X-ray imaging apparatus

Abstract

An X-ray imaging apparatus according to one embodiment comprises: an X-ray generation module which accommodates a first X-ray tube group including a first X-ray tube and a second X-ray tube group including a second X-ray tube that has an output lower than that of the first X-ray tube, and which includes an irradiation window formed on the bottom surface thereof so as to irradiate the outside with X-rays emitted from the first X-ray tube group and the second X-ray tube group; a detector for receiving X-rays emitted from the first X-ray tube group and the second X-ray tube group and transmitted through a subject; and a rotation arm which connects the X-ray generation module and the detector and which rotates about a first axis, wherein the first X-ray tube group and the second X-ray tube group are arranged side by side along a second axis perpendicular to the first axis and parallel to the bottom surface.

Description

X-ray imaging device

[0001] The present disclosure relates to an X-ray imaging device.

[0002] This disclosure is derived from research conducted as part of the 'BRIDGE Convergence Research and Development Project' with funding from the government (Ministry of Science and ICT) and support from the National Research Foundation of Korea.

[0003] [Project ID: RS-2023-00240135, Research Title: Development of a Patient-Specific Carbon Nano X-ray Tube-Based Multi-Source C-arm CT Imaging System Equipped with 3D Position Tracking Navigation for Robotic Surgery Image Guidance]

[0004] X-rays are electromagnetic waves with good penetrating power through objects and can be used for non-destructive and non-contact observation of the internal structures of objects or the human body. Electrons emitted from the cathode electrode are accelerated by the anode electrode and collide with it, and only a portion (less than about 1%) of the electrical energy applied to the X-ray tube is emitted as X-rays from the anode electrode. The X-rays emitted from the anode electrode are extracted to the outside of the X-ray tube and can be used for non-destructive and non-contact observation of the internal structures of objects or the human body.

[0005] The present disclosure provides technology related to an X-ray imaging device.

[0006] One aspect of the present disclosure provides embodiments of an X-ray imaging device. An X-ray imaging device according to one embodiment comprises: an X-ray generating module that accommodates a first X-ray tube group including a first X-ray tube and a second X-ray tube group including a second X-ray tube having a lower output than the first X-ray tube, and includes an irradiation window formed on a bottom surface for irradiating X-rays emitted from the first X-ray tube group and the second X-ray tube group to the outside; a detector that receives X-rays emitted from the first X-ray tube group and the second X-ray tube group and transmitted through a subject; and a rotating arm that connects the X-ray generating module and the detector and rotates about a first axis, wherein the first X-ray tube group and the second X-ray tube group may be arranged side by side along a second axis perpendicular to the first axis and parallel to the bottom surface.

[0007] In one embodiment, the first X-ray tube group may include a plurality of first X-ray tubes arranged along the first axis direction, and the second X-ray tube group may include a plurality of second X-ray tubes arranged along the first axis direction.

[0008] In one embodiment, a shielding module may be further included to control the irradiation field of X-rays irradiated to the outside of the X-ray generating module, which overlaps with at least a part of the irradiation window.

[0009] In one embodiment, the shielding module may include a first set of shielding plates that move along the second axis direction and adjust the degree of overlap with the irradiation window.

[0010] In one embodiment, the shielding module may further include a second shielding plate set that is fixed to the bottom surface and is positioned perpendicularly to the first shielding plate set with respect to the center of the irradiation window.

[0011] In one embodiment, the first X-ray tube and the second X-ray tube may each be arranged to form an acute angle with respect to the bottom surface.

[0012] In one embodiment, the first X-ray tube and the second X-ray tube may each be arranged to form an angle of 5 degrees or more and 10 degrees or less with respect to the bottom surface.

[0013] In one embodiment, the first region where X-rays emitted by the first X-ray tube are irradiated to the detector and the second region where X-rays emitted by the second X-ray tube are irradiated to the detector may overlap each other.

