JP2004180931A - X-ray image pickup device - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To enable an X-ray image pickup device to transfer a picked-up image to an image reading-out device provided at an arbitrary location by eliminating the deviation between the picked-up image and a patient ID at the time of using a cable-less digital X-ray detector. <P>SOLUTION: This X-ray image pickup device is constituted to transmit header information, such as the patient ID, portion information, image processing information, etc., from a radiograph control section to the cable-less digital X-ray detector in the moment radiography is decided (for example, a second switch is pressed down) at the time of performing photographing by using the X-ray detector. The X-ray detector is constituted to collectively manage photographed X-ray images and the header information by storing the images and information in a nonvolatile memory. Consequently, even when the X-ray detector is carried to any location immediately after X-ray exposure is performed or an uncommucable condition occurs due to a worsened radio wave environment, the management of the images is carried out without causing any problem nor confusion even when image information is transferred from the X-ray detector to the image reading-out device with a time lag, because the X-tray images and header information are collectively managed. <P>COPYRIGHT: (C)2004,JPO&NCIPI

Description

[0001]
TECHNICAL FIELD OF THE INVENTION
The present invention relates to an X-ray imaging apparatus using a solid-state imaging device composed of a plurality of pixels for creating an image, and more particularly to an X-ray imaging apparatus using a cableless imaging unit.
[0002]
[Prior art]
In a conventional X-ray imaging apparatus, an X-ray beam is projected from an X-ray source through an object to be analyzed such as a medical patient, and after the X-ray beam passes through a subject, a screen film cassette, a film autochanger, and a CR (Computed radiography) are used. ), FPD (Flat Panel Detector) or the like.
[0003]
In consumer electronics, cameras are in the transition from analog film cameras to digital cameras. In X-ray photography, a high-resolution solid-state X-ray detector using an FPD has been proposed, which is composed of a two-dimensional array using detection elements represented by 2000 to 4000 photodiodes in each dimension. Is done. Each element produces an electrical signal corresponding to the pixel luminance of the X-ray image projected on the detector. The signals from each detection element are read out individually and digitized before being image processed, stored and displayed. X-ray photography is also in the same state as consumer equipment.
[0004]
[Patent Document 1]
JP-A-6-342099
[0005]
[Problems to be solved by the invention]
However, due to its principle, it is difficult to reduce the size of an X-ray digital imaging device using an imaging optical system like a consumer, and it has been proposed in Japanese Patent Application Laid-Open No. 6-342099 such as an X-ray screen film cassette. It was difficult to make it small and thin. However, with the improvement of thinning and high-reliability technology, the realization thereof is becoming possible.
[0006]
In using such a wireless thin X-ray imaging apparatus such as a conventional screen film cassette, a point which was not a problem in the conventional wired X-ray imaging apparatus is newly taken up as a problem.
[0007]
Accordingly, an object of the present invention is to provide an X-ray imaging apparatus that does not cause any trouble in image management even if image information is transferred from the X-ray detector to an image reading apparatus due to time lag. I do.
[0008]
[Means for Solving the Problems]
In order to achieve such an object, an X-ray imaging apparatus of the present invention is an X-ray imaging apparatus including a two-dimensional planar radiation detection unit, and a communication control unit capable of wirelessly communicating with the detection unit, The communication control means transmits image header information to the detection means, and the detection means stores management means for collectively managing the acquired image and the image header information, and stores the acquired image and the image header information. Storage means.
[0009]
BEST MODE FOR CARRYING OUT THE INVENTION
Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings.
FIG. 1 is a configuration block diagram of an X-ray imaging system showing one embodiment of the present invention. Reference numeral 10 denotes an X-ray room, 12 denotes an X-ray control room, and 14 denotes a diagnostic room and other operation rooms.
In the X-ray control room 12, a system controller 20 for controlling the overall operation of the present X-ray imaging system is arranged. An operator interface 22 including an X-ray exposure request SW, a touch panel, a mouse, a keyboard, a joystick, a foot switch, and the like is used by the operator 21 to input various commands to the system controller 20. The instruction content of the operator 21 includes, for example, imaging conditions (still image / moving image, X-ray tube voltage, tube current, X-ray irradiation time, etc.), imaging timing, image processing conditions, subject ID, and a method of processing a captured image. and so on. The imaging controller 24 controls an X-ray imaging system placed in the X-ray room 10, and the image processor 26 processes an image of the X-ray room 10 using the X-ray imaging system. The image processing in the image processor 26 includes, for example, image data correction, spatial filtering, recursive processing, gradation processing, scattered radiation correction, and dynamic range (DR) compression processing.
[0010]
Reference numeral 28 denotes a large-capacity, high-speed storage device that stores basic image data processed by the image processor 26, and is composed of, for example, a hard disk array such as (RAID). Reference numeral 30 denotes a monitor display (hereinafter abbreviated as a monitor) for displaying an image, 32 a display controller for controlling the monitor 30 to display various characters and images, and 34 a large-capacity external storage device (for example, an optical Magnetic disks) and 36 connect the devices in the X-ray control room 12 to the devices in the diagnostic room and other operation rooms 14 and transfer the images captured in the X-ray room 10 to the devices in the diagnostic room and other operation rooms 14. It is a LAN board.
[0011]
An X-ray generator 40 that generates X-rays is placed in the X-ray room 10. The X-ray generator 40 includes an X-ray tube 42 that generates X-rays, a high-pressure source 44 controlled by the imaging controller 24 to drive the X-ray tube 42, and an X-ray generated by the X-ray tube 42. It comprises an X-ray aperture 46 for narrowing the beam to a desired imaging area. A subject 50 as a patient lies on the imaging bed 48. The imaging bed 48 is driven according to a control signal from the imaging controller 24, and can change the direction of the subject with respect to the X-ray beam from the X-ray generator 40. An X-ray detector 52 that detects an X-ray beam transmitted through the subject 50 and the imaging bed 48 is arranged below the imaging bed 48.
[0012]
The X-ray detector 52 includes a laminate of a grid 54, a scintillator 56, a photodetector array 58, and an X-ray exposure monitor 60, and a driver 62 for driving the photodetector array 58. The grid 54 is provided to reduce the influence of X-ray scattering caused by transmitting through the subject 50. The grid 54 includes an X-ray low-absorbing member and a high-absorbing member, and has, for example, a stripe structure of A1 and Pb. At the time of X-ray irradiation, the X-ray detector 52 operates based on the setting from the imaging controller 24 so that moire does not occur due to the relationship between the grid ratio of the photodetector array 58 and the grid 54. The grid 54 is vibrated according to the control signal of 62.
