JP2009028426A - Radiographic imaging system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a radiographic imaging system by which information of more accurate radiographic image can be obtained. <P>SOLUTION: A signal-detecting part 124 detects signals which are sent from a signal-generating part 122 located on a radiation-detecting cassette 24, and a cassette position-calculating part 126 calculates a position and direction of a grid of the radiation-detecting cassette 24 in relation to the signal-detecting part 124 on the basis of the signals detected by the signal-detecting part 124. From the calculated position and direction, and from a distance which is in a photographable range provided by a radiation source-controlling part 78, a radiation source position-calculating part 128 calculates a position and direction of a radiation source 74 in relation to the grid at a distance which is in the photographable range. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates to a radiographic imaging system including a radiation conversion panel that detects radiation transmitted through a subject and converts the radiation into radiation image information.

  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 an operating room or the like, it is necessary to be able to immediately read out and display a radiation image from a radiation conversion panel after imaging in order to perform a quick and accurate treatment on a patient. Radiation detection using a solid-state detector that converts radiation directly into electrical signals, or converts radiation into visible light with a scintillator and then converts it into electrical signals to read out as a radiation conversion panel that can meet such demands A vessel has been developed.

  By the way, in the operating room, the patient lies on the top of the bed, and the radiation detection cassette that accommodates the radiation conversion panel is disposed between the patient and the top so as to include, for example, the imaging part of the subject (patient). Or arranged directly below the top plate (see Patent Documents 1 to 4). In this state, a radiation image is taken by irradiating the radiation detection cassette with radiation from a radiation source through the subject.

JP 2003-172783 A JP 2005-204857 A JP 2006-218140 A Japanese Patent Laid-Open No. 2006-280782

  However, in Patent Document 1, the radiation source can grasp the imaging region of the subject (patient) from the imaging conditions transmitted from the radiation detection cassette, but the positional relationship between the radiation source and the radiation detection cassette is the radiation with respect to the subject. Since it is not possible to grasp whether or not the positional relationship is within the imageable range where the image can be captured, it is highly accurate if radiographic images are captured in a state where the positional relationship is not within the imageable range. Radiation image information cannot be obtained.

  In Patent Document 2, it is possible to detect the position of the radiation detection cassette relative to the top of the bed. On the other hand, in Patent Documents 3 and 4, the position of the radiation detection cassette is moved relative to the top of the bed. However, the radiation source cannot be moved in accordance with the change in the position of the radiation detection cassette with respect to the top plate. Even in this case, if radiographic images are captured in a state where the positional relationship between the radiation source and the radiation detection cassette is not within the imaging range, high-accuracy radiographic image information cannot be obtained.

  The present invention has been made in view of the above-described problems, and an object thereof is to provide a radiographic imaging system that can obtain radiographic image information with higher accuracy.

The radiographic imaging system of the present invention is
A radiation source that outputs radiation;
A radiation detection cassette having a radiation conversion panel for detecting the radiation transmitted through the subject and converting it into radiation image information;
A bed on which the subject is lying and the radiation detection cassette can be placed;
Position detecting means;
Radiation source position calculation means,
The position detection means detects the position and direction of the radiation detection cassette relative to the position detection means;
The radiation source position calculation means calculates the position and direction of the radiation source with respect to the radiation detection cassette within a shootable range in which a radiographic image can be taken with respect to the subject, based on the position and direction of the radiation detection cassette. It is characterized by doing.

  According to the present invention, the position detection unit automatically detects the position and direction of the radiation detection cassette relative to the position detection unit, and the radiation source position calculation unit performs imaging based on the position and direction of the radiation detection cassette. The position and direction of the radiation source with respect to the radiation detection cassette within a possible range are automatically calculated.

  This makes it possible to easily and accurately adjust the positional relationship between the radiation source and the radiation detection cassette to the positional relationship within the imaging range before capturing a radiographic image. Radiation image information can be obtained.

  FIG. 1 is an explanatory diagram of an operating room 12 in which a radiographic imaging system 10 according to the present embodiment is installed. In the operating room 12, an operating table (bed) 16 on which the patient 14 lies is disposed, and an instrument table 20 on which various instruments used by the doctor 18 for surgery are placed is disposed on the side of the operating table 16. The Around the operating table 16, various devices necessary for the 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 as a subject with radiation X having a dose according to imaging conditions, and a radiation detector 40 for detecting the radiation X transmitted through the patient 14 (FIG. 2). Control the radiation detection cassette 24 with built-in), a display device 26 for displaying a radiation image based on the radiation X detected by the radiation detector 40, the imaging device 22, the radiation detection cassette 24 and the display device 26. Console (control device) 28. In addition, between the imaging device 22, the radiation detection cassette 24, the display device 26, the console 28, and a transmitter / receiver 134 (see FIG. 6) in the operating table 16 described later, signals by wireless communication using UWB (Ultra Wide Band) are transmitted. Transmission / reception is performed.

  The imaging device 22 is connected to the free arm 30 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 32 and can be moved to a position where the doctor 18 can easily confirm the captured radiographic image.

