CN111896991A - Radiation imaging detection method and device - Google Patents
Radiation imaging detection method and device Download PDFInfo
- Publication number
- CN111896991A CN111896991A CN202010735827.2A CN202010735827A CN111896991A CN 111896991 A CN111896991 A CN 111896991A CN 202010735827 A CN202010735827 A CN 202010735827A CN 111896991 A CN111896991 A CN 111896991A
- Authority
- CN
- China
- Prior art keywords
- detector
- counting
- integration
- signal
- processing
- 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.)
- Pending
Links
- 238000003384 imaging method Methods 0.000 title claims abstract description 97
- 230000005855 radiation Effects 0.000 title claims abstract description 76
- 238000001514 detection method Methods 0.000 title claims abstract description 57
- 238000010191 image analysis Methods 0.000 claims abstract description 27
- 230000010354 integration Effects 0.000 claims description 107
- 238000012545 processing Methods 0.000 claims description 69
- 238000000034 method Methods 0.000 claims description 48
- 230000008569 process Effects 0.000 claims description 27
- 238000005070 sampling Methods 0.000 claims description 6
- XUIMIQQOPSSXEZ-UHFFFAOYSA-N Silicon Chemical compound [Si] XUIMIQQOPSSXEZ-UHFFFAOYSA-N 0.000 claims description 4
- 229910052710 silicon Inorganic materials 0.000 claims description 4
- 239000010703 silicon Substances 0.000 claims description 4
- 230000002596 correlated effect Effects 0.000 claims description 3
- 239000013307 optical fiber Substances 0.000 claims description 2
- 239000002245 particle Substances 0.000 abstract description 26
- 238000005259 measurement Methods 0.000 abstract description 11
- 239000000126 substance Substances 0.000 abstract description 7
- 238000010586 diagram Methods 0.000 description 20
- 239000003990 capacitor Substances 0.000 description 5
- 230000000875 corresponding effect Effects 0.000 description 4
- 238000005516 engineering process Methods 0.000 description 4
- 239000013078 crystal Substances 0.000 description 3
- 239000000463 material Substances 0.000 description 3
- 230000003321 amplification Effects 0.000 description 2
- 230000002238 attenuated effect Effects 0.000 description 2
- 230000005540 biological transmission Effects 0.000 description 2
- 230000008878 coupling Effects 0.000 description 2
- 238000010168 coupling process Methods 0.000 description 2
- 238000005859 coupling reaction Methods 0.000 description 2
- 238000003199 nucleic acid amplification method Methods 0.000 description 2
- 239000000523 sample Substances 0.000 description 2
- 238000007493 shaping process Methods 0.000 description 2
- 229910004613 CdTe Inorganic materials 0.000 description 1
- 229910001218 Gallium arsenide Inorganic materials 0.000 description 1
- 238000009825 accumulation Methods 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 238000013461 design Methods 0.000 description 1
- 239000000284 extract Substances 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 230000004044 response Effects 0.000 description 1
- 239000004065 semiconductor Substances 0.000 description 1
- 238000001228 spectrum Methods 0.000 description 1
Images
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/24—Measuring radiation intensity with semiconductor detectors
- G01T1/246—Measuring radiation intensity with semiconductor detectors utilizing latent read-out, e.g. charge stored and read-out later
Abstract
The application provides a radiation imaging detection method and a radiation imaging detection device, wherein two channels are integrated at one end of a detector, or the integral and the count value of rays or particles in a certain time are respectively and simultaneously collected at the two ends of the detector for carrying out image analysis and reconstruction, so that the measurement with high intensity and large dynamic range can be realized, the information such as particle energy can be acquired at relatively low count rate, better image and substance component resolution can be realized, and the dose required by radiation imaging can be reduced. Therefore, the resolution of the image can be improved on the premise of reducing the dosage required by radiation imaging.
Description
Technical Field
The present invention relates to the field of radiation imaging technology, and in particular, to a radiation imaging detection method and apparatus.
Background
In a radiation imaging system, the transmission, scattering or diffraction image formed after the ray or particle and the detected object react is often related to the internal structure and composition of the substance; whereas transmission, scatter or diffraction images are typically detected by the distribution of the position of the radiation intensity.
