Medical imaging equipment, combined detector thereof and image data reading method

Abstract

The invention provides medical imaging equipment and a composite detector and an image data reading method thereof, the composite detector comprises a photon counting detection module with a first ray detection surface and an energy integration detection module with a second ray detection surface, and the first ray detection surface extends in a strip shape along a first direction; and a photon counting detection module is arranged between the two energy integration detection modules, so that second ray detection surfaces are arranged on the two sides of the first ray detection surface in the second direction. Compared with a traditional energy integration flat panel detector, the photon counting detection module can be locally adopted under the condition of limited cost, electronic noise can be reduced, spatial resolution and multi-energy-level imaging can be improved, and the energy integration flat panel detector is suitable for large-scale popularization and application. According to the composite mode that the strip-shaped first ray detection surface is arranged between the two second ray detection surfaces, the photon counting detection module with a smaller area can be used for obtaining local high-performance detection information in a single direction in a full image of the detector.

Description

Technical Field

[0001] The present invention relates to the technical field of medical equipment, and in particular to a medical imaging device and a composite detector and an image data reading method thereof. Background Art

[0002] Energy-integrating flat-panel detectors (FPDs) are widely used in medical imaging systems (such as X-ray imaging) due to their simple process, low cost and large field of view. They can perform real-time planar radiographic imaging, such as fluoroscopy, digital subtraction angiography and cone beam CT, to facilitate better treatment planning, monitoring and evaluation.

[0003] However, FPDs cannot provide the ability to reliably resolve low-contrast anatomical features required to reliably resolve low-contrast lesions, lack the high-resolution capability to visualize fine structures such as stent kinks and narrowing, and lack the spectral and quantitative imaging capabilities that physicians greatly require. The main reason is that the detection principle of FPD hardware is flawed, such as the low quantization bit of the analog-to-digital converter, the afterglow and related hysteresis effects of the scintillator material, the poor charge mobility in the amorphous silicon-based thin-film transistor array, and the pixel design associated with these.

[0004] Semiconductor-based photon counting detectors (PCDs) have many advantages over energy-integrating FPDs, including but not limited to: the energy threshold of PCDs can almost completely eliminate electronic noise, negligible detector hysteresis effects, and low-contrast resolution brought about by favorable X-ray photon energy weighting; PCDs have higher spatial resolution than the pixel merging required in scintillator FPD acquisition; and PCDs can obtain spectral information at multiple energy levels.

[0005] However, photon counting detectors are expensive, and the cost increases linearly with the increase of X-ray sensing area. The high-cost solution of using photon counting detection technology for all panels has created obstacles to clinical promotion and application; the response of large-area photon counting detectors is uneven; and in low-contrast conditions, the scattering of X-rays has a non-negligible negative impact on the image of large-area photon counting detectors.

[0006] In the prior art, there are hybrid detectors that are designed by integrating the imaging technology of PCD and the imaging technology of FPD. The hybrid detectors are compatible with the advantages of energy integrating detectors and photon counting detectors. Existing hybrid detectors usually stack PCDs on one side of a vertical direction of an FPD, but the detection surface of the PCD is usually a narrow beam and its volume is also large. It is necessary to add a displacement device to transfer the PCD before FPD image acquisition can be performed, which affects the use of the FPD. If the composite detector solution with a PCD attached next to the FPD also requires the overall adjustment of the position of the FPD before the PCD imaging acquisition can be performed, so that the imaging results of the two parts do not affect each other.

[0007] In summary, during the imaging and acquisition process, the existing hybrid detectors need to move the position of one of the detectors before the imaging and acquisition of the other detector can be performed. The operation process is relatively complicated, and the two detectors cannot receive rays and form images at the same time. The stacked hybrid detectors in the prior art are large in size, heavy in weight, and have a complex manufacturing process. The performance of the acquired local images cannot reach the highest level. Summary of the invention

[0008] The object of the present invention is to provide a medical imaging device and a composite detector thereof, which can obtain local high-performance images within a limited cost, simplify the manufacturing process, reduce the volume, and can simultaneously perform energy-integrating radiographic imaging and photon-counting radiographic imaging.

[0009] In order to solve the above technical problems, based on the first aspect of the present invention, the present invention provides a composite detector, which includes:

[0010] A photon counting detection module, comprising a first ray detection surface, wherein the first ray detection surface extends in a first direction in a strip shape;

[0011] An energy integration detection module having a second ray detection surface;

[0012] At least two of the energy-integrating detection modules are arranged in sequence along the second direction, and the photon counting detection module is arranged between two adjacent energy-integrating detection modules, so that the second ray detection surface is provided on both sides of the first ray detection surface along the second direction, and the second direction is parallel to the first ray detection surface and perpendicular to the first direction.

[0013] Optionally, the first ray detection surface is coplanar with at least one of the second ray detection surfaces; or, the first ray detection surface is skewed with the second ray detection surface.

[0014] Optionally, the edge of the second ray detection surface is in an arc shape, or the second ray detection surface is in a curved shape, or the second ray detection surface is in a flat shape.

[0015] Optionally, the photon counting detection module includes a photon counting detection main circuit and at least one photon counting detection unit, the photon counting detection unit is electrically connected to the photon counting detection main circuit, and the photon counting detection unit has a photon counting detection reference plane;

[0016] Wherein: one of the photon counting detection units extends in a strip shape so that the photon counting detection reference plane forms the first ray detection plane; or, a plurality of the photon counting detection units are arranged in a row in sequence along the first direction, the photon counting detection module includes at least one row of the photon counting detection units, and the photon counting detection reference planes of all the photon counting detection units are coplanar to form the first ray detection plane.

