Multi-spectral X-ray array imaging system

Abstract

The present application relates to the field of area array imaging technology, and specifically to a multi-energy spectrum X-ray area array imaging system, comprising: a first emitting assembly for emitting high-flux incident X-rays; a filtering pixel assembly comprising a substrate located on the emitting side of the first emitting assembly and macro-pixels disposed on the substrate, wherein the macro-pixels include a plurality of sub-filters with different attenuation coefficients, each sub-filter comprising a plurality of sub-filters constituting a sub-pixel; wherein the incident X-rays are filtered and modulated by the macro-pixels before passing through an imaging object to form a plurality of outgoing X-rays based on different sub-pixels; and an area array detector for detecting the plurality of outgoing X-rays to obtain imaging information. The present application has the advantages of higher energy spectrum resolution, better incident X-ray imaging effect, lower detection cost, and strong practical operability.

Description

Technical Field

[0001] The present application relates to the field of area array imaging technology, and in particular to a multi-energy spectrum X-ray area array imaging system. Background Art

[0002] In modern medical diagnosis, X-ray computed tomography (CT) technology has been widely used. It uses a non-contact detection method based on the absorption characteristics of X-rays by different materials. By detecting the attenuation characteristics of X-rays after passing through the material, it can obtain internal structural information and material composition of the object.

[0003] At present, in the field of X-ray imaging, energy-integrating detectors obtain all photons (flux is about 10 6 ~10 9 cps / mm 2 ) intensity, is the mainstream technology in current products. Traditional X-ray CT uses energy-integrating detectors, which receive X-ray photons of varying energies as a whole after passing through an object. This reflects the average attenuation characteristics of the X-rays, making it difficult to distinguish between X-ray photons of varying energies and materials with similar density distributions. This limits qualitative and quantitative analysis of materials and is susceptible to interference from radiation hardening and noise. Consequently, traditional X-ray imaging technology suffers from poor image quality and can only produce grayscale images, failing to produce multi-energy color images. Diagnosis of symptoms requires experienced physicians based on image contours and grayscale levels.

[0004] A long-term development direction in X-ray imaging is the transition from single-energy black-and-white images to multi-energy color images. This effectively distinguishes materials of varying densities and, when combined with subtraction algorithms, extracts features of target objects. Attempts have been made to achieve limited energy resolution with integral detection using multiple exposures of incident X-rays with varying energy spectra and side-incidence detection using multiple detectors. However, this "pseudo-multi-energy approach" suffers from low energy resolution and limited practical application value.

[0005] Furthermore, the industry is pinning its hopes on photon counting technology to achieve multi-energy spectrum X-ray detection. Photon counting detectors have the energy resolution capability of single X-ray photons and can simultaneously measure photon counting data of multiple energy thresholds. The energy-identified photons can be used to obtain multi-energy color images based on their attenuation characteristics. Multi-energy spectrum X-ray imaging technology has the advantages of accurate material resolution, high imaging signal-to-noise ratio, strong practicality, and low radiation dose, and has broad prospects for use in the field of medical imaging. However, current photon counting detectors have many limitations - low counting rate (<10 8 cps / mm 2), poor counting stability, counting rate limited by dead time, etc., which restricts the multi-energy X-ray detection effect based on this technology and limits the development speed and application prospects of energy spectrum detection based on photon counting technology. Summary of the Invention

[0006] In order to improve the energy spectrum resolution and imaging effect, reduce the detection cost and enhance the practical operability, the purpose of this application is to provide a multi-energy spectrum X-ray array imaging system.

[0007] In the first aspect, the multi-spectral X-ray array imaging system provided by this application adopts the following technical solutions:

[0008] A multi-energy spectrum X-ray array imaging system, comprising:

[0009] a first emitting assembly for emitting high flux incident X-rays;

[0010] a filter pixel assembly comprising a substrate located on the emitting side of the first emitting assembly, and a macro-pixel disposed on the substrate, the macro-pixel comprising a plurality of sub-filters having different attenuation coefficients, each sub-filter comprising a plurality of sub-filters constituting a sub-pixel; wherein the incident X-ray is filtered and modulated by the macro-pixel before passing through an imaging object to form a plurality of outgoing X-rays based on different sub-pixels;

[0011] The area array detection component is used to detect a plurality of the outgoing X-rays to obtain imaging information.

