KR20070007512A - A digital radiography system using a flat-panel type x-ray source and the method of using the same - Google Patents

Abstract

A digital radiography system using a flat-panel type X-rays source and a method for detecting radiography using the same are provided to reduce a photographing space and to prevent overheat of the X-rays source by generating X-rays over a large area. An X-rays source(200) has a cathode(210) and a flat-panel type anode(222) opposite to the cathode. A first grid(250) contacts with a surface of the X-rays source emitting X-rays to determine a traveling direction of the X-rays. A second grid(510) selectively enters the X-rays passing through an object(300). A digital X-rays detection unit(500) has a phosphor screen(520) generating visible rays in response to the X-rays irradiated through the second grid, and an optical guide(530) guiding the visible rays towards an optical detector(540). A microprocessor(600) is connected to the X-rays source and the digital X-rays detector.

Description

A digital radiography system using a flat x-ray source and an x-ray image detection method using the same {a digital radiography system using a flat-panel type X-ray source and the method of using the same}

1 is a cross-sectional view schematically showing an X-ray generator according to the prior art.

Figure 2 is a schematic diagram showing a digital X-ray imaging system according to the prior art.

3 is a perspective view showing the configuration of a light detector used in the conventional digital X-ray imaging system shown in FIG.

Figure 4 is a schematic diagram showing the configuration of a digital X-ray imaging system using a flat plate X-ray source according to the present invention.

FIG. 5 is a diagram for explaining the configuration of a control circuit for selectively driving cathodes of each pixel type in a flat panel X-ray source using a field emission device according to the present invention; FIG.

6 is a conceptual diagram illustrating a driving principle of a flat plate X-ray source using the field emission device according to the present invention.

7 is an exploded perspective view showing the configuration of an X-ray detector used in a digital X-ray imaging system according to the present invention.

<Description of the symbols for the main parts of the drawings>

110, 200: X-ray source 111: vacuum tube

112, 210: cathode 113, 222: anode

114, 220: target material 115, 214: electron beam

120, 224: X-ray 130, 300: Subject

140, 500: digital X-ray detector 142: grid

144, 540: light detector 150, 600: microprocessor

202: substrate 232: switching means

234: column scanning driver 236: row scanning driver

238 power source 250 first grid

260: shielding film 252: X-ray absorption region

254: X-ray transmission region 510: Second grid

520: fluorescent screen 530: light guide

The present invention relates to a digital X-ray imaging system using a flat plate X-ray source and an X-ray image detection method using the same, and provides a high resolution digital X-ray image while using a smaller amount of X-rays in a narrower space than a conventional system. The present invention relates to a digital X-ray imaging system having a flat plate type X-ray source and an X-ray image detection method using the same.

With the recent development of the digital industry, medical imaging equipments are also being converted and improved digitally. As part of this aspect, recently, digital radiography (DR), which acquires digital X-ray images using existing X-ray tubes and digital radiation image detectors, has been developed to replace existing X-ray films. In addition, higher quality X-ray images are required to improve the diagnostic ability.

X-rays, which are generally used for clinical and industrial purposes, are generated through X-ray tubes invented in the early days. 1 is a cross-sectional view showing an X-ray generator according to the prior art, wherein the electron beam 115 accelerated from the filament-shaped cathode 112 provided in the vacuum tube 111 is a target material on the anode 113 in a high energy state ( 114 is a principle of generating an X-ray 120 of a cone beam type.

In the digital X-ray imaging apparatus, in order to detect and image X-rays, a system using a digital X-ray image detector instead of a conventional film has been developed and used. The digital X-ray image detector detects the energy and position of the absorbed X-rays by directly or indirectly detecting the energy of the X-rays absorbed at each position by pixel-type small photo detectors in a matrix form. X-rays are stored or imaged by digitizing and sending them to a microprocessor.

The type of digital X-ray detector for detecting X-rays is a direct method of directly absorbing X-rays and outputting an electrical signal proportional to the absorbed energy, and absorbing X-rays into a fluorescent screen, The visible light generated in the fluorescent screen in proportion to the energy of the X-rays absorbed by the fluorescent screen may be classified into an indirect method of outputting an electrical signal proportional to the amount of visible light absorbed by the pixel type photo detector.