[0017] Optionally, the photon counting detection unit includes:

[0018] A photoelectric conversion substrate, one end surface of which is configured as the photon counting detection reference surface;

[0019] An electrical signal acquisition substrate, which is electrically connected to the photoelectric conversion substrate;

[0020] A photon counting detection circuit is electrically connected to the electrical signal acquisition substrate and to the photon detection main circuit.

[0021] Optionally, the energy-integrating detection module includes an energy-integrating substrate and an energy-integrating detection circuit electrically connected to the energy-integrating substrate, and one end surface of the energy-integrating substrate is configured as the second ray detection surface.

[0022] Optionally, the photon counting detection module and the energy integration detection module are configured by splicing, and the first ray detection surface and the second ray detection surface each have a plurality of evenly arranged pixels; a splicing gap along the second direction between the pixel of the first ray detection surface closest to the energy integration detection module and the pixel of the second ray detection surface closest to the photon number detection module is less than or equal to the size of the two pixels.

[0023] Optionally, the stitching gap is equal to the size of one pixel or equal to the size of two pixels.

[0024] To solve the above technical problems, based on the second aspect of the present invention, the present invention further provides an image data reading method applied to the above composite detector, wherein the first ray detection surface includes a plurality of photon counting detection reference surfaces sequentially arranged along the first direction, and the second ray detection surface includes a plurality of energy integration detection reference surfaces sequentially arranged along the second direction; the image data reading method includes:

[0025] sequentially reading one of the energy-integrating detection modules through the second data reading mode, reading the photon counting detection module through the first data reading mode, and reading another of the energy-integrating detection modules through the third data reading mode;

[0026] and / or, while reading the photon counting detection module through the first data reading mode, simultaneously reading the two energy integration detection modules through the third data reading mode

[0027] Wherein, the data reading mode of the composite detector includes a first data reading mode, a second data reading mode and a third data reading mode;

[0028] The first data reading mode is configured to: sequentially read out image data of each of the photon counting detection reference surfaces along the first direction;

[0029] The second data reading mode is configured to: sequentially read out the image data of each of the energy integration detection reference planes in the energy integration detection module along the second direction and in a direction close to the photon counting detection module;

[0030] The third data reading mode is configured to sequentially read out the image data of each of the energy integration detection reference surfaces in the energy integration detection module along the second direction and away from the photon counting detection module.

[0031] In order to solve the above technical problems, based on the fourth aspect of the present invention, the present invention also provides a storage medium, on which a readable and writable program is stored, and the above image data reading method is implemented when the program is executed.

[0032] In order to solve the above technical problems, based on the fourth aspect of the present invention, the present invention further provides a medical imaging device, comprising:

[0033] a C-shaped arm having opposite ends;

[0034] a radiation source, which is disposed on one end of the C-shaped arm;

[0035] The composite detector as described above is arranged on the other end of the C-shaped arm, and the first radiation detection surface and the second radiation detection surface face the radiation source;

[0036] A beam limiter is arranged on the ray source to limit the rays emitted by the ray source to a line beam of a predetermined shape.

[0037] Optionally, the C-shaped arm is rotatable around a first reference line; and / or, the C-shaped arm is rotatable around the second reference line; and / or, the compound detector is rotatable around the second reference line; wherein, the second reference line is a line connecting the two ends of the C-shaped arm, and the first reference line is parallel to the plane where the C-shaped arm is located and perpendicular to the second reference line.

[0038] The composite detector as above, by setting a photon counting detection module between two energy integration detection modules, realizes the combination of the first ray detection surface and the second ray detection surface, thereby realizing the combination of two ray imaging methods, namely energy integration imaging and photon counting imaging. Compared with the traditional energy integration flat-panel detector, the present invention can locally adopt a photon counting detection module under limited cost, which can reduce electronic noise, improve contrast, improve spatial resolution and multi-level imaging. The composite method in which the strip-shaped first ray detection surface is set between the two second ray detection surfaces can use a smaller photon counting detection module to obtain local high-performance detection information in a single direction in the full-frame image of the detector. In terms of 2D imaging, the composite flat-panel detector with strip-shaped high-performance information can provide noise reduction, enhancement and other effects for the information around the strip and even the entire detector through traditional image processing or artificial intelligence algorithms. Compared with the composite detection method of local square distribution, it can be reduced to a one-dimensional method for local strip performance reduction processing or full-frame noise reduction, enhancement and other processing.

[0039] It should be noted that the medical imaging device of the present invention includes the above-mentioned composite detector, so it also has the beneficial technical effects brought by the composite detector, which will not be repeated here. BRIEF DESCRIPTION OF THE DRAWINGS

[0040] Those skilled in the art should understand that the drawings are provided for a better understanding of the present invention and do not constitute any limitation on the scope of the present invention.