[0013]
In the scintillator 56, the base substance of the phosphor is excited (absorbed) by high-energy X-rays, and the recombination energy generates fluorescence in the visible region. That is, X-rays are converted into visible light. The fluorescence may be due to the host itself such as CaWo4 or CdWo4, or may be due to the emission center substance added to the host such as CsI: Tl or ZnS: Ag. The photodetector array 58 converts the visible light from the scintillator 56 into an electric signal.
[0014]
In the present embodiment, the scintillator 56 and the photodetector array 58 have different structures. However, it is needless to say that the present invention can be applied to a structure in which a detector directly converts X-rays into electrons. For example, a radiation (X-ray) detector including a light receiving unit such as amorphous Se or PbI2 and an amorphous silicon TFT is used.
[0015]
The X-ray exposure monitor 60 is provided for monitoring the amount of X-ray transmission. The X-ray exposure monitor 60 may directly detect X-rays using a light receiving element made of crystalline silicon or the like, or may detect fluorescence from the scintillator 56. In this embodiment, the X-ray exposure monitor 60 is composed of an amorphous silicon light-receiving element formed on the back surface of the substrate of the photodetector array 58, and the oversight light transmitted through the photodetector array 58 (in proportion to the X-ray dose). ) Is detected, and the light amount information is transmitted to the imaging controller 24. The imaging controller 24 controls the high-voltage generation power supply 40 based on the information from the X-ray exposure monitor 60 to adjust the X-ray dose.
[0016]
The driver 62 drives the photodetector array 58 under the control of the imaging controller 24, and reads a signal from each pixel. The operation of the photodetector array 58 and the driver 62 will be described later in detail.
[0017]
Further, another thin X-ray detector 152 is connected to the system controller 20 via the repeater 153 for imaging of limbs and the like. Although one thin X-ray detector 152 is shown in FIG. 1 as a representative of a plurality of types of sensors, the thin X-ray detector 152 differs in spatial resolution or the size of the thin X-ray detector 152, that is, the size of the imaging region. The different ones can be used interchangeably. The most significant difference between the X-ray detector 52 and the thin X-ray detector 152 is that the thin X-ray detector 152 has a thickness comparable to that of a film screen cassette. ing.
[0018]
Furthermore, the thin X-ray detector 152 has no built-in grid 54, a simple power supply, a large capacity (10 to 20 images) non-volatile memory, and a cable-less image with the repeater 153. Signals and control can be exchanged. A stacked body of the scintillator 56, the photodetector array 58, and the X-ray exposure monitor 60, a driver 62 for driving the photodetector array 58, and the like are similarly incorporated. The cable 154 can be operated with or without the cable 154. When the cable 154 is used, the image transfer can be performed at a high speed, so that the operations of image acquisition, processing, and confirmation after X-ray imaging are achieved in a shorter time. Further, since there is no need for charging, photographing can be continued for a long time. In addition to relaying communication with the thin X-ray detector 152, the repeater 153 has a function as an automatic ID assignment, a charger, and a holder when not in use. A normal connection point between the repeater 153 and the thin X-ray detector 152 must use a connector that is easily detachable and has high reliability.
[0019]
Further, there may be a case where an image data reading terminal 160 from the thin X-ray detector 152 is installed in another operation room 14 or the like. An X-ray image can be read from the X-ray detector 152. The image data reading terminal 160 has an X-ray image reading function of the repeater 153 and an image processing and management function of the system controller 20, and transfers the X-ray image to an image server or the like.
[0020]
The diagnostic room and other operation rooms 14 are connected to a HIS / LIS or the like for instructing information on an imaging subject and an imaging method via a LAN board, or perform image processing on an image from the LAN board 36. An image processing terminal 70 for assisting diagnosis, a video display monitor 72 for displaying images (moving images / still images) from the LAN board 36, an image printer 74, and a file server 76 for storing image data are provided.
[0021]
A control signal from the system controller 20 for each device can be generated by an instruction from the operator interface 22 in the X-ray control room 12, or from the image processing terminal 70 in the diagnostic room or other operation room 14. is there.
[0022]
Next, a basic operation of the system controller 20 will be described. The system controller 20 instructs an imaging controller 24 that controls a sequence of the X-ray imaging system to perform imaging conditions based on an instruction from the operator 21. The imaging controller 24 generates an X-ray generator based on the instruction. By driving the imaging bed 40 and the X-ray detector 52, an X-ray image is captured. The X-ray image signal output from the X-ray detector 52 is supplied to the image processor 26, subjected to image processing designated by the operator 21, displayed on the monitor 30, and at the same time, stored in the storage device 28 as basic image data. Is stored in The system controller 20 further performs re-image processing and image display of the result, transfer of image data to a device on a network, storage, video display, film printing, and the like, based on instructions from the operator 21.
[0023]
Next, the basic operation of the system shown in FIG. 1 will be described according to the flow of signals. The high voltage source 44 of the X-ray generator 40 applies a high voltage for X-ray generation to the X-ray tube 42 according to a control signal from the imaging controller 24. As a result, the X-ray tube 42 generates an X-ray beam. The generated X-ray beam is applied to a subject 50 as a patient via an X-ray aperture 46. The X-ray stop 46 is controlled by the imaging controller 24 according to the position to be irradiated with the X-ray beam. That is, the X-ray stop 46 shapes the X-ray beam so as not to perform unnecessary X-ray irradiation in accordance with the change of the imaging region.
[0024]
The X-ray beam output from the X-ray generator 40 passes through the subject 50 lying on the X-ray transparent imaging bed 48 and the imaging bed 48 and enters the X-ray detector 52. Note that the imaging bed 48 is controlled by the imaging controller 24 so that the X-ray beam is transmitted through different parts or directions of the subject 50. When the thin X-ray detector 152 is used, the operator 21 operates the thin X-ray detector so that the X-ray beam output from the X-ray generator 40 passes through the subject 50 and enters the thin X-ray detector. The line detector 152 and the subject 50 are adjusted.
[0025]
The grid 54 of the X-ray detector 52 reduces the influence of X-ray scattering caused by transmission through the subject 50. The imaging controller 24 vibrates the grid 54 during X-ray irradiation so that moire does not occur due to the relationship between the grid ratio of the photodetector array 58 and the grid 54. In the scintillator 56, the base substance of the phosphor is excited (absorbs X-rays) by high-energy X-rays, and generates fluorescence in a visible region by recombination energy generated at that time.
