JP2007061386A - Radiation image photographing system and console display device - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a radiation image photographing system capable of shortening time required for radiation image photographing and improving photographing efficiency by improving the portability of a console. <P>SOLUTION: An X-ray control chamber R2 is provided with a console display device 7 for displaying photographed X-ray images or the like. The console display device 7 is provided with a display device 71 for displaying the X-ray images or the like and display is controlled by a controller 72 similarly provided in the console display device 7. Also, the console display device 7 is provided with a communication part 3 capable of performing radio communication with a radio repeater 2 similarly installed in the X-ray control chamber R2. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

    The present invention relates to a radiographic image capturing system and a console display device, and more particularly to a radiographic image capturing system and a console display device provided with wireless communication means.

  Conventionally, radiation images represented by X-ray images have been widely used for medical diagnosis. A radiation image is an image obtained by irradiating a subject with radiation such as X-rays and detecting the intensity distribution of the radiation transmitted through the subject.

  In order to obtain this radiation image, an imaging device using CR (Computed Radiography) or a film is known. However, since a radiographic imaging system using CR requires a long period of time from several tens of seconds to several minutes to confirm the captured image after irradiating radiation, it is necessary to perform imaging when confirming a defect in the captured image. It may be necessary to recall the subject outside the room and perform re-shooting.

Therefore, in recent years, in order to obtain a radiographic image, a radiographic imaging system using an FPD (Flat Panel Detector) that detects radiation transmitted through a subject, converts it into an electrical signal, and stores it as radiographic image information has been proposed. (For example, refer to Patent Document 1 and Patent Document 2). The radiographic image capturing system using this FPD can confirm an image captured after irradiation with radiation in a short time of several seconds.

In addition, a technique is disclosed in which when an FPD capable of wireless communication with a radiographic imaging apparatus exists, the console can recognize and control each FPD by giving an identification number to each FPD. (For example, refer to Patent Document 3). An FPD capable of wireless communication can improve portability, and has a merit that imaging efficiency can be improved because a plurality of FPDs can be used while radiographic imaging is performed.
JP2002-200062 JP2002-200063 JP2002-191586

  However, even if the portability of the FPD is improved as in Patent Document 3, if the console is placed away from the FPD, for example, in the vicinity of the radiation irradiation switch in a room different from the console, It is necessary for the person to move the room in order to operate the FPD after confirming the image by radiography on the console, and there is a problem that it takes time and labor for the image shooting operation.

  The present invention has been made in view of the above points, and provides a radiographic imaging system capable of improving radiographic imaging efficiency by reducing the time taken for radiographic imaging by improving the portability of the console. It is an object to do.

In order to solve such a problem, the invention described in claim 1
A cassette for communicating the generated image data via a cassette communication unit;
A radiographic imaging system in which a console including a console communication unit that wirelessly communicates the cassette communication unit and the image data and a console control unit that controls driving of the console communication unit can communicate via a communication network. In
A portable console display device provided with a communication unit that communicates the image data with the console communication unit, a display unit that displays the image data, and a control unit that controls driving of the display unit. It is the radiographic imaging system characterized by this.

  According to a second aspect of the present invention, in the radiographic image capturing system according to the first aspect, the communication unit performs wireless communication with the console communication unit.

  According to a third aspect of the present invention, in the radiographic imaging system according to the first or second aspect, the console display device includes an internal power source that is a power supply source to the console display device. Features.

  According to a fourth aspect of the present invention, in the radiographic imaging system according to any one of the first to third aspects, the console display device includes an input unit for inputting a driving condition of the console. It is characterized by that.

  According to a fifth aspect of the present invention, in the radiographic imaging system according to any one of the first to fourth aspects, the cassette includes a cassette power source that is a power supply source to the cassette, and the cassette power source. And a cassette control unit for controlling the driving of the inside.

  According to a sixth aspect of the present invention, in the radiographic image capturing system according to any one of the first to fifth aspects, the cassette communication unit wirelessly communicates with the console.

  The invention according to claim 7 is provided with a communication unit that communicates the generated image data with a console communication unit, a display unit that displays the image data, and a control unit that controls driving of the display unit, It is a console display device characterized by having portability.

  According to an eighth aspect of the present invention, in the console display device according to the seventh aspect, the communication unit performs wireless communication with the console communication unit.