[0014] In one embodiment, the output voltage of each of the first X-ray tubes may be 90 kV or higher and 120 kV or lower, and the output voltage of each of the second X-ray tubes may be 60 kV or higher and 80 kV or lower.

[0015] In one embodiment, the power consumed in each of the first X-ray tube and the second X-ray tube can be maintained at the same level.

[0016] According to one embodiment of the present disclosure, the amount of radiation exposure to a subject can be minimized by adjusting the energy output of X-rays transmitted to the subject according to the characteristics of the subject.

[0017] According to one embodiment of the present disclosure, the quality of the image obtained can be improved by adjusting the X-ray transmittance according to the hardness of the tissue of the subject.

[0018] According to one embodiment of the present disclosure, the time required to reconstruct a three-dimensional CT (Computed Tomography) image can be reduced.

[0019] According to one embodiment of the present disclosure, a more accurate diagnostic image can be provided.

[0020] The effects according to the technology of the present disclosure are not limited to those mentioned above, and other unmentioned effects will be clearly understood by a person skilled in the art from the description of the present disclosure.

[0021] FIG. 1 is a perspective view of an X-ray imaging device according to one embodiment of the present disclosure.

[0022] Figure 2 is a simplified diagram of an X-ray imaging device cut along A-A' of Figure 1.

[0023] Figure 3 is a simplified diagram of an X-ray imaging device cut along B-B' of Figure 1.

[0024] FIG. 4 is a front view of an X-ray generating module according to one embodiment of the present disclosure.

[0025] Figure 5 is a bottom perspective view of the X-ray generating module of Figure 1.

[0026] Figure 6 is an enlarged view of area C of Figure 5.

[0027] FIG. 7 is a simplified diagram illustrating an area where X-rays are irradiated onto the surface of a detector according to one embodiment of the present disclosure.

[0028] The embodiments of the present disclosure are illustrative for the purpose of explaining the technical concept of the present disclosure. The scope of rights according to the present disclosure is not limited to the embodiments presented below or the specific description thereof.

[0029] All technical and scientific terms used in this disclosure, unless otherwise defined, have the meaning generally understood by those skilled in the art to which this disclosure pertains. All terms used in this disclosure are selected for the purpose of further clarifying this disclosure and are not selected to limit the scope of the rights under this disclosure.

[0030] Expressions such as “comprising,” “comprising,” “having,” etc. used in this disclosure should be understood as open-ended terms implying the possibility of including other embodiments, unless otherwise stated in the phrase or sentence containing such expressions.

[0031] Unless otherwise stated, singular expressions described in this disclosure may include a plural meaning, and this applies likewise to singular expressions described in the claims.

[0032] Expressions such as "first," "second," etc. used in this disclosure are used to distinguish multiple components from one another and do not limit the order or importance of said components.

[0033] In the present disclosure, where it is stated that a component is "connected" or "connected" to another component, it should be understood that the component may be directly connected or connected to the other component, or connected or connected through a new component.

[0034] The dimensions and numbers described in this disclosure are not limited to the stated dimensions and numbers alone. Unless otherwise specified, such dimensions and numbers may be understood to mean the stated values ​​and equivalent ranges including them. For example, the dimension '50 mm' described in this disclosure may be understood to include 'about 50 mm'.

[0035] Embodiments of the present disclosure will be described below with reference to the attached drawings. In the attached drawings, identical or corresponding components are given the same reference numerals. Furthermore, in the description of the embodiments below, the description of identical or corresponding components may be omitted. However, even if a description of a component is omitted, it is not intended that such component is not included in any embodiment.

[0036] Furthermore, all drawings used in the following description are schematic, and the relationships between the dimensions of each element and the ratios of each element depicted in the drawings do not necessarily correspond to reality. Additionally, the relationships between the dimensions of each element and the ratios of each element do not necessarily correspond to one another among multiple drawings.

[0037] FIG. 1 is a perspective view of an X-ray imaging device (1) according to one embodiment of the present disclosure.

