as shown in FIG. 4, a battery 48 that is a power source of the electronic cassette 28, a power supply control unit 50 that controls power supply from the battery 48, and a radiation detector 44 are provided inside the housing 40. A cassette control unit 52 that controls driving and a transmission / reception unit 54 that transmits and receives signals including image information of the radiation X detected by the radiation detector 44 to and from the cradle 30, the portable information terminal 32, and the console 34 are accommodated. . The cassette control unit 52 and the transmission / reception unit 54 are preferably provided with a lead plate or the like on the irradiation surface side of the housing 40 in order to avoid damage due to irradiation with the radiation X.

  Further, as shown in FIG. 3, a display unit 62 such as an LED is provided on the side surface of the housing 40. When an LED is used as the display unit 62, for example, a green LED 62a indicating that the electronic cassette is suitable this time is installed. Of course, a red LED 62b may be provided to indicate that the electronic cassette 28 is not suitable this time.

  Further, the housing 40 incorporates a three-dimensional magnetic sensor 200 (see FIG. 6) using, for example, a Hall element that detects a magnetic field generated by a magnetic field generator 39 installed in the radiation source 24.

The output voltages Vx, Vy, Vz of the three-dimensional magnetic sensor 200 are
Vx = S _BX Bsinθcosφ
Vy = S _BY Bsinθsinφ
Vz = S _BZ Bcosθ
It becomes. In the present embodiment, the output voltages Vx, Vy, and Vz are digitally converted and output as X-axis component data Dx, Y-axis component data Dy, and Z-axis component data Dz.

S _BX , S _BY , and S _BZ are the magnetic sensitivities of the Hall elements, θ is the angle from the xy plane to the z direction, and φ is the angle from the xz plane to the y direction.

Therefore, the distance Ld from the magnetic field generator 39 to the electronic cassette 28 can be obtained by calculating the following formula (1).
Ld = √ (Dx ² + Dy ² + Dz ² ) (1)

  As shown in FIG. 4, the radiation detector 44 includes a thin film transistor (TFT) formed of a photoelectric conversion layer 64 made of a substance such as amorphous selenium (a-Se) that senses radiation X and generates charges. ) After the generated charge is stored in the storage capacitor 68, the TFT 66 is sequentially turned on for each row, and the charge is read out as an image signal. In FIG. 3, only the connection relationship between one pixel 70 including the photoelectric conversion layer 64 and the storage capacitor 68 and one TFT 66 is shown, and the configuration of the other pixels 70 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 electronic cassette 28.

  A gate line 72 extending parallel to the row direction and a signal line 74 extending parallel to the column direction are connected to the TFT 66 connected to each pixel 70. Each gate line 72 is connected to a line scanning drive unit 76, and each signal line 74 is connected to a multiplexer 78 constituting a reading circuit.

  Control signals Von and Voff for controlling on / off of the TFTs 66 arranged in the row direction are supplied from the line scanning drive unit 76 to the gate line 72. In this case, the line scan driving unit 76 includes a plurality of switches SW1 for switching the gate lines 72, and a first address decoder 80 for outputting a selection signal for selecting one of the switches SW1. An address signal is supplied from the cassette control unit 52 to the first address decoder 80.

  Further, the charge held in the storage capacitor 68 of each pixel 70 flows out to the signal line 74 through the TFTs 66 arranged in the column direction. This charge is amplified by the amplifier 82. A multiplexer 78 is connected to the amplifier 82 via a sample and hold circuit 84. The multiplexer 78 includes a plurality of switches SW2 for switching the signal lines 74, and a second address decoder 86 that outputs a selection signal for selecting one of the switches SW2. An address signal is supplied from the cassette control unit 52 to the second address decoder 86. An A / D converter 88 is connected to the multiplexer 78, and radiation image information converted into a digital signal by the A / D converter 88 is supplied to the cassette control unit 52.

  Further, an image memory 89 for storing radiation image information detected by the radiation detector 44 is installed in the housing 40 of the electronic cassette 28. The radiation image information is transmitted to the cradle 30, the portable information terminal 32, and the console 34 via the transmission / reception unit 54. The radiographic image information is transmitted in a compressed state as necessary.