[0012] By adopting the above technical solution, first of all, the energy spectrum resolution is higher and the incident X-ray imaging effect is better: the mathematical combination of sub-filters with different attenuation coefficients constitutes a filter pixel component, which realizes flexible and accurate decomposition and modulation of the high-flux incident X-ray energy spectrum. In conjunction with the area array detection sub-component detection, fine-resolution imaging information is obtained. Its energy resolution can reach 3.1% @ 59keV, which means that the minimum energy value that the detector can distinguish for a photon energy of 59.5keV is 59.5×3.1%=1.8445keV, which is comparable to the performance of photon counting detectors and far exceeds the "pseudo-multiple" performance of energy integrating detectors. The multi-energy solution has real application value and solves the problem that traditional X-ray imaging technology has poor imaging quality and requires experienced doctors to judge the disease by image contours and grayscale. Secondly, the detection cost is lower and the actual operability is stronger: although the resolution of photon counting energy spectrum detection is higher in theory, it is subject to many practical factors, such as complex circuit design and strict single crystal requirements. As a result, on the one hand, the current photon counting energy spectrum detection is far from its theoretical resolution; on the other hand, it brings extremely high costs in the purification of high-purity raw materials, strict single crystal good product screening, and electronic design and tape-out of complex functions. The multi-energy spectrum X-ray array imaging system of the present application does not require expensive circuit design and strict single crystal screening. It can be completed by mathematically combining sub-filters to form a filter pixel component under the array detection component, which greatly reduces the cost, has high resolution, and is not limited by counting rate.

[0013] Optionally, the k absorption limits corresponding to the multiple seed filters divide the energy range of the incident X-ray into multiple energy windows;

[0014] The area array detection component includes:

[0015] a detection module, configured to detect each of the emitted X-rays to obtain a corresponding first electrical signal;

[0016] An acquisition module is used to obtain energy spectra of blank emitted X-rays based on different energy windows;

[0017] A calculation module is connected to the detection module and the acquisition module, and is used to obtain imaging information according to the first electrical signal and the partial energy spectrum.

[0018] By adopting the above technical solution, the energy window is divided based on the k absorption limit corresponding to multiple seed filters, blank outgoing X-rays are generated without passing through the imaging object, and the energy spectra of the blank outgoing X-rays based on different energy windows are obtained. On the basis of accurate decomposition and modulation of the high-flux X-ray energy spectrum by cooperating with the filter pixel components, the energy spectrum signals under the filter materials corresponding to various attenuation coefficients are superimposed to achieve ultra-high-resolution energy spectrum calculation and detection.

[0019] Optionally, the energy spectra of the blank outgoing X-rays based on different energy windows are obtained by detecting through a dot matrix detection mechanism, and the acquisition module is used to acquire the energy spectra of the blank outgoing X-rays based on different energy windows from the dot matrix detection component, wherein the dot matrix detection mechanism includes:

[0020] The blank detection module is used to detect the blank emitted X-rays to obtain the second electrical signal S i , i∈(1,n); attenuation constant determination module, used to determine the attenuation constant C of each blank outgoing X-ray based on different energy windows ij , i∈(1,n), j∈(1,m);

[0021] Energy spectrum inversion module is used based on the formula Inverse solution to obtain the energy spectrum

[0022] By adopting the above technical solution, based on the detection principle of energy integration, on the basis of detecting and obtaining the second electrical signal of the blank outgoing X-ray, the attenuation constant of each blank outgoing X-ray based on different energy windows is determined, and then the inverse solution of the divided energy spectrum is achieved, and the energy spectrum signal of the blank outgoing X-ray under the filter materials corresponding to various attenuation coefficients is obtained, and good imaging information is obtained in combination with the first electrical signal.

[0023] Optionally, the blank detection module includes:

[0024] a second emitting assembly for emitting high flux incident X-rays;

[0025] a plurality of single filters, each of which has a one-to-one correspondence with an attenuation coefficient of each of the plurality of seed filters, wherein the plurality of single filters are sequentially arranged on the emission side of the second emission assembly, so that the incident X-ray is filtered and modulated by each of the single filters to obtain a corresponding blank emission X-ray;

[0026] Dot matrix detector, used to detect blank outgoing X-rays to obtain the second electrical signal S i , i∈(1,n).

[0027] By adopting the above technical solution, based on the detection principle of energy integration, the incident X-rays are spectrally modulated by multiple single filters, and then detected by a dot matrix detector to obtain a second electrical signal, which has lower detection costs and stronger practical operability.

[0028] Optionally, the calculation module is configured to obtain imaging information based on the first electrical signal and the energy spectrum, including:

[0029] Based on Inverse solution to obtain imaging information D ij , i∈(1,n), j∈(1,m), where Fi , i∈(1,n) is the first electrical signal.