[0026]
The photodetector array 58 arranged adjacent to the scintillator 56 converts the fluorescence generated by the scintillator 56 into an electric signal. That is, the scintillator 56 converts the X-ray image into a top-view light image, and the photodetector array 58 converts the top-view light image into an electric signal. The X-ray exposure monitor 60 detects the oversight light (proportional to the X-ray dose) transmitted through the photodetector array 58 and supplies the detected amount information to the imaging controller 24. The imaging controller 24 controls the high-voltage generating power supply 44 based on the X-ray exposure information to block or adjust the X-rays. The driver 62 drives the photodetector array 58 under the control of the imaging controller 24, and reads a pixel signal from each photodetector.
[0027]
Pixel signals output from the X-ray detector 52 and the thin X-ray detector 152 are output to the image processor 26 in the X-ray control room 12. Since the X-ray room 10 contains a large amount of noise due to the generation of X-rays, the signal transmission path from the X-ray detector 52 to the image processor 26 needs to have high noise resistance. It is needless to say that it is desirable to use a digital transmission system having the error correction function described above, or to use a twisted pair cable or an optical fiber with a shield using a differential driver.
[0028]
The image processor 26 switches the display format of the image signal based on a command from the system controller 20, which will be described in detail later. In addition, the image processor 26 performs correction, spatial filtering, and recursive processing of the image signal in real time. Gradation processing, scattered radiation correction, DR compression processing, and the like can be performed. The image processed by the image processor 26 is displayed on the screen of the monitor 30. Image information (basic image) on which only image correction has been performed simultaneously with the real-time image processing is stored in the storage device 28. Further, based on the instruction of the operator 21, the image information stored in the storage device 28 is reconfigured to satisfy a predetermined standard (for example, Image Save & Carry (IS & C)), and then the external storage device 34 and the file -Stored on a hard disk or the like in the server 76.
[0029]
The devices in the X-ray control room 12 are connected to a LAN (or WAN) via a LAN board 36. Of course, a plurality of X-ray imaging systems can be connected to the LAN. The LAN board 36 outputs image data according to a predetermined protocol (for example, Digital Imaging and Communications in Medicine (DICOM)). By displaying a high-resolution still image and a moving image of the X-ray image on the screen of the monitor 72 connected to the LAN (or WAN), real-time remote diagnosis by a doctor can be performed almost simultaneously with X-ray imaging.
[0030]
FIG. 2 shows an example of an equivalent circuit of a constituent unit of the photodetector array 58. One element is composed of a photodetector 80 and a switching thin film transistor (TFT) 82 for controlling accumulation and reading of electric charges, and is generally formed of amorphous silicon (a-Si) on a glass substrate. The light detection unit 80 further includes a parallel circuit of a photodiode 80a and a capacitor 80b, and describes a charge due to the photoelectric effect as a constant current source 81. The capacitor 80b may be a parasitic capacitance of the photodiode 80a or an additional capacitor for improving a dynamic range of the photodiode 80a. The cathode of the photodetector 80 (photodiode 80a) is connected to a bias power supply 85 via a bias wiring Lb that is a common electrode (D electrode). The anode of the photodetector 80 (photodiode 80a) is connected from a gate electrode (G electrode) to a capacitor 86 and a charge readout preamplifier 88 via a switching TFT. The input of the preamplifier 88 is also connected to the ground via a reset switch 90 and a signal line bias power supply 91.
[0031]
First, the switching TFT 82 and the reset switch 90 are temporarily turned on, the capacitor 80b is reset, and the switching TFT 82 and the reset switch 90 are turned off. Thereafter, X-rays are generated and the X-rays are emitted to the subject 50. The scintillator 54 transmits the subject 50, converts the X-ray image into a visible light image, and the photodiode 80a becomes conductive by the visible light image, and discharges the charge of the capacitor 80b. The switching TFT 82 is turned on to connect the capacitor 80b and the capacitor 86. As a result, the information on the discharge amount of the capacitor 80b is also transmitted to the capacitor 86. The voltage is amplified by the preamplifier 88 by the charge stored in the capacitor 86, or the charge-voltage conversion is performed by the capacitor 89 shown by a dotted line, and is output to the outside.
[0032]
Next, a photoelectric conversion operation in the case where the photoelectric conversion element shown in FIG. 2 is extended two-dimensionally will be described. FIG. 3 is an equivalent circuit of a photodetector array 58 having a two-dimensional array of photoelectric conversion elements. Since the two-dimensional read operation is the same for the two types of equivalent circuits, FIG. 3 shows the two-dimensional read operation using the equivalent circuit shown in FIG.
[0033]
The photodetector array 58 is composed of about 2000 × 2000 to 4000 × 4000 pixels, and the array area is about 200 mm × 200 mm to 500 mm × 500 mm. In FIG. 3, the photodetector array 58 is composed of 4096 × 4096 pixels, and the array area is 430 mm × 430 mm. Therefore, the size of one pixel is about 105 × 105 μm. 4096 pixels arranged in the horizontal direction are defined as one block, and 4096 blocks are arranged in the vertical direction to form a two-dimensional configuration.
[0034]
In FIG. 3, the photodetector array composed of 4096 × 4096 pixels is constituted by one substrate, but it is needless to say that four photodetector arrays having 2048 × 2048 pixels may be combined. In this case, although the trouble of assembling the four photodetector arrays is required, the yield of each photodetector array is improved, so that there is an advantage that the yield is improved as a whole.
[0035]
As described with reference to FIG. 2, one pixel includes one photodetector 80 and one switching TFT 82. The photoelectric conversion elements PD (1, 1) to (4096, 4096) correspond to the light detection unit 80, and the transfer switches SW (1, 1) to (4096, 4096) correspond to the switching TFT 82. The gate electrode (G electrode) of the photoelectric conversion element PD (m, n) is connected to a common column signal line Lcm for that column via a corresponding switch SW (m, n). For example, the photoelectric conversion elements PD (1, 1) to (4096, 1) in the first column are connected to the first column signal line Lc1. All the common electrodes (D electrodes) of the photoelectric conversion elements PD (m, n) are connected to a bias power supply 85 via a bias wiring Lb.
[0036]
The control terminals of the switches SW (m, n) in the same row are connected to a common row selection line Lrn. For example, the switches SW (1,1) to (1,4096) in the first row are connected to the row selection line Lr1. The row selection lines Lr1 to 4096 are connected to the imaging controller 24 via the line selector 92. The line selector 92 decodes a control signal from the imaging controller 24 and determines which line of the signal charge of the photoelectric conversion element should be read out. It comprises a switch element 96. With this configuration, the signal charge of the photoelectric conversion element PD (m, n) connected to the switch SW (m, n) connected to an arbitrary line Lrn can be read. As the simplest configuration, the line selector 92 may be configured simply by a shift register used for a liquid crystal display or the like.
