CN116262047A - X-ray detector, detection method and X-ray imaging device - Google Patents

X-ray detector, detection method and X-ray imaging device Download PDF

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Publication number
CN116262047A
CN116262047A CN202111539753.6A CN202111539753A CN116262047A CN 116262047 A CN116262047 A CN 116262047A CN 202111539753 A CN202111539753 A CN 202111539753A CN 116262047 A CN116262047 A CN 116262047A
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layer
detection unit
ray
arrays
detector
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周铖龙
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Shanghai United Imaging Healthcare Co Ltd
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Shanghai United Imaging Healthcare Co Ltd
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/42—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4266—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a plurality of detector units
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computerised tomographs
    • A61B6/032—Transmission computed tomography [CT]
    • A61B6/035—Mechanical aspects of CT
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/42—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4275—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis using a detector unit almost surrounding the patient, e.g. more than 180°
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
    • Y02P—CLIMATE CHANGE MITIGATION TECHNOLOGIES IN THE PRODUCTION OR PROCESSING OF GOODS
    • Y02P70/00—Climate change mitigation technologies in the production process for final industrial or consumer products
    • Y02P70/50—Manufacturing or production processes characterised by the final manufactured product

Abstract

The invention provides an X-ray detector, a detection method and an X-ray imaging device, wherein the X-ray detector comprises at least a plurality of layers of detection unit arrays, and the plurality of layers of detection unit arrays comprise a first layer of detection unit arrays and a second layer of detection unit arrays; the first layer of detection unit arrays have a first reaction cross section for X-rays, and the second layer of detection unit arrays have a second reaction cross section for X-rays, the first reaction cross section being greater than or less than the second reaction cross section. Therefore, X photons can mainly generate Compton scattering on a detection unit array relatively close to an X-ray emission source, and photoelectric effect on a detection unit array relatively far away from the X-ray emission source, so that the main rays of the incident X photons can be determined according to the position relationship between the tracks of the X photons detected by each layer of detection unit array and the X-ray emission source; and calculating the total energy of the X photons which are detected by each layer of detection unit array and are primary rays, and completing energy spectrum detection.

Description

X-ray detector, detection method and X-ray imaging device
Technical Field
The present invention relates to the field of energy spectrum detection technology, and in particular, to an X-ray detector, a detection method, and an X-ray imaging apparatus.
Background
Each detection unit of the CT detector receives X-rays that include a portion of the primary rays from the Focal spot of the tube that do not interact with each other and a portion of the scattered rays that change direction after having interacted with the scanned object or other objects on the machine before reaching the detector. Wherein the specific gravity of the scattered rays can severely interfere with the final CT image quality. In the 3 rd generation CT detector, because the positions of the detector and the focal point of the bulb are rigidly fixed, the specific gravity of scattered rays reaching the detector is reduced by designing an anti-Scatter Grid (ASG), fig. 1 is a schematic diagram of ASG shielding scattered rays in the third generation CT detector, in which the extension line of the ASG side wall is aligned with the focal point of the bulb, so that the main rays can enter the detection unit through the gap between the ASG side walls, and the scattered rays can be absorbed by the ASG side walls and shielded because of the change of the directions of the scattered rays.
The 4 th generation static CT detection generally has the detector and the bulb focus distributed in a ring shape over the whole scanning aperture, and each detection unit receives the rays from the focus at different positions during the scanning process, as shown in fig. 2, and the incidence angles of the X-rays emitted by different bulb focuses are not consistent for the same detector unit. Therefore, the ASG cannot achieve the purpose of suppressing the specific gravity of scattered rays. Shielding of scattered radiation in 4 generation CT is therefore an unsolved problem.
Disclosure of Invention
The invention aims to provide an X-ray detector, a detection method and an X-ray imaging device, which are used for identifying scattered rays and primary rays through track detection of incident X-photons, so that the effect of the scattered rays on an image is reduced.
In order to solve the technical problems, the invention provides an X-ray detector, which comprises a plurality of layers of detection unit arrays, wherein the plurality of layers of detection unit arrays are arranged side by side along a set direction;
the plurality of layers of detection unit arrays comprise a first layer of detection unit arrays and a second layer of detection unit arrays;
the first layer of detection unit arrays have a first reaction cross section for X-rays, and the second layer of detection unit arrays have a second reaction cross section for X-rays, the first reaction cross section being greater than or less than the second reaction cross section.