[0030] By adopting the above technical solution, imaging information is obtained by inverse analysis based on the first electrical signal and the energy spectrum, which reduces the detection cost and improves the practical operability.

[0031] Optionally, the multi-energy spectrum X-ray array imaging system further includes a fusion component for obtaining an image based on the imaging information.

[0032] By adopting the above technical solution, the problem that traditional X-ray imaging technology can only draw grayscale images but cannot obtain multi-energy color images is solved. After obtaining fine-resolution imaging information, color images can be fused to improve the recognition effect of imaged objects.

[0033] Optionally, the substrate includes a plate body and grooves arranged in a matrix on the plate body, and the sub-filters are arranged in the grooves in a one-to-one correspondence.

[0034] By adopting the above technical solution, a groove is provided on the plate body to provide a sub-filter installation space, which not only improves the sub-pixel construction effect but also facilitates installation and positioning.

[0035] Optionally, the sub-filters arranged in the groove constitute a plurality of repeating units, and each of the repeating units includes one of each type of sub-filter.

[0036] By adopting the above technical solution, the setting of the repeating units can achieve uniform distribution of each seed filter, improve the light modulation effect, and increase the imaging information acquisition effect.

[0037] Preferably, the multi-energy spectrum X-ray array imaging system also includes a first tungsten steel collimation component, which includes a first tungsten steel plate and a plurality of first collimation holes arranged in a matrix arranged through the first tungsten steel plate, wherein the first tungsten steel plate is attached to the side of the filtering pixel component away from the first emitting component.

[0038] By adopting the above technical solution, the setting of the first tungsten steel collimation component reduces the energy crosstalk between the pixels corresponding to each sub-filter and improves the detection accuracy.

[0039] Preferably, the multi-energy spectrum X-ray array imaging system also includes a second tungsten steel collimation assembly, which includes a second tungsten steel plate and a plurality of second collimation holes arranged in a matrix arranged through the second tungsten steel plate, wherein the second tungsten steel plate is attached to the side of the imaging object away from the filtering pixel assembly.

[0040] By adopting the above technical solution, the further arrangement of the second tungsten steel collimation component further reduces the energy crosstalk between the X-rays emitted by the imaging object and improves the detection accuracy.

[0041] In summary, this application includes at least one of the following beneficial technical effects:

[0042] 1. Higher energy spectrum resolution and better incident X-ray imaging: The mathematical combination of sub-filters with different attenuation coefficients forms a filter pixel component, achieving flexible and accurate decomposition and modulation of the high-flux incident X-ray energy spectrum. Combined with area array detection, fine-resolution imaging information is obtained. Its energy resolution reaches 3.1% @ 59keV, comparable to the performance of photon counting detectors and far exceeding the "pseudo-multi-energy solution" of energy integrating detectors. It has real application value and solves the problem of poor imaging quality of traditional X-ray imaging technology, which requires experienced doctors to judge the disease based on image contours and grayscale.

[0043] 2. Lower detection costs and stronger practical operability: Although theoretically, photon counting spectrum detection has higher resolution, it is subject to many practical factors, such as complex circuit design and strict single crystal requirements. As a result, on the one hand, current photon counting spectrum detection is far from achieving its theoretical resolution; on the other hand, it brings extremely high costs in high-purity raw material purification, strict single crystal quality screening, complex functional electronics design and wafer production. The multi-spectral X-ray array imaging system of the present application does not require expensive circuit design and strict single crystal screening. It only requires the mathematical combination of sub-filters to form a filter pixel component and cooperate with the array detection to complete the task. The cost is greatly reduced, the resolution is high, and there is no count rate limit.

[0044] 3. During the preparation of the filter pixel assembly, grooves are set on the board body to provide space for sub-filter installation, which not only improves the sub-pixel construction effect but also facilitates installation and positioning. Furthermore, two-stage tungsten steel collimation is introduced to greatly reduce energy crosstalk between pixels, enabling accurate identification of the energy spectrum. BRIEF DESCRIPTION OF THE DRAWINGS

[0045] Figure 1 This is a physical picture of the filter pixel component prepared in Example 1 of the present application;

[0046] Figure 2 This is a layout diagram of the sub-filter board of the filter pixel assembly prepared in Example 1 of the present application;

[0047] Figure 3 This is an arrangement diagram of a repeating unit consisting of a filter pixel assembly corresponding to a sub-filter plate prepared in another embodiment of the present application;

