JP2008142093A - Radiography system and radiography cassette - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a radiography cassette dispensing with restriction of a storage amount or securing charging time. <P>SOLUTION: A cassette 5 as the radiograph data for creating radiograph data by radiography includes: a cassette communication part capable of communicating with a console; a radiography panel for creating the radiograph data; a cassette control part for causing the radiograph data created in the radiography panel to be transmitted from the cassette communication part to the console; and a fuel cell 510 for supplying power to the cassette communication part, the radiography panel, and the cassette control part. <P>COPYRIGHT: (C)2008,JPO&INPIT

Description

  The present invention relates to a radiographic imaging system and a radiographic imaging cassette that generate a radiographic image of a subject.

  Conventionally, X-ray images have been widely used for diagnosis of medical conditions in the medical field. In particular, intensifying screen-film X-ray images have been developed as an imaging system that combines high reliability and excellent cost performance as a result of high sensitivity and high image quality in a long history. Used in medical settings around the world. In recent years, a “CR (computed radiography) system” using a photostimulable phosphor panel as an X-ray imaging panel has been put into practical use, and high sensitivity and improvement in image quality have been continued day and night.

By the way, in the CR system, a relatively long time of several tens of seconds to several minutes is required from the X-ray imaging until the X-ray image is generated. As a result of checking the X-ray image, the X-ray imaging is poor. In such a case, X-ray imaging must be performed again, and a longer time is required until an X-ray image is generated. For this reason, a “DR (Digital Radiography) system” using an “FPD (Flat Panel Detector)” that requires a short time of several seconds from X-ray imaging to generation of the X-ray image is proposed today (for example, patents). In the DR system described in Patent Document 1, in particular, the wireless thin FPD is applied as the FPD, and the information management of captured images is also improved.
JP 2004-180931 A

However, in the DR system described in Patent Document 1, a large-capacity capacitor or a secondary battery is used as an FPD power source (see paragraph 0072). Therefore, when a large-capacity capacitor is used as the power source, rapid charging is performed. However, when the secondary battery is used as the power source, there is a disadvantage that a sufficient charging time must be ensured.
SUMMARY OF THE INVENTION An object of the present invention is to provide a radiographic imaging system and a radiographic imaging cassette that do not require restrictions on the amount of power storage or securing charging time.

In order to solve the above-described problem, a radiographic imaging system according to claim 1 is provided.
A radiographic imaging cassette that generates radiographic image data by radiography;
A console for displaying a radiation image on a display unit using the radiation image data;
With
The radiographic imaging cassette is
A cassette communication unit capable of communicating with the console;
A radiation imaging panel for generating the radiation image data;
A cassette controller that transmits the radiation image data generated by the radiation imaging panel from the cassette communication unit to the console;
A fuel cell that supplies power to the cassette communication unit, the radiation imaging panel, and the cassette control unit;
Have
The console is
A console communication unit that receives the radiation image data transmitted from the cassette communication unit;
The radiographic image is displayed on the display unit based on the radiographic image data received by the console communication unit.

The invention described in claim 2
In the radiographic imaging system of Claim 1,
The fuel cell is
A fuel unit mounting portion to which a fuel unit for storing fuel can be attached and detached;
A power generation unit that receives power from the fuel unit mounted on the fuel unit mounting unit and generates power;
It is characterized by having.

The invention described in claim 3
In the radiographic imaging system of Claim 2,
The fuel cell is
The fuel unit has a plurality of fuel unit mounting portions that can be separately attached to and detached from each other, and fuel can be supplied to the power generation unit from any of the fuel units mounted on the plurality of fuel unit mounting portions. It is characterized by being.

The invention according to claim 4
In the radiographic imaging system as described in any one of Claims 1-3,
The fuel cell is characterized in that fuel can be supplied from the fuel unit to the power generation unit regardless of the orientation of the radiographic imaging cassette, and the power generation unit can generate power.

The invention described in claim 5
In the radiographic imaging system as described in any one of Claims 1-4,
The radiographic imaging cassette is
It has a ventilation part which blows the heat generated in the radiation imaging panel toward the fuel cell.

The invention described in claim 6
In the radiographic imaging system as described in any one of Claims 1-5,
The radiation imaging panel is
A scintillator that converts radiation into fluorescence;
A protective layer for protecting the scintillator;
A support for supporting the scintillator;
Have
The scintillator is covered with the protective layer and the support.

The invention described in claim 7
In the radiographic imaging system as described in any one of Claims 1-6,
The cassette control unit transmits power supply state information indicating a supply state of power from the fuel cell from the cassette communication unit to the console,
The console causes the display unit to display the power supply state from the fuel cell using the power supply state information received by the console communication unit.

The invention according to claim 8 provides:
In the radiographic imaging system as described in any one of Claims 1-7,
The cassette communication unit can communicate with the console wirelessly.

The invention according to claim 9 is:
In the radiographic imaging system as described in any one of Claims 1-8,
A wireless repeater capable of wireless communication with the cassette communication unit,
The console communication unit can communicate with the wireless repeater via a communication cable.

The invention according to claim 10 is:
In the radiographic imaging system as described in any one of Claims 1-9,
The console is a portable terminal.

The invention according to claim 11
A radiographic imaging cassette that generates radiographic image data by radiography,
A cassette communication unit capable of communicating with the console;
A radiation imaging panel for generating the radiation image data;
A cassette controller that transmits the radiation image data generated by the radiation imaging panel from the cassette communication unit to the console;
A fuel cell that supplies power to the cassette communication unit, the radiation imaging panel, and the cassette control unit;
It is characterized by having.

The invention according to claim 12
In the cassette for radiographic imaging of Claim 11,
The fuel cell is
A fuel unit mounting portion to which a fuel unit for storing fuel is detachable;
A power generation unit that receives power from the fuel unit mounted on the fuel unit mounting unit and generates power;
It is characterized by having.

The invention according to claim 13
The radiographic imaging cassette according to claim 12,
The fuel cell is
The fuel unit has a plurality of fuel unit mounting portions that can be separately attached to and detached from each other, and fuel can be supplied to the power generation unit from any of the fuel units mounted on the plurality of fuel unit mounting portions. It is characterized by being.

The invention according to claim 14
In the cassette for radiographic imaging as described in any one of Claims 11-13,
The fuel cell is characterized in that fuel can be supplied from the fuel unit to the power generation unit and can be generated by the power generation unit regardless of the orientation of the radiographic imaging cassette.

The invention according to claim 15 is:
In the cassette for radiographic imaging as described in any one of Claims 11-14,
It has a ventilation part which blows the heat generated in the radiation imaging panel toward the fuel cell.

The invention described in claim 16
In the cassette for radiographic imaging as described in any one of Claims 11-15,
The radiation imaging panel is
A scintillator that converts radiation into fluorescence;
A protective layer for protecting the scintillator;
A support for supporting the scintillator;
Have
The scintillator is covered with the protective layer and the support.

The invention described in claim 17
In the cassette for radiographic imaging as described in any one of Claims 11-16,
The cassette control unit transmits power supply state information indicating a supply state of power from the fuel cell from the cassette communication unit to the console.

The invention described in claim 18
In the cassette for radiographic imaging as described in any one of Claims 11-17,
The cassette communication unit can communicate wirelessly.

  In this specification, the “console” is a device for the operator to communicate with the cassette, and a separate display device or operation device may be connectable, or the display device or operation device. May be integrated. The “imaging operation” is an operation necessary for obtaining radiographic image data by radiography. For example, in the case of the panel shown in the embodiment, initialization of the panel, accumulation of electric energy generated by radiation irradiation is stored. The operations of reading electrical signals and converting image data are applicable. The “imaging ready state” is a state in which radiation image data can be obtained immediately by this imaging operation.

  In the inventions according to claims 1 and 11, since the radiographic cassette has a fuel cell, there is no need to restrict the amount of electricity stored or to secure a charging time. Thus, it is possible to supply power quickly and sufficiently, and as a result, the total imaging efficiency of the entire radiation imaging can be improved by repeating the cycle of confirming the radiation image from the radiation imaging.

  In the second and twelfth aspects of the present invention, the fuel unit is detachable from the fuel unit mounting portion and supplies fuel from the fuel unit to the power generation unit. Therefore, when replenishment is necessary, the fuel unit is replaced. Therefore, it is possible to improve the total imaging efficiency of the entire radiographic imaging by repeating the cycle of confirming the radiographic image from the radiographic imaging.

  According to the third and thirteenth aspects of the present invention, each fuel unit can be separately attached to and detached from each other, and fuel can be supplied from any of the fuel units to the power generation unit. While the fuel unit is being replaced, fuel can be supplied from another fuel unit to the power generation unit. Therefore, it is possible to repeat the cycle of transmitting radiographic image data from radiography even during replacement of the fuel unit, and to improve the total radiographic efficiency of the entire radiographic imaging that repeats the cycle of confirming radiographic images from radiography. Can do.