  FIG. 5 is a configuration block diagram of the radiographic image capturing system 10. Connected to the console 34 is a radiology information system (RIS) 90 for comprehensively managing radiographic image information and other information handled in the radiology department in the hospital, and the RIS 90 stores medical information in the hospital. A medical information system (HIS) 92 that is centrally managed is connected.

  In addition, as shown in FIG. 6, the power supply control unit 50 of the electronic cassette 28 supplies power to the cassette control unit 52 and the transmission / reception unit 54 based on the ON operation of a switch (not shown). When it is determined that there is an output (when an activation signal Sa is output from an activation processing unit 204 of the cassette control unit 52 described later), control is performed so that power is supplied to the radiation detector 44 and other electronic circuits.

  As shown in FIG. 6, the cassette control unit 52 of the electronic cassette 28 obtains the distance data Ld based on the output data from the image capturing determination unit 94 and the three-dimensional magnetic sensor 200 that determines whether or not the mode can be shifted to the image capturing mode. A distance calculating unit 202 for calculating, an activation processing unit 204 that performs an activation process when the console 34 is designated as a compatible electronic cassette 28, and a display control unit 206 that controls display on the display unit 62. .

  The imaging possibility determination unit 94 determines at least the remaining amount detection unit 96 that detects the remaining amount of the battery 48 and whether or not the detected remaining amount is equal to or greater than a predetermined amount (the amount of power required for one exposure). A remaining amount discriminating unit 98, a dose calculating unit 100 that calculates the cumulative dose of the radiation detector 44, and an exposure dose discriminating unit 102 that discriminates whether or not the calculated cumulative dose exceeds an allowable amount. Have.

  If the remaining amount determination unit 98 determines that the remaining amount is equal to or greater than the predetermined amount and the exposure dose determination unit 102 determines that the cumulative exposure dose does not exceed the allowable amount, the imaging capability determination unit 94 permits When the signal Sc is output and the remaining amount determining unit 98 determines that the remaining amount is less than the predetermined amount, or the exposed dose determining unit 102 determines that the accumulated exposure dose exceeds the allowable amount, A non-permission signal Sd is output from the photographing enable determination unit 94. The permission signal Sc is supplied to the distance calculation unit 202, the display control unit 206, and the transmission / reception unit 54, and the non-permission signal Sd is supplied to the display control unit 206 and the transmission / reception unit 54.

  The distance calculation unit 202 calculates the distance from the electronic cassette 28 to the radiation source 24 (magnetic field generation unit 39) based on the input of the permission signal Sc from the imaging possibility determination unit 94. Specifically, it is obtained by calculating the above-described equation (1) based on the X-axis component data Dx, Y-axis component data Dy, and Z-axis component data Dz output from the three-dimensional magnetic sensor 200. The obtained distance Ld (distance data) is supplied to the transmission / reception unit 54.

  The transmission / reception unit 54 transmits the non-permission signal Sd to the console 34 together with the ID information of the electronic cassette 28 when the non-permission signal Sd is supplied, and when the distance data Ld is supplied together with the permission signal Sc. The permission signal Sc and the distance data Ld are transmitted to the console 34 as transmission information Da regarding the distance together with the ID information of the electronic cassette 28.

  Accordingly, the console 34 can recognize which electronic cassette 28 is in a photographing enabled state by referring to the permission signal Sc or the non-permission signal Sd of the transmission data sent from each electronic cassette 28. .

  As shown in FIG. 3, when the green LED 62 a and the red LED 62 b are installed as the display unit 62, the display control unit 206 displays the red color based on the output of the non-permission signal Sd from the photographing enable determination unit 94. Only the LED 62b is turned on, and based on the output of the permission signal Sc from the photographing enable determination unit 94, only the green LED 62a is turned on, and the start signal Sa is output from the start processing unit 204. For example, control is performed so that only the green LED 62a blinks (flicker display). That is, the display unit 62 and the display control unit 206 function as notification means for notifying that “not imageable”, “capable of imaging”, and “capable of imaging and the electronic cassette closest to the radiation source”. To do.