Optionally, in the X-ray detector,
the first layer of detection unit arrays are the detection unit arrays at the uppermost layer along the set direction, and the material forming the first layer of detection unit arrays has a first atomic number;
the second layer of detection unit arrays are positioned at the lower part of the detection unit array at the uppermost layer, and the material forming the second layer of detection unit arrays has a second atomic number;
wherein the first atomic number is less than the second atomic number.
Optionally, in the X-ray detector, the first layer of the array of detection units has a first thickness, and the second layer of the array of detection units has a second thickness.
Optionally, in the X-ray detector, the X-ray detector includes a plurality of layers of the first layer of the detecting unit arrays, and the plurality of layers of the first layer of the detecting unit arrays are sequentially arranged along a set direction and are all located above the second layer of the detecting unit arrays.
Optionally, in the X-ray detector, two adjacent layers of the detecting unit arrays are arranged at intervals.
Optionally, in the X-ray detector, the material of the second layer of the detecting unit array includes at least one of cadmium antimonide, zinc antimonide and cadmium antimonide, and the material of the first layer of the detecting unit array includes at least one of silicon and gallium arsenide.
The invention also provides a method for energy spectrum detection by using the X-ray detector, which comprises the following steps:
determining the main ray of the incident X-photon according to the position relationship between the track of the X-photon detected by each layer of detection unit array and the X-ray emission source;
calculating total energy of the incident X-ray main rays detected by each layer of the detection unit array to obtain projection data;
reconstructing a spectrum image of the detection object according to the projection data.
Optionally, in the method for performing energy spectrum detection, determining, according to a positional relationship between a track of an X-photon detected by each layer of the detection unit array and an X-ray emission source, a primary ray of the incident X-photon includes:
judging whether the extension line of the detected X-ray track is in the plane of the X-ray emission source and the distance between the extension line and the X-ray emission source is in a preset range, if so, determining the extension line as a main ray.
The present invention also provides an X-ray imaging apparatus comprising:
an X-ray generator for generating X-rays;
the detector is arranged opposite to the X-ray generator and comprises a plurality of layers of detection unit arrays, wherein the plurality of layers of detection unit arrays comprise a first layer of detection unit arrays and a second layer of detection unit arrays;
the distance between the first layer of detection unit array and the X-ray generator is smaller than that between the second layer of detection unit array and the X-ray generator;
the energy of the X-rays which can be deposited on the first layer detection unit array is different from the energy of the X-rays which can be deposited on the second layer detection unit array; or the probability of the interaction of the X-ray with the first layer detection unit array is smaller than the probability of the interaction of the X-ray with the second layer detection unit array.
Optionally, the first layer of detection unit arrays and the second layer of detection unit arrays are stacked along a set direction, and the set direction is a direction in which the X-ray generator points to the detector.
In summary, in the X-ray detector, the detection method and the X-ray imaging apparatus provided by the present invention, the X-ray detector includes at least a plurality of layers of detection unit arrays, and the plurality of layers of detection unit arrays are arranged side by side along a set direction; the plurality of layers of detection unit arrays comprise a first layer of detection unit arrays and a second layer of detection unit arrays; the first layer of detection unit arrays have a first reaction cross section for X-rays, and the second layer of detection unit arrays have a second reaction cross section for X-rays, the first reaction cross section being greater than or less than the second reaction cross section. Thus, X photons can mainly undergo Compton scattering on the detection unit arrays relatively close to the X-ray emission source, and photoelectric effect can mainly occur on the detection unit arrays relatively far away from the X-ray emission source, so that all residual energy of the X photons can be detected as far as possible, and the main ray of the incident X photons can be determined according to the position relation between the track of the X photons detected by each layer of detection unit arrays and the X-ray emission source; and calculating the total energy of the X photons which are detected by each layer of the detection unit array and are primary rays, and finishing energy spectrum detection.