[0048] Figure 4 This is a physical picture of the second tungsten steel collimation assembly prepared in Example 3 of the present application;

[0049] Figure 5 This is the image obtained in Example 3 of the present application without a filtering pixel component;

[0050] Figure 6 This is the image corresponding to the imaging information between the aluminum and copper energy windows in Example 3 of the present application;

[0051] Figure 7 This is the image corresponding to the imaging information between the copper and gold energy windows in Example 3 of the present application;

[0052] Figure 8 This is an image corresponding to the imaging information between the gold and tantalum energy windows in Example 3 of the present application. DETAILED DESCRIPTION

[0053] The following is combined with Figure 1 -Attached Figure 8 , further details of this application are given.

[0054] Example 1:

[0055] A multi-energy spectrum X-ray area array imaging system includes a first emission component, a filter pixel component, and an area array detection component;

[0056] (1) Regarding the first transmitting component

[0057] The first emitting assembly emits high flux incident X-rays. In some real-time examples, the first emitting assembly includes an emitter capable of emitting high flux incident X-rays with a continuous spectrum. The emitter may be a tube, also known as an X-ray tube or an X-ray tube. In order to improve the collimation effect of the incident X-rays, the light is maximized in efficiency. coupling In order to enter the required device or receive the optical signal with maximum efficiency, in this embodiment, the first transmitting component also includes a collimating mold, which is arranged behind the tube to collimate the X-ray cone beam emitted by the tube, so that the divergent light becomes parallel light to obtain the incident X-ray.

[0058] (2) About the filter pixel component

[0059] The filter pixel assembly includes a substrate and a macro-pixel disposed on the substrate; the substrate is located on the emitting side of the first emitting assembly. In some embodiments, the substrate is located on the side of the collimator mold away from the emitter. The substrate includes a plate body and a matrix of grooves disposed on the plate body; the macro-pixel includes a plurality of sub-filters with different attenuation coefficients, each sub-filter includes a plurality of sub-filters and constitutes a sub-pixel, and the sub-filters are disposed in the grooves in a one-to-one correspondence;

[0060] In implementation, the preparation of the filter pixel component may include the following steps:

[0061] S101, processing k*k substrate, also known as filter board mold;

[0062] In some embodiments, the size and shape of the filter plate mold are set according to actual use requirements. In this embodiment, the size and shape of the filter plate mold are set to match the TFT (TFT) circuit board. Wherein, m ≥ 64, and commonly used sizes are 64*64, 96*96, and 218*218. The larger the m value, the better the imaging effect.

[0063] In implementation, refer to Figure 1 The filter plate mold can be a flat plastic plate obtained by 3D printing. The flat plastic plate constitutes a substrate. The substrate has k*k grooves arranged in a matrix. Each groove is equivalent to a pixel. In some embodiments, each groove is only tens to hundreds of microns, which is very small.

[0064] S102, determining the number of types of filter materials corresponding to the filled sub-filters, and preparing the sub-filters;

[0065] In some embodiments, there may be 4-9 types, which are set according to the test requirements; Figure 2 In this embodiment, there are four types of filter materials, the filter materials corresponding to the four sub-filters are Al (aluminum), Cu (copper), Au (gold), and Ta (tantalum), and four sub-filters are manufactured using the four filter materials;

[0066] In some implementations, the filter material used for filling can be selected from elements with atomic numbers ranging from a=40 (Zr) to a=83 (Bi) (excluding radioactive and a few scarce elements). During the preparation of the sub-filter:

[0067] Metals that can be formed into sheets are directly used as filters, such as Nb (niobium), Mo (molybdenum), Ag (silver), In (indium), Sn (tin), Te (tellurium), Ta (tantalum), W (tungsten), Au (gold), Pb (lead), etc.

[0068] Metal elements that cannot be directly formed into sheets can be prepared by mixing their oxides, chlorides or sulfates with PVB and pressing them into sheets. Specifically:

[0069] Prepared by mixing their oxides with PVB and pressing them into tablets, such as: ZrO2 (zirconium dioxide), RuO2 (ruthenium dioxide), CdO (chromium oxide), Sb2O3 (antimony trioxide), La2O3 (lanthanum trioxide), CeO2 (cerium dioxide), Pr6O4 (praseodymium tetroxide), Nd2O3 (neodymium trioxide), Sm2O3 (samarium trioxide), Eu2O3 (europium trioxide), Gd2O3 (gadolinium trioxide), Dy2O3 (dysprosium trioxide), Ho2O3 (holmium trioxide), Er2O3 (erbium trioxide), Tm2O3 (thulium trioxide), Yb2O3 (ytterbium trioxide), Lu2O3 (lutetium trioxide), HfO2 (hafnium dioxide), IrO2 (iridium dioxide), Bi2O3 (bismuth trioxide);

