CN111227857A - Detector module, detector and CT equipment - Google Patents
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Abstract
The application discloses detector module, detector and CT equipment. The detector module is used for detecting rays emitted by an X-ray source of a CT host computer after being attenuated by a scanned object and comprises a support and a plurality of detector sub-modules arranged on the support. Each detector sub-module includes a top surface to receive radiation, and the top surfaces of the plurality of detector sub-modules are arranged along a Z-direction arc or a straight line of the CT rotation system. The top surfaces of the detector sub-modules form a receiving field corresponding to the irradiation field of the X-ray source in a YZ plane of the CT rotating system, the receiving field is asymmetric relative to a focus reference plane of the X-ray source, the focus reference plane passes through the focus center of the X-ray source and is parallel to an XY plane of the CT rotating system. The detector module can reduce the performance parameter requirement of an X-ray source and the manufacturing cost and difficulty of a CT device with large Z-direction coverage (such as 512 layers).
Description
Technical Field
The present application relates to the field of computed tomography, and more particularly, to a detector module, a detector and a CT apparatus.
Background
With the development of CT (Computed Tomography), a coverage area of a single scanning human body is required to be larger, and accordingly, the number of layers of detectors is larger, and an irradiation field of an X-ray source serving as a detector signal source is also required to be larger while more detector sub-modules are required to be mounted on a housing.
Disclosure of Invention
To overcome some or all of the problems of the related art, the present application provides a detector module. The detector module is used for detecting rays emitted by an X-ray source of a CT host computer after being attenuated by a scanned object and comprises a support and a plurality of detector sub-modules mounted on the support, wherein each detector sub-module comprises a top surface for receiving the rays, and the top surfaces of the plurality of detector sub-modules are arranged along the Z-direction arc or straight line of a CT rotating system of the CT host computer; the top surfaces of the detector sub-modules form a receiving field corresponding to the irradiation field of the X-ray source in a YZ plane of the CT rotating system, the receiving field is asymmetric relative to a focus reference plane of the X-ray source, the focus reference plane passes through the focus center of the X-ray source and is parallel to an XY plane of the CT rotating system.
Optionally, the top surfaces of all the detector sub-modules are distributed on the arcs of the same target circle with the center of the focus of the X-ray source as the center, or the top surfaces of a plurality of the detector sub-modules are distributed on the arcs of target circles with unequal radii with the center of the focus of the X-ray source as the center.
Optionally, the radius of the target circle tangent to the top surfaces of the detector sub-modules close to both sides of the focus reference plane is Rc, the radius of the target circle tangent to the top surfaces of the detector sub-modules away from the focus reference plane is Rf, Rc < Rf.
Optionally, the sum of the widths of the top surfaces of the detector sub-modules on one side of the focus reference plane in the Z-direction is greater than the sum of the widths of the top surfaces of the detector sub-modules on the other side of the focus reference plane in the Z-direction so that the receive field is asymmetric with respect to the focus reference plane.
Optionally, the X-ray source comprises a target disk, the receiving field close to the target disk being smaller than the receiving field far from the target disk.
Optionally, top surfaces of the plurality of detector sub-modules are equal or unequal in width in the Z-direction.
Optionally, the width of the top surface of the detector sub-module close to the focus reference plane in the X-direction is larger than the width of the top surface of the detector sub-module far from the focus reference plane in the X-direction so that the width of the top surface in the X-direction shows a decreasing trend from the focus reference plane in the Z-direction away from the focus reference plane.
Optionally, the width of the top surface of the detector sub-module close to the focus reference plane in the X direction is larger than the width of the top surface of the detector sub-module far from the focus reference plane in the X direction further includes: the top surfaces of the detector sub-modules which are equidistant from the focus reference plane have the same width in the X direction, or the top surfaces of the detector sub-modules which are within a preset range from the focus reference plane by the preset distance have the same width in the X direction; alternatively, the plurality of detector sub-modules within the predetermined range outside the predetermined distance from the focus reference plane are cuboids, and the top surface of each detector sub-module within the second predetermined range has an equal width in the X-direction, an equal width in the Z-direction, and an equal height in the Y-direction.
Optionally, the top surface of at least one of the plurality of detector sub-modules is trapezoidal in shape.
Optionally, the trapezoid is an isosceles trapezoid.
Optionally, each of the detector sub-modules comprises an array of scintillator pixels, each scintillator pixel of the array comprising a top surface to receive the ray; the scintillator pixel array of the detector sub-module having a top surface shaped as a trapezoid includes edge scintillator pixels along the Z-direction and on both sides of the array, the top surface of each edge scintillator pixel being shaped as a trapezoid.
Optionally, the top surfaces of all scintillator pixels of the scintillator pixel array are trapezoidal; alternatively, the scintillator pixel array includes intermediate scintillator pixels located between edge scintillator pixels, the top surfaces of the edge scintillator pixels being trapezoidal, the top surfaces of the intermediate scintillator pixels being rectangular.
Optionally, each of the detector sub-modules includes a bottom surface opposite the top surface and sides connected to the top and bottom surfaces, the sides being perpendicular to an XZ plane of the CT rotation system.
The application also discloses a detector, which comprises a shell and a plurality of any one of the detector modules, wherein the plurality of the detector modules are arranged on the shell in parallel along the X direction of the CT rotating system.
The present application further discloses a CT apparatus comprising a gantry, an X-ray source, and a detector of any of the foregoing, wherein the gantry comprises an opening for receiving a scanned object; the X-ray source is used for emitting rays to the scanning object; the detector is disposed on an opposite side of the opening from the X-ray source for receiving radiation attenuated by the scanned object and converting the radiation into an electrical signal.