Drawings
FIG. 1 is a schematic view of ASG shielding scattered radiation in a third generation CT;
FIG. 2 is a schematic diagram of a fourth generation CT detector and distribution of X-ray emission sources and ray incidence;
FIG. 3 is a schematic top view of an X-ray detector according to an embodiment of the present invention;
FIG. 4 is a schematic side view of an X-ray detector according to an embodiment of the present invention;
FIG. 5 is a schematic flow chart of a detection method according to an embodiment of the present invention;
fig. 6 is a schematic diagram illustrating an X-ray track detection effect of an X-ray detector according to an embodiment of the present invention.
Detailed Description
The invention will be described in detail with reference to the drawings and the embodiments, in order to make the objects, advantages and features of the invention more apparent. It should be noted that the drawings are in a very simplified form and are not drawn to scale, merely for convenience and clarity in aiding in the description of embodiments of the invention. Furthermore, the structures shown in the drawings are often part of actual structures. In particular, the drawings are shown with different emphasis instead being placed upon illustrating the various embodiments. It should be further understood that the terms "first," "second," "third," and the like in this specification are used merely for distinguishing between various components, elements, steps, etc. in the specification and not for indicating a logical or sequential relationship between the various components, elements, steps, etc., unless otherwise indicated.
The X-photons interact with the object by spectroscopic effects, compton scattering and coherent scattering, wherein the proportion of coherent scattering is negligible with respect to the X-ray energy region.
When the photoelectric effect occurs, the X-photons lose all energy once, and the energy of the X-photons is proportional to the 5 th power of the atomic number of the material atomic interaction section (the number of nuclear protons of the material contained in the detector):
σ photoelectric device ∝Z 5 ；
When Compton scattering occurs, X photons can interact with a substance multiple times, gradually losing energy, which is proportional to the 1 st power of the atomic number of the interaction cross section of the substance atoms:
σ compton (R) ∝Z 1 ；
Thus, the probability of occurrence of a photoelectric interaction can be adjusted by selecting different detector materials.
In view of this, an embodiment of the present invention provides an X-ray detector, including a plurality of layers of detection unit arrays, where the plurality of layers of detection unit arrays are arranged side by side along a set direction; the setting direction may be, for example, the direction in which the X-ray generator is directed towards the detector, or the direction in which the X-ray generator is directed towards the patient bed. The plurality of layers of the detector element arrays may be arranged side by side along the set direction, for example, a plurality of layers of the detector element arrays may be stacked along the set direction such that each layer of the detector element arrays has a different distance from the X-ray generator.
The plurality of layers of detection unit arrays comprise a first layer of detection unit arrays and a second layer of detection unit arrays;
the first layer of detection unit arrays has a first reaction cross section for X-rays, and the second layer of detection unit arrays has a second reaction cross section for X-rays, the first reaction cross section being greater than or less than the second reaction cross section. The reaction cross section indicates the probability of a photon beam of X-rays interacting with all target targets of the medium, for example: the probability of a photon beam of X-rays to undergo photoelectric effect, compton scattering and/or coherent scattering with the detector cell array. In this embodiment, the first reaction cross section is larger than the second reaction cross section represents: the probability of the interaction of the photon beam of the X-ray with the first layer of detection unit array is larger than the probability of the interaction of the photon beam of the X-ray with the second layer of detection unit array. Correspondingly, the first reaction cross section is smaller than the second reaction cross section represents: the probability of the interaction of the photon beam of the X-ray with the first layer of detection unit arrays is smaller than the probability of the interaction of the photon beam of the X-ray with the second layer of detection unit arrays. Therefore, by setting the detection unit arrays with different positions into different reaction cross sections, scattered rays and main rays are more easily identified through track detection of incident X-photons, and the effect of the scattered rays on the image is further reduced.
When the X-ray detector provided in this embodiment is used to detect the energy of X-photons, the detection unit array having a relatively large reaction cross section may be disposed at a relatively farther position from the X-ray emission source, and the detection unit array having a relatively smaller reaction cross section may be disposed at a relatively nearer position from the X-ray emission source. In this way, the X-photons can mainly generate Compton scattering on the detection unit array relatively close to the X-ray generator, and mainly generate photoelectric effect on the detection unit array relatively far away from the X-ray generator, so as to detect all the residual energy of the X-photons as far as possible, and further, the main ray of the incident X-photons can be determined according to the position relation between the track of the X-photons detected by each layer of detection unit array and the X-ray emission source; and calculating the total energy of the X photons which are detected by each layer of the detection unit array and are primary rays, and finishing energy spectrum detection.