  FIG. 2 is an internal configuration diagram of the radiation detection cassette 24. The radiation detection cassette 24 includes a casing (housing) 34 made of a material that transmits the radiation X. Inside the casing 34 are a grid 38 that removes scattered radiation of the radiation X by the patient 14 from the irradiation surface 36 side of the casing 34 to which the radiation X is irradiated, and a radiation detector that detects the radiation X transmitted through the patient 14 ( Radiation conversion panel) 40 and lead plate 42 that absorbs backscattered rays of radiation X are arranged in this order. Note that the irradiation surface 36 of the casing 34 may be configured as a grid 38.

  The casing 34 includes a battery 44 that is a power source of the radiation detection cassette 24, a cassette control unit 46 that drives and controls the radiation detector 40 using electric power supplied from the battery 44, and detection by the radiation detector 40. A transmitter / receiver (first wireless communication means) 48 that transmits and receives a signal including information on the radiation X to and from the console 28 is accommodated. The cassette controller 46 and the transmitter / receiver 48 are preferably provided with a lead plate or the like on the irradiation surface 36 side of the casing 34 in order to avoid damage due to irradiation with the radiation X.

  FIG. 3 is a plan view of the radiation detection cassette 24. FIG. 4 is a side view of the imaging device 22, the radiation detection cassette 24, and the operating table 16. As shown in FIGS. 2 to 4, the grid 38, the radiation detector 40, and the lead plate 42 are not disposed at the four corners on the irradiation surface 36 side of the casing 34, and the signal generator 122 is provided at these four corners. Each is arranged. On the other hand, corresponding to these four signal generators 122, there are a signal detector 124, a cassette position calculator 126, a radiation source position calculator (radiation source position calculator) 128, and a transceiver 134 in the operating table 16. A casing 170 is housed (see FIGS. 4 and 6).

  In this case, the signal detection unit 124 detects each signal transmitted from the four signal generation units 122. Specifically, each signal generator 122 is a magnet or a magnetic generator, and the signal detector 124 is a three-axis magnetic field that detects a magnetic field generated continuously or intermittently from each of the magnets or the magnetic generator. It is a sensor.

  Further, as shown in FIG. 4, the distance between the imaging device 22 and the radiation detection cassette 24, more specifically, the distance between the radiation source 74 of the imaging device 22 and the grid 38 constituting the radiation detection cassette 24 is d. Then, in the radiographic image capturing system 10, the distance d is adjusted so that the radiographic image can be captured with respect to the patient 14 (for example, the distance df indicating the radiographable range) when the radiographic image is captured. Later, the patient 14 is irradiated with radiation X from the imaging device 22. The distance d is adjusted by moving the imaging device 22 to a desired position by controlling the free arm 30 by a radiation source movement control unit (moving means) 132 (see FIG. 6) described later, or by a doctor. 18 or a radiographer in charge manually moves the arm 30 and the imaging device 22 by any method.

  FIG. 5 is a circuit configuration block diagram of the radiation detector 40. The radiation detector 40 has a photoelectric conversion layer 51 made of a material such as amorphous selenium (a-Se) that senses the radiation X and generates charges on an array of thin film transistor (TFT) 52. After the generated charge is stored in the storage capacitor 53, the TFT 52 is sequentially turned on for each row, and the charge is read as an image signal. In FIG. 5, only the connection relationship between one pixel 50 including the photoelectric conversion layer 51 and the storage capacitor 53 and one TFT 52 is shown, and the configuration of the other pixels 50 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 40 in the radiation detection cassette 24.

  A gate line 54 extending parallel to the row direction and a signal line 56 extending parallel to the column direction are connected to the TFT 52 connected to each pixel 50. Each gate line 54 is connected to a line scanning drive unit 58, and each signal line 56 is connected to a multiplexer 66 constituting a reading circuit. Control signals Von and Voff for controlling on / off of the TFTs 52 arranged in the row direction are supplied from the line scanning drive unit 58 to the gate line 54. In this case, the line scan driving unit 58 includes a plurality of switches SW1 for switching the gate lines 54 and an address decoder 60 for outputting a selection signal for selecting one of the switches SW1. An address signal is supplied from the cassette control unit 46 to the address decoder 60.

  In addition, the charge held in the storage capacitor 53 of each pixel 50 flows out to the signal line 56 through the TFTs 52 arranged in the column direction. This charge is amplified by the amplifier 62. A multiplexer 66 is connected to the amplifier 62 via a sample and hold circuit 64. The multiplexer 66 includes a plurality of switches SW2 for switching the signal line 56, and an address decoder 68 for outputting a selection signal for selecting one of the switches SW2. An address signal is supplied from the cassette control unit 46 to the address decoder 68. An A / D converter 70 is connected to the multiplexer 66, and radiation image information converted into a digital signal by the A / D converter 70 is supplied to the cassette control unit 46.

  FIG. 6 is a configuration block diagram of the radiation image capturing system 10 including the imaging device 22, the radiation detection cassette 24, the display device 26, and the console 28. 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 imaging apparatus 22 includes an imaging switch 72, a radiation source 74, a transceiver (second wireless communication unit) 76, a radiation source control unit 78, and a warning unit (warning unit) 120.

  The transceiver 76 receives a shooting condition from the console 28 by wireless communication, and transmits a shooting completion signal by wireless communication to the console 28. The transmitter / receiver 76 can wirelessly communicate with the transmitter / receiver 48 of the radiation detection cassette 24 and the transmitter / receiver 134 in the operating table 16.