The technical scheme provided by the embodiment of the application at least has the following beneficial effects:
1. because the top surfaces of the detector sub-modules form a receiving domain corresponding to the irradiation domain of the X-ray source in the YZ plane of the CT rotating system, the receiving domain is asymmetric relative to the focus reference plane of the X-ray source, so that the radiation of the X-ray source can be fully utilized according to the irradiation characteristics of the X-ray source, and the requirements on the performance parameters of the X-ray source (such as a bulb tube emitting X-rays) and the manufacturing difficulty and cost of a CT device with a large Z-direction coverage range (such as 512 layers) are reduced.
2. The top surface of the detector sub-module forms a receiving field, and in a state that the Z direction is asymmetric relative to the focus reference plane, the X-direction gap between adjacent modules at different positions in the Z direction is more uneven and has larger deviation than in a state that the modules are symmetric in the Z direction. The top surfaces of the detector sub-modules are distributed on the circular arcs of target circles with the focus center of the X-ray source as the center and unequal radiuses, so that X-direction gaps of adjacent detector modules at different positions in the Z direction are equal or deviation values are as small as possible, the cost of the X-ray source is reduced, image quality is guaranteed or even optimized, in addition, when electric signals generated by the detector modules are processed at the later stage, data are corrected easily, and data processing can be simplified.
3. Since the radius of the target circle tangent to the top surfaces of the detector sub-modules close to both sides of the focus reference plane is Rc and the radius of the target circle tangent to the top surfaces of the detector sub-modules far from the focus reference plane is Rf, Rc < Rf, the advantages are: the X-direction gaps of the adjacent detector modules at different positions in the Z direction are equal or have deviation values as small as possible, and when the electric signals generated by the detector modules are processed in the later period, the data are corrected more easily, and the data processing can be simplified.
4. Because the width of the top surface of the detector sub-module close to the focus reference surface in the X direction is larger than that of the top surface of the detector sub-module far away from the focus reference surface in the X direction, the width of the top surface in the X direction is reduced from the focus reference surface along the Z direction, so that the X direction gaps of adjacent detector modules at different positions in the Z direction are equal or have the deviation value as small as possible, the physical area of the acquired image of the CT detector is increased, and the data processing is simplified; furthermore, the performance parameter requirements of the X-ray source (such as a bulb tube emitting X-rays) and the manufacturing difficulty and cost of the CT device with large Z-direction coverage (such as 512 layers) can be reduced.
5. Since the plurality of detector sub-modules within a second predetermined range apart from the focus reference plane by a second predetermined distance are rectangular parallelepipeds, the top surface of each detector sub-module within the second predetermined range has the same width in the X-direction, the same width in the Z-direction, and the same height in the Y-direction, the variety of detector sub-modules is reduced, and cost optimization is achieved.
6. Since the top surfaces of the edge scintillator pixels in the detector sub-module having the trapezoidal shape are trapezoidal, the X-ray receiving area can be maximally utilized, and the image quality can be finally improved. In the case where the top surfaces of the edge scintillator pixels are trapezoidal in shape and the top surfaces of the intermediate scintillator pixels are rectangular, the X-ray receiving area can be more maximally utilized, eventually improving the image quality. In the case where the top surfaces of all scintillator pixels are trapezoidal, the X-ray receiving area can be maximally utilized, eventually improving the image quality.
7. When designing and manufacturing a detector with a large coverage in the Z direction, in a state where a receiving area formed by the top surface of the detector sub-module is asymmetric in the Z direction, an X-direction gap between adjacent modules at different positions in the Z direction is more uneven and has a larger deviation than in a state where the modules are symmetric in the Z direction. The trapezoidal shape of the top surface of the at least one detector sub-module solves this problem and ensures or even optimizes image quality while reducing the cost of the X-ray source.
It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory only and are not restrictive of the application.
Drawings
The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate embodiments consistent with the present application and together with the description, serve to explain the principles of the application.
FIG. 1 is a schematic diagram of the state of X-rays emitted by a bulb;
FIG. 2 is a schematic diagram of a CT apparatus;
FIG. 3 is a schematic illustration of a receiving field corresponding to an illumination field formed by a detector module of the present application;
FIG. 4 is a schematic diagram of a detector constructed from the detector modules of the present application;
FIG. 5 is a schematic diagram of a first detector module configuration;
FIG. 6 is a projection view of the detector module shown in FIG. 5 in the YZ plane of the CT rotational system;
FIG. 7 is a schematic diagram of a second detector module configuration;
FIG. 8 is a projection view of the detector module shown in FIG. 7 in the YZ plane of the CT rotational system;
FIG. 9 is a projection of a third detector module in the XZ plane of the CT rotational system;
FIG. 10 is a projection of a fourth detector module in the XZ plane of the CT rotational system;
FIG. 11 is a projection of a fifth detector module in the XZ plane of a CT rotational system;
FIG. 12 is a projection of a sixth detector module in the XZ plane of a CT rotational system;
FIG. 13 is a schematic diagram of a scintillator pixel array of a trapezoidal detector sub-module;
FIG. 14 is a schematic diagram of a scintillator pixel array of another trapezoidal detector sub-module;
FIG. 15 is a schematic diagram of another asymmetric distribution of the receiving domains of a detector module;
fig. 16 is a projection view of a seventh detector module in the YZ plane.