Photo detectors that detect X-rays in a focused manner use amorphous selenium as a sensor material and form a flat structure. In the direct method, X-rays are directly detected by a pixel type photodetector without using a fluorescent screen, so the spatial resolution is determined only by the pixel size. However, in order to ensure sufficient detection efficiency, the thickness of the photodetector must be thick enough, and high voltage must be used to form a sufficient electric field at this thickness. Therefore, the electrical stability is relatively insufficient, and the amorphous selenium used in the direct method is a material. Due to the nature of the use of the limitation of the temperature requires attention to use outdoors, there is a disadvantage that the image lag (image lag) due to the afterimage is somewhat severe.

Photo detectors that detect X-rays indirectly include amorphous silicon as a sensor material and have a flat plate-like structure, or a charge-coulped device (CCD) or CMOS camera in combination with an optical lens. In the indirect method, amorphous silicon is used as a sensor material. A pixel-structured amorphous silicon photodiode is arranged in a matrix form over a large area, and light is directly connected to an image of visible light generated in the fluorescent screen by directly bonding the fluorescent screen. It uses the principle of detecting by diode and has the advantage of high detection efficiency for X-rays. Here, the output signal is proportional to the amount of visible light absorbed and the amount of visible light is proportional to the energy of X-rays absorbed in the fluorescent screen, so that the final output signal is proportional to the energy of the absorbed X-rays. In addition, by using a high atomic number and a high density material as a fluorescent screen, the detection efficiency for X-rays is good and the low voltage is sufficient to operate the photo detector, and thus the electrical stability is excellent. However, in the use of a fluorescent screen, when the X-ray is absorbed inside the fluorescent screen, the visible light generated at that position is scattered, so that visible light is detected not only at the pixel corresponding to the point where the original X-ray is absorbed, but also at the surrounding pixels. There is a disadvantage that the spatial resolution is lowered. On the other hand, among the indirect X-ray detection methods, an optical lens and a CCD or CMOS camera are used in combination, which uses a principle of acquiring an image by capturing an image formed on a fluorescent screen with a camera through an optical lens, and the production cost is high. There is an advantage that it is relatively cheap compared to the former. However, since this method does not have a separate light multiplication function, most of the light generated in the fluorescent screen is lost, and only a very small amount of light reaches the lens, which requires a large amount of X-rays to secure sufficient light. There is this.

FIG. 2 is a schematic view showing a digital X-ray imaging system according to the prior art, and FIG. 3 is a perspective view showing the configuration of a light detector used in the conventional digital X-ray imaging system shown in FIG.

Referring to FIG. 2, the subject 130 is located between the X-ray tube 110 and the digital X-ray detector 140, and is a conical beam type emitted from the X-ray tube 110 according to a signal from the microprocessor 150. The X-ray 120 is irradiated to the subject 130, the X-ray 120 passing through the subject 130 is detected through the digital X-ray detector 140 and connected to the digital X-ray detector 140 A process of acquiring an image through the display of 150 is shown. The digital X-ray detector 140 has a photo detector 144 in a matrix arrangement.

As described above, the X-rays according to the prior art are emitted in the form of a conical beam so that the structure of the subject is geometrically enlarged so as to obtain almost parallel X-rays in order to prevent distortion of the obtained image. Keep some distance between subjects. This requires more powerful X-rays, and in the process of generating X-rays, most of the electron energy is converted into heat, and excessive load is applied to the X-ray tube, resulting in a decrease in the life of the X-ray tube. In addition, X-rays scatter a large amount while passing through the subject, and the scattered X-rays are detected by another photo detector adjacent to the photo detector at a predetermined position and act as a noise, thereby reducing the contrast of the X-ray image. . Therefore, the non-scattering grid 142 is provided in front of the photo detector 144 arranged in a matrix form to prevent the generation of noise due to scattering lines. However, when the non-scattering grid is installed in order to prevent noise caused by scattered X-rays while passing through the subject, the grid line may be formed by the difference between the line spacing of the grid and the pixel size of the digital light detector provided in a matrix form. There is a problem in that an aliasing effect occurs and a moire phenomenon occurs due to the inhomogeneity of the grid line, causing a diagnosis error.

Therefore, in order to solve the above problems, a parallel X-ray from a surface light source can be obtained by using a flat panel X-ray source using a field emission device, thereby shortening the distance between the X-ray source and the subject to perform X-ray imaging. It is possible to reduce the space, obtain a high-resolution image with a small amount of X-rays by using a digital X-ray detector having a light multiplication means, and have a flat plate X-ray source that can reduce the radiation exposure of the subject. An object of the present invention is to provide a digital X-ray imaging system and an X-ray detection method using the same.