  According to a ninth aspect of the present invention, in the console display device according to the seventh or eighth aspect of the present invention, the console display device further includes an input unit for inputting a condition for generating image data by the cassette.

  According to the first aspect of the present invention, since the portable console display device can be used, the console display device can be moved not only to the radiation control room but also to the radiation imaging room to display image data. There is an effect.

  According to the second aspect of the present invention, since the console display device can perform wireless communication with the console, the portability of the console display device can be further improved.

  According to the third aspect of the invention, since the console display device includes the internal power supply, the portability of the console display device can be further improved.

  According to the invention described in claim 4, since the console display device is provided with an input unit for inputting the drive condition of the console, the console display device can input not only the image display but also the drive condition of the console. There is an effect that the convenience of the console display device can be further improved.

  According to the invention described in claim 5, since the cassette is provided with a cassette power supply which is an internal power supply, it has portability. As a result, the operator can freely move the cassette, so that the imaging efficiency can be improved.

  According to the sixth aspect of the present invention, since the cassette can perform wireless communication with the console, it is not necessary to always connect the cassette to the communication cable, and the portability of the cassette can be further improved. Thereby, since the operator can move the cassette more freely, there is an effect that the photographing efficiency can be further improved.

  According to the invention described in claim 7, since the portable console display device can be used, the console display device can be moved not only to the radiation control room but also to the radiation imaging room to display image data. There is an effect.

  According to the invention described in claim 8, since the console display device can perform wireless communication with the console, the portability of the console display device can be further improved.

  According to the ninth aspect of the present invention, since the console display device includes the internal power supply, the portability of the console display device can be further improved.

  Hereinafter, embodiments of the present invention will be described with reference to the drawings.

  An embodiment of an X-ray imaging system according to the present invention will be described with reference to FIGS.

  As shown in FIG. 1, an X-ray imaging system 1000 according to this embodiment is a system that assumes X-ray imaging performed in a hospital. For example, an X-ray imaging room R1 that irradiates a subject with X-rays. And an X-ray control room R2 that controls the X-rays irradiated by the X-ray engineer to the subject.

  The X-ray imaging room R1 is provided with a portable console 1 that has the portability of controlling the entire X-ray imaging system and performing control of X-ray imaging and image processing of acquired X-ray images. . The console 1 performs wireless communication via a wireless repeater 2 that is also installed in the X-ray imaging room R1.

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

  As the input unit 11, for example, a touch panel, a keyboard, or the like can be used, and an operator can perform X-ray imaging conditions such as an X-ray tube voltage, an X-ray tube current, and an X-ray irradiation time via the input unit 11. Instruction contents such as an X-ray imaging control condition such as an imaging region and an imaging method, an image processing condition, an image output condition, cassette selection information, order selection information, and a subject ID are input.

  The console control unit 12 determines imaging conditions based on the instruction contents input from the input unit 11 and the order information of the HIS / RIS 91, and relates to the imaging conditions to the X-ray source 3 and the cassette 4 via the console communication unit 13. The imaging condition information is transmitted, and the X-ray source 3 and the cassette 4 are controlled during X-ray image imaging. Further, the console control unit 12 causes the image storage unit 14 to temporarily store the X-ray image data received by the console communication unit 13 from the cassette 4. The console control unit 12 controls the image processing unit 15 to create thumbnail image data from the X-ray image data temporarily stored in the image storage unit 14. Then, the console control unit 12 performs image processing based on the instruction content received by the input unit 11 and the order information of the HIS / RIS 91 on the X-ray image data by the image processing unit 15, and the image-processed X-ray The image storage unit 14 is controlled to store the image data. Then, based on the X-ray image data image-processed by the image processing unit 15, the console control unit 12 further determines the X-ray image data based on the contents of instructions input to the console 1 via the input unit 11 thereafter. Re-image processing and display of the image processing result, and transfer, save and display X-ray image data to an external device on the network.

As the console control unit 12, 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 3, the cassette 4, 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. read from the ROM and executable by the CPU in various processes controlled by the CPU of the console control unit 12. 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 13 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.