Further, in this embodiment, the first layer of detecting unit arrays may be the detecting unit array located at the uppermost layer along the set direction, facing the X-ray emission source/X-ray generator, and being the detecting unit array located at the smallest/nearest distance from the X-ray generator in the X-ray detector, and the material forming the first layer of detecting unit arrays has a first atomic number; the second layer of detection unit arrays are positioned at the lower part of the detection unit array at the uppermost layer, face an X-ray emission source/an X-ray generator, have a distance from the X-ray detector greater than that of the first layer of detection unit arrays, and are formed by materials with a second atomic number; wherein the first atomic number is less than the second atomic number. That is, in the set direction, the second-layer detecting unit array at the lower layer has a larger atomic number than the material used for the first-layer detecting unit array at the upper layer. The set direction is understood here to be the direction along which the primary X-ray beam is incident, i.e. the direction in which the X-ray generator is directed towards the detector or the direction in which the X-ray generator is directed towards the patient bed. When the first layer detecting unit array is different from the second layer detecting unit array, the probability of the interaction of the X-ray and the first layer detecting unit is different from the probability of the interaction of the X-ray and the second layer detecting unit array, wherein the interaction can be, for example, photoelectric effect, compton scattering, coherent scattering and the like, the larger the atomic number is, the larger the specific gravity of the probability of occurrence of the photoelectric effect is, the lower the specific gravity of the probability of occurrence of compton scattering is, and the atomic number of the second layer detecting unit is larger than the thick sub-number of the first layer detecting unit, so that the X-ray is mainly compton scattering on the first layer detecting unit array and the photoelectric effect is mainly generated on the second layer detecting unit array.
Further, the first layer of the detecting unit array has a first thickness, the second layer of the detecting unit array has a second thickness, when the second layer of the detecting unit array is positioned at the lower layer, the second thickness is larger than the first thickness, the larger the thickness is, the higher the probability of generating the photoelectric effect is, and the lower the probability of generating the Compton scattering is, so that X-rays are mainly generated on the first layer of the detecting unit array and mainly generated on the second layer of the detecting unit array by designing the thickness of the second layer of the detecting unit array to be larger than the thickness of the first layer of the detecting unit array.
That is, the magnitude relation of the atomic numbers and thicknesses of the second-layer detecting unit array and the first-layer detecting unit array includes the following three cases:
(1) The first thickness is equal to the second thickness, the second thick sub-number being greater than the first atomic number;
(2) The first atomic number is equal to the second atomic number, the second thickness being greater than the first thickness;
(3) The second thickness is greater than the first thickness, and the second atomic number is greater than the first atomic number.
However, since the thickness of the detection unit itself is not too large, the X-ray detector provided in this embodiment preferably uses the above-described (1) or (3) th scheme for the first-layer detection unit array and the second-layer detection unit array.
In this embodiment, in order to provide the detector with position resolution, a plurality of detection units are distributed in a two-dimensional array to constitute one detection unit array per layer, and as shown in fig. 3, a plurality of detection units are sequentially distributed in the X-direction and the Z-direction to constitute the detection unit array. In addition, in this embodiment, the interval between two adjacent detecting units may be 0, but in order to improve the position resolution of the X-ray, it is preferable that the interval between the detecting unit arrays of different layers be properly adjusted so that the adjacent detecting unit arrays of two layers are spaced apart from each other, as shown in fig. 4, in the Y direction, a certain distance is provided between the adjacent detecting unit arrays.
In the actual scanning process, X-rays are emitted from the focal position of the bulb tube, and photoelectric effect and scattering occur at a certain probability when the X-rays pass through a scanned object. The X-photons having the photoelectric effect are absorbed and the termination position is changed, and the scattered X-photons damage a certain energy and deflect at a certain angle. If the direction of travel of the X-ray is unchanged during the whole detection process before entering the detector surface position, such X-ray is called primary ray; conversely, a change in direction is referred to as a scattered ray. The scattered X photons after deflection change the travelling direction and then enter the detection units at other positions, and interference signals are generated.