Digital X-ray imaging system having a flat plate X-ray source according to the present invention to achieve the above object,

Pixel-type cathodes arranged in a matrix form and a planar anode on the side opposite to the cathode and facing the cathode, on which a target material into which the accelerated electrons are incident is stacked; A flat plate X-ray source for generating X-rays by individually driving a cathode provided in a pixel form;

A first grid which is provided in contact with a surface from which the X-rays are emitted from the X-ray source and determines a traveling direction of the X-rays;

A second grid selectively incident X-rays emitted through the first grid and passing through the subject;

A fluorescent screen having the same area as the planar X-ray source, being in close contact with the second grid and generating visible light in response to the X-rays incident through the second grid; and the visible light generated by the fluorescent screen. A digital X-ray detector comprising a light guide for guiding the light beam to the light detector and a light detector for converting the visible light guided through the light guide into an image signal;

Connected to the planar X-ray source and the digital X-ray detector to synchronize the operations of the planar X-ray source and the digital X-ray detector, and to control an operation sequence of the cathodes of the planar X-ray source arranged in a pixel form; And a microprocessor for imaging and storing the image signal transmitted from the digital X-ray detector.

X-ray image detection method using a digital X-ray imaging system having a flat plate X-ray source according to the present invention to achieve the above object,

In the X-ray image detection method using a digital X-ray imaging system having a flat plate X-ray source having the above configuration,

Inputting an operation order of the cathodes of the planar X-ray source arranged in pixel form to a microprocessor;

Synchronizing operations of the X-ray source and the digital X-ray detector to sequentially generate an image signal corresponding to each pixel;

Applying power to a cathode of a corresponding pixel according to an input scan order to sequentially emit X-rays from each pixel of the X-ray source in a selected order;

Detecting an X-ray passing through the subject with a digital X-ray detector and transmitting an image signal corresponding to each pixel to a microprocessor;

And collecting the image signals transmitted to the microprocessor to implement an image, and display or store the image.

Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the accompanying drawings.

Figure 4 is a schematic diagram showing the configuration of a digital X-ray imaging system using a flat plate X-ray source according to the present invention, Figure 5 is a flat plate X-ray source using a field emission device according to the present invention, A diagram for describing a configuration of a control circuit for selectively driving pixel type cathodes.

First, referring to FIG. 4, the digital X-ray imaging system according to the present invention includes a flat panel X-ray source 200 which is composed of a field emission device, which can sequentially scan and emit parallel X-rays, and X Determines the shape and direction of X-rays emitted from the source, absorbs the scattered X-rays while passing through the first grid 250 and the object 300 provided on the front of the X-ray source 200, non-scattering A second grid 510 for inducing only X-rays to enter the digital X-ray detector 500, a digital X-ray detector 500 for converting the incident X-rays through the subject 300 into an image signal, and X The microprocessor 600 controls the source 200 and the digital X-ray detector 500 and collects image signals to form an image, and displays or stores the image.

Referring to FIG. 5, in the X-ray source 200, a pixel-shaped cathode 210 arranged in a matrix form is connected to a row scanning driver 236, a column scanning driver 234, and a power source 238, respectively. An anode 222 provided to face the cathode 210 is connected to the power source 238. In this case, the cathode 210 has a switching means 232 between the scan drivers 234 and 236 and the power supply 238. The scan drivers 234 and 236 are connected to the microprocessor 600, respectively.

The X-ray source is driven in the following way.

When a scan signal is transmitted from the microprocessor 600 to the respective scan drivers 234 and 236 according to a pre-entered operation order, each of the scan drivers 234 and 236 performs switching means for the corresponding pixel according to the transmitted signal. The power source 238 is applied to the cathode 210 of the selected pixel by turning on 232, and the electron beam 214 is generated in the selected pixel by the voltage difference between the cathode 210 and the anode 222. The electron beam 214 strikes the target material 220 on the anode 222 to generate an X-ray 224. (See Figure 6)

Next, each component of the X-ray imaging system according to the present invention will be described.

6 is a conceptual diagram illustrating a driving principle of a flat plate X-ray source using a field emission device according to the present invention, and FIG. 7 is an exploded view showing the configuration of an X-ray detector used in a digital X-ray imaging system according to the present invention. As a perspective view, it demonstrates in connection with FIG.