The existing radiation intensity measurement mainly has two independent modes of integration and counting, taking X-ray imaging as an example:
the integration type detection integrates the current generated by all X-ray photons over a period of time, and the charge value obtained by the integration is taken as the intensity of the X-ray.
The integral detection has simple structure and wide detectable intensity range, and is the main mode adopted by the medical and industrial X-ray imaging system at present. However, this detection method cannot distinguish between individual X-ray energies, so that other methods are required to achieve dual-energy detection, which means higher radiation doses are required.
Counting-type detection amplifies and discriminates the signal generated by each X-ray photon in the detector and records the number of photons over a period of time as the intensity of the X-ray.
The counting type detection can obtain the energy information of single X-ray, and dual-energy or even multi-energy imaging can be realized by setting a plurality of energy window thresholds, so that the image resolution is improved, and the dosage is reduced. However, this detection method has a high requirement on the time response of the detector, and as the intensity of the incident X-ray increases, the accumulation of the detector signal becomes severe, resulting in a loss of count and a distortion of the energy spectrum.
Disclosure of Invention
In view of the above, the present application provides a radiation imaging detection method and apparatus, which can improve the resolution of an image on the premise of reducing the dose required for radiation imaging.
In order to solve the technical problem, the technical scheme of the application is realized as follows:
in one embodiment, a radiation imaging detection method is provided, wherein two signal processing channels are integrated in a read-out circuit of a detector, wherein the two signal processing channels are an integration channel and a counting channel; the method comprises the following steps:
integrating the detector signal through the integration channel;
counting the detector signals through the counting channel;
and outputting an integration result of the integration processing and a counting result of the counting processing to the imaging platform, and enabling the imaging platform to perform image analysis and reconstruction according to the set range of the radiation intensity, the integration result and the counting result.
In another embodiment, there is provided a radiation imaging detection method, the method comprising:
reading out detection detector signals from two ends of the detector respectively;
performing integration processing when a detector signal is read out through one end of the optical fiber;
counting is carried out when the other end reads out the signal of the detector;
and outputting an integration result of the integration processing and a counting result of the counting processing to the imaging platform, and enabling the imaging platform to perform image analysis and reconstruction according to the set range of the radiation intensity, the integration result and the counting result.
In another embodiment, a radiation imaging detection apparatus is provided, wherein two signal processing channels are integrated in a readout circuit of a detector, wherein the two signal processing channels are an integration channel and a counting channel; the device comprises: an integrating unit, a counting unit and an output unit;
the integration unit is used for carrying out integration processing on the detector signal through the integration channel;
the counting unit is used for counting the detector signals through the counting channel;
the output unit is used for outputting an integration result of the integration processing performed by the integration unit and a counting result of the counting processing performed by the counting unit to the imaging platform, so that the imaging platform performs image analysis and reconstruction according to the set range of the radiation intensity, the integration result and the counting result.
In another embodiment, a radiation imaging detection apparatus is provided, which reads out detection detector signals from a detector through two ends respectively; the device comprises: an integrating unit, a counting unit and an output unit;
the integration unit is used for performing integration processing when a detector signal is read out through one end of the detector;
the counting unit is used for counting when the other end of the detector reads out the detector signal;
the output unit is used for outputting an integration result of the integration processing performed by the integration unit and a counting result of the counting processing performed by the counting unit to the imaging platform, so that the imaging platform performs image analysis and reconstruction according to the set range of the radiation intensity, the integration result and the counting result.
According to the technical scheme, the two channels are integrated at one end of the detector, or the integral sum and the count value of rays or particles in a certain time are respectively and simultaneously collected at the two ends of the detector for image analysis and reconstruction, so that the measurement with high intensity and large dynamic range can be realized, the information such as particle energy can be acquired at relatively low counting rate, the resolution of images and material components can be better realized, and the dose required by radiation imaging can be reduced. Therefore, the resolution of the image can be improved on the premise of reducing the dosage required by radiation imaging.
Drawings
In order to more clearly illustrate the technical solutions in the embodiments of the present application, the drawings needed to be used in the description of the embodiments are briefly introduced below, and it is obvious that the drawings in the following description are only some embodiments of the present application, and it is obvious for those skilled in the art to obtain other drawings based on these drawings without inventive labor.