  In the inventions according to claims 4 and 14, since the fuel cell can supply fuel from the fuel unit and generate electric power regardless of the orientation of the radiographic cassette, the radiographic cassette can be tilted or inverted. Even in this case, electric power can be supplied from the fuel cell. Therefore, it is not necessary to pay attention to the orientation of the radiographic imaging cassette, and it is possible to improve the total imaging efficiency of the entire radiographic imaging that repeats the cycle of confirming the radiographic image from the radiographic imaging.

  In the invention according to claims 5 and 15, since the heat generated in the radiation imaging panel is blown to the fuel cell by the blowing section, the power generation efficiency of the fuel cell can be improved, and in the radiation imaging panel The occurrence of unevenness in the temperature distribution is suppressed. Therefore, it is possible to suppress the occurrence of uneven sensitivity in the radiation imaging panel and obtain a good radiation image.

  In the inventions according to claims 6 and 16, since the scintillator is covered with the protective layer and the support, water vapor generated during power generation by the fuel cell is blocked by the protective layer and the support and reaches the scintillator. Hateful. Therefore, it is possible to prevent the scintillator from being deteriorated by moisture.

  In the seventh and 17th aspects of the invention, the power supply state information is transmitted to the console, so that the console can be controlled using the power supply state information. Further, in the invention described in claim 7, since the display relating to the power supply state is displayed on the display unit, it is possible to instantaneously determine whether or not radiation imaging can be performed immediately. Therefore, if radiography can be performed immediately, radiography can be started immediately. On the other hand, if radiography cannot be performed immediately, other operations can be performed before radiography can be performed. As a result, it is possible to improve the total imaging efficiency of the entire radiographic imaging in which the cycle of confirming the radiographic image from the radiographic imaging is repeated.

  In the inventions according to claims 8 and 18, since the cassette communication unit can communicate with the console wirelessly, a communication cable is unnecessary, and the cassette is attached while paying attention so that the cable does not get entangled with the subject. The situation of handling can be avoided. Therefore, it is possible to concentrate the radiographer on the radiographic imaging to reduce mistakes in the radiographic imaging, and it is possible to improve the imaging efficiency of the entire radiographic imaging that repeats the cycle of confirming the radiographic image from the radiographic imaging.

  By the way, the radiographic imaging cassette is installed in a radiographic room covered with a radiation shielding member, while the console is often installed outside the radiographic room. Since the console communication unit can communicate with the wireless repeater via a communication cable, the wireless communication device is installed between the cassette communication unit and the wireless repeater by installing the wireless repeater in the radiation imaging room. Wireless communication and wired communication between the radio relay unit and console communication unit between the inside and outside of the radiography room can be performed satisfactorily. The total imaging efficiency of the entire repeated radiography can be improved.

  In addition, as described above, when the radiographic imaging cassette is in the radiographic room and the console is installed outside the radiographic room, the photographer instructs the subject in the radiographic room about the imaging position and the like during radiography. After that, it moves outside the radiography room and starts generating a radiographic image of the subject. However, in the invention according to claim 10, since the console is a portable terminal, the console can start image processing of radiation image data while instructing the subject about the imaging position and the like in the radiation imaging room. The moving time from the inside of the room to the outside can be used for the image processing time of the radiation image data. As a result, the time from radiography to generation of a radiographic image can be shortened, and as a result, the total imaging efficiency of the entire radiography can be improved by repeating the cycle of confirming the radiographic image from radiography.

Hereinafter, embodiments of the present invention will be described with reference to the drawings.
The description in the embodiment section of the invention indicates the form that the inventor recognizes as the best for carrying out the invention, and at a glance the terms used in the scope of the invention and the claims, Although there are expressions that are asserted or defined, these are expressions for identifying the form that the inventor recognizes as the best, and are terms used in the scope of the invention and claims. Is not specified or limited.

[First embodiment]
A first embodiment of a radiographic imaging system according to the present invention will be described with reference to FIGS. X-rays are a type of radiation.

  As shown in FIG. 1, an X-ray imaging system 1000 according to the first embodiment is a system that assumes X-ray imaging performed in a hospital. For example, X-ray imaging that irradiates a subject with X-rays The room R1 is arranged in an X-ray control room R2 that performs control of X-rays irradiated to the subject by the X-ray engineer, image processing of X-ray images acquired by irradiating X-rays, and the like.

  A console 1 is provided in the X-ray control room R2. The entire X-ray imaging system is controlled by the console 1, and X-ray imaging control and image processing of the acquired X-ray image are performed.

  The console 1 is connected to an operation input unit 2 through which an operator inputs an imaging preparation instruction, an imaging instruction, and instruction content. As the operation input unit 2, for example, an X-ray irradiation request switch, a touch panel, a mouse, a keyboard, a joystick, or the like can be used, and an X-ray tube voltage, an X-ray tube current, X Instruction contents such as X-ray imaging conditions such as X-ray irradiation time, X-ray imaging control conditions such as imaging timing, imaging region, imaging method, image processing conditions, image output conditions, cassette selection information, order selection information, subject ID, etc. are input Is done.

  Further, a display unit 3 for displaying an X-ray image or the like is connected to the console 1, and the display is controlled by a display control unit 11 constituting the console 1. As the display unit 3, for example, a liquid crystal monitor, a monitor such as a CRT (Cathode Ray Tube) monitor, electronic paper, an electronic film, or the like can be used. The display unit 3 displays characters such as X-ray imaging conditions and image processing conditions and X-ray images.

  Further, the console 1 includes a display control unit 11, an input unit 12, a console control unit 13, a console communication unit 14, an image processing unit 15, an image storage unit 16, a console power supply unit 17, a network communication unit 18, and the like. The display control unit 11, the input unit 12, the console control unit 13, the console communication unit 14, the image processing unit 15, the image storage unit 16, the console power supply unit 17, and the network communication unit 18 are each connected to a bus and exchange data. Is possible.

  The input unit 12 receives the instruction content from the operation input unit 2.

  The console control unit 13 determines the imaging conditions based on the instruction content received by the input unit 12 and the order information of the HIS / RIS 71, and performs imaging related to the imaging conditions to the X-ray source 4 and the cassette 5 via the console communication unit 14. The condition information is transmitted, and the X-ray source 4 and the cassette 5 are controlled to take an X-ray image. Further, the console control unit 13 causes the image storage unit 16 to temporarily store the X-ray image data received by the console communication unit 14 from the cassette 5.

  In addition, the console control unit 13 causes the image processing unit 15 to create thumbnail image data from the X-ray image data temporarily stored in the image storage unit 16. The display control unit 11 controls the display unit 3 to display a thumbnail image based on the created thumbnail image data.

  Then, the console control unit 13 causes the image processing unit 15 to perform image processing on the X-ray image data based on the instruction content received by the input unit 12 and the order information of the HIS / RIS 71, and the X-ray image subjected to this image processing. The image storage unit 16 is controlled to store the data. Then, based on the X-ray image data obtained as a result of the image processing by the image processing unit 15, the display control unit 11 is controlled so that the display unit 3 displays the thumbnail image of the processing result.

  Further, the console control unit 13 re-images the X-ray image data and displays the image processing result based on the instruction content received by the input unit 12 from the operation input unit 2 thereafter. Transfer, save, and display image data to external devices on the network.

  As the console control unit 13, it is possible to apply a motherboard on which a CPU (Central Processing Unit) and a memory such as a RAM (Random Access Memory) and a ROM (Read Only Memory) are mounted.

  The CPU reads a program stored in the ROM or hard disk, expands the program on the RAM, and controls each part of the console 1, the X-ray source 4, the cassette 5, and an external device according to the expanded program. Further, the CPU reads out various processing programs including a system program stored in the ROM or the hard disk, develops them on the RAM, and executes various processes described later.

  The RAM is a volatile memory, and temporarily stores various programs, input or output data, etc. that are read from the ROM and can be executed by the CPU in various processes that are executed and controlled by the CPU of the console control unit 13. Form a work area.

  The ROM is, for example, a non-volatile memory, and stores a system program executed by the CPU, various programs corresponding to the system program, and the like. These various programs are stored in the form of readable program codes, and the CPU sequentially executes operations according to the program codes.

  A hard disk may be used instead of the ROM. In this case, the hard disk stores a system program executed by the CPU and various application programs. The hard disk receives and stores various application programs such as the program of the present invention from the console communication unit 14 from other devices such as a server via a network line transmission medium. Also good. Further, the CPU receives various application programs such as the program of the present invention from a storage device such as a hard disk of a server provided on the network, develops it on the RAM, and performs various processes such as the process of the present invention. It may be.

  Based on the control of the console control unit 13, the display control unit 11 controls the display unit 3 to display images, characters, and the like based on image data, character data, and the like. A graphic board or the like can be used for the display control unit 11.