[0070] Prepared by mixing its chloride with PVB and pressing it into tablets, such as PdCl2 (lead dichloride), CsCl (cesium chloride), TiCl (thallium chloride);

[0071] In the form of tablets mixed with PVB, for example, BaSO4 (barium sulfate) and HgSO4 (mercury sulfate);

[0072] In some embodiments, the mass ratio of the element compound (oxide, chloride or sulfate) to PVB is 1:0.4-0.6. In this embodiment, the mass ratio is 1:0.5.

[0073] S103, loading;

[0074] The sub-filters are installed in the grooves on the plate body in a one-to-one correspondence, and the sub-filters form a plurality of repeating units, each of which includes one of each sub-filter type;

[0075] In this embodiment, referring to Figure 2 , fill the grooves of the board body with four pre-prepared sub-filters in a specific array order (2*2) to obtain a filter pixel component;

[0076] In some embodiments, the relative positions of the four seed filters can be adjusted without affecting the imaging results. The specific array order essentially requires that each seed filter be distributed as evenly as possible on the entire pixel panel. Therefore, in another embodiment, the specific array order of the four seed filters can also refer to Figure 3 , set to 1*4; for 4 seed filters, the specific array order of filling can be 3*3; for 4 seed filters, the specific array order of filling can be 2*3;

[0077] After filling, all the pixel points corresponding to each sub-filter constitute a sub-pixel, and four sub-pixels form a larger macro-pixel.

[0078] The incident X-ray is filtered and modulated by the macro-pixel and then passes through the imaging object to form a plurality of outgoing X-rays based on different sub-pixels;

[0079] (3) Regarding the area array detection component, the area array detection component detects the plurality of outgoing X-rays to obtain imaging information. In some embodiments, the area array detection component includes a detection module, an acquisition module, and a calculation module;

[0080] (3.1) About the detection module

[0081] The detection module detects each of the emitted X-rays to obtain a corresponding first electrical signal F i , i∈(1,n), in this embodiment, the detection module may be a planar array detector, n=4, and the first electrical signal obtained synchronously includes {F1, F2, F3, F4};

[0082] (3.2) About obtaining modules

[0083] The acquisition module obtains the energy spectrum of the blank outgoing X-ray based on different energy windows, where:

[0084] (3.2.1) The k absorption limits corresponding to the various seed filters divide the energy range of the incident X-ray into multiple energy windows. In this embodiment, the energy range of the incident X-ray is set to (E min ,E max ), in (E min ,E max ) energy range, the four seed filters divide the energy range into five energy windows W based on the K absorption limit. j , j∈(1,5), that is, 5 energy windows W j Sequentially record them as {W1, W2, W3, W4, W5}. Specifically, (E min ,E max ) is 0-100KeV as an example, 5 energy windows W j The corresponding values ​​are {0-K1, K1-K2, K2-K3, K3-K4, K4-100KeV}, i.e., {0-1.562KeV, 1.562-9.883KeV, 9.883-67.405KeV, 67.405-80.729KeV, 80.729-100KeV}. In some embodiments, the n seed filters divide the energy range into m energy windows W based on the K absorption limit. j , j∈(1,m), the specific number relationship is determined according to the actual size relationship;

[0085] (3.2.2) The energy spectra of the blank outgoing X-rays based on different energy windows are determined by a dot matrix detection mechanism. The acquisition module acquires the energy spectra of the blank outgoing X-rays based on different energy windows from the dot matrix detection mechanism. In some real-time examples, the dot matrix detection mechanism includes a blank detection module, an attenuation constant determination module, and an energy spectrum inversion module.

[0086] First, regarding the blank detection module, the blank detection module detects the blank emitted X-rays to obtain a second electrical signal S i , i∈(1,n), in some embodiments, the blank detection module includes a second emission component, a plurality of single filters, and a dot matrix detector;

[0087] The second emitting assembly emits high flux incident X-rays. In some embodiments, the second emitting assembly includes an emitter capable of emitting high flux incident X-rays with a continuous spectrum. The emitter may be a tube, also known as an X-ray tube or an X-ray tube. In order to improve the collimation effect of the incident X-rays, the light is maximized in efficiency. coupling In order to enter the required device or to receive the optical signal with maximum efficiency, in this embodiment, the second transmitting assembly further includes a collimating mold, which is arranged behind the tube and collimates the X-ray cone beam emitted by the tube, so that the divergent light becomes parallel light to obtain the incident X-ray;

[0088] The attenuation coefficients of the multiple single filters correspond one-to-one to the attenuation coefficients of the multiple sub-filters. In this embodiment, the multiple single filters are four types of single filters, and the corresponding filter materials are Al (aluminum), Cu (copper), Au (gold), and Ta (tantalum).