  The radiation source control unit 78 controls the radiation source 74 based on the imaging start signal supplied from the imaging switch 72 and the imaging conditions supplied from the transceiver 76. The radiation source 74 outputs the radiation X based on the control from the radiation source control unit 78. The radiation source controller 78 controls the signal detector 124 to detect a signal transmitted from the signal generator 122 via the transceivers 76 and 134 based on the imaging start signal and the imaging conditions. At the same time, the radiation source position calculation unit 128 is controlled to calculate the position and direction of the radiation source 74 with respect to the grid 38 of the radiation detection cassette 24 when the distance d is the distance df. Further, the radiation source controller 78 receives the position and direction of the radiation source 74 calculated by the radiation source position calculator 128 via the transceivers 134 and 76. The distance df is information included in the imaging condition supplied from the console 28 to the radiation source controller 78 via the transceivers 96 and 76, as will be described later.

  The radiation source controller 78 then outputs a control signal for adjusting the distance d to the distance df to the radiation source movement controller 132 based on reception of the position and direction of the radiation source 74. Based on the control signal from the radiation source control unit 78, the radiation source movement control unit 132 moves the imaging device 22 to a predetermined position according to the distance df by the free arm 30 until the distance d matches the distance df. After the movement of the imaging device 22 is completed, a response signal indicating the completion of movement is output to the radiation source controller 78.

  Further, the radiation source control unit 78 captures that the distance d is not adjusted to the distance df based on the reception of the position and direction of the radiation source 74, that is, the positional relationship between the radiation detection cassette 24 and the radiation source 74 is captured. A warning signal indicating that the positional relationship is not within the possible range is output to the warning unit 120. On the other hand, when the response signal is input from the radiation source movement control unit 132, the warning signal to the warning unit 120 is output. Stop output.

  The warning unit 120 indicates that the distance d is not adjusted to the distance df by light emission of a light emitting diode (LED), for example, in the time zone when the warning signal is input from the radiation source control unit 78. 18 or notify the radiologist.

  On the other hand, the casing 170 built in the operating table 16 accommodates the signal detection unit 124, the cassette position calculation unit 126, the radiation source position calculation unit 128, and the transceiver 134 as described above.

  The transceiver 134 can transmit and receive signals by wireless communication with the transceivers 48, 76, and 96. As described above, the signal detection unit 124 detects a signal transmitted from the signal generation unit 122 based on the control from the radiation source control unit 78.

  The cassette position calculation unit 126 is based on the signal from the signal generation unit 122 detected by the signal detection unit 124, and more specifically, the position and direction of the radiation detection cassette 24 with respect to the signal detection unit 124. The position and direction of the grid 38 (see FIGS. 2 to 4) are calculated. As described above, each signal generation unit 122 is a magnet or a magnetic generator, and the signal detection unit 124 detects a magnetic field generated continuously or intermittently from each of the magnets or the magnetic generator. It is. Therefore, the cassette position calculation unit 126 calculates, for example, the three-dimensional position and direction of the signal generation unit 122 relative to the signal detection unit 124 based on the strength of each magnetic field detected by the magnetic field sensor. Based on the position and direction, the position and direction of the grid 38 with respect to the signal detection unit 124 are calculated. Therefore, the signal generation unit 122, the signal detection unit 124, and the cassette position calculation unit 126 constitute a position detection unit 129 that detects the position and direction of the grid 38.

  The radiation source position calculation unit 128 is based on the position and direction of the radiation detection cassette 24 (grid 38) with respect to the signal detection unit 124 calculated by the cassette position calculation unit 126 based on the control from the radiation source control unit 78. Then, the position and direction of the radiation source 74 with respect to the grid 38 when the distance d is the distance df is calculated, and the calculated position and direction of the radiation source 74 are wirelessly communicated via the transceivers 134 and 76 with respect to the imaging apparatus 22. Transmit to the radiation source controller 78.

  The cassette controller 46 of the radiation detection cassette 24 includes an address signal generator 80, an image memory 82, and a cassette ID memory 84.

  The address signal generator 80 supplies an address signal to the address decoder 60 of the line scan driver 58 and the address decoder 68 of the multiplexer 66 that constitute the radiation detector 40. The image memory 82 stores the radiation image information detected by the radiation detector 40. The cassette ID memory 84 stores cassette ID information for specifying the radiation detection cassette 24.

  The transceiver 48 receives a transmission request signal from the console 28 by wireless communication, and wirelessly communicates the cassette ID information stored in the cassette ID memory 84 and the radiation image information stored in the image memory 82 to the console 28. Send by.

  The display device 26 includes a receiver 90 that receives radiation image information from the console 28, a display control unit 92 that performs display control of the received radiation image information, and a display that displays the radiation image information processed by the display control unit 92. Part 94.

  The console 28 includes a transceiver 96, an imaging condition management unit 98, an image processing unit (image processing means) 100, an image memory 101, a patient information management unit 102, and a cassette information management unit 104.

  The transmitter / receiver 96 transmits / receives necessary information including radiographic image information to / from the imaging device 22, the radiation detection cassette 24, the display device 26, and the transmitter / receiver 134 in the operating table 16 by wireless communication. The shooting condition management unit 98 manages shooting conditions necessary for shooting by the shooting device 22. The image processing unit 100 performs image processing on the radiation image information transmitted from the radiation detection cassette 24. An image memory 101 stores the radiation image information subjected to the image processing. The patient information management unit 102 manages patient information of the patient 14 to be imaged. The cassette information management unit 104 manages the cassette ID information transmitted from the radiation detection cassette 24.