The console communication unit 13 can communicate with the X-ray source 3 and the cassette 4 via the wireless repeater 2, and can transmit a control signal based on the instruction content to the X-ray source 3 and the cassette 4. X-ray image data from can be received.
The console communication unit 13 communicates various information between the console 1 and an external device via the wireless repeater 2. As an external device, for example, a HIS / RIS (Hospital Information System / Radiology Information System) 91, an imager 92, an image processing terminal 93, a viewer 94, a file server 95, etc. are connected. Is possible.
The HIS / RIS 91 obtains subject information, imaging region, imaging method, and the like from the HIS / RIS main body, and provides them to the console 1. The imager 92 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 terminal 93 performs processing for X-ray image data output from the console 1 and processing for CAD (Computer Aided Diagnosis), and stores it in the file server 95. The viewer 94 displays an X-ray image based on the X-ray image data output from the console 1. The file server 95 is a file server that stores X-ray image data that has undergone processed image processing. The console communication unit 13 outputs X-ray image data to an external device according to a predetermined protocol such as DICOM (Digital Imaging and Communications in Medicine).

  The image storage unit 14 temporarily stores X-ray image data received from the cassette 4 by the console communication unit 13 and stores X-ray image data subjected to image processing. As the image storage unit 14, it is possible to use a hard disk, a silicon disk, or the like, which is a large-capacity and high-speed storage device.

  The image processing unit 15 performs image processing on the X-ray image data received from the cassette 4 by the console communication unit 13. The image processing unit 15 performs image data correction processing, enlargement compression processing, spatial filtering processing, recursive processing, gradation processing, scattered radiation correction processing, grid correction processing, frequency enhancement processing, dynamic range (DR) based on the instruction content. Image processing such as compression processing is performed.

  As the console power source 16, an internal power source (not shown) such as a battery or a battery is used to supply power to each part constituting the console 1. When a battery is used as the console power source 16, it needs to be charged.

  In the X-ray imaging room R1, an X-ray source 3 that irradiates the subject with X-rays and a cassette 4 that detects the X-rays applied to the subject and acquires X-ray image data are arranged. The cassette 4 in this embodiment is portable.

  The X-ray source 3 includes a high-voltage generation source 31 that generates a high-voltage and an X-ray tube 32 that generates X-rays when a high-voltage is applied by the high-voltage generation source 31. An X-ray aperture device (not shown) for adjusting the X-ray irradiation range is provided at the X-ray irradiation port of the X-ray tube 32. 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 3 is provided with an X-ray source control unit 33, and the high-pressure generation source 31 and the X-ray tube 32 are connected to the X-ray source control unit 33, respectively. The X-ray source control unit 33 is connected to the wireless repeater 2 by the communication cable 6 and drives and controls each unit of the X-ray source 3 based on a control signal transmitted from the console communication unit 13. That is, the high pressure generation source 31 and the X-ray tube 32 are controlled.

X-rays that have passed through the subject from the X-ray source 3 are incident on the cassette 4. The position of the cassette 4 is adjusted by the operator so that the X-ray is transmitted to a desired position of the subject before X-ray imaging.
In the cassette 4, a cassette power supply 41, a cassette communication unit 42, a cassette control unit 43, and a panel 44 are disposed. The cassette power supply 41, the cassette communication unit 42, the cassette control unit 43, and the panel 44 are each connected to a bus in the cassette 4.

The cassette power supply 41 supplies electric power to each unit disposed in the cassette 4. The cassette power supply 41 is provided with a capacitor that can be charged and can handle power consumed during photographing. As the capacitor, an electrolytic double layer capacitor can be applied. As the cassette power supply 41, a primary battery such as a manganese battery, a nickel / cadmium battery, a mercury battery, or a lead battery that requires battery replacement, or a rechargeable secondary battery can be applied.
From the viewpoint of imaging efficiency, the capacity of the cassette power supply 41 is preferably 4 or more (especially 7 or more) in terms of the number of X-ray images of the maximum size that can be taken continuously.
The capacity of the cassette power supply 41 is 100 or less (especially 50 times or less) when converted from the maximum number of X-ray images that can be taken continuously from the viewpoint of size reduction, weight reduction, and cost reduction. It is preferable that

  The cassette communication unit 42 is configured to be able to perform wireless communication with the console communication unit 13, and transmits / receives control signals between the cassette communication unit 42 and the console communication unit 13, and console communication from the cassette communication unit 42. X-ray image data can be transmitted to the unit 13.

  The cassette control unit 43 controls each unit provided in the cassette 4 based on the control signal of the console 1 received by the cassette communication unit 42.