The X-ray detector provided in this embodiment may record the position information (if a reaction occurs) of the X-ray photon in each layer, and in this regard, as shown in fig. 5, the embodiment further provides an energy spectrum detection method, which includes the following steps:
s11, determining the main ray of the incident X-ray according to the position relation between the track of the X-ray detected by each layer of detection unit array and the X-ray emission source;
s12, calculating the total energy of X photons which are detected by each layer of the detection unit array and are primary rays, so as to obtain projection data.
S13, reconstructing a spectrum image of the detection object according to the projection data.
In step S11, the principal ray of the incident X-ray may be determined as follows: judging whether the distance between the extension line of the detected X-ray track and the X-ray emission source is within a preset range or not in the plane where the X-ray emission source is located (namely, the virtual focus of the X-ray track extension line), and if so, determining the X-ray as a main ray.
In other embodiments, the principal ray of the incident X-ray photon may also be determined as follows: and judging whether an included angle between an extension line of the detected X-ray track and the normal incidence direction of the X-ray emission source is within a preset range, and if so, determining the X-ray as a main ray.
In yet another embodiment, an embodiment of the present application further provides a multi-energy spectrum detection method, including:
firstly, scanning a detection object through X-rays of a plurality of energy spectrums in respective set ranges;
secondly, determining the main ray of the X-ray of each energy spectrum according to the position relation between the track of the X-photon detected by each layer of detection unit array and the X-ray emission source;
thirdly, calculating the total energy of the main rays of the X-rays of each energy spectrum detected by each layer of the detection unit array, and determining multi-energy spectrum projection data; the method comprises the steps of,
and obtaining the detection object image under each energy spectrum according to the multi-energy spectrum projection data.
Optionally, separation/differentiation of the materials contained in the detection object can be further realized based on the detection object image.
In order to distinguish the primary ray and the scattered ray as accurately as possible, in this embodiment, preferably, the X-ray detector includes more than two layers of the first layer of detecting unit arrays having the first atomic number and the first thickness, and at least two layers of the first layer of detecting unit arrays are sequentially arranged along a set direction and are all located at an upper portion of the second layer of detecting unit arrays. That is, the X-ray detector provided in this embodiment includes at least two layers of detection unit arrays mainly generating compton scattering, and are all located above the detection unit arrays mainly generating photoelectric effect. In this way, the photoelectrons can be compton scattered on more than two layers of the detection unit arrays, so that the aim of distinguishing all scattered rays as far as possible is fulfilled.
Fig. 3 shows an X-ray detector as an example of the present embodiment, including: layer1, layer2 and layer3, layer1, layer2 and layer3 are arranged at intervals; layer1, layer2 selects a low atomic number detector material to reduce the reaction cross section of the photoelectric effect, and the material may include one of silicon (Si) or gallium arsenide (GaAs), but other low atomic number detector materials may also be selected, which is not limited in this application; the layer3 selects the solid and thickness of the detector with larger atomic number to improve the reaction section of the photoelectric effect, and the material can comprise at least one of cadmium antimonide (CdTe), zinc antimonide (ZnTe) and cadmium antimonide (CdZnTe), but other detector materials with high atomic number can also be selected, and the application is not limited to the method; in an ideal situation, the incident photoelectrons scatter (compton scattering) on Layer1, layer2 and the photoelectric effect on Layer3, so that all the remaining energy is absorbed by Layer 3.
Fig. 6 is a schematic diagram showing an X-ray track detection effect of the X-ray detector according to the example of the present embodiment. Wherein 1, 2 … k+2 represent different detector units, d1 represents the interval between layer1 and layer2, d2 represents the interval between layer2 and layer3, the included angle between the track extension line and the vertical incidence direction of the X-ray emission source is theta, the distance between the virtual focus of the extension line of the track extension line of the X-ray and the X-ray emission source is d, and when theta or d is within the preset range, the corresponding ray is judged to be the main ray.