  The console communication unit 14 is connected to the X-ray source 4 and the wireless repeater 6 via a communication cable, and the console communication unit 14 can communicate with the cassette 5 via the wireless repeater 6. The console communication unit 14 can transmit a control signal based on the instruction content to the X-ray source 4 and the cassette 5 by analog communication or digital communication, and can receive X-ray image data from the cassette 5.

  The communication cable connecting the console communication unit 14 to the X-ray source 4 and the wireless repeater 6 is detachable. When the communication cable is connected, image transfer can be performed at high speed, so that X-ray image acquisition by X-ray imaging, X-ray image processing, X-ray image confirmation, and the like can be performed in a shorter time.

  The image processing unit 15 performs image processing on the X-ray image data received from the cassette 5 by the console communication unit 14. The image processing unit 15 corrects X-ray image data based on the instruction content, enlargement / compression processing, spatial filtering processing, recursive processing, gradation processing, scattered radiation correction processing, grid correction processing, frequency enhancement processing, dynamic range ( DR) Image processing such as compression processing is performed.

  The image storage unit 16 temporarily stores X-ray image data received from the cassette 5 by the console communication unit 14 and stores X-ray image data subjected to image processing. As the image storage unit 16, it is possible to use a hard disk that is a large-capacity and high-speed storage device, a hard disk array such as a RAID (Redundant Array of Independent Disks), a silicon disk, or the like.

  The console power supply unit 17 is supplied with power from an external power source (not shown) such as an AC power source or an internal power source (not shown) such as a battery or a battery, and supplies power to each part constituting the console 1. is doing. The external power supply of the console power supply unit 17 is detachable. When the console power supply unit 17 is supplied with power from an external power supply, it is not necessary to charge, so it is possible to take a picture for a long time.

  The network communication unit 18 communicates various information between the console 1 and an external device via a LAN (Local Area Network). As an external device, for example, a HIS / RIS (Hospital Information System / Radiology Information System) terminal 71, an imager 72, an image processing device 73, a viewer 74, a file server 75, and the like are connected. It is possible. The network communication unit 18 outputs X-ray image data to an external device according to a predetermined protocol such as DICOM (Digital Imaging and Communications in Medicine).

  The HIS / RIS terminal 71 acquires subject information, imaging region, imaging method, and the like from the HIS / RIS and provides them to the console 1. The imager 72 records an X-ray image on an image recording medium such as a film based on the X-ray image data output from the console 1. The image processing apparatus 73 performs processing for X-ray image data output from the console 1 and processing for CAD (Computer Aided Diagnosis) and stores the processed data in the file server 75. The viewer 74 displays an X-ray image based on the X-ray image data output from the console 1. The file server 75 is a file server that stores X-ray image data that has undergone processed image processing. The network communication unit 18 outputs X-ray image data to an external device according to a predetermined protocol such as DICOM (Digital Imaging and Communications in Medicine).

  In the present embodiment, the display control unit 11 and the console control unit 13 are provided separately, but the display control unit 11 and the console control unit 13 may be integrated. For example, it is possible to use a motherboard on which a CPU and a memory are mounted as the console control unit 13 and use a graphic subsystem built in the motherboard as the display control unit 11. The console control unit 13 may also serve as the display control unit 11. In this embodiment, the image processing unit 15 is separate from the console control unit 13, but the console control unit 13 may also serve as the image processing unit 15.

  In the X-ray imaging room R1, an X-ray source 4 for irradiating a subject with X-rays and a cassette 5 for detecting X-rays irradiated on the subject and acquiring X-ray image data are installed. In the present embodiment, the X-ray imaging room R1 is a room covered with an X-ray shielding member so that the X-rays of the X-ray source 4 do not leak out of the X-ray imaging room R1, and the cassette 5 is It is portable and can be taken out of the X-ray room R1.

  Further, a radio repeater 6 is installed in the X-ray imaging room R1. The wireless repeater 6 performs wireless communication with the cassette 5. Therefore, a communication cable is not required for communication between the cassette 5 and the wireless repeater 6, and the cassette 5 is handled while paying attention so that the cable does not get tangled with the subject during X-ray imaging. The situation can be avoided.

  The wireless repeater 6 communicates with the console 1 via a communication cable. Then, the X-ray image data acquired by the cassette 5 is transmitted to the console 1 via the wireless repeater 6, and control signals and various information are communicated between the console 1 and the cassette 5.

Thus, in this embodiment, the cassette 5 and the wireless repeater 6 are installed inside the X-ray imaging room R1, and the console 1 is installed outside (the X-ray control room R2). 5 and the wireless repeater 6 can be satisfactorily performed inside without being influenced by the X-ray shielding member of the X-ray radiographing room R1, while the communication between the wireless repeater 6 and the console 1 is X. This can be performed well inside and outside the radiographing room R1.
The wireless repeater 6 may have a holder function when the cassette 5 is not used.

  In the above description, the console 1 is described as being installed in the X-ray control room R2. However, the console 1 may be a portable terminal capable of wireless communication. In this case, a radio repeater is also installed in the X-ray control room R2, and the console communication unit 14 can wirelessly communicate with the radio repeater 6 in the X-ray imaging room R1 and the radio repeater in the X-ray control room R2. As a result, it is preferable to be able to communicate with the cassette 5 both in the X-ray imaging room R1 and in the X-ray control room R2.

  Thereby, the radiographer confirms the X-ray image on the console 1 while giving an instruction to the radiographer about the radiographing position and the like in the X-ray radiographing room R1 as well as in the X-ray control room R2, Image processing of X-ray image data can be started, the X-ray image can be confirmed by the movement time between the X-ray imaging room R1 and the X-ray control room R2, and image processing of X-ray image data Can be started, and the total imaging efficiency of the whole X-ray imaging can be improved by repeating the cycle of confirming the X-ray image from the X-ray imaging.

  The X-ray source 4 is provided with a high voltage generation source 41 that generates a high voltage and an X-ray tube 42 that generates X-rays when a high voltage is applied by the high voltage generation source 41. An X-ray diaphragm device (not shown) for adjusting the X-ray irradiation range is provided at the X-ray irradiation port of the X-ray tube 42. Since the X-ray diaphragm device controls the X-ray irradiation direction according to the control signal from the console 1, the X-ray irradiation range is adjusted according to the imaging region.

  Further, the X-ray source 4 is provided with an X-ray source control unit 43, and the high-pressure generation source 41 and the X-ray tube 42 are connected to the X-ray source control unit 43, respectively. The X-ray source control unit 43 drives and controls each unit of the X-ray source 4 based on the control signal transmitted from the console communication unit 14. That is, the high pressure generation source 41 and the X-ray tube 42 are controlled.

  X-rays transmitted through the subject from the X-ray source 4 are incident on a cassette 5 as a radiographic imaging cassette. The cassette 5 is adjusted in position by the operator so that X-rays are transmitted to a desired position of the subject before X-ray imaging.

  In the cassette 5, an internal power supply unit 51, a cassette communication unit 52, a cassette control unit 53, and a panel 54 are disposed. The internal power supply unit 51, the cassette communication unit 52, the cassette control unit 53, and the panel 54 are each connected to a bus in the cassette 5.

The internal power supply unit 51 supplies electric power to each unit disposed in the cassette 5, and specifically includes a fuel cell 510 (see FIG. 5, which will be described later). The internal power supply unit 51 preferably has a second power supply that can be charged by the fuel cell 510 and supplies power when the fuel cell 510 is not in operation. Examples of the second power source include a capacitor and a secondary battery, and an electrolytic double layer capacitor is particularly preferable. From the viewpoint of imaging efficiency, the capacity of the second power source is preferably 4 or more (especially 7 or more) in terms of the maximum number of X-ray images that can be taken continuously. Further, the capacity of the internal power supply unit 51 is 100 or less (especially 50 or less) in terms of the maximum number of X-ray images that can be taken continuously from the viewpoint of size reduction, weight reduction, and cost reduction. ) Is preferable.

  The cassette communication unit 52 is configured to be able to wirelessly communicate with the console communication unit 14 via the wireless repeater 6, and transmits / receives signals between the cassette communication unit 52 and the console communication unit 14. X-ray image data can be transmitted from the communication unit 52 to the console communication unit 14.

  The cassette control unit 53 controls each unit disposed in the cassette 5 based on the control signal received by the cassette communication unit 52.

  The panel 54 generates and outputs X-ray image data based on the X-ray transmitted through the subject. The panel 54 of the present embodiment is an indirect flat panel detector (FPD).

  FIG. 2 is a perspective view showing a schematic configuration of the cassette 5, and FIG. 3 is a sectional view of the cassette 5 with the panel 54 as the center. In the present embodiment, the example shown in FIGS. 2 and 3 will be described. However, the present invention is not limited to this example, and the scintillator has a different thickness or type or a different panel area that is the area of the imaging region. It is also applicable to use. The greater the thickness of the scintillator, the higher the sensitivity, and the thinner the scintillator, the higher the spatial resolution. The spectral sensitivity varies depending on the type of scintillator.