The X-ray source 200 is provided on the substrate 202 in a vacuum chamber (not shown) and arranged in a matrix form in a pixel form opposite to the cathode 210, and provided to the cathode 210. A field emission device including a plate-type anode 222 on which the target material 220 to which the accelerated electron beam is incident from the cathode 210 is stacked is formed. In this case, a gate electrode (not shown) may be further provided between the cathode 210 and the anode 222 so as to lower the driving voltage and favor high voltage switching.

The cathode 210 may be a micro tip, a metal-insulator composite, a diamond-based material (DLC; Diamon Like Carbon), a nanomaterial, or the like, and preferably a carbon nanotube (CNT; Carbon) having high field emission characteristics. Nano Tube) can be used by laminating on cathode materials of metals.

The anode 222 is made of aluminum or copper. At this time, the anode 222 serves as a filter for filtering the X-rays having a low energy. That is, among the X-rays 224 generated from the target material 220, the X-rays 224 having a relatively low energy that does not help the image acquisition is absorbed by the anode 222 acting as a filter to the subject 300 To suppress unnecessary radiation The anode 222 may be formed to a thickness of 1 to 2.5mm when formed of aluminum. The target material 220 may be made of tungsten or a tungsten alloy material, and may be made of molybdenum in mammography equipment, which is a breast cancer screening apparatus. The target material 220 usually has a thickness of several to several tens of micrometers, and when tungsten is used, it is formed to a thickness of 20 to 30 micrometers.

The front surface of the X-ray source 200 is further provided with a first grid 250 of the matrix form having the same area as the X-ray source 200. The first grid 250 determines the traveling direction of the X-ray 224 emitted from the X-ray source 200. The first grid 250 is divided into an X-ray transmission region 254 and an X-ray absorption region 252. In this case, the X-ray transmission region 254 may be formed of graphite fiber or plastic, and the X-ray absorption region 252 may be formed of lead or cerrobend. The first grid 250 is formed in the form of a pencil beam in the form of X-rays, and is formed in a thickness of 1 to 2mm so that the parallel X-rays can be emitted.

In addition, the rear surface of the X-ray source 200 is further provided with a shielding film 260 for blocking the X-rays emitted in a direction other than the predetermined travel direction. The shielding film 260 may reduce the damage caused by radiation by capturing X-rays radiated in a direction other than a predetermined direction. The shielding film 260 is preferably made of a material capable of absorbing X-rays, such as lead.

Since the plate-shaped X-ray source 200 according to the present invention generates a low-intensity X-ray over a relatively large area, since the heat associated with X-ray generation is relatively small, it is generated from the X-ray source using an air cooling method using air circulation. The heat to be cooled can be cooled. In addition, when a separate heat dissipation structure is required, the X-ray source 200 may be cooled by installing a thermo-electric cooler (TEC) at the rear of the X-ray source 200.

In the present invention, the digital X-ray detector 500 is made by the combination of the fluorescent screen 520, the light guide 530 and the photo detector 540, the fluorescent screen 520 to which the X-ray 224 is incident The second grid 510 is provided on the front surface.

The second grid 510 has the same area as the area of the X-ray source 200, and has a matrix like the first grid 250. The second grid 510 injects X-rays emitted from each pixel of the X-ray source 200 to a position corresponding to the pixels, and absorbs scattered lines generated while the X-rays 224 pass through the subject. Prevents X-rays from being detected in areas other than the predetermined position of the digital X-ray detector. The second grid 510 may be formed of the same structure and material as the first grid 250. The X-ray transmissive regions of the first grid 250 and the second grid 510 coincide with each other to prevent the above signal and moire from occurring.

The fluorescent screen 520 absorbs X-rays 224 incident through the second grid 510 to generate visible light. In the digital X-ray imaging system according to the present invention, unlike the conventional digital X-ray imaging system using a pixel type photo detector arranged in a matrix form, a single digital X-ray imaging system is connected to the fluorescent screen 520 through the light guide 530. By using the photo detector 540, since visible light generated in the fluorescent screen 520 must be continuously detected by X-rays sequentially irradiated for each pixel according to a predetermined sequence, generation of visible light and It is desirable to use a fluorescent screen 520 that has a high extinction rate.