FIG. 1 is a schematic view of an exemplary radiation imaging system in an embodiment of the present application;
FIG. 2 is a schematic diagram of an indirect detector and readout configuration;
FIG. 3 is a schematic diagram of a direct detector and its readout structure;
FIG. 4 is a schematic view of a radiation imaging detection process according to an embodiment of the present application;
FIG. 5 is a schematic view of a radiation imaging detection process according to a second embodiment of the present application;
fig. 6 is a schematic structural diagram of a single-terminal hybrid imaging readout circuit according to a second embodiment of the present application;
FIG. 7 is a schematic view of a radiation imaging detection process in the third embodiment of the present application;
FIG. 8 is a schematic diagram of a single-terminal hybrid imaging readout current structure according to a third embodiment;
FIG. 9 is a schematic view of a radiation imaging detection process in the fourth embodiment of the present application;
FIG. 10 is a schematic view of a radiation imaging detection process in the fifth embodiment of the present application;
FIG. 11(a) is a schematic diagram of a fifth embodiment of a readout circuit at the integration end;
fig. 11(b) is a schematic diagram of a readout circuit of the counting end in the fifth embodiment.
FIG. 12 is a schematic view of a radiation imaging detection process in the fifth embodiment of the present application;
fig. 13(a) is a schematic structural diagram of a readout circuit of an integrating terminal in a sixth embodiment;
FIG. 13(b) is a schematic diagram of a reading circuit of the sixth embodiment
FIG. 14 is a schematic diagram of an apparatus according to one embodiment of the present disclosure;
fig. 15 is a schematic structural diagram of an apparatus applied to the technology described in the fourth embodiment of the present application.
Detailed Description
The technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the drawings in the embodiments of the present application, and it is obvious that the described embodiments are only a part of the embodiments of the present application, and not all of the embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present application.
The terms "first," "second," "third," "fourth," and the like in the description and in the claims, as well as in the drawings, if any, are used for distinguishing between similar elements and not necessarily for describing a particular sequential or chronological order. It is to be understood that the data so used is interchangeable under appropriate circumstances such that the embodiments of the invention described herein are, for example, capable of operation in sequences other than those illustrated or otherwise described herein. Furthermore, the terms "comprising" and "having," as well as any variations thereof, are intended to cover non-exclusive inclusions. For example, a process, method, system, article, or apparatus that comprises a list of steps or elements is not necessarily limited to those steps or elements explicitly listed, but may include other steps or elements not explicitly listed or inherent to such process, method, article, or apparatus.
The technical solution of the present invention will be described in detail with specific examples. Several of the following embodiments may be combined with each other and some details of the same or similar concepts or processes may not be repeated in some embodiments.
The embodiment of the application provides a radiation imaging detection method, which performs integration and counting mixed type radiation imaging detection. The method is used for carrying out image analysis and reconstruction by simultaneously collecting integral and count values of rays or particles within a certain time, can realize measurement with high intensity and large dynamic range, and can also obtain information such as particle energy and the like at relatively low count rate so as to realize better resolution of images and material components and reduce the dose required by radiation imaging.
Referring to fig. 1, fig. 1 is a schematic view of an exemplary radiation imaging system in an embodiment of the present application. The system comprises: the device comprises a radiation source, a detected object, a detector and an imaging platform.
The detector mainly comprises a sensor and a reading circuit: the sensor converts the rays or particles into a current signal, and the read-out circuit amplifies and processes the current signal and extracts the required information. The detector is usually composed of several units, distributed in one or two dimensions. The detector units are independent detector modules, and can also be independent pixels processed on the same detector module. Each detector unit receives only the radiation or particles within the respective covered area and converts them into a current signal with a certain efficiency. A plurality of detector units may then enable a measurement of the spatial distribution of the radiation or particle intensity, thus forming an image. The detector units distributed in one dimension are generally required to realize two-dimensional image detection through scanning; also a small area two-dimensional detector needs to be scanned to achieve larger area image detection.