Detailed Description
Reference will now be made in detail to the exemplary embodiments, examples of which are illustrated in the accompanying drawings. When the following description refers to the accompanying drawings, like numbers in different drawings represent the same or similar elements unless otherwise indicated. The embodiments described in the following exemplary embodiments do not represent all embodiments consistent with the present application. Rather, they are merely examples of apparatus and methods consistent with certain aspects of the present application, as detailed in the appended claims.
The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the application. As used in this application and the appended claims, the singular forms "a", "an", and "the" are intended to include the plural forms as well, unless the context clearly indicates otherwise.
It should be understood that the terms "first," "second," and the like as used in the description and in the claims, do not denote any order, quantity, or importance, but rather are used to distinguish one element from another. Similarly, the use of the terms "a" or "an" and the like do not denote a limitation of quantity, but rather denote the presence of at least one; "plurality" means two or more than two. Unless otherwise indicated, "front", "rear", "lower" and/or "upper" and the like are for convenience of description and are not limited to one position or one spatial orientation. The word "comprising" or "comprises", and the like, means that the element or item listed as preceding "comprising" or "includes" covers the element or item listed as following "comprising" or "includes" and its equivalents, and does not exclude other elements or items.
Exemplary embodiments of the present application will be described in detail below with reference to the accompanying drawings. In the following embodiments, features of the embodiments can be supplemented with each other or combined with each other without conflict.
Referring to fig. 1, an X-ray tube (alternatively referred to as a tube) includes a target disk 1 having a focal point F with a focal center, e.g., the focal center is the geometric center of a square focal point when the focal point F is square. In order to solve the problems that the manufacturing difficulty and the cost of the Z-direction large coverage CT device are high due to the X-ray tube with a larger target angle, the inventor of the present application finds that: the X-ray irradiation field that can be used by the detector of the existing CT apparatus is symmetrical with respect to the focus reference plane L of the X-ray tube, as shown by the fan angle a and the fan angle B in fig. 1, in order to obtain a larger irradiation field (i.e. make the fan angle a and the fan angle B larger), the X-ray tube with a larger target angle needs to be used, thus making the CT apparatus difficult to manufacture and expensive. To solve this problem and satisfy the requirement of large irradiation field, the inventors thought: if the C area can be used, the irradiation area can be increased, accordingly, the requirement on the performance parameters of the X-ray tube is reduced (for example, the target angle of the X-ray tube does not need to be too large), and further, the manufacturing difficulty and the cost of the CT device with the large Z-direction coverage range are reduced. Accordingly, the inventors of the present application have developed a detector module, a detector, and a CT apparatus. In order to facilitate a clearer understanding of the present application, the relevant contents of the CT apparatus will be described as follows:
referring to fig. 2, the CT device shown in fig. 2 is a medical device, however, the skilled person will understand that the CT device may be a device for security inspection (e.g. a security inspection machine). Since these apparatuses include a detector, the constitution will be described only by way of example of a CT machine for medical treatment as follows: the medical apparatus comprises a gantry 10, an X-ray source 20, a detector 30 and a carrier 40. The gantry 10 is formed with an opening 11 for receiving the scan object 50. The illustrated coordinate system is the coordinate system of the rotatable CT rotation system relative to the gantry 10. The CT rotational system includes at least the X-ray source 20 and the detector 30. As shown, the coordinate system includes mutually perpendicular X, Y and Z axes, and accordingly, in the following description, the Z direction is a direction along the Z axis, and the X direction is a direction along the X axis. The Z-axis is the rotation axis of the CT rotation system, and is parallel to the coronal plane of the scanned object 50 (patient in the medical field), defining the slice direction of the CT apparatus. The X-axis and the Y-axis define a plane perpendicular to the Z-axis, the X-axis being generally along the channel direction of the detector 30. The X-ray source 20 and the detector 30 rotate circumferentially about the Z-axis as a group.
The scan object 50 is placed on the stage 40, and may be located within the opening 11 together with the stage 40. In the field of security inspection, the scanning object is baggage or a human body, which may be transported by a transportation device to pass through the opening 11. The X-ray source 20 and the detector 30 are arranged on opposite sides of the opening 11. The X-ray source 20 is used to emit a fan-shaped or cone-shaped beam of radiation toward the scanned object 50. The X-ray source 20 projects an X-ray beam from its focal point F to the scan object 50.
Referring to fig. 4 to 12, the detector 30 of the present application for detecting the attenuated radiation emitted from the X-ray source 20 of the CT main machine by the scanned object 50 includes a plurality of detector modules 3 (one detector module 3 is shown in the dashed line box of fig. 4) and a housing 302. A plurality of detector modules 3 are arranged side by side on the housing 302 in the X direction of the CT rotating system.