  On the other hand, as shown in FIG. 5, the first control unit 110 of the cradle 30 controls the charging processing unit 112 that performs the charging process of the battery 48 of the electronic cassette 28, while from the console 34 via the first transmission / reception unit 114. The received information is displayed on the first display unit 116, and the first speaker 118 is sounded as necessary. The first display unit 116 may display the radiographic image information acquired by the electronic cassette 28 as a preview image.

  As shown in FIG. 5, the second control unit 124 of the portable information terminal 32 supplies the imaging signal generated by the imaging switch 126 that drives the radiation source 24 to the radiation source control device 26 via the second transmission / reception unit 128. To do. The second control unit 124 displays information received from the console 34 via the second transmission / reception unit 128 on the second display unit 130 and causes the second speaker 132 to ring as necessary. The second display unit 130 may display radiation image information acquired by the electronic cassette 28 as a preview image. Note that the portable information terminal 32 includes an operation unit 134 that can set necessary information.

  As shown in FIG. 5, the console 34 transmits and receives necessary information to and from the third control unit 142, the radiation source control device 26, the electronic cassette 28, the cradle 30, and the portable information terminal 32 by wireless communication. Transmission / reception unit 144, patient information setting unit 146 for setting patient information, imaging menu setting unit 147 for selecting and setting the imaging region of patient 22 from the imaging menu, and imaging conditions necessary for imaging by the radiation source control device 26 An imaging condition setting unit 148 that sets the image, an image processing unit 150 that performs image processing on the radiographic image information transmitted from the electronic cassette 28, an image memory 152 that stores the processed radiographic image information, and radiographic image information and patient information A third display unit 154 for displaying a shooting menu and the like, and a third speaker 156 for sounding an alarm as necessary.

  The patient information is information for specifying the patient 22 such as the name, sex, and patient ID number of the patient 22. The imaging menu is a menu for selecting an imaging region of the patient 22, and as the imaging region, for example, the head, chest, limbs, etc. of the patient 22 can be raised. The imaging conditions are conditions for determining a tube voltage, a tube current, an irradiation time, and the like for irradiating the imaging region of the patient 22 with radiation X having an appropriate dose. Imaging ordering information including patient information, imaging menus, and imaging conditions can be set directly on the console 34 or supplied externally to the console 34 via the RIS 90.

  Moreover, the 3rd control part 142 of the console 34 has the electronic cassette selection part 208, as shown in FIG.

  The electronic cassette selection unit 208 extracts distance data Ld from transmission information (permission signal Sc, distance data Ld, and ID information) related to the distance sent from the electronic cassette 28 that can be photographed, and out of the extracted distance data Ld. The smallest distance data is detected and transmitted as transmission information Db related to activation via the third transmission / reception unit 144. The transmission information Db related to the activation stores ID information (ID information corresponding to the detected smallest distance data) and matching designation data (designation data indicating that this time is matched).

  In the electronic cassette 28, the transmission information Db related to activation sent from the third transmission / reception unit 144 is received only by the electronic cassette 28 corresponding to the ID information stored in the transmission information Db, and the activation processing of the cassette control unit 52 is performed. Supplied to the unit 204. The activation processing unit 204 supplies the activation signal Sa to the power supply control unit 50 and the display control unit 206 at the stage where the adaptation designation data is detected in the supplied transmission information Db.

  The power supply control unit 50 controls the power supply to the radiation detector 44 and other electronic circuits based on the input of the activation signal Sa from the activation processing unit 204.

  Based on the input of the activation signal Sa from the activation processing unit 204, the display control unit 206 performs control so that, for example, only the green LED 62a of the display unit 154 blinks (flicker display).

  The radiographic imaging system 10 is basically configured as described above, and the operation thereof will be described next.