  The console 28 may be installed outside the operating room 12 as long as it can transmit and receive signals to and from the imaging device 22, the radiation detection cassette 24, the display device 26, and the transceiver 134 by wireless communication. Good.

  The imaging conditions are conditions for determining tube voltage, tube current, irradiation time, and the like for irradiating the patient 14 with the radiation X having an appropriate dose. Conditions such as a distance df indicating a photographing range, a photographing part, a photographing method, and the like can be given. The patient information is information for identifying the patient 14 such as the name, sex, and patient ID number of the patient 14. The imaging ordering information including these imaging conditions and patient information can be set directly on the console 28 or supplied to the console 28 from the outside via the RIS 29.

  The radiographic image capturing system 10 according to the present embodiment is basically configured as described above, and the operation thereof will be described next.

  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 the patient information management unit 102 of the console 28 prior to imaging. In addition, when the imaging region and the imaging method are determined in advance, these imaging conditions are registered in the imaging condition management unit 98 in advance. In the state where the above preparatory work is completed, the operation for the patient 14 is performed.

  When radiographing is performed during surgery, the doctor 18 or a radiographer in charge takes the radiation detection cassette 24 at a predetermined position between the patient 14 and the operating table 16 with the irradiation surface 36 facing the imaging device 22 side. Is installed. Next, after appropriately moving the imaging device 22 to a position facing the radiation detection cassette 24, the imaging switch 72 is operated to perform imaging.

  FIG. 7 is a flowchart for explaining the operation of the radiographic imaging system 10 from the registration (step S1) and the operation of the imaging switch 72 (step S2) to the irradiation of the radiation X to the patient 14 (step S17). It is.

  In step S1, the above-described preparatory work is performed. In step S2, when the doctor 18 or the radiologist operates the imaging switch 72 (see FIG. 6), the radiation source control unit 78 of the imaging apparatus 22 passes through the transceivers 76 and 96. Then, the console 28 is requested to transmit imaging conditions (step S3).

  The console 28 receives the request in step S4, and then transmits the imaging conditions related to the imaging region of the patient 14 registered in the imaging condition management unit 98 to the imaging apparatus 22 via the transceivers 96 and 76. (Step S5). When receiving the imaging condition in step S6, the radiation source control unit 78 controls the signal detection unit 124 to detect a signal transmitted from the signal generation unit 122 via the transceivers 76 and 134, and The distance df in the imaging condition is supplied to the radiation source position calculation unit 128, and the position and direction of the radiation source 74 with respect to the radiation detection cassette 24 (grid 38) when the distance d is the supplied distance df are calculated. In this manner, the radiation source position calculation unit 128 is controlled (step S7).

  In step S <b> 8, the signal detection unit 124 and the radiation source position calculation unit 128 receive the control contents by wireless communication from the radiation source control unit 78 via the transceivers 76 and 134, respectively, while the signal generation unit 122 The signal is transmitted continuously or intermittently (step S9). Therefore, the signal detection unit 124 detects a signal transmitted from the signal generation unit 122 based on the control from the radiation source control unit 78, and outputs the detected signal to the cassette position calculation unit 126 (step S10). The cassette position calculation unit 126 calculates the position and direction of the grid 38 relative to the signal detection unit 124 based on the signal from the signal detection unit 124, and outputs the calculated position and direction to the radiation source position calculation unit 128 ( Step S11).

  The radiation source position calculation unit 128 uses the distance df supplied from the radiation source control unit 78 and the position and direction of the grid 38 supplied from the cassette position calculation unit 126 when the distance d is the distance df. The position and direction of the radiation source 74 with respect to the grid 38 are calculated (step S12). The radiation source position calculation unit 128 transmits the calculated position and direction of the radiation source 74 as a response signal to the control from the radiation source control unit 78 to the radiation source control unit 78 by wireless communication via the transceivers 134 and 76. (Step S13).

  In step S14, when receiving the response signal, the radiation source controller 78 determines whether to move the radiation source 74 based on the position and direction of the radiation source 74 in the response signal (step S15). ). In this case, the radiation source control unit 78 detects the current position of the radiation source 74 using, for example, a three-dimensional position sensor (not shown) disposed in the imaging apparatus 22, and the radiation source 74 in the response signal. It is determined whether or not the radiation source 74 is to be moved based on the comparison with the position and direction.

  When it is determined in step S15 that the radiation source 74 is moved to the position and direction in the response signal, the radiation source control unit 78 transmits a control signal for adjusting the distance d to the distance df. While outputting to the control part 132, the warning signal which shows that the distance d is not adjusted to the distance df is output to the warning part 120 (step S16).