[0038] The X-ray imaging device (1) may be a device that irradiates X-rays toward a subject (e.g., subject (T) in FIG. 2), acquires an image of the X-rays that have passed through the subject (T), and, based on the acquired image, photographs the interior of the subject (T) or detects defects in the subject (T). The X-ray imaging device (1) may include an X-ray generating module (10), a detector (20), a rotating arm (30), and a shielding module (14).

[0039] An X-ray generating module (10) according to one embodiment may accommodate one or more groups of X-ray tubes (e.g., a first group of X-ray tubes (11) and a second group of X-ray tubes (12) of FIG. 2) inside. The X-ray generating module (10) irradiates X-rays toward a subject (e.g., a subject (T) of FIG. 2), and the X-rays that pass through the subject (T) reach the receiving surface (20a) of the detector (20).

[0040] A detector (20) according to one embodiment may be positioned on one side in the direction in which X-rays are emitted from an X-ray generating module (10). Accordingly, the detector (20) may receive X-rays irradiated from the X-ray generating module (10). Specifically, the detector (20) may receive X-rays that have passed through a subject (T), convert them into electrical signals, and convert the converted electrical signals into X-ray transmission images. According to one embodiment, the detector (20) may be provided in a flat plate shape, but is not necessarily limited thereto.

[0041] According to one embodiment, the rotating arm (30) can connect the X-ray generating module (10) and the detector (20). One end of the rotating arm (30) can be connected to the side of the X-ray generating module (10), and the other end of the rotating arm (30) can be connected to the side of the detector (20). That is, when the X-ray imaging device (1) is viewed from the side (e.g., the +Y direction in FIG. 1), the rotating arm (30) can have a 'C' shape. Due to the shape characteristics of the rotating arm (30), the X-rays emitted from the X-ray generating module (10) can pass through the subject (e.g., the subject (T) in FIG. 2) without being obstructed by other structures such as the rotating arm (30) and reach the receiving surface (20a) of the detector (20) completely.

[0042] In one embodiment, the rotating arm (30) is connected to the main body (40) of the X-ray imaging device (1) and can rotate about a first axis (A1). The first axis (A1) is directed toward the front of the X-ray imaging device (1) (e.g., the +Z direction in FIG. 1). By rotating the rotating arm (30) about the first axis (A1), various parts of a subject (T) having a three-dimensional shape (e.g., the subject (T) in FIG. 2) can be photographed even while the subject (T) is in a fixed state, and a three-dimensional CT image can be restored.

[0043] Hereinafter, with reference to FIGS. 2 and FIGS. 3, a group of X-ray tubes (11, 12) disposed inside an X-ray generating module (10) will be described.

[0044] FIG. 2 is a simplified diagram of an X-ray imaging device (1) cut along A-A' of FIG. 1. Referring to FIG. 2, the X-ray generating module (10) may include a first X-ray tube group (11) and a second X-ray tube group (12). In one embodiment, the first X-ray tube group (11) may include one or more first X-ray tubes (111). In one embodiment, the second X-ray tube group (12) may include one or more second X-ray tubes (121). Each second X-ray tube (121) belonging to the second X-ray tube group (12) may have a lower output than each first X-ray tube (111) belonging to the first X-ray tube group (11). That is, the first X-ray tube (111) may have a higher output voltage than the second X-ray tube (121). For example, the output voltage of each first X-ray tube (111) may be 90 kV or higher and 120 kV or lower. For example, the output voltage of each second X-ray tube (121) may be 60 kV or higher and 80 kV or lower. However, even in this case, the power consumed by each first X-ray tube (111) and second X-ray tube (121) may be maintained at the same level. That is, since power is calculated as the product of the output voltage and the internal current, the strength of the internal current of the first X-ray tube (111) is lower than the strength of the internal current of the second X-ray tube (121).