[0089] In implementation, multiple single filters are sequentially arranged on the emission side of the second emission assembly. In this embodiment, they are arranged on the side of the corresponding collimator mold away from the corresponding emitter, so that the incident X-ray is filtered and modulated by each single filter to obtain the corresponding blank emission X-ray; the dot matrix detector detects the blank emission X-ray to obtain the second electrical signal S i , i∈(1,n), in this embodiment, the incident X-rays generated by the tube are collimated by the collimation mold, and then partially attenuated by the single filter. The outgoing X-rays are detected by the detector, and the second electrical signal S of the outgoing X-rays is obtained. i , i∈(1,n), n=4, the second electrical signal is {S1, S2, S3, S4};

[0090] Among them, any single filter Z i , i∈(1,4) corresponds to the second electrical signal S i For example, the acquisition:

[0091]

[0092] In formula (1), ∫ is the integral symbol; η is the proportional coefficient; is the incident X-ray energy spectrum (to be solved); E is the energy of the incident X-ray; E min ,E max It is obtained by setting the tube. In this embodiment, it can be set to 0-100KeV, that is, E min =0KeV, E max =100KeV;

[0093] μ i (E) is a single filter Z i The attenuation coefficient, d i For a single filter Z i The thickness of the single filter Z i The attenuation of incident X-rays with energy E is E×e -μi(E)di ;

[0094] Let C i (E) = E × e -μi(E)di , then formula (1) can be simplified as:

[0095]

[0096] In summary, the four second electrical signals of the outgoing X-rays are obtained, which are:

[0097]

[0098] Second, regarding the attenuation constant determination module, the attenuation constant determination module is used to determine the attenuation constant C of each blank emitted X-ray based on different energy windows. ij , i∈(1,n), j∈(1,m);

[0099] In some embodiments, it is approximately considered that E on a specific energy window is a constant, and the attenuation coefficient of a single filter can be found, so it is approximately considered that each single filter Z i In each energy window W j C in (j∈(1,m)) i (E) = (E × e -μi(E)di ) is a constant, denoted as C i (E)=C ij .

[0100] In this embodiment, taking i=1 as an example, C i (E)=C ij Include {C 11 、C 12 、C 13 、C 14 、C 15}, a total of 5 items, namely Specifically include:

[0101]

[0102] at this time In each energy window, it is a constant value, and discretization is performed, so have to:

[0103]

[0104] The above formula includes:

[0105]

[0106] Third, about the energy spectrum inversion module

[0107] The energy spectrum inverse solution module is based on the formula Inverse solution to obtain the energy spectrum

[0108] In this embodiment, the energy spectrum inversion module is based on Four types of acquisition:

[0109]

[0110] Solve the least squares solution to obtain the energy spectrum of the incident X-ray

[0111] (3.3) A computing module connected to the detection module and the acquisition module, the computing module obtains imaging information based on the first electrical signal and the energy spectrum;

[0112] In the implementation, the detection module detects once, and the first electrical signal F detected by the detection module i ; i∈(1,m), recorded as:

[0113]

[0114] The above formula includes:

[0115]

[0116] Combine the above m formulas into the following formula:

[0117] Based on Inverse solution to obtain imaging information D ij , i∈(1,n), j∈(1,m), where F i , i∈(1,n) is the first electrical signal.

[0118] In this embodiment, the first electrical signal F i ; i∈(1,4), recorded as:

[0119]

[0120] The above formula includes:

[0121]

[0122] Combine the above four equations into the following equation:

[0123] Inverse solution to obtain imaging information D ij , i∈(1,n), j∈(1,5);

[0124] Based on the above including C 11 、C 12 、C 13 、C 14 、C 15 ;

[0125] C 21 、C 22 、C 23 、C 24 、C 25 ;

[0126] C 31 、C 32 、C 33 、C 34 、C 35 ;

[0127] C 41 、C 42 、C 43 、C 44 、C 45 , constituting imaging information;

[0128] In summary, first, a blank experiment is performed with a single filter without adding an imaging object, with the aim of inversely obtaining the spectra. Then, after adding an imaging object, the imaging information of the imaging object is obtained based on the spectra obtained from the blank experiment and the detected electrical signals.