  The panel 44 outputs X-ray image data based on the X-rays transmitted through the subject. The panel 44 of the present embodiment is an indirect flat panel detector (FPD).

FIG. 2 is a perspective view showing a schematic configuration of the cassette 4, and FIG. 3 is a cross-sectional view of the cassette 4 centering on the panel 44.
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.

A scintillator 441 for detecting X-rays transmitted through the subject and converting the detected X-rays into fluorescence in the visible region (hereinafter referred to as “visible light”) extends in the uppermost layer of the panel 44.
The scintillator 441 includes a phosphor as a main component. The scintillator 441 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.

Under the scintillator 441, a photodetector 442 made of amorphous silicon is stacked and extended. The photodetector 442 converts visible light emitted from the scintillator 441 into electrical energy and outputs the electrical energy. .
The panel 44 is preferably composed of pixels of 1000 × 1000 pixels or more (particularly 2000 × 2000 pixels or more) from the viewpoint of diagnosis of diagnosis using an X-ray image. Moreover, it is preferable that the panel 44 is comprised by the pixel of 10,000x10,000 pixels or less (especially 6000x6000 pixels or less) from a viewpoint of a human visual limit and the image processing speed of a X-ray image.
The size of the imaging region of the panel 44 is preferably an area of 10 cm × 10 cm or more (particularly, 20 cm × 20 cm or more) from the viewpoint of diagnostic performance by X-ray images. Further, the size of the imaging region of the panel 44 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 a cassette.
The size of one pixel of the panel 44 is preferably 40 μm × 40 μm or more (especially 70 μm × 70 μm or more) from the viewpoint of reducing the amount of X-ray exposure. In addition, the size of one pixel of the panel 44 is preferably 200 μm × 200 μm or less (especially 160 μm × 160 μm or less) from the viewpoint of the diagnostic property of diagnosis using an X-ray image.
In the present embodiment, an example will be described in which the panel 44 includes 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, as shown in FIG. 4, a circuit configuration centering on the photodetector 442 will be described.

  As shown in FIG. 4, the light detector 442 has a two-dimensionally arranged collection electrode 4421 for reading out the electrical energy accumulated in accordance with the intensity of the irradiated X-rays. The collection electrode 4421 is configured as one electrode of a capacitor 4424 so that electric energy is stored in the capacitor 4424. Here, one collecting electrode 4421 corresponds to one pixel of the X-ray image data.

  A scanning line 4422 and a signal line 4423 are provided between the collecting electrodes 4421 adjacent to each other. The scanning line 4422 and the signal line 4423 are orthogonal to each other.

The capacitor 4424 is connected to a switching thin film transistor 4425 (TFT: Thin Film Transistor, hereinafter referred to as a transistor) that controls storage and reading of electric energy. The transistor 4425 has a drain electrode or a source electrode connected to the collection electrode 4421 and a gate electrode connected to the scanning line 4422. When the drain electrode is connected to the scan line 4422, the source electrode is connected to the signal line 4423, and when the source electrode is connected to the collection electrode 4421, the drain electrode is connected to the signal line 4423. In the panel 44, an initialization transistor 4427 to which, for example, a drain electrode is connected is provided on the signal line 4423. The source electrode of the initialization transistor 4427 is grounded. The gate electrode is connected to the reset line 4426.
Note that the transistor 4425 and the initialization transistor 4427 are preferably formed using a silicon stacked structure or an organic semiconductor.

In addition, a reset line 4426 to which a reset signal RT is transmitted from the scan drive circuit 443 is connected to the scan drive circuit 443 at right angles to the signal line 4423.
A gate electrode of an initialization transistor 4427 that is turned on by a reset signal RT is connected to the reset line 4426. In the initialization transistor 4427, the gate electrode is connected to the reset line 4426, the drain electrode is connected to the signal line 4423, and the source electrode is grounded. When the source electrode is connected to the signal line 4423, the drain electrode is grounded.
When the reset signal RT is supplied from the scan drive circuit 443 to turn on the initialization transistor 4427 and the read signal RS is supplied from the scan drive circuit 443 to turn on the transistor 4425, the signal is accumulated in the capacitor 4424. Electrical energy is released out of the photodetector 442 through the transistor 4425. Hereinafter, the release of the electrical energy accumulated in the capacitor 4424 when the reset signal RT is supplied is referred to as reset (initialization) of the photodetector 442.
In addition, a scan drive circuit 443 that supplies a read signal RS to the scan line 4422 is connected to the scan line 4422. The transistor 4425 connected to the scan line 4422 to which the read signal RS is supplied is turned on, and electric energy accumulated in the capacitor 4424 connected to the transistor 4425 is read and supplied to the signal line 4423. That is, by driving the transistor 4425, a signal for each pixel of the X-ray image data can be generated.