[0041] Figure 1 is a side view schematic diagram of a composite detector according to an embodiment of the present invention;

[0042] Figure 2 is another side view of a composite detector according to an embodiment of the present invention;

[0043] Figure 3 is a top view schematic diagram of a composite detector according to an embodiment of the present invention;

[0044] Figure 4is another schematic diagram of a composite detector in a top view according to an embodiment of the present invention;

[0045] Figure 5 is another schematic diagram of a composite detector in a top view according to an embodiment of the present invention;

[0046] Figure 6 is a schematic diagram of a second ray detection surface of an energy integration detection module in an embodiment of the present invention being in an arc shape;

[0047] Figure 7 It is a schematic diagram of a photon counting detection module and an energy integration detection module of a composite detector according to an embodiment of the present invention;

[0048] Figure 8 is a schematic diagram of a photon counting detection module according to an embodiment of the present invention;

[0049] Fig. 9 is another schematic diagram of a photon counting detection module according to an embodiment of the present invention;

[0050] Fig.10 It is a schematic diagram of splicing a photon counting detection module and an energy integration detection module according to an embodiment of the present invention;

[0051] Fig.11 is a schematic diagram of a data reading mode of a composite detector according to an embodiment of the present invention;

[0052] Fig.12 is another schematic diagram of a data reading mode of a composite detector according to an embodiment of the present invention;

[0053] Fig.13 is a schematic diagram of a medical imaging device according to an embodiment of the present invention;

[0054] Fig.14 is another schematic diagram of a medical imaging device according to an embodiment of the present invention;

[0055] Fig.15 is a schematic diagram of a medical imaging device in a 2D full-frame imaging mode according to an embodiment of the present invention;

[0056] Fig.16 is a schematic diagram of a medical imaging device in accordance with an embodiment of the present invention performing a 2D strip imaging mode;

[0057] Fig.17 is a schematic diagram of a medical imaging device in a 3D full-frame imaging mode according to an embodiment of the present invention;

[0058] Fig.18 It is a schematic diagram of a medical imaging device according to an embodiment of the present invention performing a 3D strip imaging mode.

[0059] In the attached figure:

[0060] 1-photon counting detection module; 10-first ray detection surface; 101-photon counting detection pixel; 11-photon detection main circuit; 12-photon counting detection unit; 120-photon counting detection reference surface; 121-photoelectric conversion substrate; 122-electric signal acquisition substrate; 123-photon counting detection circuit; 124-signal transmission interface; 125-third mechanical frame; 126-photon counting data interface; 13-first mechanical frame; 14-first detection interface;

[0061] 2-energy integration detection module; 20-second ray detection surface; 201-energy integration detection pixel; 21-energy integration substrate; 22-energy integration detection circuit; 23-second mechanical frame; 24-second detection interface;

[0062] 3-composite detection circuit; 4-composite detection interface; 5-composite mechanical frame; 6-composite housing;

[0063] 100-compound detector; 200-radiation source; 300-C-arm; 400-beam limiter; 500-examination bed; 600-patient.

[0064] a-first direction; b-second direction; c-first baseline; d-second baseline; e-three-dimensional imaging area; f-conical beam; g-fan beam; h-stitching gap; k1-first data reading mode; k2-second data reading mode; k3-third data reading mode. DETAILED DESCRIPTION

[0065] In order to make the purpose, advantages and features of the present invention clearer, the present invention is further described in detail below in conjunction with the accompanying drawings and specific embodiments. It should be noted that the drawings are all in a very simplified form and are not drawn to scale, and are only used to conveniently and clearly assist in explaining the purpose of the embodiments of the present invention. In addition, the structure shown in the drawings is often a part of the actual structure. In particular, the emphasis of each drawing is different, and sometimes different scales are used.

[0066] As used in the present invention, the singular forms "one", "an" and "the" include plural objects, the term "or" is generally used to include the meaning of "and / or", the term "several" is generally used to include the meaning of "at least one", and the term "at least two" is generally used to include the meaning of "two or more". In addition, the terms "first", "second" and "third" are only used for descriptive purposes and cannot be understood as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Therefore, the features defined as "first", "second" and "third" may explicitly or implicitly include one or at least two of the features, "one end" and "the other end" and "the proximal end" and "the distal end" generally refer to two corresponding parts, which include not only the endpoints, and the terms "installed", "connected" and "connected" should be understood in a broad sense, for example, it can be a fixed connection, a detachable connection, or an integral body; it can be a mechanical connection or an electrical connection; it can be directly connected or indirectly connected through an intermediate medium, it can be the internal connection of two elements or the interaction relationship between two elements. In addition, as used in the present invention, an element disposed on another element generally only indicates that there is a connection, coupling, cooperation or transmission relationship between the two elements, and the connection, coupling, cooperation or transmission between the two elements may be direct or indirect through an intermediate element, and cannot be understood as indicating or implying the spatial position relationship between the two elements, that is, one element may be in any orientation such as inside, outside, above, below or on one side of another element, unless otherwise clearly indicated in the content. For ordinary technicians in this field, the specific meanings of the above terms in the present invention can be understood according to specific circumstances.