[0045] Referring further to FIG. 2, a first group of X-ray tubes (11) and a second group of X-ray tubes (12) can be arranged side by side within an X-ray generating module (10). Specifically, the first group of X-ray tubes (11) and the second group of X-ray tubes (12) can be arranged side by side along a second axis (A2) that is perpendicular to the first axis (A1) and parallel to the receiving surface (20a) of the detector (20) (e.g., the +Y direction in FIG. 2). By arranging the first group of X-ray tubes (11) and the second group of X-ray tubes (12), which have different outputs from each other, side by side along the second axis (A2) and irradiating X-rays toward a subject (T), X-rays with appropriate outputs are transmitted according to the density level of the subject (T) area, thereby enabling the acquisition of high-quality images and reducing the radiation exposure of the subject (T).

[0046] FIG. 3 is a simplified diagram of an X-ray imaging device (1) cut along B-B' of FIG. 1. In one embodiment according to FIG. 3, the first X-ray tube group (11) includes two first X-ray tubes (111, 112), but according to the embodiment, the first X-ray tube group (11) may include two or more first X-ray tubes. A plurality of first X-ray tubes (111, 112) included in the first X-ray tube group (11) may be arranged side by side along the direction of the first axis (A1). Additionally, the second X-ray tube group (12) may also include two or more second X-ray tubes (e.g., X-ray tube (121) of FIG. 2), and a plurality of second X-ray tubes included in the second X-ray tube group (12) may also be arranged side by side along the direction of the first axis (A1). That is, a plurality of first X-ray tubes (111, 112) may be arranged in parallel in a direction perpendicular to the direction in which the first X-ray tube group (11) and the second X-ray tube group (12) described with reference to FIG. 2 are arranged (direction of the second axis (A2)). Additionally, a plurality of second X-ray tubes may also be arranged in parallel in a direction perpendicular to the direction in which the first X-ray tube group (11) and the second X-ray tube group (12) described with reference to FIG. 2 are arranged (direction of the second axis (A2)). By arranging X-ray tube groups (11, 12) having the same output in parallel along the direction of the first axis (A1), the field of view (FOV) of the X-ray generating module (10) can be expanded. And the more individual X-ray tubes included in one X-ray tube group (11, 12), the greater the degree of expansion of the field of view (FOV) of the X-ray generating module (10).

[0047] Referring to FIGS. 2 and 3, a first X-ray tube group (11) containing two first X-ray tubes and a second X-ray tube group (12) containing two second X-ray tubes are arranged side by side inside the X-ray generating module (10), so that a total of four X-ray tubes are arranged in a 2×2 array inside the X-ray generating module (10). However, the embodiment according to FIGS. 2 and 3 is merely exemplary, and if there are m groups of X-ray tubes (11, 12) having different outputs and n individual X-ray tubes included in each group of X-ray tubes (11, 12), the X-ray tubes arranged inside the X-ray generating module (10) may be formed in an m×n array (where m and n are natural numbers).

[0048] FIG. 4 is a front view of an X-ray generating module (10) according to one embodiment of the present disclosure. Referring to FIG. 4, the X-ray generating module (10) may accommodate a first X-ray tube group (11) and a second X-ray tube group (12) inside it. To accommodate the first X-ray tube group (11) and the second X-ray tube group (12), the X-ray generating module (10) may have a housing shape. In the embodiment illustrated in FIG. 4, the X-ray generating module (10) includes a bottom surface (10a), a top surface (10b) formed on the opposite side of the bottom surface (10a), and a side surface (10c) formed between the bottom surface (10a) and the top surface (10b). The bottom surface (10a) of the X-ray generating module (10) includes an irradiation window (13) for expelling X-rays emitted from the first X-ray tube group (11) and the second X-ray tube group (12) to the outside. The irradiation window (13) may include a first window (131) and a second window (132). The first window (131) is positioned close to the X-ray tube group (11, 12) and can selectively pass specific wavelengths or energies, or filter X-rays of a specific frequency band. The second window (132) is formed below the first window (131) and is directly exposed to the outside of the X-ray generating module (10). The second window (132) can serve to protect the inside of the X-ray generating module (10), which is filled with insulating liquid, from external dust or shock.