  When capturing a radiographic image of the patient 22, the patient information setting unit 146 of the console 34 is used to set the patient information of the patient 22 and the imaging condition setting unit 148 is used to set necessary imaging conditions. Also, using the imaging menu setting unit 147, a desired imaging region, for example, the chest, head, limbs, and the like is selected and set from the imaging menu displayed on the third display unit 154.

  The set patient information, imaging conditions, and imaging site are transmitted to the portable information terminal 32 owned by the engineer and displayed on the second display unit 130 thereof. In this case, the engineer can confirm the patient information, the imaging conditions, and the imaging region displayed on the second display unit 130 of the portable information terminal 32, and can make a desired imaging preparation.

  At this time, it is determined whether or not each electronic cassette 28 can be imaged by the image-capturing determination unit 94, and only the red LED 62b of the display unit 62, for example, is lit on the electronic cassette 28 that is determined not to be imaged. , Notify that shooting is not possible. On the other hand, the electronic cassette 28 determined to be photographable (electronic cassette 28 that can be photographed) informs that only the green LED 62a of the display unit 62 is lit, for example, and photography is possible. In particular, the imageable electronic cassette 28 calculates the distance Ld from the magnetic field generator 39 based on data from the built-in three-dimensional magnetic sensor 200. Then, transmission information Da including distance data Ld and ID information is transmitted from the electronic cassette 28 that can be photographed to the console 34.

  The console 34 selects the electronic cassette 28 closest to the radiation source 24 from the distance data Ld of the transmission information Da regarding the received distance, and transmits the transmission information Db regarding the activation including the ID information and the conformity designation data.

  In the electronic cassette 28 corresponding to the ID information stored in the transmission information related to the activation, power is supplied to the radiation detector 44 and other electronic circuits by the power supply control unit 50, and only the green LED 62a of the display unit 62, for example, is supplied. Flashes (flicker display). That is, it is notified that the electronic cassette 28 can be photographed and is closest to the radiation source 24.

  The engineer selects the electronic cassette 28 whose green LED 62a is blinking (flicker display), and performs a normal operation on the electronic cassette 28.

  That is, first, the engineer installs the selected electronic cassette 28 at a desired imaging region of the patient 22 selected from the imaging menu.

  When the electronic cassette 28 is installed in an appropriate state for the patient 22, the engineer operates the imaging switch 126 of the portable information terminal 32 to capture a radiographic image. When the imaging switch 126 is operated, the second control unit 124 of the portable information terminal 32 transmits an imaging start signal to the radiation source control device 26 via the second transmission / reception unit 128. The radiation source control device 26 that has received the imaging start signal controls the radiation source 24 according to the imaging conditions supplied in advance from the console 34 and irradiates the patient 22 with the radiation X.

  The radiation X transmitted through the patient 22 is irradiated with the radiation detector 44 after the scattered radiation is removed by the grid 42 of the electronic cassette 28, and an electric signal is transmitted by the photoelectric conversion layer 64 of each pixel 70 constituting the radiation detector 44. And is stored as charges in the storage capacitor 68 (see FIG. 4). Next, the charge information that is the radiation image information of the patient 22 held in each storage capacitor 68 is read according to the address signal supplied from the cassette control unit 52 to the line scanning drive unit 76 and the multiplexer 78.

  That is, the first address decoder 80 of the line scan driving unit 76 outputs a selection signal according to the address signal supplied from the cassette control unit 52, selects one of the switches SW1, and is connected to the corresponding gate line 72. A control signal Von is supplied to the gate of the TFT 66. On the other hand, the second address decoder 86 of the multiplexer 78 outputs a selection signal according to the address signal supplied from the cassette control unit 52 and sequentially switches the switch SW2, and is connected to the gate line 72 selected by the line scan driving unit 76. The radiographic image information which is the charge information held in the storage capacitor 68 of each pixel 70 is sequentially read out via the signal line 74.

  The radiation image information read from the storage capacitor 68 of each pixel 70 connected to the selected gate line 72 of the radiation detector 44 is amplified by each amplifier 82 and then sampled by each sample and hold circuit 84. The signal is supplied to the A / D converter 88 via the multiplexer 78 and converted into a digital signal. The radiation image information converted into the digital signal is temporarily stored in the image memory 89 of the cassette control unit 52.