[0067] Figure 1 is a side view schematic diagram of a composite detector according to an embodiment of the present invention, Figure 2 is another side view of a composite detector according to an embodiment of the present invention. Figure 3 is a top view schematic diagram of a composite detector according to an embodiment of the present invention, Figure 4 is another schematic diagram of a composite detector according to an embodiment of the present invention, viewed from above. Figure 5 FIG. 1 is another schematic diagram of a composite detector according to an embodiment of the present invention. Figure 1-Figure 5As shown, an embodiment of the present invention schematically provides a composite detector 100, which includes a photon counting detection module 1 and an energy integration detection module 2, and the number of the photon counting detection module 1 is at least one, and the number of the energy integration detection module is at least two. The photon counting detection module 1 has a first ray detection surface 10, and the first ray detection surface 10 extends along the first direction a in a strip shape, which can be understood as the first ray detection surface 10 is in a rectangular plane shape. Preferably, the photon counting detection module 1 is in a strip shape, and the first ray detection surface 10 is located on one of the end surfaces of the photon counting detection module 1. The photon counting detection module 1 detects rays through the first ray detection surface 10, and obtains a photon counting medical image by photon counting. The energy integration detection module 2 has a second ray detection surface 20, and the second ray detection surface 20 can be in a plane shape or a curved surface shape, which is not limited in this embodiment. The energy integration detection module 2 detects rays through the second ray detection surface 20, and obtains an energy integration medical image by energy integration. The radiation is emitted by the radiation source of the medical imaging device. In one embodiment, the radiation source includes, for example, a tube, and the emitted radiation is an X-ray. At least two energy-integrating detection modules 2 are arranged in sequence along the second direction, and a strip-shaped photon counting detection module 1 is arranged in the gap between two adjacent energy-integrating detection modules 2, so that the first radiation detection surface 10 is provided with a second radiation detection surface 20 on both sides along the second direction b. The second direction b is parallel to the first radiation detection surface 10 and perpendicular to the first direction a. It can be understood that the first direction a is also the length direction of the strip-shaped first radiation detection surface 10, and the second direction b is also the width direction of the strip-shaped first radiation detection surface 10. The area of ​​the second radiation detection surface 20 is greater than the area of ​​the first radiation detection surface 10. Exemplarily, the second radiation detection surface 20 and the first radiation detection surface 10 are of the same length, and the width of the second radiation detection surface 20 (the dimension along the second direction b) is greater than the width of the first radiation detection surface 10. Preferably, the widths of the two second ray detection surfaces 20 along the second direction b are equal, that is, it is understood that the first ray detection surface 10 is arranged in the middle of the two ray detection surfaces. The photon counting detection module 1 and the energy integration detection module 2 can be arranged in a splicing manner, and the photon counting detection module 1 is spliced ​​between the two energy integration detection modules 2.

[0068] Considering that the photon counting detection module 1 is relatively expensive and the energy integrating detection module 2 is widely used and relatively low in cost, this embodiment preferably configures two energy integrating detection modules 2 and one photon counting detection module, and the photon counting detection module 1 is arranged between the two energy integrating detection modules 2 .

[0069] In this way, the composite detector 100 of this embodiment can obtain medical images with no electronic noise, high spatial resolution and multi-level image information based on the photon counting detection module 1, and can obtain large-area medical images based on the low-cost and widely used energy integration detection module 2. The composite detector 100 using photon counting and energy integration has many advantages. Within a limited cost, the photon counting detector can be used locally to reduce local electronic noise, improve contrast, improve spatial resolution, multi-level imaging, etc.; after the performance of the photon counting detection module 1 is reduced, it can be compatible with the widely used energy integration detection module 2.

[0070] Preferably, the first radiation detection surface 10 is coplanar with at least one second radiation detection surface 20. More preferably, the first radiation detection surface 10 and the two second radiation detection surfaces 20 are on the same plane ( Figure 1 In some other embodiments, the first ray detection surface 10 and the second ray detection surface 20 are not in the same plane ( Figure 2 As shown), the two second ray detection surfaces 20 are not on the same plane with the first ray detection surface 10. The two second ray detection surfaces 20 may be on the same plane or not. It should be noted that when the photon counting detection module 1 and the energy integration detection module 2 are spliced ​​together and the first ray detection surface 10 and the second ray detection surface 20 are coplanar, there is a splicing gap h between the first ray detection surface 10 and the second ray detection surface 20 along the second direction b, and the size of the splicing gap can be adjusted by mechanical adjustment. When the photon counting detection module 1 and the energy integration detection module 2 are spliced ​​together and the first ray detection surface 10 and the second ray detection surface 20 are not coplanar, there is no splicing gap h between the first ray detection surface 10 and the second ray detection surface 20 along the second direction b, and it can be considered that the first ray detection surface 10 and the second ray detection surface 20 have an overlapping part in the normal direction of the first ray detection surface 10.

[0071] Preferably, the edge of the second ray detection surface 20 is in the shape of a curved surface ( Figure 6), or the second ray detection surface 20 is in the shape of a curved surface (similar to a hemispherical surface). In this way, whether the first ray detection surface 10 and the second ray detection surface 20 are arranged in the same plane or in different planes, the effective detection area of ​​the second ray detection surface 20 for rays can be increased, more rays can be detected, and a better quality image can be obtained. Furthermore, in the case where the first ray detection surface 10 and the second ray detection surface 20 are arranged in different planes, the side of the energy integration detection module 20 cannot detect the received rays, and the edge of the second ray detection surface 20 is in the shape of an arc or the second ray detection surface 20 is in the shape of a curved surface, which can detect as many rays as possible from the side of the energy integration detection module 2. It should be noted that the curved second ray detection surface 20 being coplanar with the first ray detection surface 10 should be understood as the tangent plane of the top or top of the curved surface being substantially coplanar with the first ray detection surface 10.

[0072] In some other embodiments, the second radiation detection surface 20 is planar as a whole.