[0049] Referring to FIG. 4, the first X-ray tube (111) may be positioned to form a constant angle (θ1) with respect to the bottom surface (10a) of the X-ray generating module (10). The second X-ray tube (121) may be positioned to form a constant angle (θ2) with respect to the bottom surface (10a) of the X-ray generating module (10). The angles (θ1, θ2) formed by each of the first X-ray tube (111) and the second X-ray tube (121) with respect to the bottom surface (10a) of the X-ray generating module (10) may be acute angles. In one embodiment, the angles (θ1, θ2) formed by each of the first X-ray tube (111) and the second X-ray tube (121) with respect to the bottom surface (10a) of the X-ray generating module (10) may be 5 degrees or more and 10 degrees or less. Each first X-ray tube (111) and second X-ray tube (121) is arranged to form a constant angle (θ1, θ2) with respect to the bottom surface (10a), thereby allowing the X-ray irradiation angle tilted relative to the horizontal plane to be corrected according to the inherent arrangement angle of the X-ray generating part (anode) contained within the X-ray tube, thereby controlling the area (irradiation field) where X-rays are irradiated.

[0050] Referring to FIG. 4, a shielding module (14) may be further included, positioned parallel to the bottom surface (10a) of the X-ray generating module (10) below the irradiation window (13). The shielding module (14) may be positioned to overlap at least a portion of the irradiation window (13). The shielding module (14) is positioned at the bottom of the second window (132) to control the area (irradiation field) where X-rays are irradiated by adjusting the irradiation angle of the X-rays emitted from the first X-ray tube group (11) and the second X-ray tube group (12). The shielding module (14) may include one or more shielding windows (e.g., shielding plates (141a, 141b, 142a, 142b) of FIG. 6). The shielding plates (141a, 141b, 142a, 142b) may be movably positioned or fixed below the irradiation window (13) to adjust the area (irradiation field) where X-rays are irradiated. The shielding module (14) may act as a collimator. The shielding module (14) may be formed of a material that absorbs X-rays, such as lead or brass.

[0051] Hereinafter, the shielding module (14) will be described in more detail with reference to FIGS. 5 and FIGS. 6. FIG. 5 is a bottom perspective view of the X-ray generating module (10) of FIG. 1. FIG. 6 is an enlarged view showing area C of FIG. 5.

[0052] Referring to FIG. 5, a shielding module (14) may be formed on the bottom surface (10a) of the X-ray generating module (10). The shielding module (14) may be formed in correspondence with the number and arrangement of X-ray tubes placed inside the X-ray generating module (10). In one embodiment, when there are m groups of X-ray tubes having different outputs (e.g., the first X-ray tube group (11) and the second X-ray tube group (12) of FIG. 2)) and n individual X-ray tubes included in each X-ray tube group (11, 12), the total number of X-ray tubes inside the X-ray generating module (10) is formed in an m×n array, so the shielding module (14) may also be formed in an m×n array on the bottom surface (10a) of the X-ray generating module (10) in correspondence with the number and arrangement of X-ray tubes (where m and n are natural numbers). For example, in the embodiment according to FIGS. 2 and FIG. 3 described above, a first X-ray tube group (11) containing two first X-ray tubes and a second X-ray tube group (12) containing two second X-ray tubes are arranged side by side inside the X-ray generating module (10), so a total of four X-ray tubes are arranged in a 2×2 array inside the X-ray generating module (10). In this case, a total of four shielding modules (14) may also be formed on the bottom surface (10a) of the X-ray generating module (10) in a 2×2 array corresponding to the number and arrangement of X-ray tubes. However, the arrangement of the shielding modules (14) is not limited to this arrangement and may be arranged corresponding to the number and arrangement of X-ray tubes placed inside the X-ray generating module (10). Referring to FIG. 6, each shielding module (14) may include a first shielding plate set (141), a second shielding plate set (142), and a driving motor (143). The first shielding plate set (141) includes two shielding plates (141a, 141b) arranged side by side along the +Y direction (e.g., the direction of the second axis (A2) in FIG. 2). The first shielding plate set (141) may be moved in the +Y direction or the -Y direction by the driving motor (143).Two shielding plates (141a, 141b) can be moved closer to each other or further apart by the drive motor (143). For example, they can be moved closer to each other by moving shielding plate (141a) in the +Y direction and shielding plate (141b) in the -Y direction. Also, for example, they can be moved further apart by moving shielding plate (141a) in the -Y direction and shielding plate (141b) in the +Y direction. By moving the first set of shielding plates (141) by the motor (143), the area (e.g., the irradiation area (21) in FIG. 7) where X-rays are irradiated on the surface (20a) of the detector (e.g., the detector (20) in FIG. 1) can be controlled.