  The panel 54 is provided with a scintillator 541 that detects X-rays transmitted through the subject and converts the detected X-rays into fluorescence in the visible region (hereinafter referred to as “visible light”) in layers.

The scintillator 541 includes a phosphor as a main component. The scintillator 541 is a layer that emits visible light by recombination energy when the host substance of the phosphor is excited (absorbed) by the irradiated X-rays. As the phosphor, for _example, those emitting fluorescence by matrix material such as _{CaWO 4, CdWO 4, CsI:} Tl, ZnS: those that emit fluorescence by emission center substance added to the matrix material, such as Ag Etc.

  A protective layer 540 is provided on the scintillator 541. The protective layer 540 protects the scintillator 541 and completely covers the top and side edges of the scintillator 541. As the protective layer 540, any material may be used as long as it has an effect of moisture protection of the scintillator 541. When a scintillator 541 uses a hygroscopic phosphor (in particular, a columnar crystal phosphor composed of an alkali halide and further an alkali halide), for example, a polycrystal formed by the CVD method disclosed in US Pat. No. 6,469,305. Organic films made of paraxylylene, organic films formed from polymers containing silazane or siloxazan type polymer compounds such as polysilazane and polysiloxazan, and moisture-proof organic films such as organic films formed by plasma polymerization It is preferable to use it.

  Under the scintillator 541, a photodetector 542 made of amorphous silicon is laminated and extends, and the visible light emitted from the scintillator 541 is converted into electric energy and output by the photodetector 542. .

  The panel 54 is preferably composed of pixels of 1000 × 1000 pixels or more (particularly 2000 × 2000 pixels or more) from the viewpoint of the diagnostic property of the diagnosis by the X-ray image. The panel 54 is preferably configured with pixels of 10,000 × 10,000 pixels or less (particularly 6000 × 6000 pixels or less) from the viewpoint of human visibility limit and image processing speed of X-ray images.

  In addition, the size of the imaging region of the panel 54 is preferably an area of 10 cm × 10 cm or more (particularly 20 cm × 20 cm or more) from the viewpoint of the diagnostic property of the diagnosis by the X-ray image. Further, the size of the imaging region of the panel 54 is preferably an area of 70 cm × 70 cm or less (particularly 50 cm × 50 cm or less) from the viewpoint of ease of handling as the cassette 5.

  The size of one pixel of the panel 54 is preferably 40 μm × 40 μm or more (particularly 70 μm × 70 μm or more) from the viewpoint of reducing the amount of X-ray exposure. Further, the size of one pixel of the panel 54 is preferably 200 μm × 200 μm or less (especially 160 μm × 160 μm or less) from the viewpoint of the diagnostic property of diagnosis by an X-ray image.

  In this embodiment, the panel 54 is composed of 4096 × 3072 pixels, the area of the imaging region is 430 mm × 320 mm, and the size of one pixel is 105 μm × 105 μm.

  Here, a circuit configuration centering on the photodetector 542 will be described.

  As shown in FIG. 4, the photodetector 542 is two-dimensionally provided with a collection electrode 5421 for reading out electrical energy accumulated according to the intensity of the irradiated X-rays. The collecting electrode 5421 is configured as one electrode of a capacitor 5424 so that electric energy is stored in the capacitor 5424. Here, one collecting electrode 5421 corresponds to one pixel of the X-ray image data.

  A scanning line 5422 and a signal line 5423 are provided between the collecting electrodes 5421 adjacent to each other. The scanning line 5422 and the signal line 5423 are orthogonal to each other.

The capacitor 5424 is connected to a switching thin film transistor 5425 (TFT: Thin Film Transistor, hereinafter simply referred to as “transistor”) that controls storage and reading of electric energy. The transistor 5425 has a drain electrode or a source electrode connected to the collection electrode 5421 and a gate electrode connected to the scan line 5422. When the drain electrode is connected to the scanning line 5422, the source electrode is connected to the signal line 5423, and when the source electrode is connected to the collection electrode 5421, the drain electrode is connected to the signal line 5423. In the panel 54, an initialization transistor 5427, for example, connected to a drain electrode is provided on the signal line 5423. The source electrode of the transistor 5427 is grounded. The gate electrode is connected to the reset line 5426.
Note that the transistor 5425 and the transistor 5427 are preferably formed using a silicon stacked structure or an organic semiconductor.

In addition, a reset line 5426 to which a reset signal RT is transmitted from the scan drive circuit 543 is connected to the scan drive circuit 543 orthogonal to the signal line 5423.
A gate electrode of an initialization transistor 5427 that is turned on by a reset signal RT is connected to the reset line 5426. In the initialization transistor 5427, the gate electrode is connected to the reset line 5426, the drain electrode is connected to the signal line 5423, and the source electrode is grounded. When the source electrode is connected to the signal line 5423, the drain electrode is grounded.

  When the reset signal RT is supplied from the scan drive circuit 543 to turn on the initialization transistor 5427 and the read signal RS is supplied from the scan drive circuit 543 to turn on the transistor 5425, the reset signal RT is accumulated in the capacitor 5424. Electric energy is released out of the photodetector 542 through the transistor 5425. Hereinafter, the release of the electrical energy accumulated in the capacitor 5424 when the reset signal RT is supplied is referred to as reset (initialization) of the photodetector 542.

  In addition, a scanning drive circuit 543 that supplies a reading signal RS to the scanning line 5422 is connected to the scanning line 5422. The transistor 5425 connected to the scan line 5422 to which the read signal RS is supplied is turned on, and electric energy accumulated in the capacitor 5424 connected to the transistor 5425 is read and supplied to the signal line 5423. That is, by driving the transistor 5425, a signal for each pixel of the X-ray image data can be generated.

  A signal reading circuit 544 is connected to the signal line 5423. The electric energy read from the signal line 5423 after being stored in the capacitor 5424 is supplied to the signal reading circuit 544. The signal reading circuit 544 includes a signal converter 5441 that supplies a voltage signal SV proportional to the amount of electrical energy supplied to the signal reading circuit 544 to the A / D converter 5442, and a voltage signal SV from the signal converter 5441. An A / D converter 5442 that converts the signal into a digital signal and supplies the digital signal to the data converter 545 is provided.

  A data conversion unit 545 is connected to the signal reading circuit 544. The data converter 545 generates X-ray image data based on the digital signal supplied from the signal reading circuit 544.

  When high-resolution X-ray image data is not required or when it is desired to acquire X-ray image data quickly, the console control unit 13 performs received thinning, pixel averaging, region extraction, etc. according to the imaging method selected by the operator. A control signal is transmitted to the cassette control unit 53. The cassette control unit 53 performs control so as to execute the following decimation, pixel averaging, region extraction, and the like in accordance with the received control signals such as decimation, pixel averaging, region extraction, and the like.

  Thinning is performed by reading out only odd-numbered columns or even-numbered columns, thereby thinning out the number of pixels to be read out to 1/4 of the total number of pixels, or similarly thinning out to 1/9, 1/16, or the like. Note that the thinning method is not limited to this method.

  The pixel average can be calculated by simultaneously driving a plurality of scanning lines 5422 and performing analog addition of two pixels in the same column direction. The pixel average is not limited to being calculated by adding two pixels, but can be easily obtained by performing analog addition of a plurality of pixels in the column signal wiring direction. Furthermore, for addition in the row direction, square pixels such as 2 × 2 can be obtained in combination with the above-described analog addition by digitally adding adjacent pixels after A / D conversion output. As a result, it is possible to read data at high speed without wasting the irradiated X-rays.

  The area extraction includes means for limiting the X-ray image data capturing area. This is because the necessary X-ray image data acquisition area is specified from the instruction content of the imaging method, and the cassette control unit 53 changes the data acquisition range of the scan drive circuit 543 based on the specified acquisition area. The panel 54 drives the changed capture range.

  A memory 546 is connected to the data conversion unit 545. The memory 546 stores the X-ray image data generated by the data conversion unit 545. The memory 546 stores gain correction data in advance.

  The memory 546 includes a RAM (Random Access Memory) and a nonvolatile memory. The memory 546 can sequentially write the X-ray image data sequentially generated by the data conversion unit 545 to the nonvolatile memory after sequentially writing it to the RAM. The non-volatile memory is composed of two or more memory components such as an EEPROM and a flash memory, and it is possible to write to the other while erasing one of the memory components.

  The capacity of the memory 546 is preferably 4 or more (particularly 10 or more) in terms of the number of images that can store images of the maximum data size from the viewpoint of shooting efficiency. Further, the capacity of the memory 546 is preferably 1000 or less (particularly 100 or less) in terms of the number of images that can store images of the maximum data size from the viewpoint of cost reduction.