Referring to fig. 3, 5 to 8 in combination with fig. 4, each detector module 3 includes a support 301 and a plurality of detector sub-modules 31a1 to 31a8 mounted to the support 301. Although 8 detector sub-modules are illustrated, the number of detector sub-modules is not limited thereto. Each detector sub-module 31a 1-31 a8 includes a top surface 311 for receiving radiation, and as shown in fig. 5-8, the top surfaces 311 of the plurality of detector sub-modules 31a 1-31 a8 are arranged in an arc along the Z-direction of the coordinate system of the CT rotating system (hereinafter simply referred to as the CT rotating system), and in various embodiments of the present application, the arc arrangement is that the top surfaces of the detector sub-modules are tangent to the arc of the target circle centered at the center of the focal point. The skilled person will appreciate that in other embodiments the top surface 311 may also be arranged linearly along the Z-direction. In the embodiments of the present application, the alignment means that the top surfaces of the detector sub-modules are coplanar or that the top surfaces of the detector sub-modules on the support are respectively located on several different planes, which are parallel to each other and which are stepped when viewed from the side of the planes. The top surfaces 311 of a plurality of said detector sub-modules 31a 1-31 a8 form a receiving field 32 corresponding to the irradiation field of said X-ray source in the YZ-plane of the CT rotation system, which receiving field 32 is asymmetrical with respect to the focal reference plane L of said X-ray source 20 (which can also be considered as target disc 1). As shown in fig. 3, the receiving field 32 includes a left receiving field 321 and a right receiving field 322 with reference to the focus reference plane L, and the left receiving field 321 and the right receiving field 322 are asymmetric with respect to the focus reference plane L. The receiving field 322 close to the target disk 1 is smaller than the receiving field 321 remote from the target disk 1. By arranging the receiving domain 32 asymmetrically relative to the focus reference plane L (the focus reference plane L passes through the focus center of the X-ray source and is parallel to the XY plane of the CT rotating system), the distribution of the top surface of the detector sub-module better conforms to the irradiation characteristics of the X-ray source, the X-ray of the C region is fully utilized, the X-ray source with a large target angle can be omitted, and the requirements on the performance parameters of the X-ray source and the manufacturing difficulty and cost of the Z-direction large coverage (such as 512 layers) CT device are reduced.
With continued reference to fig. 5 and 6, in one embodiment, top surfaces 311 of all detector sub-modules 31a 1-31 a8 are distributed over an arc of the same target circle centered on a focal center of a focal spot F of the X-ray source. While fig. 5 and 6 illustrate 8 detector sub-modules 31a 1-31 a8, skilled artisans will appreciate that the specific number of detector sub-modules is not limited thereto, depending on the number of detector layers in any embodiment. As shown in fig. 5 and 6, the top surface 311 of each of the detector sub-modules 31a 1-31 a8 has an equal width in the Z-direction, such that the number of detector sub-modules on the left side (5, 31a1, 31a2, 31a3, 31a4, and 31a5, respectively) is greater than the number of detector sub-modules on the right side (3, 31a6, 31a7, 31a8, respectively) at the focus reference plane L. In fig. 6, the focus reference plane L is extended towards the detector sub-module in order to illustrate the asymmetry specifically. By such a design, the sum of the widths of the detector sub-modules on one side of the focus reference plane L in the Z direction is larger than the sum of the widths of the detector sub-modules on the other side of the focus reference plane L in the Z direction, so that the receiving field is asymmetrical with respect to the focus reference plane L of the X-ray source.
Referring to fig. 7 and 8, in one embodiment, top surfaces 311 of a plurality of detector sub-modules 31a 1-31 a8 are distributed on arcs of a target circle of unequal radius centered at a focal point F of X-ray source 20. Fig. 7 and 8 illustrate two radii R1 and R2, the top surface 311 of the first through third detector sub-modules 31a1 through 31a3 and the top surfaces of the seventh and eighth detector sub-modules 31a7 and 31a8 are distributed on and tangent to a target circle of radius R2, and the top surfaces 311 of the fourth through sixth detector sub-modules 31a4 through 31a6 are distributed on and tangent to a target circle of radius R1, where R1< R2. In fig. 8, the top surfaces of the detector sub-modules are of equal width in the Z-direction, and the number of detector sub-modules on the left side of the focus reference plane L is greater than the number of detector sub-modules on the right side (the left side comprises at least 4 detector sub-modules 31a1 to 31a4, and the right side comprises at least 3 detector sub-modules 31a6 to 31a8), so that the sum of the widths of the detector sub-modules on one side of the focus reference plane L in the Z-direction is greater than the sum of the widths of the detector sub-modules on the other side of the focus reference plane L in the Z-direction to make the receiving field asymmetric with respect to the focus reference plane.
When designing and manufacturing a detector with a large coverage in the Z-direction, the top surface of the detector module has a more uneven X-direction gap between adjacent modules at different positions in the Z-direction in a state of Z-direction asymmetry than in a state of Z-direction symmetry, and the X-direction gap has a larger deviation. The top surfaces of the detector sub-modules are distributed on the circular arcs of target circles with the focus center of the X-ray source as the center and unequal radiuses, so that X-direction gaps of adjacent detector modules at different positions in the Z direction are equal or deviation values are as small as possible, the cost of the X-ray source is reduced, image quality is guaranteed or even optimized, in addition, when electric signals generated by the detector modules are processed at the later stage, data are corrected easily, and data processing can be simplified.
With continued reference to fig. 7 and 8, in one embodiment, the radius of the target circle tangent to the top surfaces of the detector sub-modules near both sides of the focus reference plane L is Rc, and the radius of the target circle tangent to the top surfaces of the detector sub-modules away from the focus reference plane is Rf, Rc < Rf. In this embodiment, the approaching and separating are relative concepts, and only two kinds of target circles are shown in fig. 8, where Rc ═ R1 and Rf ═ R2. Since fig. 7 and 8 only illustrate two radii, three or more radius values may be provided, which may or may not be completely equal, depending on the actual situation. Three radius values are illustrated below, and others are analogized. In order to illustrate the case of a target circle having three radius values, the following will be described by taking fig. 7 and 8 as an example:
in the direction of the drawing plane of fig. 8, from left to right, the first and second detector submodules 31a1 and 31a2 are compared with the third detector submodule 31a3, the first and second detector submodules 31a1 and 31a2 are detector submodules far from the focus reference plane L, the radius of the tangent target circle is R2, the third detector submodule 31a3 is a detector submodule near the focus reference plane L, and the radii of the tangent target circles are Rc, respectively, and are illustrated by a dashed line in fig. 8 because they are illustrated by fig. 8; compared to the fourth detector submodule 31a4, the third detector submodule 31a3 has the fourth detector submodule 31a4 being a detector submodule close to the focus reference plane L, and the target circle radius tangent to the fourth detector submodule 31a4 being R1, from which Rc < Rf, R1< Rc < R2 can be obtained.