[0037]
The column signal lines Lc1 to 4096 are connected to the signal readout circuit 100 controlled by the imaging controller 24. In the signal read circuit 100, reset switches 102-1 to 4096 reset the column signal lines Lc1 to 4096 to the reset reference potential 101, respectively. Reference numerals 106-1 to 4096 denote preamplifiers for amplifying signal potentials from the column signal lines Lc1 to 4096, respectively, and reference numerals 108-1 to 4096 denote sample / hold (S / H) circuits for sampling and holding outputs of the preamplifiers 106-1 to 4096, respectively. An analog multiplexer 112 multiplexes the outputs of 108-1 to 4096 on the time axis. Reference numeral 112 denotes an A / D converter for digitizing the analog output of the multiplexer 110. The output of the A / D converter 112 is supplied to the image processor 26.
[0038]
In the photodetector array shown in FIG. 3, 4096 × 4096 pixels are divided into 4096 columns by column signal lines Lc1 to 4096, and signal charges of 4096 pixels per row are simultaneously read out, and each column signal line Lc1 4096, pre-amplifiers 106-1 to 4096 and S / H circuits 108-1 to 4096 are transferred to analog multiplexer 110, where they are time-division multiplexed and sequentially converted to digital signals by A / D converter 112. I do.
[0039]
Although FIG. 3 shows that the signal readout circuit 100 includes only one A / D converter 112, the A / D conversion is actually performed simultaneously by 4 to 32 systems. This is because it is necessary to shorten the image signal reading time without unnecessarily increasing the analog signal band and the A / D conversion rate. The accumulation time of the signal charge and the A / D conversion time are closely related. If the A / D conversion is performed at a high speed, the bandwidth of the analog circuit is widened and it is difficult to achieve a desired S / N. Short reading times are required. Although the output of the multiplexer 110 may be A / D converted by many A / D converters, the cost increases as the number of A / D converters increases. Therefore, an appropriate number of A / D converters are used in consideration of the above points.
[0040]
Since the X-ray irradiation time is approximately 10 to 500 msec, it is appropriate to set the capture time or charge accumulation time of the entire screen to the order of 100 msec or slightly shorter. For example, in order to sequentially drive all the pixels and capture an image in 100 msec, the analog signal band is set to about 50 MHz, and A / D conversion is performed at a sampling rate of, for example, 10 MHz. Vessel is required. In this embodiment, A / D conversion is performed simultaneously in 16 systems. The outputs of the 16 A / D converters are input to corresponding 16 memories (not shown) such as FIFOs. By selecting and switching the memory, image data corresponding to one continuous scanning line is transferred to the image processor 26.
[0041]
FIG. 4 is a schematic timing chart of sensor reading. Two-dimensional driving in a case where a still image is captured by one X-ray irradiation will be described together with FIG.
601 is an X-ray irradiation request control signal, 602 is an X-ray irradiation state, 603 is a current of the current source 81 in the sensor, 604 is a control state of the row selection line Lrn, and 605 is a signal to the AD converter 112. Each of the analog inputs is schematically shown.
[0042]
All the column signal lines Lc are connected to the reset reference potential 101 while the bias lines are kept at the bias value Vs at the time of photoelectric conversion, and the column signal lines are reset. Thereafter, a positive voltage Vgh is applied to the row selection wiring Lr1, SW (1,1) to (1,4096) are turned on, and the G electrode of the photoelectric conversion element in the first column is reset to Vbt. Next, the row selection wiring Lr1 is set to the positive voltage Vgl, and SW (1,1) to (1,4096) are turned off. The row selection is sequentially repeated to reset all the pixels, and the photographing preparation is completed. The above operation is the same as the operation of reading out the signal charge, and there is no choice as to whether or not to take in the signal charge. Therefore, this reset operation is hereinafter referred to as “idle reading”.
[0043]
During this idle reading operation, it is possible to set all the row selection lines Lr to Vgh at the same time, but in this case, when the read preparation is completed, the signal line potential greatly deviates from the reset voltage Vbt, and the high S / N It is difficult to get a signal. In the above-described example, the row selection wiring Lr is reset from 1 to 4096. However, resetting can be performed in an arbitrary order under the control of the driver 62 based on the setting of the imaging controller 24.
[0044]
The idle reading operation is repeated to wait for an X-ray exposure request. When an irradiation request is issued, a blank reading operation is performed again to prepare for X-ray irradiation in preparation for image acquisition. When preparation for image acquisition is completed, X-rays are emitted in accordance with an instruction from the imaging controller 24.
[0045]
After the X-ray exposure, the signal charges of the photoelectric conversion element 80 are read. First, Vgh is applied to the row selection wiring Lr for a row (for example, Lr1) in which the photoelectric conversion element array is provided, and the accumulated charge signal is output to the signal wirings Lc1 to Lc4096. Signals for 4096 pixels are read out simultaneously from the column signal lines Lc1 to 4096 one by one.
[0046]
Next, Vgh is applied to a different row selection line Lr (for example, Lr2), and a stored charge signal is output to the signal lines Lc1 to 4096. Signals for 4096 pixels are read out simultaneously from the column signal lines Lc1 to 4096 one by one. This operation is sequentially repeated for 4096 column signal lines to read out all image information.
[0047]
During the above operation, the charge accumulation time of each sensor is from the time when the reset operation is completed, that is, the time when the TFT 82 in the idle reading is turned off to the time when the TFT 82 is turned on for the next charge reading. Therefore, the accumulation time / time differs for each line selection line.
[0048]
After reading out the X-ray image, an image for correction is obtained. This is used for correcting an X-ray image, and is correction data necessary for acquiring a high-quality image. The basic image acquisition method is the same except that X-rays are not exposed. The charge accumulation time is the same when reading an X-ray image and when reading a corrected image.
[0049]
Further, when high-resolution image information is not required or when it is desired to increase the image data capturing speed, it is not necessary to always capture all image information. , Thinning, pixel averaging, and region extraction are set in the driver 62.
[0050]
In order to perform the thinning, first, when the row selection wiring Lr1 is selected and a signal is output from the column signal wiring Lc, for example, n of Lc2n-1 (n: natural number) is increased by one from 0 so as to increase by one. When a column is read and then a row is selected, the value of m of the row selection wiring Lr2m-1 (m: natural number) is incremented by one from 1 to read a signal of one row. In this example, the number of pixels is reduced to 1/4, but the driver 62 reduces the number of pixels to 1/9, 1/16, etc. according to the setting instruction of the imaging controller 24.