  Based on the control signal from the radiation source control unit 78, the radiation source movement control unit 132 moves the imaging device 22 to a predetermined position corresponding to the distance df by the universal arm 30 until the distance d matches the distance df. . On the other hand, the warning unit 120 confirms that the distance d is not adjusted to the distance df by the light emission of the LED in the time zone when the warning signal is input from the radiation source control unit 78. Notify

  The radiation source movement control unit 132 outputs a response signal indicating completion of movement to the radiation source control unit 78 after the movement of the imaging apparatus 22 is completed. The radiation source controller 78 stops the output of the warning signal to the warning unit 120 based on the input of the response signal, and stops the notification to the doctor 18 or the radiologist by the warning unit 120, The radiation source 74 is controlled according to the imaging conditions, and the patient 14 is irradiated with the radiation X having a predetermined dose (step S17).

  In step S15, the current position of the radiation source 74 matches the position and direction of the radiation source 74 in the response signal, that is, the distance d and the distance df match, and the radiation detection cassette 24 Since the radiation source 74 is within the imaging range, the radiation source control unit 78 performs the process of step S17 without performing the process of step S16 when it is not necessary to move the radiation source 74.

  In step S <b> 17 and subsequent steps, the radiation X transmitted through the patient 14 is irradiated with the radiation detector 40 after the scattered radiation is removed by the grid 38 of the radiation detection cassette 24, and each pixel 50 constituting the radiation detector 40. Is converted into an electric signal by the photoelectric conversion layer 51 and is held as a charge in the storage capacitor 53 (see FIG. 5). Next, the charge information which is the radiographic image information of the patient 14 held in each storage capacitor 53 is in accordance with the address signal supplied from the address signal generation unit 80 constituting the cassette control unit 46 to the line scanning drive unit 58 and the multiplexer 66. Read out.

  That is, the address decoder 60 of the line scan driver 58 outputs a selection signal according to the address signal supplied from the address signal generator 80, selects one of the switches SW1, and the TFT 52 connected to the corresponding gate line 54. A control signal Von is supplied to the gates of the two. On the other hand, the address decoder 68 of the multiplexer 66 outputs a selection signal in accordance with the address signal supplied from the address signal generation unit 80, sequentially switches the switch SW2, and is connected to the gate line 54 selected by the line scan driving unit 58. Radiation image information, which is charge information held in the storage capacitor 53 of each pixel 50, is sequentially read out via the signal line 56.

  The radiation image information read from the storage capacitor 53 of each pixel 50 connected to the selected gate line 54 of the radiation detector 40 is amplified by each amplifier 62 and then sampled by each sample and hold circuit 64. The signal is supplied to the A / D converter 70 via the multiplexer 66 and converted into a digital signal. The radiographic image information converted into the digital signal is temporarily stored in the image memory 82 of the cassette control unit 46.

  Similarly, the address decoder 60 of the line scan driving unit 58 sequentially switches the switch SW1 in accordance with the address signal supplied from the address signal generating unit 80, and the storage capacitor 53 of each pixel 50 connected to each gate line 54. The stored radiation image information, which is charge information, is read through the signal line 56 and stored in the image memory 82 of the cassette control unit 46 through the multiplexer 66 and the A / D converter 70.

  The radiation image information stored in the image memory 82 is transmitted to the console 28 by wireless communication via the transceiver 48.

  The radiographic image information transmitted to the console 28 is received by the transmitter / receiver 96, subjected to predetermined image processing in the image processing unit 100, and then associated with the patient information of the patient 14 registered in the patient information management unit 102. Stored in the image memory 101.

  The radiographic image information subjected to the image processing is transmitted from the transceiver 96 to the display device 26. The display device 26 that has received the radiation image information by the receiver 90 controls the display unit 94 by the display control unit 92 to display the radiation image. The doctor 18 performs the operation while confirming the radiation image displayed on the display unit 94.

  As described above, according to the radiographic imaging system 10 according to this embodiment, the position detection unit 129 automatically determines the position and direction of the grid 38 of the radiation detection cassette 24 with respect to the signal detection unit 124 of the position detection unit 129. Then, the radiation source position calculation unit 128 automatically calculates the position and direction of the radiation source 74 with respect to the grid 38 within the imageable range (distance df) based on the position and direction of the grid 38.

  This makes it possible to easily and accurately adjust the positional relationship between the radiation source 74 and the radiation detection cassette 24 to the positional relationship within the imageable range before capturing a radiographic image. Image information can be obtained.

  When the distance d and the distance df do not match, that is, when the position and direction of the radiation source 74 with respect to the radiation detection cassette 24 are not within the imaging range, the radiation source movement control unit 132 is The photographing device 22 is automatically moved by the free arm 30 so that the two coincide. In this case, the radiation source position calculation unit 128 automatically calculates the position and direction of the radiation source 74 with respect to the grid 38 when the distance d is the distance df, and the radiation source movement control unit 132 calculates the calculated position. Since the radiation source 74 is automatically adjusted in the direction and the direction, the distance d can be adjusted to the distance df reliably and with high accuracy, and as a result, more accurate radiation image information can be easily obtained, and It is possible to reduce the burden on the doctor 18 or the radiographer in taking a radiographic image.

  Further, even when the doctor 18 or the radiographer manually adjusts the distance d before taking the radiographic image by manually operating the free arm 30, the radiation source position calculation unit 128 uses the grid when the distance d is the distance df. Since the position and direction of the radiation source 74 with respect to 38 are automatically calculated, the burden on the doctor 18 or the radiographer can be remarkably reduced, and radiographic images can be taken efficiently.