  A support body 547 on a flat plate formed of a glass substrate is provided below the photodetector 542, and the stacked structure of the protective layer 540, the scintillator 541, and the photodetector 542 is supported by the support body 547. In the panel 54, the scintillator 541 has a configuration in which the upper and side edges are completely covered with a protective layer 540 and the lower part is completely covered with a support 547. Therefore, water vapor generated in a fuel cell 510 serving as an internal power supply unit 51 described later is blocked by the protective layer 540 and the support 547, and the scintillator 541 can be prevented from being deteriorated by moisture.

  As described above, the cassette 5 is driven by the power from the internal power supply unit 51 and is portable and cableless. Since the cassette communication unit 52 and the console communication unit 14 communicate via wireless communication, the console 1 The operability is good and the shooting efficiency can be improved while maintaining the linkage with the camera.

  An X-ray dose sensor 548 is provided on the lower surface of the support 547. The X-ray dose sensor 548 detects the X-ray dose that has passed through the photodetector 542, and transmits a predetermined X-ray dose signal to the cassette control unit 53 when the X-ray dose reaches a predetermined amount. In this embodiment, an amorphous silicon light receiving element is used as the X-ray dose sensor 548. However, the X-ray dose sensor is not limited to this, and an X-ray sensor that directly detects X-rays using a light receiving element made of crystalline silicon or a sensor that detects fluorescence using a scintillator may be used.

  In the present embodiment, the panel 54 (including the scintillator 541, the photodetector 542, the scanning drive circuit 543, the signal reading circuit 544, the data conversion unit 545, the memory 546, the X-ray dose sensor 548, etc.) having the above-described configuration. It functions as a “radiation imaging panel” that generates an X-ray image of a subject.

  Next, a specific configuration and operation of the internal power supply unit 51 will be described.

  As shown in FIG. 5, a handle 55 is provided on the side of the cassette 5, and a fuel cell 510 that functions as the internal power supply unit 51 is provided at the center of the handle 55. The fuel cell 510 has two fuel unit mounting portions 515 to which a fuel unit 511 can be attached and detached, and a power generation portion 512.

  The fuel unit 511 includes a fuel tank 511a that stores fuel (a mixture of methanol and water) as a power generation source, and a water tank 511b that stores water generated during power generation. Each fuel unit 511 is separately replaceable (detachable) with respect to the fuel unit mounting portion 515, and each fuel unit 511 generates fuel from the fuel tank 511a of the fuel unit 511 mounted on the two fuel unit mounting portions 515. 512 can be supplied.

  The power generation unit 512 is built in the handle 55 and is disposed between the two fuel unit mounting portions 515. Specifically, the power generation unit 512 includes an anode (fuel electrode), a cathode (air electrode), and a solid polymer film, and the solid polymer film is disposed between the anode and the cathode. ing.

  An exhaust port 513 communicating with the power generation unit 512 is provided at a position corresponding to the power generation unit 512 of the handle 55. The exhaust port 513 exhausts heat generated in the power generation unit 512 and carbon dioxide and water vapor generated in the power generation unit 512 to the atmosphere.

  Microfans 514 serving as air blowing units are respectively provided at the two base end portions of the handle 55. The micro fan 514 mainly supplies air (oxygen) inside the cassette 5 to the power generation unit 512, but is interposed at a position between the panel 54 and the handle 55. At the same time, heat generated by the panel 54 is also supplied to the power generation unit 512.

  Therefore, in the cassette 5, the heat generated in the panel 54 is used for each reaction of the above formulas (1) and (2), and the power generation efficiency of the power generation unit 512 can be improved. Further, since heat and water vapor generated in the power generation unit 512 are blown toward the power generation unit 512 so as to be exhausted from the exhaust port 513, unevenness in temperature distribution in the panel 54 is suppressed, and the scintillator 541 is suppressed. Can suppress the occurrence of non-uniformity in sensitivity, can suppress the adverse effect of water vapor, and as a result can obtain a good X-ray image, and also suppress the deterioration of the scintillator 541 and the deterioration of electrical components such as circuits. It is done.

  The fuel cell 510 having the above configuration has a configuration in which fuel can be supplied from each fuel unit 511 to the power generation unit 512 and power generation by the power generation unit 512 regardless of the installation state of the cassette 5.

When the power generation unit 512 generates power in the fuel cell 510, fuel is supplied from the fuel tank 511a to the anode of the power generation unit 512, and a reaction according to the following formula (1) occurs at the anode.
CH ₃ OH + H ₂ O → CO ₂ + 6H ⁺ + 6e ⁺ (1)
The carbon dioxide produced by the reaction of the above formula (1) is exhausted from the exhaust port 513 to the atmosphere as a by-product, hydrogen ions pass through the solid polymer film and move to the cathode, electrons are taken out and the cassette 5 It becomes a power source supplied to each part.

On the other hand, at the cathode, hydrogen ions that have passed through the solid polymer membrane and oxygen supplied from the microfan 514 are supplied, and a reaction according to the following formula (2) occurs.
O ₂ + 4H ⁺ + 4e ⁺ → 2H ₂ O (2)
The water generated by the reaction of the above formula (2) is stored in the water tank 511b of the fuel unit 511 as a byproduct. By such an action, electric power is supplied from the fuel cell 510 as the internal power supply unit 51 to the cassette communication unit 52, the cassette control unit 53, the panel 54, and the like of the cassette 5.

  Here, an example in which the fuel cell 510 is provided on the handle 55 has been shown. However, as shown in FIG. 6, the fuel cell 510 is provided directly on the side of the cassette 5 and the microfan 514 is provided on the back side of the power generation unit 512. It is good also as a structure which provides. Further, in the configuration of the fuel cell 510 shown in FIGS. 5 and 6, the number of the fuel units 511 may be appropriately changed, and each fuel unit 511 is configured only from the fuel tank 511a (without the water tank 511b). The by-product water generated by the reaction of the above formula (2) may be exhausted to the atmosphere as water vapor, or each fuel tank 511a is provided with an inlet and fuel is sequentially supplied from the inlet. It is good also as a structure which can do.

  Next, the operation of the X-ray imaging system 1000 according to the first embodiment of the present invention will be described.

  The scanning drive circuit 543 is kept in the OFF state until the imaging preparation instruction signal is received from the console control unit 13. In order to maintain the off state, the scanning line 5422, the signal line 5423, and the reset line 5426 are set to the same potential, and no bias is applied to the collection electrode 5421. Alternatively, the power supply of the signal reading circuit 544 may be kept off, and the potentials of the scanning line 5422, the signal line 5423, and the reset line 5426 may be set to the GND potential.

The state in which no bias is applied to the scanning drive circuit 543 and the signal reading circuit 544 includes a photographing standby mode and a sleep mode.
Note that in the imaging standby mode, not only a bias potential is not applied to the photodiode, but also the scan driving circuit 543 and the signal reading circuit 544 rise quickly, so that power is not supplied to the scanning driving circuit 543 and the signal reading circuit 544 as well. However, power consumption can be further suppressed, which is preferable. Further, since no signal is generated in the imaging standby mode, it is preferable not to supply power to the data conversion unit 545 because it can further reduce power consumption.

  It is also preferable to provide a sleep mode that consumes less power than the shooting standby mode. Then, it is preferable to shift to the sleep mode after the captured image is completely transmitted to the console 1. In the sleep mode, it is preferable that the high-speed transmission function or the entire transmission function of the cassette communication unit 52 and the power supply to the memory are stopped while leaving only the function necessary for starting up to the shooting standby mode according to an instruction from the console 1. That is, in the sleep mode, a bias potential is not applied to the photodiode, and power is supplied to the high-speed transmission function or the entire transmission function of the scanning drive circuit 543, the signal reading circuit 544, the data conversion unit 545, the memory 546, and the cassette communication unit 52. It is preferable not to supply.

  In this manner, in the imaging standby mode and the sleep mode controlled state in which the power consumption per unit time is lower than the imaging enabled state, the scanning line 5422, the signal line 5423, and the reset line 5426 are set to the same potential, and the collecting electrode 5421 is applied. Since no bias is applied, that is, a voltage is not substantially applied to a plurality of pixels, deterioration is suppressed by applying a voltage to the PD or TFT, that is, deterioration of a plurality of pixels is suppressed. Can do. In addition, useless power consumption can be suppressed.

  Then, for example, the input unit 12 is instructed to take an image such that the 1st switch of the X-ray irradiation switch is turned on or a predetermined item such as subject information or imaging information is input via the operation input unit 2. Or the order information is received from the HIS / RIS 71, the console control unit 13 determines the photographing condition based on the instruction content of the operator or the order information from the HIS / RIS 71, and the like. An imaging preparation instruction signal based on the conditions is transmitted to the X-ray source control unit 43 and the cassette control unit 53 via the console communication unit 14 to shift to an imaging enabled state.