[0051]
In addition, regarding the pixel average, by applying Vgh to the row selection wirings Lr2m and Lr2m + 1 at the same time during the above operation, the TFTs 2m and 2n and the TFTs 2m + 1 and 2n are simultaneously turned on, and analog addition of two pixels in the column direction is performed. Things are possible. This is not limited to the addition of two pixels, but indicates that analog addition of a plurality of pixels in the column signal wiring direction can be easily performed. Further, for the addition in the row direction, adjacent pixels (Lc2n and Lc2n + 1) are digitally added after the A / D conversion output to obtain an added value of 2 × 2 square pixels together with the above-described analog addition. Can be. This makes it possible to read data at high speed without wasting the irradiated X-rays. In addition, as a method of reducing the total number of pixels and aiming at high speed, there is a method of limiting an image capturing area. That is, the operator 21 inputs a necessary area from the operator interface 22, and based on the input, the imaging controller 24 issues an instruction to the driver 62, and the driver 62 changes the data capture range to perform two-dimensional detection. Drives the vessel array.
[0052]
In this embodiment, 1024 × 1024 pixels are captured at 30 F / S in the high-speed capture mode. That is, in the entire area of the two-dimensional detector array, addition processing of 4 × 4 pixels is performed and thinned out to 1/16, and in the smallest area, an image is taken without thinning out in a 1024 × 1024 area. By taking an image in this way, a digital zoom image can be obtained.
[0053]
FIG. 5 is a timing chart including the imaging operation of the X-ray detector 52. The operation of the X-ray detector 52 will be described mainly with reference to FIG.
701 is an imaging request signal to the operator interface 22, 702 is an actual X-ray exposure state, 703 is an imaging request signal from the imaging controller 24 to the driver 62 based on an instruction of the operator 21, 704 is an X-ray detector 52, an imaging ready signal 52, a driving signal 705 for the grid 54, a power control signal 706 in the X-ray detector 52, and a driving state 707 for the X-ray detector (particularly, a charge reading operation from the photodetector array 58). Each is manifested. Reference numeral 708 conceptually represents a transfer state of image data and a state of image processing and display.
[0054]
The driver 62 waits with the power control turned off as indicated by 706 until there is a detector preparation request or an imaging request from the operator 21. Specifically, in FIG. 3, the potentials of the row selection line Lr, the column signal line Lc, and the bias wiring Lb are maintained at the same potential (particularly the signal GND level) by a switch (not shown), and no bias is applied to the photodetector array 58. Further, the power supply including the signal readout circuit 100, the line selector 92, and the bias power supply 84 or 85 may be cut off to keep the potentials of the row selection line Lr, column signal line Lc, and bias wiring Lb at the GND potential. .
[0055]
The imaging controller 24 causes the X-ray generator 40 to transition to the imaging ready state and the X-ray detector 52 to enter the imaging preparation state according to the instruction (7011stSW) of the imaging preparation request from the operator 21 to the operator interface 22. Give instructions to move to. Upon receiving the instruction, the driver 62 applies a bias to the photodetector array 58 and repeats the blank reading Fi. The request instruction may be, for example, a first switch of an exposure request SW to the X-ray generator (usually, a rotor up of a tube is started), or a predetermined time period for the X-ray detector 52 to prepare for imaging ( For example, when it takes several seconds or more), it is an instruction to start preparation of the X-ray detector 52. In this case, the operator 21 does not need to consciously issue an instruction to request preparation for imaging to the X-ray detector 52. That is, when the subject information, the imaging information, and the like are input to the operator interface 22, the imaging controller 24 interprets the instruction as a detector preparation request instruction and sets the X-ray detector 52 in the detector preparation state. You may move to.
[0056]
In the detector preparation state, in the photoelectric conversion mode, after the idle reading, to prevent the dark current from gradually accumulating in the photodetector 80 and keep the capacitor 80b (c) in a saturated state, the idle reading Fi is set to a predetermined value. Repeat at intervals. The drive performed during a period in which an actual X-ray emission request is not issued while the imaging preparation request from the operator 21 is present, that is, the drive in which the idle reading Fi performed in the detector preparation state is repeated at a predetermined time interval T1 is performed thereafter. The period during which the idling drive is being performed and the detector is ready is called “idling drive period”. Since the duration of the idling drive period is undefined in practical use, T1 is set to be shorter than that in the normal photographing operation in order to minimize the read operation in which the photodetector array 58 (particularly, the TFT 82) is loaded. The idling idle reading drive Fi which is set to be longer and has a shorter ON time of the TFT 82 than the normal reading driving Fr is performed.
[0057]
Next, acquisition of an X-ray image centered on the X-ray detector 52 will be described. The driving of the X-ray detector 52 at the time of acquiring an X-ray image mainly includes acquisition of two images. As indicated by reference numeral 707, one is an X-ray image acquisition drive, and the other is a correction dark image acquisition drive. Each drive is almost the same, and the main difference is whether or not there is an operation for performing X-ray irradiation. Further, each drive is composed of three parts: an imaging preparation sequence, charge accumulation (exposure window), and image reading.
[0058]
Hereinafter, the X-ray image acquisition will be described sequentially. In response to an imaging request instruction (701: 2nd SW) from the operator 21 to the operator interface 22, the imaging controller 24 controls the imaging operation while synchronizing the X-ray generator 40 and the X-ray detector 52. The imaging request signal is asserted to the X-ray detector at the timing indicated by the X-ray exposure request signal 703 in accordance with the imaging request instruction (701: 2nd SW). The driver performs a predetermined imaging preparation sequence drive in response to the imaging request signal as shown in an imaging driving state 707.
[0059]
Specifically, when refresh is necessary, the refresh is performed, and the dedicated blank reading Fp for the imaging sequence is performed a predetermined number of times and the dedicated blank reading Fpf for the charge storage state is performed to be in the charge accumulation state (imaging window: T4). Transition. At that time, the number of times of the idle reading Fp and the time interval T2 for the imaging sequence are performed based on values set in advance prior to the imaging request from the imaging controller 24. In this case, the optimum drive is automatically selected and switched depending on whether the operability or the image quality is important according to the request of the operator 21 or the imaging part. In the period (T3) from the request for exposure to the completion of the preparation for imaging, it is actually required that the required time is short. Therefore, the blank reading Fp dedicated to the imaging preparation sequence is performed. Further, when an exposure request is issued from any state of the idling drive, the operability is improved by shortening the period (T3) from the exposure request to the completion of shooting preparation by immediately starting the imaging preparation sequence drive. Plan.