  Similarly, the first address decoder 80 of the line scan driving unit 76 sequentially switches the switch SW1 according to the address signal supplied from the cassette control unit 52, and the storage capacitor 68 of each pixel 70 connected to each gate line 72. The radiographic image information, which is the charge information held in the signal, is read out via the signal line 74 and stored in the image memory 89 of the cassette control unit 52 via the multiplexer 78 and the A / D converter 88.

  The radiation image information stored in the image memory 89 is transmitted to the console 34 by wireless communication via the transmission / reception unit 54, subjected to image processing by the image processing unit 150, and then associated with the patient information. Stored in 152. Next, the radiation image information stored in the image memory 152 is displayed on the third display unit 154.

  On the other hand, the radiographic image information stored in the image memory 89 of the electronic cassette 28 is subjected to data compression processing by the cassette control unit 52 and then transmitted to the cradle 30 or the portable information terminal 32 to be transmitted as a compressed image to the first display unit 116 or It can be displayed on the second display unit 130. The engineer can check the compressed image displayed on the first display unit 116 or the second display unit 130 and determine whether or not re-shooting is necessary. The radiographic image information can be quickly displayed because the amount of information is reduced by data compression.

  The battery 48 is depleted in the electronic cassette 28 on which the radiographic image information has been imaged. In this case, the electronic cassette 28 is charged by being mounted on the cradle 30.

  As described above, in the radiographic image capturing system 10, the electronic cassette 28 placed at the position closest to the radiation source 24 among the plurality of electronic cassettes 28 placed in the photographing room 36 is notified. The time from when the electronic cassette 28 is specified until the start of shooting can be shortened, the shooting time can be shortened and the battery consumption can be suppressed, and the working efficiency can be improved.

  In particular, in the present embodiment, power is supplied to all electronic circuits including the radiation detector 44 only for the electronic cassette 28 placed closest to the radiation source 24. It can be effectively reduced.

  In the above-described example, one electronic cassette 28 placed closest to the radiation source 24 among the plurality of electronic cassettes 28 placed in the imaging room 36 is notified. Such an embodiment is also preferably employed.

  That is, since the transmission information Da related to the distance is transmitted from the plurality of electronic cassettes 28 that can be photographed to the console 34, the third control unit 142 of the console 34 receives the plurality of ID information and the corresponding distance data. Create a list by sorting in ascending order of distance. The created list is displayed on the third display unit 154 of the console 34 and also transmitted to the cradle 30 and the portable information terminal 32, whereby the first display unit 116 of the cradle 30 and the second display of the portable information terminal 32. It may be displayed on the unit 130 as well. Thus, the engineer can select the electronic cassette 28 that can be photographed and is closest to the radiation source 24 while looking at the list displayed on the second display unit 130 or the like of the portable information terminal 32. Of course, since the shooting room 36 is equipped with a bed and various devices, it is not always easy to take out the first list candidate (the electronic cassette corresponding to the ID information set at the top of the list). Absent. The bed and equipment must be bypassed, and on the contrary, work time may be required. Therefore, the engineer can quickly find the electronic cassette 28 that is close to the radiation source 24 from a plurality of candidates displayed in the list and is easily located.

  In addition, as other aspects, the sketch information in the photographing room 36 stored in a memory (not shown) of the console 34, address data (world coordinates, etc.) on the sketch indicating the storage position of the electronic cassette 28, and the above-mentioned The list data is transmitted to the cradle 30 and the portable information terminal 32. Then, the first display unit 116 of the cradle 30 and the second of the portable information terminal 32 are provided via the first control unit 110 of the cradle 30, the second control unit 124 of the portable information terminal 32, and the third control unit 142 of the console 34. The floor plan in the photographing room 36 is displayed on the display unit 130 and the third display unit 154 of the console 34, and in the floor plan, the position corresponding to the storage position of the electronic cassette 28 that can be photographed corresponds to the order of the list. You may make it display the map which displayed the number which carried out. This allows the engineer to quickly find the electronic cassette 28 that is close to the radiation source 24 and in an easily accessible position by looking at the map.