  A signal reading circuit 444 is connected to the signal line 4423. The electric energy read from the signal line 4423 after being stored in the capacitor 4424 is supplied to the signal reading circuit 444. The signal reading circuit 444 includes a signal converter 4441 that supplies a voltage signal SV proportional to the amount of electrical energy supplied to the signal reading circuit 444 to the A / D converter 4442, and a voltage signal SV from the signal converter 4441. An A / D converter 4442 that converts the signal into a digital signal and supplies the digital signal to the data converter 445 is provided.

  A data conversion unit 445 is connected to the signal reading circuit 444. The data converter 445 generates X-ray image data based on the digital signal supplied from the signal reading circuit 444.

When high resolution image data is not needed or when it is desired to acquire image data quickly, the console control unit 12 receives control signals such as thinning, pixel average, and region extraction according to the imaging method selected by the operator. It transmits to the control part 43. The cassette control unit 43 performs control so as to execute the following decimation, pixel averaging, region extraction, and the like according to the received control signals such as decimation, pixel averaging, and region extraction.
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 4422 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 has means for limiting the image data capture area. This is because the acquisition area of the necessary image data is specified from the instruction content of the photographing method, etc., and the cassette control unit 43 changes the data acquisition range of the scanning drive circuit 443 based on the specified acquisition area. The panel 44 drives the taken-in range.

A memory 446 is connected to the data conversion unit 445. The memory 446 stores the X-ray image data generated by the data conversion unit 445. The memory 446 stores gain correction data in advance.
The memory 446 includes a RAM (Random Access Memory) and a nonvolatile memory. The memory 446 can be written into the nonvolatile memory at a time after sequentially writing into 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 446 is preferably 4 or more (especially 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. In addition, the capacity of the memory 446 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 447 on a flat plate formed of a glass substrate is provided below the photodetector 442, and the stacked structure of the scintillator 441 and the photodetector 442 is supported by the support body 447.

  An X-ray dose sensor 448 is provided on the lower surface of the support 447. The X-ray dose sensor 448 detects the X-ray dose that has passed through the photodetector 442, and transmits a predetermined X-ray dose signal to the cassette control unit 43 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 448. 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 X-ray control room R2, an operation input unit 5 through which an operator inputs an imaging preparation instruction or imaging support is arranged in a state of being connected to the wireless repeater 2 installed in the X-ray imaging room R1 by a communication cable 6. Has been. For example, an X-ray irradiation request switch or a joystick can be used as the operation input unit 5.

  Further, the X-ray control room R2 is provided with a console display device 7 for displaying a photographed X-ray image and the like. The console display device 7 is provided with a display unit 71 that displays an X-ray image or the like, and the display is controlled by a control unit 72 provided in the console display device 7. As the display unit 71, for example, a liquid crystal monitor or an electronic film can be used, and characters and images such as X-ray imaging conditions and image processing conditions can be displayed in addition to X-ray images.

  In addition, the console display device 7 is provided with a communication unit 73 capable of performing wireless communication with the wireless repeater 8 installed in the X-ray control room R2. The wireless repeater 8 is connected to the wireless repeater 2 installed in the X-ray imaging room R1 by a communication cable 6. The communication unit 73 can communicate with the console communication unit 13 via the wireless repeater 8 and can transmit and receive control signals and image data to and from the console communication unit 13. Further, when the console display device 7 moves into the X-ray imaging room R1, wireless communication can be performed directly between the communication unit 73 and the console communication unit 13 without using the wireless repeater 2. ing.

  Further, the console display device 7 is provided with an internal power supply 74 such as a battery or a battery, and supplies power to each part of the console display device 7. For this reason, the console display device can be operated without being connected to an external power supply, and therefore it is not necessary to connect to a connection cable or the like with the external power supply. When a battery is used as the internal power source 74, it is necessary to charge in accordance with power consumption.

  As described above, the console display device 7 is a portable display device having portability, and the operator can freely carry the X-ray imaging room R1 as well as the X-ray control room R2.