Since Rc < Rf, it is thus ensured that the X-gaps of adjacent detector modules 3 at different positions in the Z-direction are equal or deviate as little as possible, so that a better image quality is obtained.
The inventors of the present application found that: to ensure consistent detector characteristics, the detector sub-modules on the detector modules are typically arranged along an arc in the Z-direction so that the focus-to-detector distance is consistent and the radiation attenuation characteristics are consistent, facilitating subsequent image processing. Since the X-direction and the Z-direction are respectively arranged along circular arcs concentric with the focal point, the top surfaces of the detector sub-modules are arranged on a spherical surface, as can be seen from spherical cutting, if a spherical surface is spliced by the detector sub-modules of square scintillator pixels, the scintillator pixels of each detector sub-module are required to be rectangles with different sizes to ensure that gaps at the spliced part are consistent, the width of the detector sub-modules at least along the Z-direction is smaller and smaller, and if the detector sub-modules are converged on a rotating shaft, the width of the detector sub-modules is theoretically zero. In practice, such ideal detector sub-modules are difficult to manufacture, and for ease of manufacture, identical square or rectangular detector sub-modules are typically used within the same CT system, and the following discussion will typically refer to a rectangle as a representative shape, and a square as a special case of a rectangle, and the principles of which are similar will not be repeated. If rectangular detection sub-modules with the same size are used, in order to ensure that the detector sub-modules positioned at the edges do not interfere with each other, a larger gap appears at the detector sub-module positioned in the middle during splicing, and particularly, as the number of layers of the CT equipment is increased, the number of detector modules spliced in the Z direction is increased, the reserved gap of the detector sub-module positioned in the middle is increased, the X-direction gap of the adjacent detector modules is larger in the whole Z direction, and the acquired data influences the image quality.
In order to solve the above problem, the present application discloses a detector module. Referring to fig. 9 to 12, it should be noted that fig. 9 to 12 are only a technical means for purposely highlighting the design of the top surface 311 of the detector sub-module as a trapezoid, so that the respective figures show the states shown in fig. 9 to 12, and it is understood by the skilled person that the actual size of the detector sub-module and the proportional relationship thereof with other detector sub-modules are not represented. Each detector sub-module comprises a top surface 311 for receiving the radiation emitted by the X-ray source 20, the width of the top surface 311 of the detector sub-module close to the focus reference plane L in the X direction is larger than the width of the top surface 311 of the detector sub-module far from the focus reference plane L in the X direction, so that the width of the top surface of each detector sub-module in the X direction is reduced from the focus reference plane in the Z direction to a direction far from the focus reference plane (such as the edge of the detector sub-module), thus, in combination with the way that the receiving domain is asymmetric relative to the focus reference plane, not only the X-direction gaps of adjacent detector modules at different positions in the Z direction are ensured to be equal or have a deviation value as small as possible, thereby realizing a CT detector with a large coverage (such as 512 layers) in the Z direction, improving the physical area of the acquired image of, the image quality is improved; furthermore, the performance parameter requirements of the X-ray source (such as an X-ray bulb tube) and the manufacturing difficulty and cost of the CT device with large Z-direction coverage (such as 512 layers) can be reduced. For example, in fig. 4, the X direction is a row, the Z direction is a column, and one column is the detector module 3 shown by the dashed box in fig. 4, and the X direction deviation of the adjacent X detector sub-modules is illustrated as follows by taking three rows of the first column and the second column as an example: the deviation in the X direction between the detector submodule in the first column and the first row and the detector submodule in the second column and the first row is denoted as a1, the deviation in the X direction between the detector submodule in the first column and the second row and the detector submodule in the second column and the second row is denoted as a2, and the deviation in the X direction between the detector submodule in the first column and the third row and the detector submodule in the second column and the third row is denoted as A3. The deviation is that the deviations A1, A2 and A3 are relative to the preset value, and the deviation is as small as possible, namely the deviation value is within a certain range from the preset value (the deviation value can be zero if necessary).
The above-described decreasing tendency is described in detail below: in fig. 9 to 12, the focus reference plane L is marked. The width of the top surface 311 of the detector sub-module close to the focus reference plane in the X-direction is larger than the width of the top surface 311 of the detector sub-module far from the focus reference plane in the X-direction so that the width of the top surface 311 in the X-direction is reduced from the focus reference plane in the Z-direction to a direction far from the focus reference plane, including the following two cases:
1. the width in the X-direction of the top surface 311 of the detector sub-module close to the focus reference plane L is larger than the width in the X-direction of the top surface 311 of the detector sub-module far from the focus reference plane L, and the widths in the X-direction of the top surfaces 311 of the detector sub-modules equidistant from the focus reference plane L are equal. For example, in fig. 9, the first to third detector sub-modules 31a1 to 31a3 are gradually close to the focus reference plane L, the top surfaces thereof have respective widths L1< L2< L3, and the top surfaces 311 of the detector sub-modules 31a3 and 31a8 which are equidistant from the focus reference plane L have the same width in the X direction, that is, L3 is equal to L8. Similarly, in fig. 10, the widths L1< L2< L3< L4 of the top surfaces 311 of the first to fourth detector sub-modules 31a1 to 31a4 in the X direction and the widths L4 ═ L7 of the top surfaces of the fourth and seventh detector sub-modules 31a4 and 31a7 in the X direction; in fig. 11, the widths L1< L2< L3< L4 of the top surfaces of the first to fourth detector sub-modules 31a1 to 31a4 in the X direction and the widths L3 ═ L8 of the top surfaces of the third and eighth detector sub-modules 31a3 and 31a8 in the X direction.