  Furthermore, when the distance d and the distance df do not match, the warning unit 120 indicates that the two do not match, that is, the position and direction of the radiation source 74 relative to the radiation detection cassette 24 The doctor 18 or the radiologist in the operating room 12 is notified that it is not the direction. This increases the burden on the doctor 18 or the radiographer when the doctor 18 or the radiographer manually moves the free arm 30 to adjust the distance d to the distance df without using the radiation source movement control unit 132. Thus, the adjustment can be efficiently performed.

  Furthermore, between the radiation detection cassette 24 and the console 28, between the radiation detection cassette 24 and the imaging device 22, between the imaging device 22 and the console 28, between the console 28 and the display device 26, and between the imaging device 22 and Signals are transmitted / received to / from the transmitter / receiver 134 in the operating table 16, between the radiation detection cassette 24 and the transmitter / receiver 134, and between the console 28 and the transmitter / receiver 134 by UWB wireless communication. That is, since the cables for transmitting and receiving the signals are not connected between the imaging device 22, the radiation detection cassette 24, the display device 26, the console 28, and the transceiver 134, for example, these are placed on the floor of the operating room 12. The cable is not arranged, and there is no possibility of hindering the work of the doctor 18 or the like. Therefore, the doctor 18 can perform his / her work efficiently. In addition, by using UWB as the wireless communication, it is possible to reduce power consumption, improve fading resistance, and improve high-speed communication compared to conventional wireless communication.

  Furthermore, the position detection means 129 includes a signal generation unit 122 arranged on the radiation detection cassette 24 side, a signal detection unit 124 and a cassette position calculation unit 126 arranged on the operating table 16 side, and a signal detection unit 124 detects the signal transmitted from the signal generator 122, and the cassette position calculator 126 calculates the position and direction of the grid 38 relative to the signal detector 124 based on the detected signal. Then, the radiation source position calculation unit 128 determines that the distance d is the distance df based on the position and direction of the grid 38 calculated by the cassette position calculation unit 126 and the distance df supplied from the radiation source control unit 78. The position and direction of the radiation source 74 with respect to the radiation detection cassette 24 at a certain time are calculated. In this case, if the signal generator 122 is a magnet or a magnetic generator, and the signal detector 124 is a three-axis magnetic field sensor that detects a magnetic field generated from each magnet or each magnetic generator, a cassette position calculator 126 can accurately calculate the position and direction of the grid 38 based on each magnetic field detected by the magnetic field sensor. Therefore, the radiation source position calculation unit 128 can also accurately calculate the position and direction of the radiation source 74 with respect to the grid 38 described above based on the accurately calculated position and direction of the grid 38 and the distance df. It becomes possible.

  In the radiographic imaging system 10 according to the present embodiment, as an example, the signal generation units 122 are arranged at the four corners on the irradiation surface 36 side of the radiation detection cassette 24, and the position detection unit 129 uses the magnetism to detect the signal detection unit. Although the case where the position and direction of the grid 38 with respect to 124 is detected has been described, if the cassette position calculation unit 126 calculates the three-dimensional position and direction of the grid 38, the number of signal generation units 122 is at least three. Preferably there is.

  Further, the number of the signal generation units 122 arranged on the radiation detection cassette 24 side is not limited to the above-described three or four, and as described later, the position detection unit 129 may be described above by any method. Depending on whether the position and direction of the grid 38 are to be detected.

  That is, when the position detection unit 129 detects the position and direction of the grid 38 using ultrasonic waves, the signal generator 122 is arranged at one of the four corners on the irradiation surface 36 side of the radiation detection cassette 24. An ultrasonic reflector, and the signal detector 124 radiates an ultrasonic wave toward the ultrasonic reflector and receives the reflected wave of the ultrasonic wave reflected by the ultrasonic reflector. The cassette position calculation unit 126 is based on the time from when the ultrasonic transceiver radiates the ultrasonic wave until the reflected wave is received and the reception direction of the reflected wave in the signal detection unit 124. The position and direction of the grid 38 are calculated.

  In addition, when the position detection unit 129 detects the position and direction of the grid 38 wirelessly using UWB, the signal generation unit 122 is disposed at any of the four corners on the irradiation surface 36 side of the radiation detection cassette 24. A wireless transmitter, the signal detector 124 is a wireless receiver for receiving a UWB wireless signal from the wireless transmitter, and a cassette position calculator 126 is configured to receive the wireless signal transmitted from the wireless transmitter. The position and direction of the grid 38 are calculated based on the time until reception by the wireless receiver and the reception direction of the wireless signal in the signal detector 124. In this case, for example, it is necessary to synchronize in advance between the signal generator 122 and the signal detector 124 using a radio clock.

  Further, when the position detection unit 129 detects the position and direction of the grid 38 wirelessly using UWB, the signal generator 122 is disposed at any of the four corners on the irradiation surface 36 side of the radiation detection cassette 24. A wireless reflector, and the signal detector 124 is a wireless transmitter / receiver that radiates a radio wave toward the wireless reflector and receives a reflected wave of the radio wave reflected by the wireless reflector, and a cassette position calculator 126 calculates the position and direction of the grid 38 based on the time from when the radio transceiver radiates the radio wave until the reflected wave is received and the reception direction of the reflected wave in the signal detector 124.

