CN215680693U - Dual-energy detector, dual-energy X-ray imaging system thereof and food detection device - Google Patents
Dual-energy detector, dual-energy X-ray imaging system thereof and food detection device Download PDFInfo
- Publication number
- CN215680693U CN215680693U CN202121036367.0U CN202121036367U CN215680693U CN 215680693 U CN215680693 U CN 215680693U CN 202121036367 U CN202121036367 U CN 202121036367U CN 215680693 U CN215680693 U CN 215680693U
- Authority
- CN
- China
- Prior art keywords
- dual
- transistor layer
- energy
- film transistor
- thin
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Images
Landscapes
- Measurement Of Radiation (AREA)
Abstract
The utility model provides a dual-energy detector, a dual-energy X-ray imaging system thereof and a food detection device, wherein the dual-energy detector comprises at least one sensor, each sensor comprises a scintillator, a first thin film transistor layer and a second thin film transistor layer, the scintillator is clamped between the first thin film transistor layer and the second thin film transistor layer to form a sandwich structure, visible light signals generated by the scintillator are received by the first thin film transistor layer and the second thin film transistor layer and generate electric signals for imaging, and one-time dual-energy signal collection is realized. The utility model simplifies the existing manufacturing process of the detector, makes the internal structure more compact, and can effectively reduce the influence of blurring and the like caused by crosstalk of scattering signals through the more compact structure, so that the imaging is clearer. Meanwhile, the structure design can separate high and low energy spectrums, and an overlapping area is reduced as much as possible.
Description
Technical Field
The utility model relates to the field of X-ray imaging systems in food detection devices, in particular to a dual-energy detector, a dual-energy X-ray imaging system and a food detection device.
Background
In the prior art, on an X-ray food detection device, a dual-energy detector system is used, different information is obtained through the difference of high and low energy imaging, and then an image obtained by subtracting the two is obtained through an image processing technology, so that more information about products can be obtained.
Generally, when the spectrum of the X-ray is continuously distributed, for example, when the X-ray imaging is excited by using a voltage of 100kV, the generated spectrum of the X-ray is a continuously distributed line ranging from 0 to 100kV, such a radiation is a continuous multi-color spectrum, each component of which contributes to the imaging, and the presented image is a comprehensive effect, and some specific information which can be represented in a certain energy band is lost.
In practice, however, the effect of imaging on the high and low energy segments is different if we look at the rays separately in terms of energy, for example in the energy interval of 30-40kV and 80-100 kV. The high energy end imaging is mainly relatively effective for hard tissue, while the low energy end imaging is relatively effective for soft tissue, so that the segmented imaging of separated energies is helpful for obtaining more information, and has great use in medical imaging to distinguish soft tissue from hard tissue.
Fig. 1 is a schematic diagram of the attenuation of X-rays. As shown in fig. 1, the attenuation ratio of the high energy spectrum and the low energy spectrum is different, the attenuation of the high energy band X-ray by the high density foreign matter is not obvious, and the attenuation of the low energy band photon by the high density foreign matter is obvious, so that better contrast information can be obtained.
At present, dual-energy detectors used in existing dual-energy X-ray imaging systems are generally classified into the following two types:
the first is the top-bottom sensor configuration, as shown in fig. 2, in which the two layers of scintillators are separated and there is a gap between them, so that X-rays will be scattered while passing through the first layer, and the scattered light will strike the second layer of scintillators, thus generating false signals, which need to be corrected by designing a special algorithm. The other mode for reducing scattering is to add a metal filter between two layers to absorb scattered rays, but the metal filter can generate photoelectrons due to photoelectric effect, and the photoelectrons can be absorbed by the lower layer, so that the filter only lightens the influence of signal interference to a certain extent and cannot completely eliminate the influence.
As shown in fig. 3, the second type is a left-right distributed sensor structure, which has the problem that the high-energy and low-energy scintillators are placed side by side, a certain gap is left between the two scintillators to avoid crosstalk of scattered signals, and X-rays in the gap part directly penetrate through the gap part and are not received, thereby causing signal waste to a certain extent. This design is more severe in situations where the incident X-ray intensity is weak, and each scintillator falls short of 1/2. The strength of the generated electric signal is weak compared with that of the noise, and an associated amplifying circuit needs to be designed at the back end.
In view of this, the present application discloses people improved the sensor structure of dual energy detector to overcome above-mentioned technical problem.
SUMMERY OF THE UTILITY MODEL
The utility model aims to overcome the defects that a dual-energy detector in the prior art cannot eliminate signal interference, is easy to generate error signals, is weak in electric signal strength and the like, and provides the dual-energy detector, a dual-energy X-ray imaging system thereof and a food detection device.