The light guide 530 collects visible light generated from the fluorescent screen 520 and guides the collected light to the light detector 540.

The photo detector 540 converts the visible light transmitted through the light guide 530 into a digital image signal, and appropriately multiplies the converted image signal to the microprocessor 600 as necessary. The photo detector 540 may be formed of an element capable of rapidly converting visible light into a digital image signal and exhibiting a multiplication effect of the signal. For example, a photo multiplier tube (PMT) or avalanche light may be used. Avalanche photodiode (APD) may be used. In this case, the light multiplying effect can be obtained with a multiplication factor of 10 ⁶ or more, thereby generating an image signal having a sufficient size with only a small amount of visible light. In other words, even if the dose of X-rays initially irradiated is sufficiently lowered, it is possible to detect an image having a desired resolution, thereby minimizing the radiation dose to the subject.

The microprocessor 600 collects an image signal transmitted from the digital X-ray detector 500 to form an X-ray image, displays it, or stores it.

Hereinafter, an operation method of a digital X-ray imaging system using a flat plate X-ray source according to the present invention will be described.

First, an operation order of the cathodes of the flat panel X-ray source 200 arranged in the form of pixels is input to the microprocessor 600. In this case, the scanning order may be assigned to all pixels constituting the flat X-ray source, but in some cases, the X-ray source is divided into predetermined portions (for example, two-quarters, four-quarters, etc.). By assigning a scan order according to each division plane, the operation order may be determined so that X-rays are emitted from two or more pixels simultaneously (that is, one per division plane). In this case, in order to detect an image signal corresponding to each pixel simultaneously scanned, the corresponding fluorescent screen is also divided into the same area, and a separate light guide and a light detector must be configured for each divided part. Using such a configuration and scanning method has the advantage of reducing the scanning time of X-rays required for photographing a subject of the same size to a magnification by a divided multiple. In addition, X-rays having energy of a different size may be emitted in accordance with the size and internal structure of the subject 300. That is, since the amount of X-rays transmitted and scattered varies depending on the size and internal structure of the subject, the dose of X-rays to the subject can be optimized by emitting X-rays having different doses for each pixel of the X-ray source.

Next, in order to sequentially generate an image signal corresponding to each pixel, operations of the X-ray source 200 and the digital X-ray detector 500 are synchronized. To this end, the microprocessor 600 serves as a host.

The microprocessor 600 then emits X-rays at any one or multiple pixels selected by the input scan order.

The X-ray 224 emitted from the pixel of the X-ray source 200 passes through the first grid 250, the subject 300, and the second grid 510, and displays a fluorescent screen 520 of the digital X-ray detector 500. ) Is incident.

The X-ray 224 strikes the fluorescent material of the fluorescent screen 520 to generate visible light, and the visible light is transmitted to the photo detector 540 through the light guide 530. The photo detector 540 converts visible light into an image signal. In this case, the photodetector 540 is connected to the fluorescent screen of the corresponding portion of the number of light detectors equal to the number of divided parts according to the number of area divisions of the X-ray source 200 through a light guide to a plurality of pixels X-rays emitted from can be detected simultaneously and converted into image signals. In this case, the signal may be multiplied using the photodetector 540 having a multiplication function as described above.

The microprocessor 600 configures an image by calculating pixel positions and energy magnitudes of the received image signal and displays or stores the image.

  Thereafter, the microprocessor 600 initializes the X-ray source 200 and the digital X-ray detector 500 for the next X-ray imaging.

As described above, in the detailed description of the present invention, specific embodiments have been described, but various modifications are possible without departing from the scope of the present invention. Therefore, the scope of the present invention should not be limited to the described embodiments, but should be defined by the claims below and equivalents thereof.

As described above, the digital X-ray imaging system using the flat plate X-ray source and the X-ray image detection method using the same according to the present invention by using a flat plate X-ray source using a field emission device in parallel pencil form over a large area Since the X-ray beam can be implemented, the photographing space can be reduced, the X-ray source can be prevented from being overheated, and the radiation exposure to the subject can be reduced.

In addition, since the X-ray source and the X-ray detector are provided in parallel, X-rays can be emitted in a predetermined order for each pixel of the X-ray source, so that the dose of X-rays irradiated for each pixel can be adjusted according to the characteristics of the subject. There is an advantage.