[0073] Figure 7 Schematic diagram of a photon counting detection module and an energy integration detection module of a composite detector according to an embodiment of the present invention. Figure 7 The composite detector 100 also includes a composite detection circuit 3, a composite detection interface 4, a composite mechanical frame 5 and a composite housing 6. The composite detection circuit 3, the composite mechanical frame 5, the photon counting detection module 1 and the energy integration detection module 2 are all located in the composite housing 6, the composite mechanical frame 5 is fixed on the inner wall of the composite housing 6, the composite detection interface 4 is located on the outer wall of the composite housing 6, the photon counting detection module 1 and the energy integration detection module 2 are all fixed on the composite mechanical frame 5, the photon counting detection module 1 and the energy integration detection module 2 are both communicated with the composite detection circuit 3, and the composite detection circuit 3 realizes information exchange with the outside world through the composite detection interface 4, including connecting the power supply to the composite detector 100, controlling the detection rays of the photon counting detection module 1 and the energy integration detection module 2 through an external controller, and reading the image information of each of the photon counting detection module 1 and the energy integration detection module 2.

[0074] Continue reading Figure 7Regarding the specific structure of the energy integration detection module 2, the energy integration detection module 2 includes an energy integration substrate 21 and an energy integration detection circuit 22 electrically connected to the integration substrate, and one end surface of the energy integration substrate 21 is configured as a second ray detection surface 20. The energy integration detection module also includes a second mechanical frame 23 and a second detection interface 24. The second mechanical frame 23 is fixed on the composite mechanical frame 5, the energy integration substrate 21 is fixed on the second mechanical frame 23, the energy integration detection circuit 22 is arranged on the second mechanical frame 23, and the energy integration detection circuit 22 is electrically connected to the composite detection circuit 3. The energy integration substrate 21 measures and receives radiation (such as X-rays), detects the incident dose of the radiation in an energy integration manner, and the energy integration detection circuit 22 processes signals about the incident dose of the radiation. The energy integration detection circuit 22 is communicatively connected to the composite detection circuit 3 via the second detection interface 24, thereby realizing information interaction between the energy integration detection module 2 and the outside world through the composite detection circuit 3, including turning on the power supply to the energy integration detection module 2, controlling the detection rays of the energy integration detection module 2 through an external controller, and reading out the image information of the energy integration detection module 2.

[0075] Figure 8 Schematic diagram of a photon counting detection module according to an embodiment of the present invention. Figure 8 The photon counting detection module 1 includes a photon counting detection main circuit 11 and at least one photon counting detection unit 12. The photon counting detection unit 12 is electrically connected to the photon counting detection main circuit 11. The photon counting detection unit 12 has a photon counting detection reference plane 120. The photon counting detection reference plane 120 can detect rays, and a first ray detection plane 10 is formed by the photon counting detection reference plane 120. The photon counting detection module 1 also includes a first mechanical frame 13 and a first detection interface 14. The first mechanical frame 13 is fixedly connected to the composite mechanical frame 5. The photon counting detection unit 12 is arranged on the first mechanical frame 13. The photon counting detection main circuit 11 is arranged on the first mechanical frame 13. The photon counting detection main circuit 11 and the composite detection circuit 3 are connected to each other through the first detection interface 14. The photon counting detection unit 12 detects the received radiation through the photon counting detection reference plane 120, and detects the incident dose of the radiation by photon counting. The photon detection main circuit 11 processes the signals of all photon counting detection units 12 regarding the incident dose of the radiation, and realizes the information interaction between the photon counting detection unit 12 and the outside world through the composite detection circuit 3, including turning on the power supply to the photon counting detection unit 12, controlling the detection radiation of the photon counting detection unit 12 through an external controller, and reading out the image information of the photon counting detection unit 12.

[0076] Continue reading Figure 8 , and refer to Figure 3-Figure 5, further, regarding the form of forming the first ray detection surface 10 by the photon counting detection reference surface 120. In one embodiment, refer to Figure 3 , a photon counting detection unit 12 extends in a strip shape so that the photon counting detection reference surface 120 forms the first ray detection surface 10. In other words, the photon counting detection module 1 includes a photon counting detection unit 12, and the photon counting detection unit 12 extends in a strip shape so that the photon counting detection reference surface 120 of the photon counting detection unit 12 extends to form the strip-shaped first ray detection surface 10. In another embodiment, refer to Figure 4 and Figure 8 , a plurality of photon counting detection units 12 are sequentially arranged in a row along the first direction a, and the photon counting detection module 1 includes a row of photon counting detection units 12, so that the photon counting detection reference surfaces 120 of the photon counting detection units 12 in the row are coplanar to form a first ray detection surface 10. In another embodiment, refer to Figure 5 In conjunction with Figure 8 The photon counting detection module 1 includes at least two parallel rows of photon counting detection units 12 , and the photon counting detection reference surfaces 120 of all the photon counting detection units 12 are coplanar to form a first ray detection surface 10 .

[0077] Continue reading Figure 8 Regarding the specific structure of the photon counting detection unit 12, the photon counting detection unit 12 includes a photoelectric conversion substrate 121, an electrical signal acquisition substrate 122, a photon counting detection circuit 123, a signal transmission interface 124, a third mechanical frame 125, and a photon counting data interface 126. One end surface of the photoelectric conversion substrate 121 is configured to be able to detect a photon counting detection reference plane 120 of rays. The electrical signal acquisition substrate 122 and the photoelectric conversion substrate 121 are arranged in parallel, and the electrical signal acquisition substrate 122 is electrically connected to the photoelectric conversion substrate 121, and the electrical signal acquisition substrate 122 is fixedly connected to the third mechanical frame 125, and the third mechanical frame 125 is fixed to the first mechanical frame 13. The photon counting detection circuit 123 is electrically connected to the electrical signal acquisition substrate 122 through the signal transmission interface 124, and is electrically connected to the photon detection main circuit 11 through the photon counting data interface 126. The photoelectric conversion substrate 121 directly converts the rays into electrical signals, the electrical signal acquisition substrate 122 acquires the electrical signals and transmits the electrical signals to the photon counting detection circuit 123 through the signal transmission interface 124, and the photon counting detection circuit 123 processes the electrical signals and transmits them to the photon detection main circuit 11 through the photon counting data interface 126.