[0060]
Now, the driver 62 starts to move the grid 54 in synchronization with the preparation of the detector array 58 for imaging. This is because the grid is imaged in an optimal moving state in synchronization with the actual X-ray irradiation 702. Also in this case, the driver 62 operates at the optimum grid movement start timing and the optimum grid movement speed set by the imaging controller.
[0061]
When the X-ray detector 52 is ready for imaging, the driver 62 returns an X-ray detector ready signal 704 to the imaging controller 24, and the imaging controller 24 performs X-ray detection based on the transition of this signal. Assert to the X-ray generator 40 as a line generation request signal 702. The X-ray generator 40 generates X-rays while the X-ray generation request signal 702 is being given. When a predetermined X-ray dose is generated, the imaging controller 24 negates the X-ray generation request signal 702 and negates the X-ray imaging request signal 703 to notify the X-ray detector 52 of the image acquisition timing. Based on this timing, the driver 62 immediately stops the grid 54 and starts the operation of the signal readout circuit 100 which has been in the standby state until then.
[0062]
After the grid 54 stationary time and a predetermined wait time for stabilizing the signal readout circuit 100, the image data is read from the X-ray detector array 58 based on the driver 62, and the raw image is acquired by the image processor 26. When the transfer is completed, the driver 62 changes the read circuit 100 to the standby state again.
[0063]
Subsequently, the X-ray detector 52 acquires a corrected image. That is, the imaging sequence for the previous imaging is repeated, a dark image without X-ray irradiation is obtained, and the correction dark image is transferred to the image processor 26. At this time, the imaging sequence may be slightly different, such as the X-ray exposure time, for each imaging. However, by reproducing the same imaging sequence including that and acquiring a dark image, a higher quality image can be obtained. can get. However, the operation of the grid 54 is not limited to this, and the grid 54 is kept stationary at the time of acquiring a dark image to suppress the influence of vibration. After the dark image is obtained, the grid 54 is initialized at a predetermined timing that does not affect the image quality.
[0064]
FIG. 6 shows the image processor 26, which shows the flow of image data. 801 is a multiplexer for selecting a data path, 802 and 803 are X-ray image and dark image frame memories, 804 is an offset correction circuit, 805 is a gain correction data frame memory, 806 is a gain correction circuit, and 807 is a defect. A correction circuit 808 represents each of the other image processing circuits.
[0065]
In FIG. 7, the X-ray image acquired by the X-ray image acquisition frame Frxo frame is stored in the X-ray image frame memory 802 via the multiplexer 801, and subsequently, the corrected image acquired by the corrected image acquisition frame Frno frame Are similarly stored in the dark image frame memory 803 via the multiplexer 801. After the storage of the dark image is completed, offset correction (for example, Frxo-Frno) is performed by the offset correction circuit 804. Subsequently, the gain correction circuit Fg is obtained using the gain correction data Fg obtained in advance and stored in the gain correction frame memory. 806 performs gain correction (for example, (Frxo-Frno) / Fg).
[0066]
The data successively transferred to the defect correction circuit 807 interpolates the image continuously so as not to cause a sense of incongruity at a dead pixel or at a joint portion of the X-ray detector 52 composed of a plurality of panels. The sensor-dependent correction processing derived from 52 is completed. In the present embodiment, the image processor 26 is configured in the system controller 20. However, the image processing function that largely depends on the photodetector array 58 described above is built in the X-ray detector 52 and the thin X-ray detector 152. May be configured.
[0067]
Then, the other image processing circuit 808 performs general image processing, for example, processing such as gradation processing, frequency processing, and emphasis processing, and then transfers the processed data to the display controller 32 to monitor it. The photographed image is displayed at 30.
[0068]
The configuration of the thin X-ray detector 152 and the repeater 153 will be described with reference to FIG. In the thin X-ray detector 152, 1001 is an MPU, 1002 is a data and drive control unit, 1003 is an image memory, 1004 is a wireless communication module, 1005 is an external connector, and 1008 is a power supply.
[0069]
The MPU 1001 controls various operations and states in the thin X-ray detector 152. Inside the MPU 1001, an individual communication key register 1006 for storing only one individual communication key 1000 described later and an effective period counter 1007 for monitoring the effective period of the individual ID key are formed by software.
[0070]
The function of the data & drive control unit 1002 performs logic level control such as communication control at the physical layer level, and also drives the photodetector array 58 based on an instruction from the MPU 1001, and performs analog output from the photodetector array 58 based on the drive. An image whose output is digitally converted by an AD converter (not shown) is captured, and the captured digital image is written to the image memory 1003. Further, it outputs the reduced image data to the repeater 153 via the wireless communication module 1004, and outputs all the image data to the repeater 153 via the connector 1005 when mechanically connected. If there is enough time in the shooting interval, all image data may be transferred using wireless communication.However, image transfer is often performed because communication for shooting operation has priority over image transfer operation. Interrupted. For this reason, it is necessary to have an image division transmission function, an image retransmission function, and the like.
[0071]
The image memory 1003 includes a volatile memory of about 2 to 3 images, for example, an SRAM, a DRAM (especially an SDRAM) and a nonvolatile memory of about 20 images, for example, a FlashROM, a battery-backed RAM, a small hard disk, and the like. ing. The nonvolatile memory may be constituted by a removable medium in some cases. In this case, the nonvolatile memory has a detachable mechanical structure.
[0072]
The power supply 1008 supplies power to all parts in the thin X-ray detector 152 by wiring (not shown). The power supply 1008 is a chargeable capacity power supply, and is formed of a large-capacity capacitor (such as an electric double-layer capacitor) that has a short charging time and can cope with large power consumption for a short time during photographing. The capacity is set so that continuous shooting of about 20 or less images can be performed. At this time, the capacity is set to, for example, about 400F. The power supply 1008 may be composed of a secondary battery or the like in some cases. However, there are more restrictions on use such as the necessity of battery replacement and a long charging time as compared with the electric double layer capacitor.
[0073]
In the repeater 153, 1011 is an MPU, 1012 is a layer data flow controller, 1015 is an image memory, and 1014 is a charger.