In addition, unlike the conventional digital X-ray imaging system, which requires a large number of photo detectors formed in a matrix, desired images can be obtained using only one or several photo detectors having a signal multiplication function, thereby reducing the manufacturing cost of the entire system. It is also possible to further reduce the radiation exposure to the subject.

Claims (13)

Pixel-type cathodes arranged in a matrix form and a planar anode on the side opposite to the cathode and facing the cathode, on which a target material into which the accelerated electrons are incident is stacked; A flat plate X-ray source for generating X-rays by individually driving a cathode provided in a pixel form; A first grid which is provided in contact with a surface from which the X-rays are emitted from the X-ray source and determines a traveling direction of the X-rays; A second grid selectively incident X-rays emitted through the first grid and passing through the subject; A fluorescent screen having the same area as the planar X-ray source, being in close contact with the second grid and generating visible light in response to the X-rays incident through the second grid; and the visible light generated by the fluorescent screen. A digital X-ray detector comprising a light guide for guiding the light beam to the light detector and a light detector for converting the visible light guided through the light guide into an image signal; Connected to the planar X-ray source and the digital X-ray detector to synchronize the operations of the planar X-ray source and the digital X-ray detector, and to control an operation sequence of the cathodes of the planar X-ray source arranged in a pixel form; A microprocessor for imaging and storing the image signal transmitted from the digital X-ray detector; Digital x-ray imaging system using a flat plate x-ray source, characterized in that it comprises a. The method of claim 1, The X-ray source is a digital X-ray imaging system using a flat plate X-ray source, characterized in that further comprising a gate electrode between the anode and the cathode. The method of claim 1, The anode is a digital X-ray imaging system using a flat plate X-ray source, characterized in that made of aluminum or copper. The method of claim 1, And the target material is formed of a material selected from the group consisting of tungsten, a tungsten alloy material and molybdenum. The method of claim 1, The cathode is a digital X-ray imaging system using a flat plate X-ray source, characterized in that made of at least one material selected from the group consisting of micro tips, diamond-based materials (DLC; Diamon Like Carbon) and carbon nanotubes. The method of claim 1, A scan driver driven by a signal transmitted from the microprocessor and selecting a pixel of an X-ray source corresponding to the transmitted signal; And a switching means for connecting the cathode of each pixel selected by the scan driver to a power source. The method of claim 1, The first grid and the second grid is a digital X-ray imaging system using a flat plate X-ray source, characterized in that the X-ray transmission region and the X-ray absorption region in the form of a lattice. The method of claim 7, wherein The X-ray transmission region is formed of graphite fiber or plastic, and the X-ray absorption region is formed of lead or cerrobend (Digital X-ray imaging system using a flat plate X-ray source). The method of claim 1, Digital X-ray imaging system using a flat panel X-ray source, characterized in that further comprising a shielding film for blocking the X-ray on the back of the X-ray source. The method of claim 1, The photo detector is a digital x-ray imaging system using a flat plate x-ray source, characterized in that the optical multiplier (PMT) or avalanche photodiode (APD). The method of claim 1, The digital X-ray detector divides the fluorescent screen into a plurality of portions having the same area, the same number of light guides as the number of divided surfaces respectively connected to each divided portion, and also the same number of lights as the number of divided surfaces. Digital x-ray imaging system using a flat plate x-ray source, characterized in that consisting of a detector. In the X-ray image detection method using a digital X-ray imaging system having a flat plate X-ray source having the configuration of claim 1, Inputting an operation order of the cathodes of the planar X-ray source arranged in pixel form to a microprocessor; Synchronizing operations of the X-ray source and the digital X-ray detector to sequentially generate an image signal corresponding to each pixel; Applying power to a cathode of a corresponding pixel according to an input scan order to sequentially emit X-rays from each pixel of the X-ray source in a selected order; Detecting an X-ray passing through the subject with a digital X-ray detector and transmitting an image signal corresponding to each pixel to a microprocessor; Collecting an image signal transmitted to the microprocessor to implement an image, displaying the image signal, or storing the image signal; X-ray image detection method using a digital X-ray imaging system having a flat plate X-ray source, comprising a. The method of claim 12, In the step of emitting X-rays from each pixel of the X-ray source, the digital X-ray source having a flat plate X-ray source, characterized in that for each pixel to emit X-rays having a different size of energy according to the size and internal structure of the subject X-ray image detection method using X-ray imaging system.

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