[0078] Fig. 9 is another schematic diagram of a photon counting detection module according to an embodiment of the present invention. Fig. 9The photon counting detection circuit 123 can be integrated into the photon detection main circuit 11, that is, all the photon counting detection units 12 share the same photon detection main circuit 11 provided with the function of the photon counting detection circuit 123.

[0079] Fig.10 FIG. 1 is a schematic diagram of the splicing of a photon counting detection module and an energy integration detection module according to an embodiment of the present invention. Fig.10 The first ray detection surface 10 and the second ray detection surface 20 each have a plurality of uniformly arranged picture elements (also called pixels, which are used as the smallest image unit to detect received rays). The picture elements of the first ray detection surface 10 can be recorded as photon counting detection picture elements 101, and the picture elements of the second ray detection surface 20 can be recorded as energy integration detection picture elements 201. The photon counting detection picture elements 101 are located on the photoelectric conversion substrate 121, and the energy integration detection picture elements 201 are located on the energy integration substrate 21. The connection between the photon counting detection module 1 and the energy integration detection module 2 is splicing, and there is a gap between the two, which can be specifically understood as a splicing gap h along the second direction b between the coplanar first ray detection surface 10 and the second ray detection surface 20, and the first ray detection surface 10 and the second ray detection surface 20 each have evenly arranged pixels. It can be further considered that the splicing gap h along the second direction b between the photon counting detection pixel 101 closest to the energy integration detection module 2 and the energy integration detection pixel 201 closest to the photon number detection module is less than or equal to the size of the two pixels, and the size of the pixel is generally between 100 microns and 150 microns. It should be noted that the splicing gap h here refers to the sum of the distance h1 from the photon counting detection pixel 101 to the edge of the photoelectric conversion substrate 121, the gap value h2 between the photoelectric conversion substrate 121 and the energy integration substrate 21, and the distance h3 from the energy integration detection pixel 201 to the edge of the energy integration substrate 21 in the second direction b, that is, h=h1+h2+h3. Preferably, h is the size of one pixel or the size of two pixels. For example, the values ​​of h1 and h3 can be configured first, and then the value of h2 can be adjusted by mechanical adjustment to make h equal to the size of one pixel or the size of two pixels. In this way, the bad line correction algorithm can be directly used to correct the image data of the composite detector 100.

[0080] Further, the first ray detection surface 10 includes a plurality of photon counting detection reference surfaces 120 sequentially arranged along the first direction a. Similarly, the second ray detection surface 20 can be considered to include a plurality of energy integration detection reference surfaces (not shown) sequentially arranged along the second direction b. It can be understood that the second ray surface is sequentially cut into a plurality of energy integration detection reference surfaces along the second direction b. This embodiment also proposes an image data reading method, which is applied to the above-mentioned composite detector 100. The data reading mode configured by the image data reading method for the composite detector 100 includes a first data reading mode k1, a second data reading mode k2 and a third data reading mode k3. Fig.11 is a schematic diagram of a data reading mode of a composite detector according to an embodiment of the present invention, see Fig.11 , the first data reading mode k1 is configured to sequentially read out the image data of each photon counting detection reference surface 120 along the first direction a; the second data reading mode k2 is configured to sequentially read out the image data of each energy integration detection reference surface in the energy integration detection module 2 along the second direction b and in a direction close to the photon counting detection module 1; the third data reading mode k3 is configured to sequentially read out the image data of each energy integration detection reference surface in the energy integration detection module 2 along the second direction b and in a direction away from the photon counting detection module 1. The image data reading method includes at least one of step A and step B.

[0081] Continue reading Fig.11 , step A: for the energy integration detection module 2, the photon counting detection module 1 and the other energy integration detection module 2 that are adjacent in sequence along the second direction b, first read the data of one of the energy integration detection modules 2 through the second data reading mode k2, then read the data of the photon counting detection module 1 through the first data reading mode k1, and finally read the data of the other energy integration detection module 2 through the third data reading mode k3.

[0082] Fig.12 is another schematic diagram of a data reading mode of a composite detector according to an embodiment of the present invention, see Fig.11 , step B: for the energy integration detection module 2, the photon counting detection module 1 and another energy integration detection module 2 that are sequentially adjacent along the second direction b, the data of the photon counting detection module 1 and the two energy integration detection modules 2 are synchronously read out, that is, the data of the photon counting detection module 1 is read through the first data reading mode k1, and the data of the two energy integration detection modules 2 are synchronously read through the third data reading mode k3. In this way, data can be read out quickly.

[0083] It should be noted that the energy-integrating detection module 2, the photon counting detection module 1 and another energy-integrating detection module 2 that are adjacent in sequence along the second direction b can be considered as a group of detection modules. For the data of a group of detection modules that need to be read, one of step A and step B can be used; for multiple photon counting detection modules 1 and multiple energy-integrating detection modules 2 to form multiple groups of detection modules, there is no common energy-integrating detection module 2 between two or more groups of detection modules that need to be read, and each group of detection modules can arbitrarily choose step A or step B to read the data; and for two groups of detection modules that need to be read that have a common energy-integrating detection module 2, step A can be used to read the data of each group of detection modules in turn.