2) The widths in the X direction of the top surfaces of the plurality of detector sub-modules within a preset range apart from the focus reference plane by a preset distance may be equal, and the preset distance and the preset range may be determined according to actual conditions, as shown in fig. 11, the preset distance is 0 detector sub-modules, and the preset range is 2 detector sub-modules, and then the widths in the X direction of the top surfaces of the four detector sub-modules 31a4, 31a5, 31a6, 31a7 near the focus reference plane L are equal, and are all L4. For another example, in fig. 12, the preset distance is 1 detector sub-module, and the preset range is two detector sub-modules, then the widths of the top surfaces of the third to fourth detector sub-modules 31a3 and 31a4 and the seventh and eighth detector sub-modules 31a7 and 31a8 in the X direction are equal, that is, L3-L4-L7-L8.
With continuing reference to FIGS. 9-12 in conjunction with FIGS. 5-8, in one embodiment, each of the detector sub-modules includes a bottom surface opposite the top surface 311 and sides connecting the top and bottom surfaces, the top surface of at least one detector sub-module is trapezoidal in shape, and in other embodiments, the sides thereof are perpendicular to the XZ plane of the CT rotation system (which may be understood as a detector sub-module shaped as a straight quadrangular prism with trapezoidal top and bottom surfaces, for ease of description, the detector module with trapezoidal top surface is referred to as a trapezoidal detector sub-module (including detector sub-modules with trapezoidal top surfaces and sides perpendicular to the XZ plane). As shown in FIG. 9, in the Z direction, eight detector sub-modules 31a1, 31a2, 31a3, 31a4, 31a5, 31a6, 31a7 and 31a8 are both trapezoidal detector sub-modules; as shown in FIG. 10, the first detector submodule 31a1 is a trapezoidal detector submodule; as shown in FIG. 11, the first through third detector sub-modules 31a1 through 31a3 and the eighth detector sub-module 31a8 are trapezoidal detector sub-modules. The skilled person will understand that the trapezoid comprises an isosceles trapezoid, a right trapezoid or another trapezoid, preferably an isosceles trapezoid, which facilitates the manufacturing of the detector and the CT apparatus and further minimizes the deviation of the X-direction gap between adjacent detector modules at different positions in the Z-direction, thereby improving the image quality, because when designing and manufacturing a detector with a large Z-direction coverage, the top surface of the detector sub-module forms a receiving field in a Z-direction asymmetric state, and the X-direction gap between adjacent modules at different positions in the Z-direction is more uneven and the deviation is larger than in a Z-direction symmetric state. The trapezoidal design of the top surface of the detector sub-module can solve the problem; moreover, the cost of the X-ray source can be reduced, and the image quality can be ensured and even optimized.
With continued reference to fig. 9-12, in one embodiment, the top surface of at least one of the plurality of detector sub-modules is rectangular in shape (the detector sub-module with a rectangular top surface is referred to as a rectangular detector sub-module). The skilled artisan will appreciate that the gradual decrease in width of the top surface of the detector sub-modules in the X-direction from the focal point reference plane along the Z-direction of the CT rotation system may be achieved by a combination of trapezoidal and rectangular detector sub-modules, as shown in fig. 10-12; or all may be implemented by trapezoidal detector sub-modules, as shown in fig. 9; of course, based on the idea that the second to eighth detector submodules 31a2 to 31a8 in fig. 10 and 12 and the second to seventh detector submodules 31a2 to 32a7 in fig. 11 may be designed as rectangular detector submodules, the width reduction in the X direction may also be realized entirely by rectangular detector submodules.
Since the overall trend of decreasing in the Z direction is to be shown, and the upper base of the trapezoid is parallel to the lower base and in general, the length of the upper base is smaller than that of the lower base, therefore, for the trapezoid detector sub-module, the width of the top surface in the X direction can be considered as one of the lower base or the upper base, and in the embodiment of the present application, for convenience of description, the width of the top surface of the trapezoid detector sub-module in the X direction is expressed by the length of the upper base; and for a rectangular detector sub-module, the width in the X direction is the side length.
Referring to fig. 11 and 12, in one embodiment, the plurality of detector sub-modules within a predetermined range from the focus reference plane by the predetermined distance are shaped as rectangular solids, a cube being a special case of a rectangular solid, the top surface of each detector sub-module within the predetermined range having an equal width in the X-direction, an equal width in the Z-direction, and an equal height in the Y-direction (i.e., the detector sub-modules within the predetermined range having equal lengths, equal widths, and equal heights). For example, in fig. 11, the preset distance is 0 detector sub-modules, the preset range is 2 detector sub-modules, such that the top surfaces of the fourth to seventh detector sub-modules 31a4, 31a5, 31a6 and 31a7 are equal in width in the X direction, equal in width in the Z direction and equal in height in the Y direction, such that the detector sub-modules are equal in length, equal in width and equal in height, and for example, in fig. 12, the preset distance is 1 detector sub-module, the preset range is 2 detector sub-modules, the top surfaces of the third detector sub-module 31a3, the fourth detector sub-module 31a4, the seventh detector sub-module 31a7 and the eighth detector sub-module 31a8 are equal in width in the X direction, equal in width in the Z direction and equal in height in the Y direction, such that the detector sub-modules are equal in length, equal in height, Equal width and equal height. The implementation mode can reduce the types of the sub-modules and achieve the aim of cost optimization.