  Further, for example, a 7-segment display or the like may be installed in the electronic cassette 28 to display numbers corresponding to the order of the list or the numbers displayed on the map. Thereby, the engineer can easily find the electronic cassette 28 that is close to the radiation source 24 and in a position where it can be easily taken out by checking the numbers displayed on the electronic cassette 28.

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

  For example, the radiation detector 44 (radiation conversion panel) accommodated in the electronic cassette 28 converts the dose of the incident radiation X directly into an electrical signal by the photoelectric conversion layer 64, but instead, the incident radiation X is incident. A radiation detector configured to once convert the radiation X into visible light with a scintillator and then convert the visible light into an electrical signal using a solid-state detection element such as amorphous silicon (a-Si) may be used ( (See Japanese Patent No. 3494683).

  Also, radiation image information can be obtained using a light conversion type radiation detector. In this light conversion type radiation detector, when radiation is incident on each solid detection element arranged in a matrix, an electrostatic latent image corresponding to the dose is accumulated and recorded in the solid detection element. When reading the electrostatic latent image, the radiation detector is irradiated with reading light, and the value of the generated current is acquired as radiation image information. The radiation detector can erase and reuse the radiation image information that is the remaining electrostatic latent image by irradiating the radiation detector with erasing light (see Japanese Patent Application Laid-Open No. 2000-105297). .

  Furthermore, a stimulable phosphor panel can also be used as the radiation conversion panel.

It is a block diagram which shows a radiographic imaging system. It is explanatory drawing which abbreviate | omits the display of a shelf, a desk, etc. as an example of the installation state of the some electronic cassette in a photo studio. It is an internal block diagram of an electronic cassette. It is a circuit block diagram of the radiation detector accommodated in an electronic cassette. 1 is a configuration block diagram of a radiographic image capturing system. It is a block diagram which shows each control part of an electronic cassette and a console as a main body.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 ... Radiation imaging system 22 ... Patient 24 ... Radiation source 26 ... Radiation source control device 28 ... Electronic cassette 34 ... Console 39 ... Magnetic field generation part 40 ... Case 44 ... Radiation detector 48 ... Battery 50 ... Electric power supply control part 52 ... cassette control unit 54 ... transmission / reception unit 94 ... photographing enable determination unit 200 ... three-dimensional magnetic sensor 202 ... distance calculation unit 204 ... activation processing unit 206 ... display control unit 208 ... electronic cassette selection unit

Claims (5)

A radiation source;
In a radiographic imaging system having a housing and two or more radiation converters having a housing and a radiation conversion panel that detects radiation from a radiation source that has passed through the subject and converts the radiation into radiation image information ,
Distance measuring means for measuring each distance from the radiation source to the two or more radiation converters;
A radiographic imaging system comprising: an informing means for informing distance information about the radiation converter based on a measurement result of the distance measuring unit. In the radiographic imaging system of Claim 1,
The notification means includes
A radiographic imaging system, wherein a radiation converter closest to the radiation source is selected and notified from among the two or more radiation converters. In the radiographic imaging system of Claim 1,
Among the two or more radiation converters, having a specifying means for specifying a radiation converter that can be shifted to a photographing mode,
The notification means includes
A radiation image capturing system, wherein a radiation converter closest to the radiation source is selected and notified from among the radiation converters that can be shifted to the imaging enable mode specified by the specifying means. In the radiographic imaging system of any one of Claims 1-3,
The distance measuring means includes
A magnetic field generator provided in the radiation source;
A three-dimensional magnetic sensor provided in each of the two or more radiation converters;
A radiographic imaging system comprising: a distance calculation unit that calculates each distance from the radiation source to the two or more radiation converters based on an output from each of the three-dimensional magnetic sensors. In the radiographic imaging system of any one of Claims 1-4,
The radiographic imaging system, wherein the magnetic field generator is an electromagnet.

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