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

  The scanning drive circuit 443 is kept off until an imaging preparation instruction or an imaging instruction is input from the operator. In order to maintain the OFF state, the scanning line 4422, the signal line 4423, and the reset line 4426 are set to the same potential, and no bias is applied to the collection electrode 4421. Alternatively, the power of the signal reading circuit 444 may be kept off, and the potentials of the scanning line 4422, the signal line 4423, and the reset line 4426 may be set to the GND potential. That is, the scanning drive circuit 443 and the signal reading circuit 444 may shift to a photographing standby mode or a sleep mode in which no potential is applied.

A state in which no bias is applied to the scanning drive circuit 443 and the signal reading circuit 444 includes a photographing standby mode and a sleep mode.
In the imaging standby mode, not only a bias potential is not applied to the photodiode, but also the scanning drive circuit 443 and the signal reading circuit 444 rise quickly, so that power is not supplied to the scanning driving circuit 443 and the signal reading circuit 444 as well. However, power consumption can be further suppressed, which is preferable. Furthermore, since no signal is generated in the imaging standby mode, it is preferable not to supply power to the data conversion unit 445 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 to stop the power supply to the high-speed transmission function or the entire transmission function of the cassette communication unit 42 and the memory, leaving only the function necessary for starting up to the shooting standby mode by an instruction from the console 1. That is, in the sleep mode, no bias potential is applied to the photodiode, and power is supplied to the high-speed transmission function or the entire transmission function of the scanning drive circuit 443, the signal reading circuit 444, the data conversion unit 445, the memory 446, and the cassette communication unit 42. It is preferable not to supply.

When the console control unit 12 receives the photographing preparation instruction, the console control unit 12 determines the photographing condition based on the instruction content of the operator or the order information from the HIS / RIS 91, and the photographing instruction based on the photographing condition. The control signal is transmitted to the X-ray source control unit 33 and the cassette control unit 43 via the console communication unit 13 to shift to the imaging preparation state.
Here, the imaging preparation instruction is an instruction that the operator inputs via the operation input unit 5, for example, like the 1st switch of the X-ray irradiation switch. In addition, input of predetermined items such as subject information and shooting information may be used as a shooting preparation instruction.

  The X-ray source control unit 33 drives and controls the high-pressure generating source 31 based on the received control signal, and shifts to a state in which a high pressure is applied to the X-ray tube 32.

  The cassette control unit 43 repeatedly resets all pixels at predetermined intervals until a shooting instruction is input in the shooting preparation state, and prevents electrical energy from being accumulated in the capacitor 4424 due to dark current. Since the time during which the shooting preparation state continues is unknown, this predetermined interval is set longer than that at the time of shooting, and the ON time of the transistor 4425 is set shorter than that at the time of shooting. As a result, in the imaging preparation state, the reading operation that loads the transistor 4425 is reduced.

  When the shooting instruction is input to the console control unit 12, the console control unit 12 determines the shooting condition based on the instruction content of the operator or the order information from the HIS / RIS 91, and the shooting instruction based on the shooting condition. Is transmitted to the X-ray source control unit 33 and the cassette control unit 43 via the console communication unit 13.

When an imaging instruction is input to the console control unit 12, the console control unit 12 controls the X-ray source 3 and the cassette 4 to perform imaging while synchronizing. Here, the imaging instruction is input by the operator via the operation input unit 5 like a 2nd switch of an X-ray irradiation switch, for example.
The console control unit 12 transmits an X-ray irradiation request signal based on the imaging instruction to the cassette control unit 43 of the cassette 4. When the cassette controller 43 receives the X-ray irradiation request signal, the cassette controller 43 initializes the panel 44 and shifts to a state in which the panel 44 can accumulate electrical 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 occurs from any state of driving in the imaging preparation state, the operability is improved by shortening the period from the exposure request to the completion of imaging preparation by entering the immediate imaging sequence driving. Plan.
When the panel 44 shifts to a state in which electrical energy can be stored, the cassette control unit 43 transmits a preparation completion signal for the cassette 4 to the console communication unit 13. When receiving the preparation end signal, the console communication unit 13 transmits a cassette preparation end signal to the console control unit 12.
When the console control unit 12 receives the X-ray irradiation instruction in a state where the cassette preparation completion signal is received, the console control unit 12 transmits an X-ray irradiation signal to the X-ray source 3. When receiving the X-ray irradiation signal, the X-ray source control unit 33 drives and controls the high-pressure generation source 31 to apply a high pressure to the X-ray tube 32 and generate X-rays from the X-ray source 3. X-rays generated from the X-ray source 3 are irradiated to the subject by adjusting the X-ray irradiation range by an X-ray diaphragm device provided at the X-ray irradiation port.