With continued reference to fig. 9-12, in fig. 9 and 12, the trapezoidal detector sub-module is located at one or both ends of the overall detector module, but it will be understood by those skilled in the art that in some embodiments, the trapezoidal detector sub-module may be located at other positions of the overall detector module as long as the tendency of the top surface of the detector sub-module to decrease in width in the X-direction is achieved.
Please refer to fig. 13 and 14 in conjunction with fig. 5 to 12. In one embodiment, each of the detector sub-modules includes a scintillator pixel array, each scintillator pixel of the scintillator pixel array including a top surface to receive the X-rays, a bottom surface opposite the top surface, and a side connecting the top and bottom surfaces. In one embodiment, the side is perpendicular to the XZ plane of the CT rotational system. The scintillator pixel array of the trapezoidal detector sub-module includes edge scintillator pixels along the Z-direction and on either side of the array, a top surface of each edge scintillator pixel being trapezoidal. In one embodiment, the scintillator pixel array includes edge scintillator pixels 3111b and intermediate scintillator pixels 3111a along the Z-direction and on either side of the array. As shown in fig. 13, the top surfaces of all scintillator pixels (edge scintillator pixel 3111b and middle scintillator pixel 3111a) are trapezoidal. As another example, as shown in fig. 14, the top surface of the edge scintillator pixel 3111b is trapezoidal (the edge scintillator pixel is a straight quadrangular prism whose top and bottom surfaces are trapezoidal), and the top surface of the middle scintillator pixel 3111a is rectangular (it can be understood that the middle scintillator pixel is a rectangular parallelepiped or a cube). In other embodiments, at least the top surfaces of the edge scintillator pixels are tapered in width in the X direction along the Z direction, as shown in fig. 13, all the top surfaces of the edge scintillator pixels 3111b are trapezoidal, and the width in the X direction thereof is tapered in the Z direction; in fig. 14, the top surface of the edge scintillator pixel 3111b is a trapezoid whose width in the X direction gradually decreases in the Z direction. Since the pixels are small, this reduction can be seen in the relationship of D1 and D2 in fig. 15, with the width of D2 being reduced relative to the width of D1 in the X-direction. In other embodiments, as shown in fig. 13, the top surfaces of the intermediate scintillator pixels are equal in width in the X-direction. By designing the top surfaces of the edge scintillator pixels to be trapezoidal, or the top surfaces of all the scintillator pixels to be trapezoidal, or the top surfaces of the middle scintillator pixel 3111a to be rectangular and the top surfaces of the edge scintillator pixels 3111b to be trapezoidal, it is possible to maximize the reception area using the rays.
Although the top surfaces of the detector sub-modules in the embodiments shown in fig. 9 to 12 have equal widths in the Z-direction, the skilled person will also understand that the asymmetric design may also be implemented in the case where the top surfaces 311 of the detector sub-modules have unequal widths in the Z-direction, in which case the length of the receiving field formed by the top surface of the focal reference plane L on one side is greater than the length of the receiving field on the other side by arranging the detector sub-modules in an arc along the Z-direction.
Referring to fig. 15 and 16, the above-mentioned scheme that the receiving field is asymmetric with respect to the focal reference plane of the X-ray source can also be applied to a detector module in which, in the detector module shown in the embodiment shown in fig. 15, the plurality of detector sub-modules include a middle detector sub-module located within a preset distance range of the focal reference plane and an edge detector sub-module located outside the preset distance range, and the focal reference plane passes through the focal center of the X-ray source and is parallel to the XY plane of the CT rotating system; each detector sub-module includes a top surface to receive the rays, the top surfaces of the edge detector sub-modules are arranged along a Z-direction arc of the CT rotation system, and the top surfaces of the middle detector sub-modules are arranged along the Z-direction straight line. As shown in fig. 15, the receiving field 32 includes a left receiving field 321 and a right receiving field 322, the left receiving field 321 and the right receiving field 322 are asymmetric with respect to the focus reference plane L, a part of the receiving field 321 and a part of the receiving field 322 are linear, and the two parts of the receiving field form a linear receiving field 323, the part of the receiving field 323 corresponds to the middle detector sub-module, the top surface of the middle detector sub-module is linear, and the other part of the receiving field corresponds to the edge detector sub-module, and the top surface of the middle detector sub-module is arc-shaped. As shown in FIG. 16, in one embodiment, the top surfaces of the detector sub-modules are of equal width in the Z-direction, two middle detector sub-modules (detector sub-modules 31a6 and 31a7) and one edge detector sub-module 31a8 to the right of the focus reference plane L, and two middle detector sub-modules 31a4 and 31a5 and three edge detector sub-modules 31a1, 31a2 and 31a3 to the left of the focus reference plane L.
The present application further discloses a detector comprising a housing and a plurality of detector modules as described in any of the above, the plurality of detector modules being arranged side by side on the housing in an X-direction of a CT rotation system.