[0129] (4) In some embodiments, the multi-energy spectrum X-ray array imaging system further includes a fusion component, which uses an algorithm to fuse imaging information to obtain a color image, that is, the collected grayscale value image (imaging information) is processed by the algorithm, and different grayscale values ​​(substances) are assigned different colors. Finally, a true color image with obvious material distinction can be obtained, which has strong application value.

[0130] The implementation principle of Example 1 of the present application is: a multi-spectrum X-ray array imaging method, comprising the following steps:

[0131] Step 1: Prepare filter pixel components

[0132] Processing k*k substrate;

[0133] Determining the number of types of filter materials corresponding to the filled sub-filters and preparing the sub-filters;

[0134] The sub-filters are mounted one by one on the substrate to form a filter pixel assembly, wherein all the pixel points corresponding to each sub-filter constitute a sub-pixel, and four sub-pixels form a larger macro-pixel;

[0135] Step 2: Build a blank detection module, that is, build a blank detection system, which includes a second emission component, multiple single filters, and a dot matrix detector;

[0136] The second transmitting assembly includes a tube and a collimator. The tube emits high-flux incident X-rays with a continuous spectrum. The collimator is located behind the tube to receive and collimate the incident X-rays.

[0137] Multiple single filters are selectively placed one by one behind the collimating mold to filter and modulate the collimated incident X-rays to obtain blank outgoing X-rays;

[0138] The dot matrix detector is located behind the single filter, receiving the blank outgoing X-rays and detecting the corresponding second electrical signal S i , the dot matrix detector can specifically be an integral type detector;

[0139] Step 3: Approximately consider that each single filter Z i In each energy window W j C in (j∈(1,m)) i (E) = (E × e -μi(E)di ) is a constant, denoted as C i (E)=C ij The attenuation constant determination module determines the attenuation constant C of each blank outgoing X-ray based on different energy windows. ij , i∈(1,n), j∈(1,m);

[0140] Step 4: The energy spectrum inverse solution module obtains the energy spectrum based on the second electrical signal and the attenuation constant.

[0141] Step 5: Build an imaging test system, which includes a first emission component, a filter pixel component, and an array detection component;

[0142] The first emitting assembly includes a tube and a collimating mold. The tube emits X-rays with a continuous spectrum and high flux. The collimating mold is located behind the tube and collimates the X-rays emitted by the tube to convert the divergent light into parallel light.

[0143] The filter pixel component is located behind the collimator mold to filter and modulate the high-flux X-rays; the imaging object is located behind the filter pixel component;

[0144] The area array detection assembly includes a detection module, an acquisition module, and a calculation module; the detection module obtains a first electrical signal corresponding to an outgoing X-ray; the acquisition module obtains a partial energy spectrum of a blank outgoing X-ray based on different energy windows; the calculation module is connected to the detection module and the acquisition module, and the calculation module obtains imaging information based on the first electrical signal and the partial energy spectrum;

[0145] Step 6: Imaging test

[0146] The detection module performs a single detection to obtain a first electrical signal of the emitted X-rays. The calculation module is connected to the detection module and the acquisition module. The calculation module obtains imaging information based on the first electrical signal and the energy spectrum. That is, overall, a blank experiment is first performed with a single filter without adding an imaging object to inversely obtain the energy spectrum. Then, after adding an imaging object, the imaging information of the imaging object can be obtained based on the energy spectrum obtained in the blank experiment and the detected electrical signal.

[0147] Example 2:

[0148] Example 2 of the present application discloses a multi-spectrum X-ray area array imaging system. Unlike Example 1, the multi-spectrum X-ray area array imaging system further includes a first tungsten steel collimation assembly, comprising a first tungsten steel plate and a plurality of first collimation holes arranged in a matrix extending through the first tungsten steel plate. The first tungsten steel plate is disposed on a side of the filter pixel assembly away from the first emission assembly.

[0149] Example 3:

[0150] Example 3 of the present application discloses a multi-spectrum X-ray area array imaging system. Unlike Example 2, the multi-spectrum X-ray area array imaging system further includes a second tungsten steel collimation assembly, comprising a second tungsten steel plate and a plurality of second collimation holes arranged in a matrix extending through the second tungsten steel plate. The second tungsten steel plate is disposed on a side of the imaging object away from the filter pixel assembly.