[0053] In one embodiment, the second shielding plate set (142) includes two shielding plates (142a, 142b) arranged side by side along the +Y direction (e.g., the direction of the first axis (A1) in FIG. 3). That is, the second shielding plate set (142) may be arranged on the bottom surface (10a) of the X-ray generating module (10) in a direction perpendicular to the first shielding plate set (141). The second shielding plate set (142) may be arranged to partially overlap with the first shielding plate set (141). The shielding plates (142a) and (142b) of the second shielding plate set (142) may be fixedly arranged on the bottom surface (10a) at a certain distance from each other.

[0054] The first shielding plate set (141) and the second shielding plate set (142) are positioned to overlap with the edge of the irradiation window (13), thereby absorbing X-rays emitted from an X-ray tube (e.g., the first X-ray tube (111, 112) of FIG. 2 and the second X-ray tube (121) of FIG. 3) placed inside the X-ray generating module (10), and controlling the area where X-rays are irradiated on the receiving surface (20a) of the detector (20) (e.g., the irradiation area (21) of FIG. 7).

[0055] FIG. 7 is a simplified diagram illustrating an irradiation area (21) in which X-rays are irradiated onto the receiving surface (20a) of a detector (20) according to one embodiment of the present disclosure. In one embodiment, the irradiation area (21) may be divided into a first X-ray irradiation area (211) and a second X-ray irradiation area (212).

[0056] The first X-ray irradiation area (211) is an area where X-rays generated from a first X-ray tube group (e.g., the first X-ray tube group (11) of FIG. 2) having a relatively high output are irradiated onto the receiving surface (20a) of the detector (20). The width (d1) of the first X-ray irradiation area (211) can be adjusted by the movement of the first shielding plate set (141) described with reference to FIG. 6. For example, if the shielding plates (141a, 141b) of the first shielding plate set (141) move in a direction that brings them closer to each other, the width (d1) of the first X-ray irradiation area (211) decreases, and if the shielding plates (141a, 141b) of the first shielding plate set (141) move in a direction that moves them further apart from each other, the width (d1) of the first X-ray irradiation area (211) increases. On the other hand, as described with reference to FIG. 6, since the second shielding plate set (142) is fixed to the bottom surface (10a) of the X-ray generating module (10), the front-to-back width (d3) of the first X-ray irradiation area (211) is adjusted in a different way. In one embodiment, the front-to-back width (d3) of the first X-ray irradiation area (211) can be adjusted by the number of each first X-ray tube (e.g., the first X-ray tubes (111, 112) of FIG. 3) belonging to the first X-ray tube group (11). For example, in the embodiment according to FIG. 3, to increase the front-to-back width (d3) of the first X-ray irradiation area (211) when the first X-ray tube group (11) includes two first X-ray tubes (111, 112), additional first X-ray tubes can be arranged side by side in the direction of the first axis (A1).