The detector module is not only suitable for imaging equipment which converts X-rays into materials such as GOS (gold germanium sulfide) of visible light particles and obtains images through photoelectric conversion, but also suitable for imaging equipment which directly converts X-rays into materials such as cadmium zinc telluride (CdZnTe, CZT) of electric signals and obtains images through data processing. Based on this, the present application further discloses a CT apparatus comprising a gantry, an X-ray source and any of the aforementioned detectors, wherein the gantry comprises an opening for receiving a scanned object. The X-ray source is used for emitting rays to the scanning object. The detector is disposed on an opposite side of the opening from the X-ray source for receiving radiation attenuated by the scanned object and converting the radiation into an electrical signal.
Although the present application has been described with reference to a preferred embodiment, it should be understood that various changes, substitutions and alterations can be made herein without departing from the spirit and scope of the application, and all changes, substitutions and alterations that fall within the spirit and scope of the application are to be understood as being covered by the following claims.
Claims (15)
1. A detector module for detecting attenuated radiation from an X-ray source of a CT mainframe by an object being scanned, the detector module comprising a support and a plurality of detector sub-modules mounted to the support, wherein,
each detector sub-module comprises a top surface for receiving rays, and the top surfaces of the plurality of detector sub-modules are arranged along an arc or a straight line in the Z direction of a CT rotating system of the CT host;
the top surfaces of the detector sub-modules form a receiving field corresponding to the irradiation field of the X-ray source in a YZ plane of the CT rotating system, the receiving field is asymmetric relative to a focus reference plane of the X-ray source, the focus reference plane passes through the focus center of the X-ray source and is parallel to an XY plane of the CT rotating system.
2. The detector module of claim 1, wherein the top surfaces of all detector sub-modules are distributed on arcs of one and the same target circle centered on the center of focus of the X-ray source, or wherein the top surfaces of a plurality of the detector sub-modules are distributed on arcs of target circles of unequal radii centered on the center of focus of the X-ray source.
3. The detector module of claim 2, wherein a radius of a target circle tangent to the top surfaces of the detector sub-modules near both sides of the focus reference plane is Rc, and a radius of a target circle tangent to the top surfaces of the detector sub-modules away from the focus reference plane is Rf, Rc < Rf.
4. The detector module of claim 1, wherein a sum of widths in the Z-direction of top surfaces of detector sub-modules on one side of the focus reference plane is greater than a sum of widths in the Z-direction of top surfaces of detector sub-modules on the other side of the focus reference plane such that the receive field is asymmetric with respect to the focus reference plane.
5. The detector module according to claim 1 or 4, characterized in that the X-ray source comprises a target disk, the receiving field close to the target disk being smaller than the receiving field remote from the target disk.
6. The detector module of claim 1, wherein top surfaces of the plurality of detector sub-modules are equal or unequal in width in the Z-direction.
7. The detector module of claim 1, wherein a width of a top surface of a detector sub-module proximate to the focus reference plane in the X-direction is greater than a width of a top surface of a detector sub-module distal from the focus reference plane in the X-direction such that the top surface exhibits a decreasing trend in the X-direction width from the focus reference plane in the Z-direction away from the focus reference plane.
8. The detector module of claim 7, wherein the width in the X-direction of the top surface of the detector sub-module proximate to the focus reference plane being greater than the width in the X-direction of the top surface of the detector sub-module distal to the focus reference plane further comprises: the top surfaces of the detector sub-modules, which are equidistant from the focus reference plane, have the same width in the X-direction, or the top surfaces of the plurality of detector sub-modules, which are within a preset range outside a preset distance from the focus reference plane, have the same width in the X-direction; alternatively, a plurality of detector sub-modules within a preset range apart from the focus reference plane by the preset distance are rectangular parallelepipeds, and the top surface of each detector sub-module within the preset range has the same width in the X-direction, the same width in the Z-direction, and the same height in the Y-direction.
9. The detector module of any of claims 7-8, wherein the top surface of at least one of the plurality of detector sub-modules is trapezoidal in shape.
10. The detector module of claim 9, wherein the trapezoid is an isosceles trapezoid.
11. The detector module of claim 9, wherein each of the detector sub-modules comprises an array of scintillator pixels, each scintillator pixel of the array including a top surface that receives the radiation;
the scintillator pixel array of the detector sub-module having a top surface shaped as a trapezoid includes edge scintillator pixels along the Z-direction and on both sides of the array, the top surface of each edge scintillator pixel being shaped as a trapezoid.
12. The detector module of claim 11, wherein the top surfaces of all scintillator pixels of the scintillator pixel array are trapezoidal;
alternatively, the scintillator pixel array includes intermediate scintillator pixels located between edge scintillator pixels, the top surfaces of the edge scintillator pixels being trapezoidal, the top surfaces of the intermediate scintillator pixels being rectangular.
13. The detector module of claim 1, wherein each of the detector sub-modules includes a bottom surface opposite the top surface and sides connected to the top and bottom surfaces, the sides being perpendicular to an XZ plane of the CT rotation system.
14. A detector comprising a housing and a plurality of detector modules according to any one of claims 1 to 13, the plurality of detector modules being juxtaposed on the housing in an X-direction of a CT rotating system.
15. A CT apparatus comprising a gantry, an X-ray source, and a detector according to claim 14, wherein,
the gantry includes an opening for receiving a scan subject;
the X-ray source is used for emitting rays to the scanning object;
the detector is disposed on an opposite side of the opening from the X-ray source for receiving radiation attenuated by the scanned object and converting the radiation into an electrical signal.
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