The MPU 1011 controls the inside of the repeater 153 and controls the plurality of thin X-ray detectors 152. Inside the MPU 1011, an individual communication key register 1006 for storing the number of the thin X-ray detectors 152 to which the individual communication keys 1000 described later can be connected, an effective period counter 1007 for monitoring the effective period of the individual ID key, and a unique communication A communication key counter 1015 for assigning a key 1000 is configured by software.
[0074]
The image data flow controller 1012 controls transfer of an X-ray image sent from the thin X-ray detector 152 based on an instruction from the MPU 1011. The image memory 1015 is a volatile memory for use as a frame buffer configured by a DRAM. In particular, during wireless communication, there is a possibility that error correction or image retransmission may be required. If data starts to flow to the system controller 20 before image transfer is completed, control in the system controller 20 is stopped. For the sake of complexity, the image is transferred to the system controller 20 after the image transfer between the thin cassette 152 and the repeater 153 is completed. Therefore, an image memory 1015 is required.
[0075]
The charger 1014 must secure sufficient capacity to rapidly charge the power supply 1008 of the thin X-ray detector 152, for example, a capacity of about 500 mWh in about 30 seconds.
[0076]
In FIG. 8, a wavy arrow between the thin X-ray detector 152 and the repeater 153 indicates wireless communication, and a dotted line indicates a wired connection or a direct connection by a connector. If a wired connection or a connector connection is made, the wireless module stops. As for the connector 1005, an ordinary connection point must be a connector that is easily detachable and has high reliability. Furthermore, data exchange including the charging operation by the charger 1014 is performed by electromagnetic coupling using a transformer or the like, and it is not always necessary to provide a clear connector 1005. However, in this case, the charging time and the transfer time are extended, and a mechanism for detecting that the thin X-ray detector 152 and the repeater 153 have come close to each other is required.
[0077]
FIG. 9 shows an example of a display screen of the operator interface 22. 1101 is an example of a display screen. Reference numeral 1102 denotes a reduced simplified image display area of the acquired image. When the thin X-ray detector 152 is used, reprocessing is performed based on the image transferred by the wireless communication, and an image is displayed in this display area. Numeral 1103 denotes an imaging target site corresponding to each X-ray detector 52 or thin X-ray detector 152, and 1104 denotes an effective X-ray detector display area. In the effective X-ray detector display area 1104, an icon representing the X-ray detector 52 or the thin X-ray detector 152 that is in a controllable state by the system controller 20 is displayed.
[0078]
A method of exchanging data and control between the thin X-ray detector 152 and the repeater 153 will be described with reference to FIG.
When there are a plurality of thin X-ray detectors 152-A (cassette / large four / □ 100 μm), 152-B (cassette / half-cut / □ 160 μm), etc. Whether or not to perform X-ray imaging using the thin X-ray detector 152 cannot be determined on the thin X-ray detector 152 side. The ID of the thin X-ray detector 152 is stored in advance in the system controller 20 including the repeater 153 with the unique X-ray detector information, and the thin X-ray that is used unilaterally by the system control 20 using the ID is used. The ID of the detector 152 may be output. In this case, for example, when many thin cassettes are commonly used in a hospital having a plurality of X-ray rooms 10, the thin X-rays used by the operator 21 are used. It is necessary to check and input the number of the detector 152 and the like.
[0079]
In this embodiment, the thin X-ray detector 152-A to be used is set in the repeater 153 as shown in Procedure 1 of FIG. 7 before imaging. At the time of step 2 in FIG. 7, first, the repeater 153 acquires the unique information of the thin X-ray detector 152 -A, transmits the acquired information to the system controller 20, and displays the presence on the operator interface 22.
[0080]
Next, the MPU 1011 in the repeater 153 allocates each other's communication keys 1000 to the thin X-ray detector 152-A based on a predetermined rule, and performs imaging control based on that.
[0081]
In the procedure 2, charging of the thin X-ray detector 152 is performed in addition to ID assignment. As described above, when a plurality of thin X-ray detectors 152 are used, the thin X-ray detectors 152 are not always connected to the repeater 153 except during imaging, and thus are likely to be left in a discharged state. Therefore, it is sufficiently considered that rapid charging is required, and a power supply capable of quick charging such as an electric double layer capacitor is more preferable than a secondary battery.
[0082]
When actually performing X-ray imaging, the operator 21 removes the thin X-ray detector 152 from the repeater 153 as shown in step 3 in FIG. The position of each of the X-ray generators 152 is adjusted. The operator 21 selects the thin X-ray detector 152-A displayed on the operator interface 22, and the relay 153 wirelessly transmits the information to the thin X-ray detector 152-A. At this time, by using the communication key 1000 previously assigned, only the thin X-ray detector 152-A is activated without activating the thin X-ray detector 152-B or the thin X-ray detector in the adjacent room. Can be active. The communication technology itself using an ID such as the communication key 1000 is very common. For example, after simply designating a communication partner using the communication key 1000, packet communication up to a predetermined bit length or a predetermined delimiter is performed.
[0083]
By the way, when activated, the thin detector 152 emits a buzzer sound at the same time as the selection display LED is turned on. Further, when the operator selects the icon 1201 at a desired timing, the thin X-ray detector 152 emits a buzzer sound or the like, and it is confirmed that the thin X-ray detector 152 used by the operator 21 is correct. You can also check. Further, a selection switch (not shown) is provided for the thin X-ray detector 152. By pressing the selection SW, the thin X-ray detector 152 whose SW is pressed is forcibly activated. Is also possible. At this time, since the selected state of the thin X-ray detector 152 is displayed on the operator interface 22, which button on the operator interface corresponds to the thin X-ray detector held by the operator 21 is described. Or you can check if it is not listed there. Alternatively, it may be configured to check whether or not the target thin X-ray detector 152 exists in front of the X-ray generator 40 using radio waves or the like.
[0084]
Thereafter, similarly, X-ray imaging can be performed using the communication key 1000 while synchronizing X-rays as shown in FIG. Here, the X-ray imaging request signal 703, the X-ray detector ready signal 704, and the X-ray exposure signal 702 are not communicated only at their transition timings but are asserted in order to minimize imaging errors. During the period, it is desirable to keep transmitting. Depending on the case, a modulated sound wave or the like may be used as the signal.
[0085]
In the present invention, at the time of X-ray irradiation, the thin X-ray detector 152 receives information on the irradiation itself (for example, the total number of times of irradiation), imaging information (for example, an imaging target portion, image processing information) from the system controller 20. Acquires image header information such as subject information (for example, subject ID) at the time of X-ray irradiation.