The utility model solves the technical problems through the following technical scheme:
the utility model provides a dual-energy detector, its characterized in that, dual-energy detector includes at least one sensor, each the sensor includes scintillator, first thin-film transistor layer and second thin-film transistor layer, the scintillator clamp is established first thin-film transistor layer with form sandwich structure between the second thin-film transistor layer, the visible light signal that the scintillator produced by first thin-film transistor layer with second thin-film transistor layer is received and is produced the signal of telecommunication and be used for the formation of image, realizes disposable dual-energy signal collection.
According to one embodiment of the utility model, the first thin-film transistor layer is located on an upper end face of the scintillator, and the second thin-film transistor layer is located on a lower end face of the scintillator.
According to one embodiment of the utility model, the scintillator is CsI, Gd2O2S or CdWO4And (4) preparing.
According to one embodiment of the utility model, the thickness of the scintillator is in the range of 100-1000 mm.
According to an embodiment of the utility model, the first thin-film transistor layer and the second thin-film transistor layer are made of amorphous silicon.
According to one embodiment of the utility model, the first thin-film transistor layer collects low-energy signals and the second thin-film transistor layer collects high-energy signals.
According to one embodiment of the utility model, the dual energy detector satisfies the following formula:
IHo＝IH·exp(-UhdMhd-UIdMId)；ILo＝IL·exp(-U′IdMhd-U′IdMId)；
wherein U represents the equivalent mass attenuation coefficient of the substance to the X-ray;
m represents the areal density (g/cm) of the substance2)；
I represents the intensity of X-rays;
ho and Lo respectively represent the incident intensity and the emergent intensity of the X ray;
H. l represents subscripts of high and low energy X-rays, respectively;
hd. ld denotes the subscripts of the high and low density species.
The utility model also provides a dual-energy X-ray imaging system which is characterized by comprising the dual-energy X-ray imaging system.
The utility model also provides a food detection device which is characterized by comprising the dual-energy X-ray imaging system.
The positive progress effects of the utility model are as follows:
the dual-energy detector, the dual-energy X-ray imaging system and the food detection device simplify the existing manufacturing process of the detector, enable the internal structure to be more compact, and can effectively reduce the influence of blurring and the like caused by crosstalk of scattering signals through the more compact structure, so that imaging is clearer. Meanwhile, the structure design can separate high and low energy spectrums, and an overlapping area is reduced as much as possible.
Drawings
The above and other features, properties and advantages of the present invention will become more apparent from the following description of the embodiments with reference to the accompanying drawings in which like reference numerals denote like features throughout the several views, wherein:
fig. 1 is a schematic diagram of the attenuation of X-rays.
Fig. 2 is a schematic diagram of the structural distribution of sensors distributed up and down in the prior art.
Fig. 3 is a schematic diagram of a structural distribution of sensors distributed left and right in the prior art.
Fig. 4 is a schematic structural diagram of a sensor in the dual-energy detector of the present invention.
Fig. 5 is a schematic image flow diagram of the X-ray imaging system of the present invention.
Detailed Description
In order to make the aforementioned objects, features and advantages of the present invention comprehensible, embodiments accompanied with figures are described in detail below.
Embodiments of the present invention will now be described in detail with reference to the accompanying drawings. Reference will now be made in detail to the preferred embodiments of the present invention, examples of which are illustrated in the accompanying drawings. Wherever possible, the same reference numbers will be used throughout the drawings to refer to the same or like parts.
Further, although the terms used in the present invention are selected from publicly known and used terms, some of the terms mentioned in the description of the present invention may be selected by the applicant at his or her discretion, the detailed meanings of which are described in relevant parts of the description herein.
Furthermore, it is required that the present invention is understood, not simply by the actual terms used but by the meaning of each term lying within.
Fig. 4 is a schematic structural diagram of a sensor in the dual-energy detector of the present invention.
As shown in fig. 4, the present invention discloses a dual-energy detector, which includes at least one sensor, each of the sensors includes a scintillator 10, a first thin-film transistor layer 20 and a second thin-film transistor layer 30, the scintillator 10 is sandwiched between the first thin-film transistor layer 20 and the second thin-film transistor layer 30 to form a sandwich structure, a visible light signal generated by the scintillator 10 is received by the first thin-film transistor layer 20 and the second thin-film transistor layer 30 and generates an electrical signal for imaging, so as to implement a disposable dual-energy signal collection.