The imaging platform is used for performing membership according to the detection result of the detector, and can be a PC, a server and the like in specific implementation.
The detector in the embodiment of the present application may be implemented as an indirect detector, or may be implemented as a direct detector.
Referring to fig. 2, fig. 2 is a schematic diagram of an indirect detector and a readout structure. The indirect detector mainly refers to a scintillation crystal and a photoelectric device, the scintillation crystal is excited to generate scintillation light after being acted with rays or particles, and finally the scintillation crystal is converted into a current signal through the photoelectric device. Common scintillators for radiation imaging include CsI, GOS, GAGG, and CdWO3, among others. Photoelectric devices can be classified into non-gain types such as Photodiodes (PDs) and gain types such as photomultiplier tubes (PMTs) and silicon photomultiplier tubes (sipms).
The example of an indirect detector using SiPM readout in the embodiments of the present application is also applicable to an indirect detector using PTM readout.
Referring to fig. 3, fig. 3 is a schematic diagram of a direct detector and its readout structure. The direct detector directly generates current signals through ionization with rays or particles, and common direct detectors for radiation imaging are mainly semiconductor detectors, including silicon, CdTe/CZT, GaAs and the like.
Whether an indirect detector or a direct detector, the radiation signal is ultimately converted into a current signal readout. The current signal can be read out from one end of the detector, or from the upper and lower ends of the detector simultaneously. From the signal amplitude, the signal read by the indirect detector is smaller by one order of magnitude than the signal read by the direct detector; however, if a SiPM readout with gain is used, the signal is 4-5 orders of magnitude larger, and the readout circuitry, especially the front-end amplification circuitry, may vary.
Example one
Two signal processing channels, an integration channel and a counting channel, are integrated in the read-out circuit of the detector.
The integration channel realizes integration of the current signal of the detector, the gain is low, and the dynamic range is large; the counting channel further amplifies, shapes and discriminates the current signal of the detector, and the discrimination of single particles (multi-energy window) is realized. Both the integral and (multi-energy window) count values will be collected, and ultimately one or both of them will be selected for image analysis and reconstruction based on the range of radiation intensities.
Referring to fig. 4, fig. 4 is a schematic view of a radiation imaging detection process according to an embodiment of the present application. The method comprises the following specific steps:
And 403, outputting an integration result of the integration processing and a counting result of the counting processing to the imaging platform, so that the imaging platform performs image analysis and reconstruction according to the set range of the radiation intensity, the integration result and the counting result.
The output integration result and the counting processing result are data collected within preset time, and the preset time is set according to actual application scenes, imaging types, experiences and the like.
And the imaging platform selects an integral result and/or a counting result according to the set range of the radiation intensity to carry out image analysis and reconstruction.
In the embodiment of the application, two channels are integrated at one end of the detector, and the integral and the count value of rays or particles in a certain time are collected respectively and are used for image analysis and reconstruction, so that the measurement with high intensity and large dynamic range can be realized, the information such as particle energy can be acquired at relatively low counting rate, the resolution of better images and material components can be realized, and the dose required by radiation imaging can be reduced. Therefore, the resolution of the image can be improved on the premise of reducing the dosage required by radiation imaging.
Example two
Two signal processing channels, an integration channel and a counting channel, are integrated in the read-out circuit of the detector. The detector in this embodiment is a direct detector or an indirect detector using PD readout.
Referring to fig. 5, fig. 5 is a schematic view of a radiation imaging detection process in the second embodiment of the present application. The method comprises the following specific steps:
The switched integrator is reset and reopened at each integration and counting cycle.
And 502, dividing the detector signal processed by the switch integrator into two paths of sub-signals.
In step 503, one of the sub-signals is processed sequentially by a Correlated double sampling Circuit (CDS) and an Analog to Digital Converter (ADC), and step 505 is executed.
And step 504, processing the other path of sub-signals through the forming circuit, the discriminator and the counter in sequence.
And 505, outputting an integration result of the integration processing and a counting result of the counting processing to the imaging platform, and enabling the imaging platform to perform image analysis and reconstruction according to the set range of the radiation intensity, the integration result and the counting result.