[0086]
The acquisition timing is preferably immediately before X-ray irradiation. This is because, when image header information is transmitted after X-ray exposure, there is a possibility that the wireless transfer will cause the communication environment to deteriorate after X-ray exposure due to the deterioration of the communication environment. This is because, when the image header information is transmitted, even after transmission of the image header information, parameters at the time of photographing may be frequently corrected, which is not efficient.
[0087]
Therefore, in the present embodiment, after the second switch is pressed in FIG. 5, the above-described image header information is transmitted from the system controller 20 to the thin X-ray detector 152. (FIG. 5709) If the image header information is too large to be ready for the X-ray exposure permission timing of the X-ray detector 152 (X-ray detector ready signal assertion in FIG. 5), the image header information is set at the timing of pressing the 1st SW. May be configured to start transmission. In any case, if the acquisition of the image header information is not completed, the X-ray detector ready signal 704 is not asserted, so that the displacement of the captured image with respect to the input of the subject ID does not occur.
[0088]
By the way, when the X-ray imaging is completed, in the cableless state, it is difficult to transfer all the captured images within a short time as in the cable connection state due to transfer speed limitation. For this reason, the reduced image is transferred first, and an image for confirming whether or not there is a clear imaging error is displayed in the reduced simplified image display area 1102 of the previously acquired image. All captured images are stored in a built-in memory in the thin X-ray detector 152. After transferring the reduced image, the entire image may be transferred immediately.However, the transfer is often interrupted due to the overlap with the next shooting, and the possibility of retransmission is high. In continuous shooting, it is more efficient to transfer all images when shooting is completed. It is only necessary that about 20 or less non-volatile image memories and a power supply capable of withstanding the photographing are mounted in the thin cassette.
[0089]
For further imaging, the thin X-ray imaging device 152 is replaced. This is because the number of images to be taken per subject is usually 20 or less, and to collect image data of the taken images quickly. That is, the state of the procedure 3 is not continued for a long time, and the procedure is repeated from the procedure 1 every time the subject 50 changes. In order to advance the work more quickly, there is almost no loss of time by preparing the thin X-ray detectors 152-B having the same specifications as the thin X-ray detectors 152-A and using them alternately. In this state, it is possible to proceed to imaging of the next subject. In FIG. 7, up to two thin X-ray detectors 152 are set in the repeater 153, but it is clear that the number may be increased.
[0090]
As described above, even if uncollected image data remains stored in the non-volatile memory in the thin X-ray detector 152 due to the deterioration of wireless communication conditions or the malfunction of the repeater 153, the image header information is stored as described above. Is stored in the thin X-ray detector 152 so that, for example, data may be read from the repeater 153 after a long time has elapsed since the imaging was performed, or a relay different from the repeater 153 at the time of imaging may be performed. Even if an image is collected from the device 153 ', there is no problem in the consistency between the image and the subject.
[0091]
Further, an object of the present invention is to provide a storage medium storing a program code of software for realizing the functions of the above-described embodiments to a system or an apparatus, and a computer (or CPU or MPU) of the system or the apparatus to store the storage medium. Needless to say, this can also be achieved by reading and executing the program code stored in the program.
[0092]
In this case, the program code itself read from the storage medium realizes the function of the above-described embodiment, and the program code itself and the storage medium storing the program code constitute the present invention.
[0093]
As a storage medium for supplying the program code, for example, a flexible disk, a hard disk, an optical disk, a magneto-optical disk, a CD-ROM, a CD-R, a magnetic tape, a nonvolatile memory card, a ROM, and the like can be used.
[0094]
When the computer executes the readout program code, 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 code. ) Performs part or all of the actual processing, and the processing realizes the functions of the above-described embodiments.
[0095]
Further, after the program code read from the storage medium is written into a memory provided in a function expansion board inserted into the computer or a function expansion unit connected to the computer, the function is executed based on the instruction of the program code. It goes without saying that a CPU or the like provided in the expansion board or the function expansion unit performs part or all of the actual processing, and the processing realizes the functions of the above-described embodiments.
[0096]
【The invention's effect】
As described above, according to the present invention, when radiography is performed with a cableless digital X-ray detector, at the moment when radiography is determined (for example, when the 2nd SW is pressed), the radiography controller controls the patient ID / part information. Transmitting header information such as image processing information to the X-ray detector; The X-ray detector can store the captured X-ray image and the header information in a nonvolatile memory and manage them collectively.
Therefore, according to the present invention, even if the X-ray detector is carried to any place immediately after the end of the X-ray exposure, or even if the radio wave environment is deteriorated and communication becomes impossible, the X-ray image and Since the header information is collectively managed, even if the image information is transferred from the X-ray detector to the image reading device due to a time lag, it is possible to avoid confusion without any problem in the image management.
[Brief description of the drawings]
FIG. 1 is a schematic configuration diagram of an X-ray imaging system according to an embodiment of the present invention.
FIG. 2 is a first photodetector equivalent circuit diagram.
FIG. 3 is a diagram illustrating a configuration example of a photodetector array.
FIG. 4 is a timing chart conceptually showing a photodetector array driving operation.
FIG. 5 is a timing chart of the X-ray imaging system according to the first embodiment.
FIG. 6 is a block diagram showing a processing flow of an acquired image.
FIG. 7 is a diagram conceptually showing a communication key assignment procedure.
FIG. 8 is a block diagram of a thin X-ray detector 152 and a repeater 153.
FIG. 9 is a diagram showing a display screen example of the operator interface 22.
[Explanation of symbols]
10 X-ray room
12 X-ray control room
14 Diagnostic room and other operation rooms
20 System controller
21 Operator
24 Imaging controller
26 Image processor
30 monitors
40 X-ray generator
48 Bed for shooting
50 subjects
52 X-ray detector
54 grid
58 Photodetector Array
62 Driver
80 Light detector
82 Switching Thin Film Transistor (TFT)
84 bias power supply
85 bias power supply
92 line selector
100 signal readout circuit
152 Thin X-ray detector
153 repeater
1000 Communication key
1003 memory
1004 Wireless communication module
1008 power supply
1014 Charger

Claims (2)

An X-ray imaging apparatus comprising two-dimensional planar radiation detection means and communication control means capable of wireless communication with the detection means,
The communication control unit transmits image header information to the detection unit, the detection unit collectively manages the acquired image and the image header information,
An X-ray imaging apparatus, comprising: storage means for storing the acquired image and the image header information. 2. The X-ray apparatus according to claim 1, wherein a timing at which the communication control unit transmits the image header is substantially the same as a timing at which the control unit and the detection unit synchronize for X-ray imaging. Imaging device.

Images