  Furthermore, when the signal generator 122 is a composite sensor composed of a geomagnetic sensor, a gravity sensor, and a three-dimensional gyro, the gravity sensor outputs the gravitational acceleration of the radiation detection cassette 24, and the geomagnetic sensor The direction of geomagnetism is output, and the three-dimensional gyro outputs the attitude of the radiation detection cassette 24. The signal detection unit 124 wirelessly receives (detects) a detection signal from the signal generation unit 122 including the gravitational acceleration, the geomagnetic direction, and the posture, and the cassette position calculation unit 126 receives the detection signal. Based on the above, the position and direction of the grid 38 are calculated.

  As described above, even when the position detection unit 129 detects the position and direction of the grid 38 by any one of magnetic, ultrasonic, wireless, and composite sensors, the position and direction of the grid 38 are accurately determined. Since the radiation source position can be calculated, the radiation source position calculation unit 128 can accurately calculate the position and direction of the radiation source 74 with respect to the grid 38 when the distance d is the distance df.

  When the position detecting unit 129 detects the position and direction of the grid 38 using the radio, the position detecting unit 129 is a UWB pulse radar and uses a pulsed radio wave that does not use a carrier wave. Thus, it is preferable to detect the position and direction of the grid 38. In this case, by setting the radio to UWB, it is possible to reduce power consumption, improve fading resistance, increase communication speed, and improve position detection accuracy.

  In the radiographic imaging system 10 according to the present embodiment, the signal generation unit 122 is disposed on the radiation detection cassette 24 side, and the signal detection unit 124, the cassette position calculation unit 126, and the radiation source position calculation unit 128 are disposed on the operating table 16 side. However, the position and direction of the grid 38 with respect to the signal detection unit 124 can be calculated, and the radiation source for the grid 38 when the distance d is the distance df based on the position and direction and the distance df. If the configuration is such that the position and direction of 74 can be calculated, instead of the above configuration, for example, the signal generation unit 122 is arranged on the operating table 16, the signal detection unit 124, the cassette position calculation unit 126, and the radiation source position. It is also possible to arrange the calculation unit 128 in the radiation detection cassette 24.

  Further, in the radiographic imaging system 10 according to the present embodiment, the radiation source movement control unit 132 drives the universal arm 30 based on the control signal from the radiation source control unit 78 so that the distance d matches the distance df. The imaging apparatus 22 is moved, but if the configuration allows the distance d to coincide with the distance df, the radiation detection cassette 24 is moved using a moving means (not shown) instead of the above configuration. A configuration in which the radiation detection cassette 24 is moved by the moving means together with the driving of the free arm 30 by the radiation source movement control unit 132 and the movement of the imaging device 22 is also possible.

  Furthermore, in the radiographic imaging system 10 according to the present embodiment, radiographic imaging is performed due to the operation of the imaging switch 72 of the doctor 18 or the radiographer, but the operation of the console 28 by the doctor 18 or the radiographer is performed. The radiographic image may be captured due to the above.

  In the above description, the warning unit 120 notifies the doctor 18 or the radiologist that the distance d and the distance df do not match, but the console 28 is connected from the radiation source control unit 78 via the transceivers 76 and 96. A warning signal may be transmitted from the console 28 to the display unit 94 via the transmitter / receiver 96, the receiver 90, and the display control unit 92 to display a warning corresponding to the warning signal. In this case, since a warning signal is transmitted to the console 28, the console 28 can easily grasp whether or not the distance d and the distance df coincide with each other.

  Furthermore, in the radiographic imaging system 10 according to the present embodiment, for example, the radiation detector 40 accommodated in the radiation detection cassette 24 converts the incident radiation X dose directly into an electrical signal by the photoelectric conversion layer 51. However, instead of this, incident radiation X is once converted into visible light by a scintillator, and then this visible light is converted into an electrical signal using a solid-state detection element such as amorphous silicon (a-Si). You may use the comprised radiation detector (refer patent 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). .

  Of course, the radiographic imaging system according to the present invention is not limited to the above-described embodiments, and various configurations can be adopted without departing from the gist of the present invention.

It is explanatory drawing of the operating room where the radiographic imaging system of this embodiment was installed. It is an internal block diagram of the radiation detection cassette of FIG. It is a top view of the radiation detection cassette of FIG. It is a side view of the imaging device of FIG. 1, a radiation detection cassette, and an operating table. It is a circuit block diagram of the radiation detector of FIG. FIG. 2 is a configuration block diagram of the radiographic image capturing system in FIG. 1. It is a flowchart for demonstrating operation | movement of the radiographic imaging system from registration to a console to irradiation of a radiation.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 ... Radiation imaging system 12 ... Operating room 14 ... Patient 16 ... Operating table 22 ... Imaging device 24 ... Radiation detection cassette 26 ... Display device 28 ... Console 29 ... RIS
31 ... HIS
34, 170 ... casing 40 ... radiation detector 44 ... battery 46 ... cassette controller 48, 76, 96, 134 ... transceiver 50 ... pixel 74 ... radiation source 82, 101 ... image memory 84 ... cassette ID memory 90 ... receiver 94 ... Display unit 98 ... Imaging condition management unit 100 ... Image processing unit 102 ... Patient information management unit 104 ... Cassette information management unit 120 ... Warning unit 122 ... Signal generation unit 124 ... Signal detection unit 126 ... Cassette position calculation unit 128 ... Radiation Source position calculation unit 129 ... position detection means 132 ... radiation source movement control unit