In the embodiment of the application, on the premise that the detector is a direct detector or an indirect detector read by PD, two channels are integrated at one end of the detector, and the integral and the count value of rays or particles in a certain time are collected respectively for image analysis and reconstruction, so that the measurement with high intensity and large dynamic range can be realized, the information such as particle energy can be acquired at relatively low count rate, better image and substance component resolution can be realized, and the dose required by radiation imaging can be reduced.
Referring to fig. 6, fig. 6 is a schematic structural diagram of a single-terminal hybrid imaging readout circuit according to a second embodiment of the present application.
In fig. 6 the detector signal (detector current signal) is first integrated on the feedback capacitance of the switched integrator, while the current signal is converted to a voltage signal.
One path of signal is subjected to CDS sampling and ADC processing to obtain an integration result;
and the other path of signal is amplified and pulse-shaped through a forming current, then is compared with the threshold value of one or more discriminators, and if the threshold value is exceeded, a corresponding counter is driven to increase by 1.
The charge range of the integrating channel is usually in the order of 1-10pC, while the signal charge amount generated by single ray or particle of the counting channel is only in the order of 0.01-0.1fC, and the difference between the two is 4-6 orders of magnitude. Therefore, single-end implementation of integration and count readout at the same time requires a large dynamic range in circuit design. The charge range of the integration channel in FIG. 6 is mainly determined by the capacitance CintDetermined to have a charge-voltage gain of 1/Cint. The gain of the counting channel is k.G1Wherein k is Cc/Cint，G1Is the charge-voltage gain of the shaping circuit. Cint、G1、CcThe specific value of (b) is set according to actual needs, and is not limited in the embodiment of the present application.
EXAMPLE III
Two signal processing channels, an integration channel and a counting channel, are integrated in the read-out circuit of the detector. The detector in this embodiment is an indirect detector using SiPM readout.
Referring to fig. 7, fig. 7 is a schematic view of a radiation imaging detection process in the third embodiment of the present application. The method comprises the following specific steps:
And 703, performing signal attenuation on one of the voltage sub-signals, and sequentially processing the voltage sub-signals through the switch integrator, the CDS and the ADC. Step 705 is performed.
And step 704, processing the other circuit of voltage sub-signals through the forming circuit, the discriminator and the counter in sequence.
In the embodiment of the application, on the premise that the detector is an indirect detector which adopts SiPM reading, two channels are integrated at one end of the detector, and the integral sum and the count value of rays or particles in a certain time are collected respectively for image analysis and reconstruction, so that the measurement with high intensity and large dynamic range can be realized, the information such as particle energy can be acquired at relatively low counting rate, better image and substance component resolution can be realized, and the dose required by radiation imaging can be reduced.
Referring to fig. 8, fig. 8 is a schematic diagram of a single-terminal hybrid imaging readout current structure according to the third embodiment. The structure is suitable for a radiation imaging detection scheme of which the detector is an indirect detector adopting SiPM reading.
The current ratio of the detector signal read out by the SiPM is large, and after the current signal is converted into a voltage signal by a current sensitive preamplifier (current sensitive preamplifier), subsequent integration and counting processing are performed.
When the integration channel is used for integration, signals need to be attenuated and then integrated; and the counting channel compares the obtained front-amplifying signal with the discriminator after the forming current is formed, and drives a corresponding counter.
The current sensitive preamplifier (current sensitive preamplifier) can adopt a circuit structure similar to that of the charge sensitive preamplifier, but has a feedback resistance capacitance time constant R 'compared with the charge sensitive preamplifier'fC′f＜＜RfCf. The current of the front-end amplifier output is attenuated to only 1/n after passing through a resistor nR, and then enters an integral channel. The counting channel is further amplified by a forming circuit, and the voltage gain is G3。
Example four
The detection detector signals are read out separately for the detector through both ends.
Referring to fig. 9, fig. 9 is a schematic view of a radiation imaging detection process in the fourth embodiment of the present application. The method comprises the following specific steps:
In step 902, a counting process is performed while reading out the detector signal through the other end.
And 903, outputting an integration result of the integration processing and a counting result of the counting processing to the imaging platform, so that the imaging platform performs image analysis and reconstruction according to the set range of the radiation intensity, the integration result and the counting result.