[0057] The second X-ray irradiation area (212) is an area where X-rays generated from a second X-ray tube group (e.g., the second X-ray tube group (12) of FIG. 2) having a relatively low output are irradiated onto the receiving surface (20a) of the detector (20). The left-right width (d2) of the second X-ray irradiation area (212) can be adjusted by the movement of the first shielding plate set (141), just as in the first X-ray irradiation area (211). The front-back width (d3) of the second X-ray irradiation area (212) can be adjusted by the number of second X-ray tubes (e.g., the second X-ray tube (121) of FIG. 2) included in the second X-ray tube group (e.g., the second X-ray tube group (12) of FIG. 2), just as in the first X-ray irradiation area (211).

[0058] In one embodiment, the first X-ray irradiation area (211) and the second X-ray irradiation area (212) may include an overlapping area (213) in which they overlap each other. The overlapping area (213) is an area where the high-power first X-ray irradiation area (211) and the low-power second X-ray irradiation area (212) are irradiated together, and can reconstruct all or part of the subject (e.g., subject (T) of FIG. 2) captured by each X-ray tube in three dimensions. In one embodiment, the width (dc) of the overlapping area (213) may be adjusted by the movement of the first shielding plate set (141). The width (dc) of the overlapping area (213) may be 2 cm or more and 20 cm or less.

[0059] Although the technical concept of the present disclosure has been described by some embodiments and examples illustrated in the accompanying drawings, it should be understood that various substitutions, modifications, and changes may be made without departing from the technical concept and scope of the present disclosure as understood by those skilled in the art to which the present disclosure pertains. Furthermore, such substitutions, modifications, and changes should be considered to fall within the scope of the appended claims.

Claims

1. An X-ray generating module comprising a first X-ray tube group including a first X-ray tube and a second X-ray tube group including a second X-ray tube having a lower output than the first X-ray tube, and an irradiation window formed on the bottom surface for irradiating X-rays emitted from the first X-ray tube group and the second X-ray tube group to the outside; A detector for receiving X-rays emitted from the first X-ray tube group and the second X-ray tube group and transmitted through a subject; and The above X-ray generating module and the above detector are connected, and the rotating arm that rotates about a first axis is included. The first X-ray tube group and the second X-ray tube group are arranged side by side along a second axis perpendicular to the first axis and parallel to the bottom surface. device.

2. In Paragraph 1, The first X-ray tube group includes a plurality of first X-ray tubes arranged along the first axis direction, and The device comprising a plurality of second X-ray tubes arranged along the first axis direction, wherein the second X-ray tube group described above is a device.

3. In Paragraph 1, A shielding module further comprising a shielding module that overlaps with at least a portion of the irradiation window and controls the irradiation field of X-rays irradiated to the outside of the X-ray generating module. device.

4. In Paragraph 3, The shielding module comprises a first set of shielding plates that moves along the second axis direction and adjusts the degree of overlap with the irradiation window. device.

5. In Paragraph 4, The shielding module further comprises a second shielding plate set that is fixed to the bottom surface and is positioned perpendicularly to the first shielding plate set with respect to the center of the irradiation window. device.

6. In Paragraph 1, Each of the first X-ray tube and the second X-ray tube is positioned to form an acute angle with respect to the bottom surface. device.

7. In Paragraph 6, Each of the first X-ray tube and the second X-ray tube is arranged to form an angle of 5 degrees or more and 10 degrees or less with respect to the bottom surface. device.

8. In Paragraph 1, The first region where X-rays emitted by the first X-ray tube are irradiated onto the detector and the second region where X-rays emitted by the second X-ray tube are irradiated onto the detector overlap each other. device.

9. In Paragraph 1, The output voltage of each of the first X-ray tubes is 90kV or higher and 120kV or lower, and the output voltage of each of the second X-ray tubes is 60kV or higher and 80kV or lower, device.

10. In Paragraph 9, The power consumed in each of the first X-ray tube and the second X-ray tube is maintained at the same level. device.

Images