  X-rays that have passed through the subject enter the cassette 4. X-rays incident on the cassette 4 are converted into visible light by the scintillator 441.

  The X-ray dose irradiated to the cassette 4 is detected by the X-ray dose sensor 448. When the X-ray irradiation amount reaches a predetermined amount, the X-ray dose sensor 448 transmits a predetermined X-ray dose signal to the cassette control unit 43. When the cassette control unit 43 receives the predetermined X-ray dose signal, it transmits an X-ray end signal to the console communication unit 13. When receiving the X-ray end signal, the console communication unit 13 transmits an X-ray end signal to the console control unit 12 and transmits an X-ray irradiation stop signal to the X-ray source control unit 33. When the X-ray source control unit 33 receives this X-ray irradiation stop signal, the X-ray source control unit 33 drives and controls the high-pressure generation source 31, and the high-pressure generation source 31 stops applying high pressure to the X-ray tube 32. As a result, the generation of X-rays stops.

  When the cassette control unit 43 transmits the X-ray irradiation end signal, the cassette control unit 43 drives and controls the scanning drive circuit 443 and the signal reading circuit 444 based on the X-ray irradiation end signal. The scan driving circuit 443 reads the electrical energy acquired by the photodetector 442 and inputs the acquired electrical energy to the signal reading circuit 444. The signal reading circuit 444 converts the input electrical energy into a digital signal. Then, the data conversion unit 445 configures the digital signal into image data. The memory 446 temporarily stores the image data configured by the data conversion unit 445.

  Subsequently, the cassette control unit 43 acquires the correction image data after acquiring the 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 image data acquisition method except that X-rays are not irradiated. The electric energy storage time is set to be equal when the image data is acquired and when the correction image data is acquired. Here, the electric energy storage time is a time from when the reset operation is completed, that is, after the transistor 4425 at the time of resetting is turned off to when the transistor 4425 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 4422.

  The data conversion unit 445 performs offset correction on the configured image data based on the acquired correction image data, and subsequently performs gain correction based on the gain correction data acquired in advance and stored in the memory 446. 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 445 is separate from the cassette control unit 43, but the cassette control unit 43 may also serve as the data conversion unit 445.

  The console control unit 12 transmits the image data temporarily stored in the memory 446 to the image storage unit 14 via the cassette communication unit 42 and the console communication unit 13 and temporarily stores the image data in the image storage unit 14. The image processing unit 15 performs image processing on the image data stored in the image storage unit 14 based on the instruction content of the operator or order information from the HIS / RIS 91 or the like. The image data subjected to the image processing is displayed on the display unit 71 of the console display device 7 via the console communication unit 13 and is simultaneously transmitted to the image storage unit 14 and stored as image data. Since the console display device 7 has portability, it can be freely carried and can be operated not only in the X-ray control room R2 but also in the X-ray imaging room R1. Thus, the operator can move to the X-ray imaging room R1 while performing image processing after X-ray irradiation, and can proceed with preparation for the next imaging while confirming the captured image. Further, based on the operator's instruction, the image processing unit 15 re-images the image data, and the display unit 71 displays the image processing result of the image data. The console communication unit 13 also transfers the image data to an imager 92, an image processing terminal 93, a viewer 94, a file server 95, and the like, which are external devices on the network. When image data is transferred from the console 1, the transferred external device functions correspondingly. That is, the imager 92 records the X-ray image data on an image recording medium such as a film. The image processing terminal 93 performs image processing of the X-ray image data and processing for CAD (Computer Aided Diagnosis), and stores it in the file server 95. The viewer 94 displays an X-ray image based on this X-ray image data. The file server 95 stores this X-ray image data.

  Even if the console display device 7 is moved from the X-ray control room R2 to the X-ray imaging room R1 after the generation of X-rays is stopped, the same as when the console display device 7 is located in the X-ray control room R2. An operation is performed to display an X-ray image acquired by X-ray imaging. At this time, the console communication unit 15 performs wireless communication with the cassette communication unit 52 to transmit and receive control signals and image data.