Preferably, the first thin-film-transistor layer 20 is located on an upper end surface of the scintillator 10, and the second thin-film-transistor layer 30 is located on a lower end surface of the scintillator 10. The scintillator 10 here preferably employs CsI, Gd2O2S or CdWO4And (4) preparing. The thickness range of the scintillator 10 is preferably 100-1000 mm.
In addition, the first thin-film-transistor layer 20 and the second thin-film-transistor layer 30 are preferably made of amorphous silicon. Where first thin-film-transistor layer 20 collects low-energy signals and second thin-film-transistor layer 30 collects high-energy signals.
The calculation of the dual-energy detector satisfies the following formula:
IHo＝IH·exp(-UhdMhd-UIdMId)；ILo＝IL·exp(-U′IdMhd-U′IdMId)；
wherein U represents the equivalent mass attenuation coefficient of the substance to the X-ray;
m represents the areal density (g/cm) of the substance2)；
I represents the intensity of X-rays;
ho and Lo respectively represent the incident intensity and the emergent intensity of the X ray;
H. l represents subscripts of high and low energy X-rays, respectively;
hd. ld denotes the subscripts of the high and low density species.
For example, for a certain point (X0, Y0), Ho and Lo attenuated by the point can be measured and solved by simultaneous equations, and M (X0, Y0) of a high-density foreign matter at the point can be obtained by eliminating the low-density Ms.
The utility model also provides a dual-energy X-ray imaging system comprising the dual-energy X-ray imaging system. The utility model also provides a food detection device comprising the dual-energy X-ray imaging system.
Fig. 5 is a schematic image flow diagram of the X-ray imaging system of the present invention.
As shown in fig. 5, the algorithm operation flow of the dual-energy X-ray imaging system of the present invention is specifically as follows:
firstly, the dual-energy detector obtains high energy and low energy, the voltage is set to be 100kV, the current is 1.5mA, and the continuous exposure mode is adopted. For example, the imaging subject is a pouched beef jerky. The X-ray is attenuated after passing through the bag, and the rest of the X-ray reaches the detector and is converted into high-low energy signals by the scintillator immediately, so that high-low energy imaging is obtained.
Then, the scintillator receiving unit for low-energy imaging is arranged at the lower end of the detector, so that the problem of magnification exists, relevant geometric correction needs to be carried out, and foreign matters can be clearly identified by subtracting the high-energy image after multiplying the image by the magnification.
According to the above description, the dual-energy detector of the present invention adopts a sandwich structure, the scintillator is in the center, and the thin film transistors are arranged above and below the scintillator for receiving signals. Therefore, visible light signals generated by the scintillator can be received by the upper and lower layers of thin film transistors and generate electric signals for imaging, dual-energy signal collection is realized at one time, and a two-layer sensor system is not required to be designed.
In summary, the dual-energy detector, the dual-energy X-ray imaging system and the food detection device of the utility model simplify the existing manufacturing process of the detector, so that the internal structure becomes more compact, and by the more compact structure, the influence of blurring and the like caused by crosstalk of scattering signals can be effectively reduced, so that the imaging is clearer. Meanwhile, the structure design can separate high and low energy spectrums, and an overlapping area is reduced as much as possible.
While specific embodiments of the utility model have been described above, it will be appreciated by those skilled in the art that these are by way of example only, and that the scope of the utility model is defined by the appended claims. Various changes and modifications to these embodiments may be made by those skilled in the art without departing from the spirit and scope of the utility model, and these changes and modifications are within the scope of the utility model.
Claims (9)
1. The utility model provides a dual-energy detector, its characterized in that, dual-energy detector includes at least one sensor, each the sensor includes scintillator, first thin-film transistor layer and second thin-film transistor layer, the scintillator clamp is established first thin-film transistor layer with form sandwich structure between the second thin-film transistor layer, the visible light signal that the scintillator produced by first thin-film transistor layer with second thin-film transistor layer is received and is produced the electric signal and be used for the formation of image, realizes disposable dual-energy signal collection.
2. The dual energy detector of claim 1, wherein the first thin film transistor layer is located on an upper end face of the scintillator and the second thin film transistor layer is located on a lower end face of the scintillator.
3. The dual energy detector of claim 1, wherein the scintillator is CsI, Gd2O2S or CdWO4And (4) preparing.
4. The dual energy detector of claim 1, wherein the scintillator has a thickness in the range of 100 and 1000 mm.
5. The dual energy detector of claim 1, wherein the first thin-film transistor layer and the second thin-film transistor layer are made of amorphous silicon.
6. The dual-energy detector of claim 1, wherein the first thin-film-transistor layer collects low-energy signals and the second thin-film-transistor layer collects high-energy signals.