The output integration result and the counting processing result are data collected within preset time, and the preset time is set according to actual application scenes, imaging types, experiences and the like.
According to the embodiment of the application, the integral and the count value of rays or particles in a certain time are collected at two ends of the detector respectively and are used for image analysis and reconstruction, the measurement with high intensity and large dynamic range can be realized, information such as particle energy can be acquired at relatively low count rate, better image and substance component resolution is realized, and the dose required by radiation imaging is reduced. According to the scheme, the dose required by radiation imaging can be reduced, and the resolution of the image can be improved.
EXAMPLE five
When the detector is an indirect detector adopting PD reading, the detector signals respectively read through the two ends account for half of the total signal, and the polarity of the signals of the detector is read by the PD;
when the detector is a direct detector, the amplitude of the detector signals respectively read out through the two ends is the same, and the polarity is opposite.
In the embodiment of the present application, an indirect detector using PD readout, or a direct detector is taken as an example.
Referring to fig. 10, fig. 10 is a schematic view of a radiation imaging detection process in the fifth embodiment of the present application. The method comprises the following specific steps:
in step 1001, the detector signal read out through one end is processed sequentially through the switch integrator, CDS and ADC. Step 1003 is performed.
In the embodiment of the application, on the premise that the detector is a direct detector or an indirect detector read by a PD (potential difference detector), the integral and the count value of rays or particles in a certain time are simultaneously and respectively collected at two ends of the detector for image analysis and reconstruction, so that the measurement with high intensity and large dynamic range can be realized, the information such as particle energy can be acquired at relatively low count rate, better image and substance component resolution can be realized, and the dose required by radiation imaging can be reduced.
Fig. 11(a) and 11(b) are schematic views of the readout current structures of the two-terminal hybrid imaging in the fifth embodiment. Fig. 11(a) is a schematic structural diagram of a readout circuit of an integrating terminal in the fifth embodiment; fig. 11(b) is a schematic diagram of a readout circuit of the counting end in the fifth embodiment.
In fig. 11(a), the switching integrator integrates on the feedback capacitor while converting the current signal to a voltage signal; CDS and ADC are used for sampling the voltage signal in turn to obtain an integration result.
The charge sensitive preamplifier (charge sensitive preamplifier) in fig. 11(b) is used to convert a current signal into a voltage signal, and the amplitude of the detection signal is proportional to the charge, and in this case, the charge sensitive preamplifier is used. The forming circuit amplifies and pulse shapes the detection signals, compares the detection signals with one or more threshold values of the discriminator, and drives a corresponding counter to increase by 1 if the detection signals exceed the threshold values.
Using double-ended readingThe charge range of the output integration channel is mainly formed by a capacitor CintDetermined to have a charge-voltage gain of 1/Cint(ii) a The counting channel adopts an integrator before charge sensitive pre-amplification replacement to realize charge-to-voltage conversion, and the gain of the integrator is 1/Cf，CfThe charge-voltage gain of the shaping circuit is G for the capacitance of the charge sensitive preamplifier2。Cint、Cf、G2The specific value of (a) is set according to the actual application.
EXAMPLE six
When the detector is an indirect detector which is read by adopting SiPM, detector signals respectively read from two ends respectively account for half of the total signal, and the polarity of the detector signals is read by the SiPM;
referring to fig. 12, fig. 12 is a schematic view of a radiation imaging detection process in the fifth embodiment of the present application. The method comprises the following specific steps:
In the embodiment of the application, on the premise that the detector is an indirect detector which adopts SiPM reading, the integral sum and the count value of rays or particles in a certain time are collected at two ends of the detector respectively and are used for image analysis and reconstruction, so that the measurement with high intensity and large dynamic range can be realized, the information such as particle energy can be acquired at relatively low counting rate, better image and substance component resolution can be realized, and the dose required by radiation imaging can be reduced. According to the scheme, the dose required by radiation imaging can be reduced, and the resolution of the image can be improved.
Fig. 13(a) and 13(b) are schematic views of the readout current structure of the two-terminal hybrid imaging in the sixth embodiment of the present application. Fig. 13(a) is a schematic structural diagram of a readout circuit of an integrating terminal in a sixth embodiment; fig. 13(b) is a schematic structural diagram of a reading circuit of a counter terminal in the sixth embodiment.