  When the X-ray source control unit 43 receives the imaging preparation instruction signal, the X-ray source control unit 43 drives and controls the high pressure generation source 41 to shift to a state in which a high pressure is applied to the X-ray tube 42.

  When the cassette control unit 53 receives the shooting preparation instruction signal, the cassette control unit 53 shifts to a shooting ready state. That is, all pixels are reset at predetermined intervals until a shooting instruction is input in a shooting enabled state, thereby preventing electrical energy from being accumulated in the capacitor 5424 due to dark current. Since the time during which the photographing enabled state is continued is unknown, the predetermined interval is set longer than that at the time of shooting, and the ON time of the transistor 5425 is set shorter than that at the time of shooting. Thus, in the photographing enabled state, the reading operation that places a load on the transistor 5425 is reduced. Then, after shifting to the photographing enabled state, the cassette control unit 53 transmits a photographing enabled state transition signal to the console 1. When the console control unit 13 receives the shootable state transition signal, the console control unit 13 controls the display control unit 11 to display the cassette shootable state display indicating that the cassette 5 has shifted to the shootable state.

  When the imaging instruction is input to the console control unit 13, the console control unit 13 determines the imaging condition based on the instruction content of the operator or the order information from the HIS / RIS 71 and the like, and sets the imaging condition information regarding the imaging condition. Then, the data is transmitted to the X-ray source control unit 43 and the cassette control unit 53 via the console communication unit 14.

  When the console control unit 13 receives an X-ray irradiation instruction from an operator such as the 2nd switch ON of the X-ray irradiation switch, for example, the console control unit 13 transmits an imaging instruction signal to the cassette control unit 53 of the cassette 5. Then, after the X-ray irradiation instruction is input to the console control unit 13, the console control unit 13 controls the X-ray source 4 and the cassette 5, and performs imaging while synchronizing.

  When the cassette control unit 53 receives the photographing instruction signal, the cassette control unit 53 initializes the panel 54 and shifts to a state in which the panel 54 can accumulate electric energy. Specifically, refresh is performed, and all pixels dedicated for the imaging sequence are reset a predetermined number of times and all pixels dedicated to the electrical energy storage state are reset, and the state transitions to the electrical energy storage state. Since it is required for practical use that the predetermined time is short from the exposure request to the completion of imaging preparation, all pixels dedicated to the imaging sequence are reset for this purpose. In addition, when an exposure request is generated from any state in which shooting is possible, the operability is improved by shortening the period from the exposure request to the completion of shooting preparation by entering the immediate imaging sequence drive. Plan.

  When the panel 54 shifts to a state in which electrical energy can be stored, the cassette control unit 53 transmits a preparation completion signal for the cassette 5 to the console communication unit 14. When receiving the preparation end signal, the console communication unit 14 transmits the preparation end signal of the cassette 5 to the console control unit 13.

The console control unit 13 transmits an X-ray irradiation signal to the X-ray source 4 when receiving the cassette preparation end signal and receiving an X-ray irradiation instruction. When receiving the X-ray irradiation signal, the X-ray source control unit 43 drives and controls the high-pressure generation source 41 to apply a high pressure to the X-ray tube 42 and generate X-rays from the X-ray source 4. X-rays generated from the X-ray source 4 are adjusted in the X-ray irradiation range by an X-ray diaphragm device provided at the X-ray irradiation port, and irradiate the subject.
In addition, the console control unit 13 controls the display control unit 11 to display during X-ray imaging indicating that X-ray imaging is being performed.

  X-rays that have passed through the subject are incident on the cassette 5. X-rays incident on the cassette 5 are converted into visible light by the scintillator 541.

  The X-ray dose irradiated to the cassette 5 is detected by the X-ray dose sensor 548. When the X-ray irradiation amount reaches a predetermined amount, the X-ray dose sensor 548 transmits a predetermined X-ray dose signal to the cassette control unit 53. When the cassette control unit 53 receives the predetermined X-ray dose signal, it transmits an X-ray end signal to the console communication unit 14 via the wireless repeater 6. When receiving the X-ray end signal, the console communication unit 14 transmits an X-ray end signal to the console control unit 13 and transmits an X-ray irradiation stop signal to the X-ray source control unit 43. When receiving the X-ray irradiation stop signal, the X-ray source control unit 43 drives and controls the high-pressure generation source 41, and the high-pressure generation source 41 stops applying high pressure to the X-ray tube 42. As a result, the generation of X-rays stops.

  When the cassette control unit 53 transmits the X-ray irradiation end signal, the cassette control unit 53 drives and controls the scanning drive circuit 543 and the signal reading circuit 544 based on the X-ray irradiation end signal. The scanning drive circuit 543 reads the electrical energy acquired by the photodetector 542 and inputs the acquired electrical energy to the signal reading circuit 544. The signal reading circuit 544 converts input electric energy into a digital signal. Then, the data conversion unit 545 configures the digital signal into X-ray image data. The memory 546 temporarily stores the X-ray image data configured by the data conversion unit 545.

  Subsequently, the cassette control unit 53 acquires the correction image data after acquiring the X-ray image data. The correction image data is dark image data that is not irradiated with X-rays, and is used for correcting an X-ray image in order to obtain a high-quality X-ray image. The correction image data acquisition method is the same as the X-ray image data acquisition method except that X-rays are not irradiated. The electric energy storage time is set to be equal when X-ray image data is acquired and when correction image data is acquired. Here, the electric energy storage time is a time from when the reset operation is completed, that is, from when the transistor 5425 at the time of resetting is turned off to when the transistor 5425 is turned on to read out electric energy next time. Therefore, the timing at which electric energy accumulation starts and the electric energy accumulation time differ depending on each scanning line 5422.

  The data conversion unit 545 performs offset correction on the configured X-ray image data based on the acquired correction image data, and subsequently gain correction based on the gain correction data acquired in advance and stored in the memory 546 To do. In the case of a panel composed of insensitive pixels or a plurality of small panels, the image is continuously interpolated so as not to cause a sense of incongruity at the joints of the small panels, and the correction process derived from the panel is completed. In this embodiment, the data conversion unit 545 is separate from the cassette control unit 53, but the cassette control unit 53 may also serve as the data conversion unit 545.

  The cassette control unit 53 transmits the X-ray image data temporarily stored in the memory 546 to the image storage unit 16 via the cassette communication unit 52, the wireless repeater 6, and the console communication unit 14, and the image storage unit 16 Save temporarily. Since the wireless repeater 6 and the console communication unit 14 are connected by a communication cable, the X-ray image data is transferred from the wireless repeater 6 to the console communication unit 14 at a high speed.

  As described above, the cassette 5 includes the memory 546 that functions by receiving power from the internal power supply unit 51 and temporarily stores the X-ray image data obtained by the panel 54 and transmitted by the cassette communication unit 52. , Functions as an accumulator between data generation from the panel 54 and communication between the cassette 5 and the console 1, and X-ray image data is transferred from the cassette 5 to the console 1 according to the communication state between the cassette 5 and the console 1. Can be transferred to. In particular, since the memory 546 is a RAM, data can be stored well even when the data generation speed from the panel 54 is high.

  When receiving the X-ray image data, the console control unit 13 temporarily stores it in the image storage unit 16. Then, the console control unit 13 performs control so as to create thumbnail image data from the X-ray image data temporarily stored in the image storage unit 16 by the image processing unit 15. The display control unit 11 controls the display unit 3 to display a thumbnail image based on the created thumbnail image data.

  Thereafter, the image processing unit 15 performs image processing on the X-ray image data based on the instruction content of the operator or order information from the HIS / RIS 71 or the like. The image-processed X-ray image data is displayed on the display unit 3 as an X-ray image and simultaneously transmitted to the image storage unit 16 and stored as X-ray image data. Further, the image processing unit 15 re-images the X-ray image data based on an instruction from the operator, and the image processing result of the X-ray image data is displayed on the display unit 3 as an X-ray image.

  Further, the network communication unit 18 transfers the X-ray image data to an imager 72, an image processing terminal 73, a viewer 74, a file server 75, etc., which are external devices on the network. When the X-ray image data is transferred from the console 1, the transferred external device functions correspondingly. That is, the imager 72 records the X-ray image data on an image recording medium such as a film. The image processing terminal 73 performs processing for the image processing of the X-ray image data and CAD (Computer Aided Diagnosis), and stores the processing in the file server 75. The viewer 74 displays an X-ray image based on this X-ray image data. The file server 75 stores this X-ray image data.

  Thus, since the console control part 13 can be controlled using the power supply state information which shows the power supply state of the cassette 5, favorable imaging | photography can be controlled and imaging | photography efficiency can be improved. Further, since it can be displayed on the display unit 3 according to the power supply state information, the operator determines whether or not the cassette 5 can immediately perform X-ray imaging, for example, imaging with another cassette or modality. Shooting efficiency can be improved by moving the image first or later.