[0084] Of course, this embodiment can also select one of the above data reading modes to read the data of the corresponding detection module. For example, when clinical diagnosis only requires high-quality photon counting medical images, the data of the photon counting detection module 1 can be read only through the first data reading mode k1, and the data of the energy integration detection module 2 can be omitted.

[0085] Based on the above-mentioned image data reading method, this embodiment further provides a storage medium, on which a readable and writable program is stored, and when the program is executed, the above-mentioned image data reading method can be implemented.

[0086] Fig.13 is a schematic diagram of a medical imaging device according to an embodiment of the present invention, Fig.13 FIG. 1 is another schematic diagram of a medical imaging device according to an embodiment of the present invention. Fig.13 and Fig.14Based on the above-mentioned compound detector 100, this embodiment further provides a medical imaging device, which includes a C-shaped arm 300, a radiation source 200, the above-mentioned compound detector 100 and a beam limiter 400. The C-shaped arm 300 has two opposite ends; the radiation source 200 is arranged at one end of the C-shaped arm 300, and the radiation source 200 is used to emit radiation, such as X-rays; the compound detector 100 is arranged at the other end of the C-shaped arm 300, and the first radiation detection surface 10 and the second radiation detection surface 20 face the radiation source 200, and the first radiation detection surface 10 and the second radiation detection surface 20 are perpendicular to the line between the two ends of the C-shaped arm 300, and the first radiation detection surface 10 and the second radiation detection surface 20 can detect the radiation emitted by the radiation source 200. The beam limiter 400 is arranged on the radiation source 200, and can limit the radiation emitted by the radiation source 200 to a beam of a predetermined shape, such as a cone beam f or a fan beam g. The C-shaped arm 300 is defined to have a first reference line c and a second reference line d, the second reference line d being a line connecting the two ends of the C-shaped arm 300, the first reference line c being parallel to the plane where the C-shaped arm 300 is located and being perpendicular to the second reference line d. The medical imaging device further includes an examination bed 500 carrying a patient 600, the second reference line d being perpendicular to the surface of the examination bed 500, and the examination bed 500 being movable relative to the C-shaped arm 300 along the direction of the first reference line c so that the patient 600 can enter and exit the C-shaped arm 300, thereby completing a medical imaging examination under the cooperation of the radiation source 200, the beam limiter 400 and the compound detector 100.

[0087] Optionally, after the composite detector 100 is arranged on the C-shaped arm 300, the length direction (ie, the first direction a) of the first ray detection surface 10 may be perpendicular to the plane defined by the C-shaped arm 300 ( Fig.13 ), or it may be a plane defined by the parallel C-shaped arm 300 ( Fig.14 In some other embodiments, the first direction a may also be arranged at an angle to the plane where the C-shaped arm 300 is located.

[0088] Furthermore, the C-shaped arm 300 can rotate around the first reference line c, the C-shaped arm 300 can also rotate around the second reference line d, and the composite detector 100 can rotate around the second reference line d.

[0089] Fig.15 is a schematic diagram of a medical imaging device in a 2D full-frame imaging mode according to an embodiment of the present invention, Fig.16 FIG. 1 is a schematic diagram of a medical imaging device according to an embodiment of the present invention performing a 2D strip imaging mode. Fig.15 and Fig.16 As shown, the medical imaging device of this embodiment can perform 2D imaging, including 2D full-frame imaging and 2D strip imaging. Specifically, in one embodiment, refer to Fig.15, the beam limiter 400 limits the shape of the ray to a cone beam f, the ray of the cone beam f attenuates after passing through the patient 600, and is received by the first ray detection surface 10 and the second ray detection surface 20, so as to detect and obtain full-frame imaging, which includes a full-frame image of strip-shaped high-performance information (obtained by the photon counting detection module 1) and a normal full-frame image (obtained by the energy integration detection module 2). It is understandable that the normal full-frame image can be directly obtained by de-energizing the strip-shaped high-performance image information and merging the operations. In another embodiment, refer to Fig.16 The beam limiter 400 limits the shape of the ray to a fan-shaped beam g, and the ray of the fan-shaped beam g can only be detected and received by the first ray detection surface 10, thereby obtaining photon counting strip imaging.

[0090] Fig.17 is a schematic diagram of a medical imaging device in a 3D full-frame imaging mode according to an embodiment of the present invention, Fig.18 FIG. 1 is a schematic diagram of a medical imaging device according to an embodiment of the present invention performing a 3D banner imaging mode. The medical imaging device can perform 3D imaging. Fig.17 , the C-arm 300 rotates around the first reference line c, and CBCT reconstruction is performed after a certain number of images are obtained, so that a CBCT three-dimensional imaging area e can be obtained. Fig.18 , the C-shaped arm 300 rotates around the first reference line c to obtain a circle of banner images, the examination bed 500 and the C-shaped arm 300 move relative to each other along the direction of the first reference line c (one of the examination bed 500 moves or the C-shaped arm 300 moves), and repeated scanning can obtain a banner image at the next position, perform CT reconstruction, and obtain a photon counting CT three-dimensional imaging result. In another embodiment, continue to refer to Fig.18 The C-arm 300 rotates around the second reference line d to obtain multi-angle 3D imaging results.

[0091] Although the present invention is disclosed as above with preferred embodiments, the above embodiments are not intended to limit the present invention. For any technician familiar with the art, without departing from the scope of the technical solution of the present invention, the technical content disclosed above can be used to make many possible changes and modifications to the technical solution of the present invention, or modified into equivalent embodiments of equivalent changes. Therefore, any simple modification, equivalent change and modification made to the above embodiments according to the technical essence of the present invention without departing from the content of the technical solution of the present invention still belongs to the scope of protection of the technical solution of the present invention.