In fig. 13(a), a detection signal at one end is processed by a current-sensitive preamplifier (current-sensitive preamplifier), and a signal obtained by processing the processed preamplifier signal by a coupling capacitor is integrated on a feedback capacitor by a switch integrator; and the CDS and the ADC are sequentially used for sampling the signals processed by the switch integrator to obtain an integration result.
The charge sensitive preamplifier (charge sensitive preamplifier) in fig. 13(b) is used for converting a current signal into a voltage signal, and the amplitude of a detection signal is proportional to the charge, and in this case, the charge sensitive preamplifier is used. The forming circuit amplifies and pulse shapes the detection signals, compares the detection signals with one or more threshold values of the discriminator, and drives a corresponding counter to increase by 1 if the detection signals exceed the threshold values.
Based on the same inventive concept, the embodiment of the present application further provides a radiation imaging detection apparatus, wherein two signal processing channels are integrated in a readout circuit of a detector, and the two signal processing channels are an integration channel and a counting channel. Referring to fig. 14, fig. 14 is a schematic structural diagram of an apparatus applied to the technology according to the first embodiment of the present application. The device comprises: an integration unit 1401, a counting unit 1402, and an output unit 1403;
an integration unit 1401, configured to perform integration processing on the detector signal through the integration channel;
a counting unit 1402, configured to perform a counting process on the detector signals through the counting channel;
an output unit 1403, configured to output the integration result of the integration processing performed by the integration unit 1401 and the count result of the count processing performed by the count unit 1402 to the imaging platform, so that the imaging platform performs image analysis and reconstruction according to the set range of the radiation intensity, and the integration result and the count result.
The units of the above embodiments may be integrated into one body, or may be separately deployed; may be combined into one unit or further divided into a plurality of sub-units.
Based on the same inventive concept, the embodiment of the present application further provides a radiation imaging detection apparatus, which respectively reads out detection detector signals through two ends for a detector. Referring to fig. 15, fig. 15 is a schematic structural diagram of an apparatus applied to the technology described in the fourth embodiment of the present application. The device comprises: an integration unit 1501, a count unit 1502, and an output unit 1503;
an integration unit 1501, configured to perform integration processing when reading out a probe signal through one end of the probe;
a counting unit 1502 for performing a counting process when a detector signal is read out through the other end of the detector;
an output unit 1503 configured to output an integration result of the integration processing performed by the integration unit 1501 and a count result of the count processing performed by the count unit 1502 to the imaging platform, so that the imaging platform performs image analysis and reconstruction according to the set range of the radiation intensity, and the integration result and the count result.
The units of the above embodiments may be integrated into one body, or may be separately deployed; may be combined into one unit or further divided into a plurality of sub-units.
The above description is only for the purpose of illustrating the preferred embodiments of the present invention and is not to be construed as limiting the invention, and any modifications, equivalents, improvements and the like made within the spirit and principle of the present invention should be included in the scope of the present invention.
Claims (10)
1. A radiation imaging detection method is characterized in that two signal processing channels are integrated in a reading circuit of a detector, wherein the two signal processing channels are an integration channel and a counting channel; the method comprises the following steps:
integrating the detector signal through the integration channel;
counting the detector signals through the counting channel;
and outputting an integration result of the integration processing and a counting result of the counting processing to the imaging platform, and enabling the imaging platform to perform image analysis and reconstruction according to the set range of the radiation intensity, the integration result and the counting result.
2. The method according to claim 1, wherein when the detector is a direct detector or an indirect detector using a light emitting diode (PD) readout, the integration processing is performed on the detector signal through the integration channel; performing a counting process on the detector signals through the counting channel, including:
processing the detector signal through a switch integrator;
dividing the detector signal processed by the switch integrator into two paths of sub-signals;
one sub-signal is processed by a correlated double sampling circuit CDS and an analog-to-digital converter ADC in sequence;
and processing the other path of sub-signals through the forming circuit, the discriminator and the counter in sequence.
3. The method of claim 1, further comprising:
the switched integrator is reset and reopened at each integration and counting cycle.