7. The dual energy detector of claim 1, wherein the dual energy detector satisfies the following equation: i isHo＝IH·exp(-UhdMhd-UIdMId)；ILo＝IL·exp(-U′IdMhd-U′IdMId)；
Wherein U represents the equivalent mass attenuation coefficient of the substance to the X-ray;
m represents the areal density (g/cm) of the substance2)；
I represents the intensity of X-rays;
ho and Lo respectively represent the incident intensity and the emergent intensity of the X ray;
H. l represents subscripts of high and low energy X-rays, respectively;
hd. ld denotes the subscripts of the high and low density species.
8. A dual energy X-ray imaging system, characterized in that it comprises a dual energy detector according to any of claims 1-7.
9. A food inspection device characterized in that it comprises the dual energy X-ray imaging system of claim 8.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202121036367.0U CN215680693U (en) | 2021-05-14 | 2021-05-14 | Dual-energy detector, dual-energy X-ray imaging system thereof and food detection device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202121036367.0U CN215680693U (en) | 2021-05-14 | 2021-05-14 | Dual-energy detector, dual-energy X-ray imaging system thereof and food detection device |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN215680693U true CN215680693U (en) | 2022-01-28 |
Family
ID=79972115
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202121036367.0U Active CN215680693U (en) | 2021-05-14 | 2021-05-14 | Dual-energy detector, dual-energy X-ray imaging system thereof and food detection device |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN215680693U (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN115425035A (en) * | 2021-05-14 | 2022-12-02 | 梅特勒-托利多(常州)测量技术有限公司 | Dual-energy detector, dual-energy X-ray imaging system thereof and food detection device |
-
2021
- 2021-05-14 CN CN202121036367.0U patent/CN215680693U/en active Active
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN115425035A (en) * | 2021-05-14 | 2022-12-02 | 梅特勒-托利多(常州)测量技术有限公司 | Dual-energy detector, dual-energy X-ray imaging system thereof and food detection device |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| So et al. | Spectral computed tomography: fundamental principles and recent developments | |
| US7613274B2 (en) | Method and system of energy integrating and photon counting using layered photon counting detector | |
| Jakubek | Data processing and image reconstruction methods for pixel detectors | |
| Johns et al. | Coherent scatter in diagnostic radiology | |
| Moy | Signal‐to‐noise ratio and spatial resolution in x‐ray electronic imagers: Is the MTF a relevant parameter? | |
| Hunt et al. | Evaluation of the imaging properties of an amorphous selenium‐based flat panel detector for digital fluoroscopy | |
| US5825032A (en) | Radiographic apparatus and image processing method | |
| Shikhaliev | Tilted angle CZT detector for photon counting/energy weighting x-ray and CT imaging | |
| JP2008510132A (en) | Anti-scatter grid for radiation detectors | |
| GB2338298A (en) | Removing X-ray Cross-talk in Low Energy X-ray Detectors | |
| Han et al. | Single-shot dual-energy x-ray imaging with a flat-panel sandwich detector for preclinical imaging | |
| JPH0527043A (en) | K-absorption edge filter and x-ray device | |
| Seferis et al. | On the response of a europium doped phosphor-coated CMOS digital imaging detector | |
| US20160206255A1 (en) | Hybrid passive/active multi-layer energy discriminating photon-counting detector | |
| Schumacher et al. | Photon counting and energy discriminating x-ray detectors-benefits and applications | |
| CN215680693U (en) | Dual-energy detector, dual-energy X-ray imaging system thereof and food detection device | |
| CN113237903B (en) | Double-layer flat panel detector cone-beam CT-based scattering correction method and device | |
| Hunt et al. | X‐ray imaging using avalanche multiplication in amorphous selenium: Investigation of depth dependent avalanche noise | |
| KR20160056194A (en) | Multi-layer flat-panel X-ray detector and multi-energy X-ray imaging method using the same | |
| Kim et al. | Signal and noise analysis of flat-panel sandwich detectors for single-shot dual-energy x-ray imaging | |
| RU2407437C2 (en) | Method of registering x-ray image of object in various ranges of x-ray irradiation spectrum | |
| CN115425035A (en) | Dual-energy detector, dual-energy X-ray imaging system thereof and food detection device | |
| Nagarkar et al. | CCD-based high resolution digital radiography system for non destructive evaluation | |
| Avila et al. | Contrast cancellation technique applied to digital x‐ray imaging using silicon strip detectors | |
| Tsutsui et al. | CdTe semiconductor X-ray imaging sensor and energy subtraction method using X-ray energy information |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| GR01 | Patent grant | ||
| GR01 | Patent grant |