Claims

1. A composite detector (100), characterized in that: include: A photon counting detection module (1) comprises a first ray detection surface (10), wherein the first ray detection surface (10) extends in a first direction (a) in a strip shape; An energy integration detection module (2) having a second ray detection surface (20); At least two of the energy-integrating detection modules (2) are arranged in sequence along the second direction (b), and the photon-counting detection module (1) is arranged between two adjacent energy-integrating detection modules (2), so that the second ray detection surfaces (20) are arranged on both sides of the first ray detection surface (10) along the second direction (b); the second direction (b) is parallel to the first ray detection surface (10) and perpendicular to the first direction (a).

2. The composite detector (100) according to claim 1, characterized in that: The first radiation detection surface (10) is coplanar with at least one of the second radiation detection surfaces (20); or the first radiation detection surface (10) is non-planar with all of the second radiation detection surfaces (20).

3. The composite detector (100) according to claim 1 or 2, characterized in that: The edge of the second ray detection surface (20) is in the shape of an arc surface, or the second ray detection surface (20) is in the shape of a curved surface, or the second ray detection surface (20) is in the shape of a plane.

4. The composite detector (100) according to claim 1, characterized in that: The photon counting detection module (1) comprises a photon counting detection main circuit (11) and at least one photon counting detection unit (12), wherein the photon counting detection unit (12) is electrically connected to the photon counting detection main circuit (11), and the photon counting detection unit (12) has a photon counting detection reference surface (120); Wherein: one of the photon counting detection units (12) extends in a strip shape so that the photon counting detection reference plane (120) forms the first ray detection plane (10); or, a plurality of the photon counting detection units (12) are sequentially arranged in a row along the first direction (a), the photon counting detection module (1) comprises at least one row of the photon counting detection units (12), and the photon counting detection reference planes (120) of all the photon counting detection units (12) are coplanar to form the first ray detection plane (10).

5. The composite detector (100) according to claim 4, characterized in that: The photon counting detection unit (12) comprises: A photoelectric conversion substrate (121), one end surface of which is configured as the photon counting detection reference surface (120); An electrical signal collection substrate (122) electrically connected to the photoelectric conversion substrate (121); A photon counting detection circuit (123) is electrically connected to the electrical signal collection substrate (122) and to the photon detection main circuit (11).

6. The composite detector (100) according to claim 1, characterized in that: The energy-integrating detection module (2) comprises an energy-integrating substrate (21) and an energy-integrating detection circuit (22) electrically connected to the energy-integrating substrate (21); one end surface of the energy-integrating substrate (21) is configured as the second ray detection surface (20).

7. The composite detector (100) according to claim 1, characterized in that: The photon counting detection module (1) and the energy integration detection module (2) are arranged in a splicing manner, and the first ray detection surface (10) and the second ray detection surface (20) each have a plurality of evenly arranged picture elements; a splicing gap (h) along the second direction (b) between a picture element of the first ray detection surface (10) closest to the energy integration detection module (2) and a picture element of the second ray detection surface (20) closest to the photon counting detection module (1) is less than or equal to the size of the two picture elements.

8. An image data reading method, applied to the composite detector (100) according to any one of claims 1 to 7, characterized in that: The first ray detection surface (10) comprises a plurality of photon counting detection reference surfaces (120) arranged in sequence along the first direction (a), and the second ray detection surface (20) comprises a plurality of energy integration detection reference surfaces arranged in sequence along the second direction (b); The image data reading method comprises: sequentially reading one of the energy-integrating detection modules (2) through the second data reading mode (k2), reading the adjacent photon counting detection module (1) through the first data reading mode (k1), and reading another adjacent energy-integrating detection module (2) through the third data reading mode (k3); and / or, while reading the photon counting detection module (1) through the first data reading mode (k1), simultaneously reading two adjacent energy integration detection modules (2) through the third data reading mode (k3); The first data reading mode (k1) is configured to: sequentially read out the image data of each of the photon counting detection reference surfaces (120) along the first direction (a); The second data reading mode (k2) is configured to: sequentially read out the image data of each of the energy integration detection reference surfaces in the energy integration detection module (2) along the second direction (b) and in a direction close to the photon counting detection module (1); The third data reading mode (k3) is configured to sequentially read out the image data of each of the energy integration detection reference surfaces in the energy integration detection module (2) along the second direction (b) and away from the photon counting detection module (1).

9. A medical imaging device, characterized in that: include: A C-shaped arm (300) having two opposing ends; A radiation source (200) disposed on one end of the C-shaped arm (300); The composite detector (100) according to any one of claims 1 to 7, which is arranged on the other end of the C-shaped arm (300), and the first radiation detection surface (10) and the second radiation detection surface (20) face the radiation source (200); A beam limiter (400) is provided on the ray source (200) to limit the rays emitted by the ray source (200) to a beam of a predetermined shape.

10. The medical imaging device according to claim 9, characterized in that: The C-shaped arm (300) is rotatable around a first reference line (c); and / or the C-shaped arm (300) is rotatable around the second reference line (d); and / or the composite detector (100) is rotatable around the second reference line (d); wherein the second reference line (d) is a line connecting two ends of the C-shaped arm (300), and the first reference line (c) is parallel to the plane where the C-shaped arm (300) is located and perpendicular to the second reference line (d).

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