[0151] Reference Figure 5 , is the image obtained without filter pixel components. After adding the pixel filter board, the energy window is between aluminum and copper, between copper and gold, and between gold and tantalum, and the corresponding images are as follows: Figure 6 、 Figure 7 、 Figure 8 As shown, it vividly demonstrates that the imaging method corresponding to the multi-energy spectrum X-ray array imaging system can realize density recognition under high-flux photons, and is expected to be applied to human medical imaging in the future, such as obtaining images of only lungs or only bones during chest X-ray.

[0152] The examples of this specific embodiment are all preferred embodiments of this application and are not intended to limit the scope of protection of this application. Identical components are represented by the same reference numerals. Therefore, any equivalent changes made based on the structure, shape, and principle of this application should be included in the scope of protection of this application.

Claims

1. Multi-spectrum X-ray array imaging system, characterized by: include: a first emitting assembly for emitting high flux incident X-rays; a filter pixel assembly comprising a substrate located on the emitting side of the first emitting assembly, and a macro-pixel disposed on the substrate, the macro-pixel comprising a plurality of sub-filters having different attenuation coefficients, each sub-filter comprising a plurality of sub-filters constituting a sub-pixel; wherein the incident X-ray is filtered and modulated by the macro-pixel before passing through an imaging object to form a plurality of outgoing X-rays based on different sub-pixels; An array detector, configured to detect a plurality of the emitted X-rays to obtain imaging information; The k absorption limits corresponding to the multiple seed filters divide the energy range of the incident X-ray into multiple energy windows; The area array detector comprises: a detection module, configured to detect each of the emitted X-rays to obtain a corresponding first electrical signal; An acquisition module is used to obtain energy spectra of blank emitted X-rays based on different energy windows; a calculation module, connected to the detection module and the acquisition module, and configured to obtain imaging information based on the first electrical signal and the energy spectrum; The acquisition module includes: The blank detection unit is used to detect the blank emitted X-rays to obtain the second electrical signal S i , i∈(1,n) ; Attenuation constant determination unit, used to determine the attenuation constant of each blank outgoing X-ray based on different energy windows ，i∈ (1,n), j∈(1,m) ; The energy spectrum inverse solution unit is used based on the formula , i∈(1,n), j∈(1,m), inverse solution to obtain the energy spectrum ,j∈(1,m) , where n is the number of sub-pixels ， m is the number of energy windows; The blank detection unit comprises: a second emitting assembly for emitting high flux incident X-rays; a plurality of single filters, each of which has a one-to-one correspondence with an attenuation coefficient of each of the plurality of seed filters, wherein the plurality of single filters are sequentially arranged on the emission side of the second emission assembly, so that the incident X-ray is filtered and modulated by each of the single filters to obtain a corresponding blank emission X-ray; Dot matrix detector, used to detect blank outgoing X-rays to obtain the second electrical signal S i , i∈(1,n) .

2. The multi-spectral X-ray array imaging system according to claim 1, characterized in that: The calculation module is configured to obtain imaging information based on the first electrical signal and the energy spectrum, including: Based on , i∈(1,n), j∈(1,m), inverse solution to obtain imaging information , i∈(1,n), j∈(1,m), where, F i , i∈(1,n) is the first electrical signal.

3. The multi-spectral X-ray array imaging system according to claim 1, characterized in that: It also includes a fusion component for obtaining an image based on the imaging information.

4. The multi-spectral X-ray array imaging system according to any one of claims 1 to 3, characterized in that: The substrate comprises a plate body and grooves arranged in a matrix on the plate body, and the sub-filters are arranged in the grooves in a one-to-one correspondence.

5. The multi-spectral X-ray array imaging system according to claim 4, characterized in that: The sub-filters arranged in the grooves form a plurality of repeating units, and each of the repeating units includes one of each type of sub-filter.

6. The multi-spectral X-ray array imaging system according to any one of claims 1 to 3, characterized in that: It also includes a first tungsten steel collimation component, which includes a first tungsten steel plate and a plurality of first collimation holes arranged in a matrix arranged through the first tungsten steel plate, wherein the first tungsten steel plate is attached to the side of the filtering pixel component away from the first emission component.

7. The multi-spectral X-ray array imaging system according to claim 6, characterized in that: It also includes a second tungsten steel collimation component, which includes a second tungsten steel plate and a plurality of second collimation holes arranged in a matrix arranged through the second tungsten steel plate, wherein the second tungsten steel plate is attached to the side of the imaging object away from the filtering pixel component.

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