  As described above, in the X-ray imaging system 1000, since the console display device 7 is portable, the console display device 7 can be freely installed not only in the X-ray control room R2 but also in the X-ray imaging room R1. Can be moved to. As a result, the operator can move to the X-ray imaging room R1 with the console display device 7 after X-ray imaging, and can process and confirm the image captured in parallel with the next imaging preparation. There is an effect that the shooting efficiency can be improved.

  In the present embodiment, an example in which X-ray imaging is performed when the cassette 4 is in the X-ray imaging room R1 and the console display device 7 is in the X-ray control room R2 has been described. When the cassette and the console display device are in the same room, an image may be acquired by irradiating X-rays. As a result, the photographed image can be confirmed at the photographing location immediately after the X-ray photographing, so that it is possible to reduce the movement time of the operator and improve the photographing efficiency.

  In this embodiment, an example in which the console display device 7 and the operation input unit 5 are separately provided has been described. However, the present invention is not limited to this, and the console display device provided with an operation input unit is integrated. May be.

  In this embodiment, an example in which the console 1 performs wireless communication with the wireless repeater 2 is shown, but the present invention is not limited to this, and the console may be connected to a communication cable. Moreover, although the console 1 showed the example which does not have a display means of a character and an image, it is not limited to this, The display part which displays a character and an image on a console, and the display control part which controls a display part are provided. Also good.

  Furthermore, in the present embodiment, an example in which the irradiation condition is input via the console 1 has been described. However, the present invention is not limited to this. For example, an operation input unit including an irradiation switch and an input unit for inputting the irradiation condition is provided. It may be used.

  In the present embodiment, an example in which the panel 44 is configured by one panel having 4096 × 3072 pixels is shown, but the present invention is not limited to this. For example, the panel 44 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 of reading the electric energy of the X-rays irradiated using the scintillator 441 and the photodetector 442 is shown, but 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 4442 is provided in the signal reading circuit 444 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 447 formed of glass is shown, but the present invention is not limited thereto, and a support body formed of resin, metal, or the like can be applied.

  In the present embodiment, the cassette 4 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 and the console is provided, the correspondence between the cassette and the console is stored in the correspondence information holding unit, the correspondence information holding unit is provided on the network or in the console, and the console controls the cassette. Is preferred.

In this embodiment, both the console 1 and the cassette 4 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 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. .

1 is a diagram showing a schematic configuration 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.

Explanation of symbols

1000 X-ray imaging system 1 Console 11 Input unit 12 Console control unit 13 Console communication unit 14 Image storage unit 15 Image processing unit 16 Console power supply 4 Cassette 41 Cassette power supply 42 Cassette communication unit 43 Cassette control unit 7 Console display device 71 Display unit 72 Control Unit 73 Communication Unit 74 Internal Power Supply 8 Wireless Repeater

Claims (9)

A cassette for communicating the generated image data via a cassette communication unit;
A radiographic imaging system in which a console including a console communication unit that wirelessly communicates the cassette communication unit and the image data and a console control unit that controls driving of the console communication unit can communicate via a communication network. In
A portable console display device provided with a communication unit that communicates the image data with the console communication unit, a display unit that displays the image data, and a control unit that controls driving of the display unit. A radiographic imaging system characterized by that.   The radiographic imaging system according to claim 1, wherein the communication unit wirelessly communicates with the console communication unit.   The radiographic imaging system according to claim 1, wherein the console display device includes an internal power source that is a power supply source to the console display device.   The radiographic imaging system according to any one of claims 1 to 3, wherein the console display device includes an input unit that inputs a driving condition of the console.   5. The cassette according to claim 1, further comprising: a cassette power source that is a power supply source for the cassette; and a cassette control unit that controls driving of the cassette power source. The radiographic imaging system according to one item.   The radiographic imaging system according to claim 1, wherein the cassette communication unit wirelessly communicates with the console.   A communication unit that communicates the generated image data with a console communication unit, a display unit that displays the image data, and a control unit that controls the driving of the display unit are provided, and is portable. Console display device.   The console display device according to claim 7, wherein the communication unit performs wireless communication with the console communication unit.   The console display device according to claim 7, further comprising an input unit for inputting image data generation conditions by the cassette.

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