  During operation of the X-ray imaging system 1000 described above, the cassette control unit 53 of the cassette 5 constantly monitors and grasps the power supply state from the fuel cell 510, and the power supply state information is It is transmitted from the cassette communication unit 52 to the console 1. In the console 1, when the console communication unit 14 receives the power supply state information, the console control unit 13 displays a display (image, character, figure, symbol) regarding the power supply state of the fuel cell 510 based on the power supply state information. The display control unit 11 is controlled so that the display unit 3 appropriately displays the display.

  With this configuration, in the X-ray imaging system 1000, during operation, the display about the power supply state of the fuel cell 510 in the cassette 5 can always be displayed on the display unit 3, and the operator can The power supply state 510 can be confirmed, and it can be instantaneously determined whether or not X-ray imaging can be performed immediately. In this case, if X-ray imaging can be performed immediately, X-ray imaging can be started immediately. On the other hand, if X-ray imaging cannot be performed immediately, other X-ray imaging can be performed before other X-ray imaging can be performed. As a result, the total imaging efficiency of the whole X-ray imaging can be improved by repeating the cycle of confirming the X-ray image from the X-ray imaging.

  When the X-ray imaging system 1000 described above is in operation, the cassette control unit 53 of the cassette 5 constantly monitors and grasps the power supply state from the second power source, and the second power source power supply state. Information may be transmitted from the cassette communication unit 52 to the console 1. In this case, when the console communication unit 14 receives the second power supply state information in the console 1, the console control unit 13 relates to the power supply state of the second power source based on the second power supply state information. It is preferable to control the display control unit 11 so that the display unit 3 may display the display (any type of display such as an image, a character, a figure, and a symbol).

  The display on the display unit 3 is preferably displayed only when the power supply state becomes defective. In addition, when the second power supply state information can also be received, a state in which X-ray imaging can be performed immediately by supplying power from either power source from both the power supply state information of the fuel cell 510 and the second power supply state information. The console control unit 13 determines (or the cassette control unit 53 makes the determination and transmits information of the determination result as power supply state information, and the console control unit 13 receives this). It is preferable that the console control unit 13 controls the display unit 3 so that X-ray imaging cannot be performed immediately by power supply from the power source.

  With this configuration, the X-ray imaging system 1000 can always display the power supply state in the cassette 5 on the display unit 3 during operation, and the operator can supply power in the cassette 5. The state can be confirmed, and whether or not X-ray imaging can be performed immediately can be determined instantaneously. In this case, if X-ray imaging can be performed immediately, X-ray imaging can be started immediately. On the other hand, if X-ray imaging cannot be performed immediately, other X-ray imaging can be performed before other X-ray imaging can be performed. As a result, the total imaging efficiency of the whole X-ray imaging can be improved by repeating the cycle of confirming the X-ray image from the X-ray imaging.

  In the present embodiment described above, the cassette 5 includes the fuel cell 510 as a power supply source for the cassette communication unit 52, the cassette control unit 53, the panel 54, etc. When it is necessary to supply the power, the fuel unit 511 is replaced and replenished with fuel each time, so that the power can be supplied quickly and sufficiently.

  In particular, since each fuel unit 511 can be exchanged and fuel can be supplied from both of the fuel units 511 to the power generation unit 512, while the fuel of one fuel unit 511 runs out and the fuel unit 511 is replaced In addition, fuel can be supplied from another fuel unit 511 to the power generation unit 512, and X-ray imaging and X-ray image generation are possible even during replacement of the fuel unit 511.

  Further, since the fuel cell 510 has a configuration in which fuel can be supplied from the fuel unit 511 to the power generation unit 512 regardless of the orientation of the cassette 5 and the power generation unit 512 can generate power, the cassette 5 is tilted or inverted. Even if the fuel cell 510 is used, power can be supplied from the fuel cell 510 to the cassette communication unit 52, the cassette control unit 53, the panel 54, etc. of the cassette 5, and X-ray imaging can be performed without paying attention to the installation state of the cassette 5. X-ray images can be generated. From the above, in this embodiment, the total imaging efficiency from X-ray imaging to X-ray image generation can be dramatically improved.

  In the present embodiment, an example in which the panel 54 is configured by one panel having 4096 × 3072 pixels is shown, but the present invention is not limited to this. For example, the panel 54 includes four panels having 2048 × 1536 pixels. What consists of a small panel can also be used. When a panel is composed of a plurality of small panels in this way, it takes time to combine four small panels into one panel, but the yield of each panel is improved, so the overall yield is also improved. However, there is an advantage that the cost is reduced.

  Furthermore, in the present embodiment, an example in which the electric energy of X-rays irradiated using the scintillator 541 and the photodetector 542 is read has been described. However, the present invention is not limited to this, and light that can directly convert X-rays into electric energy. It is possible to apply a detector. For example, an X-ray detector composed of an X-ray electric energy conversion unit using amorphous Se, PbI2, or the like and an amorphous silicon TFT or the like may be used.

In this embodiment, an example in which one A / D converter 5442 is provided in the signal reading circuit 544 is shown, but the present invention is not limited to this, and a plurality of A / D converters can be applied. is there.
The number of A / D converters is preferably 4 or more, particularly 8 or more in order to shorten the image reading time and obtain a desired S / N ratio.
The number of A / D converters is preferably 64 or less, particularly 32 or less, in order to reduce cost and size. Thereby, the analog signal band and the A / D conversion rate are not increased unnecessarily.

  In this embodiment, an example of the support body 547 formed of glass is shown, but the present invention is not limited to this, and a support body formed of resin, metal, or the like can be applied.

  In the present embodiment, the cassette 5 and the console 1 are shown in a one-to-one correspondence. However, the present invention is not limited to this, and the cassette and the console are one-to-one M, N-to-one, N-to-M. (N and M are natural numbers of 2 or more) and can be used in correspondence. At this time, the network between the cassette 5 and the console 1 is provided, the correspondence between the cassette 5 and the console 1 is stored in the correspondence information holding unit, and the correspondence information holding unit is provided on the network or in the console 1. However, it is preferable to control the cassette 5.

  In this embodiment, both the console 1 and the cassette 5 supply a storage medium storing a software program for realizing the functions of the above-described embodiments to the system or apparatus, and the computer (or computer) of the system or apparatus (or Needless to say, this can also be achieved when the CPU or MPU) reads and executes a program stored in a storage medium. Further, as a storage medium for storing a program or the like, it may be stored in a storage medium such as a nonvolatile memory, a volatile memory backed up by a power source, a ROM memory, a magnetic disk such as an optical disk or a hard disk, or a magneto-optical disk. .

  Further, by executing the program read by the computer, not only the functions of the above-described embodiments are realized, but also an OS (basic system or operating system) running on the computer based on the instruction of the program. However, it is needless to say that a case where the function of the above-described embodiment is realized by performing part or all of the actual processing and the processing is included.

  Furthermore, after the program read from the storage medium is written in the memory provided in the function expansion board inserted into the computer or the function expansion unit connected to the computer, the function expansion is performed based on the instruction of the program code. It goes without saying that the CPU or the like provided in the board or the function expansion unit performs part or all of the actual processing and the functions of the above-described embodiments are realized by the processing.

  Further, such a program may be provided from the outside via a network or a line. Even when an externally supplied program is used, the program may be stored in a storage medium such as a nonvolatile memory, a volatile memory backed up by a power source, a magnetic disk such as an optical disk or a hard disk, or a magneto-optical disk. .

[Second Embodiment]
Next, a second embodiment of the X-ray imaging system will be described with reference to FIG.
However, in 2nd embodiment, the structure of the operation input part differs in said 1st embodiment (refer FIG. 7). The operation input unit includes an X-ray irradiation switch, an X-ray source instruction content input unit, and a console instruction content input unit. The X-ray irradiation switch and the X-ray source instruction content input unit are connected to the X-ray source control unit. The console instruction content input unit is connected to the console input unit. Further, unlike the first embodiment, the console communication unit is connected to the wireless repeater, but is not connected to the X-ray source control unit. Other configurations are the same as those in the first embodiment.
In the second embodiment, the description will be made with the operation input unit and the X-ray source control unit as the center, and the same points as those in the first embodiment will be denoted by the same reference numerals as those described above, and detailed description thereof will be given. Is omitted.

FIG. 7 shows a schematic configuration of an X-ray imaging system 1000 according to the second embodiment.
As shown in FIG. 7, the operation input unit 2 includes an X-ray irradiation switch 21 for inputting an imaging preparation instruction and an imaging instruction by the operator, and an X-ray for inputting the instruction content to the X-ray source control unit 43 by the operator. A source instruction content input unit 22 and a console instruction content input unit 23 for inputting instruction content to the console 1 by an operator are provided. The instruction content includes X-ray imaging conditions such as X-ray tube voltage, X-ray tube current and X-ray irradiation time, X-ray imaging control conditions such as imaging timing, imaging region and imaging method, image processing conditions, and images. There are output conditions, cassette selection information, order selection information, subject ID, and the like.