Claims (13)

A radiation source that outputs radiation;
A radiation detection cassette having a radiation conversion panel for detecting the radiation transmitted through the subject and converting it into radiation image information;
A bed on which the subject is lying and the radiation detection cassette can be placed;
Position detecting means;
Radiation source position calculation means,
The position detection means detects the position and direction of the radiation detection cassette relative to the position detection means;
The radiation source position calculation means calculates the position and direction of the radiation source with respect to the radiation detection cassette within a shootable range in which a radiographic image can be taken with respect to the subject, based on the position and direction of the radiation detection cassette. A radiographic imaging system characterized by: The system of claim 1, wherein
The radiographic imaging system further comprising a moving means for moving the radiation source based on the position and direction of the radiation source calculated by the radiation source position calculating means. The system according to claim 1 or 2,
A radiographic imaging system further comprising warning means for notifying the outside that the position and direction of the radiation source relative to the radiation detection cassette are not within the imaging range. The system according to any one of claims 1 to 3,
The position detection means includes a signal generation unit disposed in the radiation detection cassette, a signal detection unit and a cassette position calculation unit disposed in the bed,
The signal detection unit detects a signal transmitted from the signal generation unit,
The cassette position calculation unit calculates a position and a direction of the radiation detection cassette with respect to the signal detection unit based on the signal. The system of claim 4, wherein
When the position detection means detects the position and direction of the radiation detection cassette using magnetism,
The signal generator is a magnet or a magnetic generator disposed at least three in the radiation detection cassette,
The signal detection unit is a three-axis magnetic field sensor that detects a magnetic field generated from each magnet or each magnetic generator,
The radiographic imaging system, wherein the cassette position calculation unit calculates the position and direction of the radiation detection cassette based on the magnetic fields detected by the magnetic field sensor. The system of claim 4, wherein
When the position detection means detects the position and direction of the radiation detection cassette using ultrasonic waves,
The signal generator is an ultrasonic reflector disposed in the radiation detection cassette;
The signal detection unit is an ultrasonic transmitter / receiver that radiates ultrasonic waves toward the ultrasonic reflector and receives a reflected wave of the ultrasonic wave reflected by the ultrasonic reflector;
The cassette position calculation unit is configured to detect the radiation detection cassette based on a time from when the ultrasonic transmitter / receiver emits the ultrasonic wave until the reflected wave is received and a reception direction of the reflected wave in the signal detection unit. A radiation imaging system characterized by calculating a position and a direction. The system of claim 4, wherein
When the position detection means detects the position and direction of the radiation detection cassette using radio,
The signal generator is a wireless transmitter disposed in the radiation detection cassette,
The signal detection unit is a wireless receiver that receives a wireless signal from the wireless transmitter,
The cassette position calculation unit is configured to detect the radiation detection cassette based on a time until the wireless signal transmitted from the wireless transmitter is received by the wireless receiver and a reception direction of the wireless signal in the wireless receiver. A radiation image photographing system characterized by calculating a position and a direction of. The system of claim 4, wherein
When the position detection means detects the position and direction of the radiation detection cassette using radio,
The signal generator is a wireless reflector disposed in the radiation detection cassette;
The signal detector is a wireless transceiver that radiates radio waves toward the wireless reflector and receives the reflected waves of the radio waves reflected by the wireless reflector,
The cassette position calculation unit is configured to determine the position of the radiation detection cassette based on a time from when the radio transceiver radiates the radio wave until the reflected wave is received and a reception direction of the reflected wave in the radio transceiver. A radiographic imaging system characterized by calculating a direction. The system according to claim 7 or 8,
The radiographic imaging system, wherein the position detecting means is a pulse radar using UWB as the radio. The system of claim 4, wherein
The signal generation unit is a composite sensor that is disposed in the radiation detection cassette and includes a geomagnetic sensor, a gravity sensor, and a three-dimensional gyro.
The gravity sensor outputs the gravitational acceleration of the radiation detection cassette,
The geomagnetic sensor outputs the direction of geomagnetism,
The three-dimensional gyro outputs a posture of the radiation detection cassette,
The signal detection unit detects a detection signal from the signal generation unit including the gravitational acceleration, the direction of the geomagnetism, and the posture;
The cassette position calculation unit calculates the position and direction of the radiation detection cassette based on the detection signal. The system according to any one of claims 1 to 10,
The radiation detection cassette includes the radiation conversion panel, the first wireless communication unit, and a battery for driving the radiation conversion panel and the first wireless communication unit. The system of claim 11, wherein
An imaging apparatus comprising: the radiation source; and second wireless communication means capable of wireless communication with the first wireless communication means;
A control device for controlling the imaging device and the radiation detection cassette;
Further comprising
The control device is transmitted to the third wireless communication means by wireless communication from the first wireless communication means and third wireless communication means capable of wireless communication with the first wireless communication means and the second wireless communication means. Alternatively, image processing means for performing predetermined image processing on the radiation image information transmitted from the first wireless communication means to the third wireless communication means by wireless communication via the second wireless communication means. A radiation image capturing system comprising: The system of claim 12, wherein
The radiographic imaging system characterized in that the wireless communication by the first to third wireless communication means is wireless communication using UWB.

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