In this embodiment, the solid line in fig. 6 represents the trajectory of an X-ray photon, and a photon emitted from the X-ray tube focal point and detected by the detector unit k of layer1 is determined as primary ray data; photons emitted from the focal spot of the X-ray tube and detected by the detector unit k of layer3 are also determined as primary ray data. During a certain scanning period, X-rays emitted from the focus of the X-ray tube pass through the surface of a detection object (die body), scatter on the die body, and are detected by the detector units k+1 of the layer1 layer and the detector unit k-1 of the layer3 layer. And connecting the two detector units in the scanning period to obtain the motion trail of the X-rays. In this embodiment, the position detected by the detector unit k+1 of layer1 is used as a first coordinate, and the position detected by the detector unit k-1 of layer3 is used as a second coordinate, so that the extension line of the track of the X-ray photon can be determined by linear fitting. The intersection point of the extended line of the X-ray track and the horizontal plane where the X-ray tube is positioned is the virtual focus. In the embodiment of the application, the virtual focus and the focus of the X-ray tube are larger than the set range, and the judgment result is that the X-rays are detected to be non-primary rays by the detector unit k+1 of the layer1 layer and the detector unit k-1 of the layer3 layer.
Furthermore, in the X-ray detector provided in this embodiment, the first thickness and/or the second thickness may be both adjustable, for example, each detector unit in each layer of the detection unit array adopts a multi-layer splicing structure, and the multi-layers are detachably connected by adhesion or the like, so that when the thickness needs to be increased, the number of layers is increased, and when the thickness needs to be reduced, the number of layers may be reduced.
Accordingly, the spectrum detection method provided in this embodiment may further include, in addition to the step S11 and the step S12, the steps of: based on the detected spectrum conditions, at least one of the following adjustments is performed:
adjusting the first thickness and/or the second thickness;
adjusting the number of layers of the array of detection cells having the second atomic number and the second thickness.
That is, the thickness and the layer number of the detection unit array can be adjusted for multiple times, so that the scattered rays can be distinguished before entering the last layer, and the last layer can absorb all the residual energy, thereby ensuring the image presentation effect.
In addition, the present embodiment also provides an X-ray imaging apparatus including:
an X-ray generator for generating X-rays;
the detector is arranged opposite to the X-ray generator and comprises a plurality of layers of detection unit arrays, wherein the plurality of layers of detection unit arrays comprise a first layer of detection unit arrays and a second layer of detection unit arrays;
the distance between the first layer of detection unit array and the X-ray generator is smaller than that between the second layer of detection unit array and the X-ray generator;
the energy of the X-rays which can be deposited on the first layer detection unit array is different from the energy of the X-rays which can be deposited on the second layer detection unit array; or the probability of the interaction of the X-ray with the first layer detection unit array is smaller than the probability of the interaction of the X-ray with the second layer detection unit array.
The first layer of detection unit arrays and the second layer of detection unit arrays are further stacked along a set direction, and the set direction is the direction in which the X-ray generator points to the detector. Illustratively, the X-ray generator and the detector are disposed opposite one another within a housing that defines a circumferential detection chamber extending in an axial direction. In this embodiment, the axial direction corresponds to the Z direction in fig. 3, the X direction is the left-right direction or the circumferential direction of the detection cavity, the Y direction is the radial direction of the detection cavity, the X direction, the Y direction and the Z direction are perpendicular to each other, the first layer of detection unit arrays and the second layer of detection unit arrays extend in the plane determined by the X direction and the Z direction, and the first layer of detection unit arrays and the second layer of detection unit arrays are stacked up and down along the Y direction. Thus, the first layer of detection unit array is closer to the center of the detection cavity, and the distance between the second layer of detection unit array and the center of the detection cavity is greater than the distance between the first layer of detection unit array and the center of the detection cavity.
In summary, the X-ray detector, the detection method and the X-ray imaging apparatus provided by the present invention include at least a plurality of layers of detection unit arrays, and the plurality of layers of detection unit arrays are arranged side by side along a set direction; the plurality of layers of detection unit arrays comprise a first layer of detection unit arrays and a second layer of detection unit arrays; the first layer of detection unit arrays have a first reaction cross section for X-rays, and the second layer of detection unit arrays have a second reaction cross section for X-rays, the first reaction cross section being greater than or less than the second reaction cross section. Thus, X photons can mainly undergo Compton scattering on the detection unit arrays relatively close to the X-ray emission source, and photoelectric effect can mainly occur on the detection unit arrays relatively far away from the X-ray emission source, so that all residual energy of the X photons can be detected as far as possible, and the main ray of the incident X photons can be determined according to the position relation between the track of the X photons detected by each layer of detection unit arrays and the X-ray emission source; and calculating the total energy of the X photons which are detected by each layer of the detection unit array and are primary rays, and finishing energy spectrum detection.