  An X-ray source control unit 43 and an input unit 12 are connected to the X-ray irradiation switch 21. The X-ray irradiation switch 21 includes a first switch that inputs an imaging preparation instruction and a second switch that inputs an imaging instruction. An instruction from the X-ray irradiation switch 21 is input to the X-ray source control unit 43 and the input unit 12. Is done. After inputting from the first switch, it can be input from the second switch.

  An X-ray source control unit 43 is connected to the X-ray source instruction content input unit 22. The X-ray source control unit 43 drives and controls the high-pressure generation source 41 and the X-ray tube 42 based on the instruction content input from the X-ray source instruction content input unit 22.

  The input unit 12 is connected to the console instruction content input unit 23. The instruction content input to the input unit 12 is transmitted to the console control unit 13. The console control unit 13 drives and controls the console 1 and the cassette 5 based on the received instruction content.

  Next, the operation of the X-ray imaging system according to the second embodiment of the present invention will be described.

  The operator presses the first switch of the X-ray irradiation switch 21 and inputs an imaging preparation instruction. The X-ray source control unit 43 drives and controls the high-pressure generation source 41 based on an imaging preparation instruction by the first switch to shift to a state in which a high pressure is applied to the X-ray tube 42. Based on the shooting preparation instruction by the first switch input to the input unit 12, the console control unit 13 transmits the shooting preparation instruction to the cassette 5 via the console communication unit 14 and the wireless repeater 6. The cassette control unit 53 repeats reset at a predetermined interval based on the received imaging preparation instruction until an imaging instruction is input, and prevents electric energy from being accumulated in the capacitor 5424 due to dark current.

  The operator presses the second switch of the X-ray irradiation switch 21 and inputs an imaging instruction. The X-ray source control unit 43 drives and controls the high-pressure generation source 41 based on an imaging instruction from the second switch, applies a high pressure to the X-ray tube 42, and generates radiation. Based on an imaging preparation instruction by the first switch input to the input unit 12, the console control unit 13 drives and controls the cassette 5 and performs imaging using radiation emitted from the X-ray source 4.

  X-rays irradiated from the X-ray source 4 pass through the subject and enter the cassette 5. Based on the X-rays incident on the cassette 5, X-ray image data is acquired and transmitted to the console 1 via the wireless repeater 6 and the console communication unit 14.

1 is a diagram showing a schematic configuration of a first embodiment of an X-ray imaging system according to the present invention. It is a perspective view which shows schematic structure of one Embodiment of the cassette by this invention. It is sectional drawing of one Embodiment of the cassette centering on the panel by this invention. It is a circuit diagram which shows the structure of one Embodiment of the circuit centering on the photodetector by this invention. It is a perspective view which shows the structure of the internal power supply of a cassette. It is a perspective view which shows the modification of the structure of FIG. It is a figure which shows schematic structure of 2nd embodiment of the X-ray imaging system by this invention.

Explanation of symbols

1000 X-ray imaging system (radiological imaging system)
DESCRIPTION OF SYMBOLS 1 Console 13 Console control part 14 Console communication part 15 Image processing part 3 Display part 5 Cassette (Cassette for radiographic imaging)
51 Internal Power Supply Unit 510 Fuel Cell 511 Fuel Unit 512 Power Generation Unit 513 Exhaust Port 514 Micro Fan (Blower Unit)
515 Fuel unit mounting part 52 Cassette communication part 53 Cassette control part 54 Panel (radiation imaging panel)
541 Scintillator (part of radiation imaging panel)
542 Photodetector (part of radiation imaging panel)
543 Scanning drive circuit (part of radiation imaging panel)
544 Signal reading circuit (part of radiation imaging panel)
545 Data converter (part of the radiation imaging panel)
546 memory (part of radiation imaging panel)
547 Support (part of radiation imaging panel)
548 X dose sensor (part of radiation imaging panel)
6 wireless repeaters

Claims (18)

A radiographic imaging cassette that generates radiographic image data by radiography;
A console for displaying a radiation image on a display unit using the radiation image data;
With
The radiographic imaging cassette is
A cassette communication unit capable of communicating with the console;
A radiation imaging panel for generating the radiation image data;
A cassette controller that transmits the radiation image data generated by the radiation imaging panel from the cassette communication unit to the console;
A fuel cell that supplies power to the cassette communication unit, the radiation imaging panel, and the cassette control unit;
Have
The console is
A console communication unit that receives the radiation image data transmitted from the cassette communication unit;
A radiographic imaging system for displaying the radiographic image on the display unit based on the radiographic image data received by the console communication unit. In the radiographic imaging system of Claim 1,
The fuel cell is
A fuel unit mounting portion to which a fuel unit for storing fuel can be attached and detached;
A power generation unit that receives power from the fuel unit mounted on the fuel unit mounting unit and generates power;
A radiographic imaging system comprising: In the radiographic imaging system of Claim 2,
The fuel cell is
The fuel unit has a plurality of fuel unit mounting portions that can be separately attached to and detached from each other, and fuel can be supplied to the power generation unit from any of the fuel units mounted on the plurality of fuel unit mounting portions. A radiographic imaging system characterized by being. In the radiographic imaging system as described in any one of Claims 1-3,
Radiation imaging, wherein the fuel cell is capable of supplying fuel from the fuel unit to the power generation unit and generating power in the power generation unit regardless of the orientation of the radiographic imaging cassette. system. In the radiographic imaging system as described in any one of Claims 1-4,
The radiographic imaging cassette is
A radiographic imaging system comprising: a blower that blows heat generated in the radiation imaging panel toward the fuel cell. In the radiographic imaging system as described in any one of Claims 1-5,
The radiation imaging panel is
A scintillator that converts radiation into fluorescence;
A protective layer for protecting the scintillator;
A support for supporting the scintillator;
Have
The radiographic image capturing system, wherein the scintillator is covered with the protective layer and the support. In the radiographic imaging system as described in any one of Claims 1-6,
The cassette control unit transmits power supply state information indicating a supply state of power from the fuel cell from the cassette communication unit to the console,
The radiographic imaging system, wherein the console causes the display unit to display the power supply state from the fuel cell using the power supply state information received by the console communication unit. In the radiographic imaging system as described in any one of Claims 1-7,
The radiographic imaging system, wherein the cassette communication unit can communicate with the console wirelessly. In the radiographic imaging system as described in any one of Claims 1-8,
A wireless repeater capable of wireless communication with the cassette communication unit,
The radiographic imaging system, wherein the console communication unit can communicate with the wireless repeater via a communication cable. In the radiographic imaging system as described in any one of Claims 1-9,
A radiographic imaging system, wherein the console is a portable terminal. A radiographic imaging cassette that generates radiographic image data by radiography,
A cassette communication unit capable of communicating with the console;
A radiation imaging panel for generating the radiation image data;
A cassette controller that transmits the radiation image data generated by the radiation imaging panel from the cassette communication unit to the console;
A fuel cell that supplies power to the cassette communication unit, the radiation imaging panel, and the cassette control unit;
A cassette for radiographic imaging. In the cassette for radiographic imaging of Claim 11,
The fuel cell is
A fuel unit mounting portion to which a fuel unit for storing fuel can be attached and detached;
A power generation unit that receives power from the fuel unit mounted on the fuel unit mounting unit and generates power;
A cassette for radiographic imaging. The radiographic imaging cassette according to claim 12,
The fuel cell is
The fuel unit has a plurality of fuel unit mounting portions that can be separately attached to and detached from each other, and fuel can be supplied to the power generation unit from any of the fuel units mounted on the plurality of fuel unit mounting portions. A cassette for radiographic imaging, characterized by being. In the cassette for radiographic imaging as described in any one of Claims 11-13,
Radiation imaging, wherein the fuel cell is capable of supplying fuel from the fuel unit to the power generation unit and generating power at the power generation unit regardless of the orientation of the radiographic imaging cassette. For cassette. In the cassette for radiographic imaging as described in any one of Claims 11-14,
A radiographic imaging cassette, comprising: a blower that blows heat generated in the radiation imaging panel toward the fuel cell. In the cassette for radiographic imaging as described in any one of Claims 11-15,
The radiation imaging panel is
A scintillator that converts radiation into fluorescence;
A protective layer for protecting the scintillator;
A support for supporting the scintillator;
Have
A radiographic imaging cassette, wherein the scintillator is covered with the protective layer and the support. In the cassette for radiographic imaging as described in any one of Claims 11-16,
The cassette for radiographic imaging, wherein the cassette control unit causes power supply state information indicating a supply state of power from the fuel cell to be transmitted from the cassette communication unit to the console. In the cassette for radiographic imaging as described in any one of Claims 11-17,
The cassette for radiographic imaging, wherein the cassette communication unit can communicate wirelessly.

Images