It should also be appreciated that while the present invention has been disclosed in the context of a preferred embodiment, the above embodiments are not intended to limit the invention. Many possible variations and modifications of the disclosed technology can be made by anyone skilled in the art without departing from the scope of the technology, or the technology can be modified to be equivalent. Therefore, any simple modification, equivalent variation and modification of the above embodiments according to the technical substance of the present invention still fall within the scope of the technical solution of the present invention.

Claims (10)

1. An X-ray detector is characterized by comprising a plurality of layers of detection unit arrays, wherein the plurality of layers of detection unit arrays are arranged side by side along a set direction;
the plurality of layers of detection unit arrays comprise a first layer of detection unit arrays and a second layer of detection unit arrays;
the first layer of detection unit arrays have a first reaction cross section for X-rays, and the second layer of detection unit arrays have a second reaction cross section for X-rays, the first reaction cross section being greater than or less than the second reaction cross section.
2. The X-ray detector of claim 1, wherein the detector comprises a plurality of detectors,
the first layer of detection unit arrays are the detection unit arrays at the uppermost layer along the set direction, and the material forming the first layer of detection unit arrays has a first atomic number;
the second layer of detection unit arrays are positioned at the lower part of the detection unit array at the uppermost layer, and the material forming the second layer of detection unit arrays has a second atomic number;
wherein the first atomic number is less than the second atomic number.
3. The X-ray detector of claim 2, wherein the first layer of detector cell arrays has a first thickness and the second layer of detector cell arrays has a second thickness.
4. The X-ray detector according to claim 2, wherein the X-ray detector comprises at least two layers of the first-layer detecting unit arrays, and the at least two layers of the first-layer detecting unit arrays are sequentially arranged along a set direction and are all located at an upper portion of the second-layer detecting unit array.
5. The X-ray detector of claim 1, wherein two adjacent layers of said arrays of detector elements are spaced apart.
6. The X-ray detector of claim 1, wherein the material of the second layer of detector cell arrays comprises at least one of cadmium antimonide, zinc antimonide, and cadmium zinc antimonide, and the material of the first layer of detector cell arrays comprises at least one of silicon and gallium arsenide.
7. A method of spectral detection using an X-ray detector according to any one of claims 1 to 6, comprising:
determining the main ray of the incident X-photon according to the position relationship between the track of the X-photon detected by each layer of detection unit array and the X-ray emission source;
calculating total energy of the incident X-ray main rays detected by each layer of the detection unit array to obtain projection data;
reconstructing a spectrum image of the detection object according to the projection data.
8. The method of spectrum sensing of claim 7 wherein determining the principal ray of the incident X-ray based on the positional relationship of the track of the X-ray detected by each layer of the array of sensing elements with the X-ray source comprises:
judging whether the extension line of the detected X-ray track is in the plane of the X-ray emission source and the distance between the extension line and the X-ray emission source is in a preset range, if so, determining the extension line as a main ray.
9. An X-ray imaging apparatus, comprising:
an X-ray generator for generating X-rays;
the detector is arranged opposite to the X-ray generator and comprises a plurality of layers of detection unit arrays, wherein the plurality of layers of detection unit arrays comprise a first layer of detection unit arrays and a second layer of detection unit arrays;
the distance between the first layer of detection unit array and the X-ray generator is smaller than that between the second layer of detection unit array and the X-ray generator;
the energy of the X-rays which can be deposited on the first layer detection unit array is different from the energy of the X-rays which can be deposited on the second layer detection unit array; or the probability of the interaction of the X-ray with the first layer detection unit array is smaller than the probability of the interaction of the X-ray with the second layer detection unit array.
10. The X-ray imaging apparatus according to claim 9, wherein the first-layer detection unit array and the second-layer detection unit array are stacked in a set direction, the set direction being a direction in which the X-ray generator is directed toward the detector.
CN202111539753.6A 2021-12-15 2021-12-15 X-ray detector, detection method and X-ray imaging device Pending CN116262047A (en)

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