4. The method of claim 1, wherein when the detector is an indirect detector using a silicon photomultiplier SiPM readout, the integrating channel integrates the detector signal; performing a counting process on the detector signals through the counting channel, including:
processing the detector signal through current sensitive preamplifier to obtain voltage signal;
dividing the voltage signal into two voltage sub-signals;
after signal attenuation is carried out on one path of voltage sub-signal, processing is carried out through a switch integrator, a CDS and an ADC in sequence;
and processing the other circuit of voltage sub-signals by the forming circuit, the discriminator and the counter in sequence.
5. A method of radiographic detection, the method comprising:
reading out detection detector signals from two ends of the detector respectively;
performing integration processing when a detector signal is read out through one end of the optical fiber;
counting is carried out when the other end reads out the signal of the detector;
and outputting an integration result of the integration processing and a counting result of the counting processing to the imaging platform, and enabling the imaging platform to perform image analysis and reconstruction according to the set range of the radiation intensity, the integration result and the counting result.
6. The method according to claim 5, characterized in that when the detector is an indirect detector using light emitting diode (PD) readout, the polarity of the detector signal is read out by PD by the detector signals respectively read out at both ends accounting for half of the total signal;
when the detector is an indirect detector which adopts a silicon photomultiplier SiPM to read, detector signals respectively read from two ends respectively account for half of the total signal, and the polarity of the detector signals is read by the SiPM;
when the detector is a direct detector, the amplitude of the detector signals respectively read out through the two ends is the same, and the polarity is opposite.
7. The method of claim 5, wherein when the detector is a direct detector or an indirect detector employing PD readout, the integrating process performed while reading out the detector signal through one of the ends comprises:
the detector signal is processed by a switch integrator, a correlated double sampling circuit CDS and an analog-to-digital converter ADC in sequence
The counting process is carried out when the detector signal is read out through the other end, and comprises the following steps:
and processing the detection detector signal through a charge sensitive preamplifier, a forming circuit, a discriminator and a counter in sequence.
8. The method of claim 5, wherein when the detector is an indirect detector using SiPM readout, the integrating process performed while reading out the detector signal through one of the ends comprises:
the detector signal is processed by current sensitive front amplifier, switch integrator, CDS and ADC
The counting process is carried out when the detector signal is read out through the other end, and comprises the following steps:
and processing the detector signal sequentially through a charge sensitive preamplifier, a forming circuit, a discriminator and a counter.
9. A radiation imaging detection device is characterized in that two signal processing channels are integrated in a read-out circuit of a detector, wherein the two signal processing channels are an integration channel and a counting channel; the device comprises: an integrating unit, a counting unit and an output unit;
the integration unit is used for carrying out integration processing on the detector signal through the integration channel;
the counting unit is used for counting the detector signals through the counting channel;
the output unit is used for outputting an integration result of the integration processing performed by the integration unit and a counting result of the counting processing performed by the counting unit to the imaging platform, so that the imaging platform performs image analysis and reconstruction according to the set range of the radiation intensity, the integration result and the counting result.
10. A radiation imaging detection device is characterized in that detection detector signals are read out from two ends of a detector respectively; the device comprises: an integrating unit, a counting unit and an output unit;
the integration unit is used for performing integration processing when a detector signal is read out through one end of the detector;
the counting unit is used for counting when the other end of the detector reads out the detector signal;
the output unit is used for outputting an integration result of the integration processing performed by the integration unit and a counting result of the counting processing performed by the counting unit to the imaging platform, so that the imaging platform performs image analysis and reconstruction according to the set range of the radiation intensity, the integration result and the counting result.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202010735827.2A CN111896991A (en) | 2020-07-28 | 2020-07-28 | Radiation imaging detection method and device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202010735827.2A CN111896991A (en) | 2020-07-28 | 2020-07-28 | Radiation imaging detection method and device |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN111896991A true CN111896991A (en) | 2020-11-06 |
Family
ID=73189325
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202010735827.2A Pending CN111896991A (en) | 2020-07-28 | 2020-07-28 | Radiation imaging detection method and device |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN111896991A (en) |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN113850093A (en) * | 2021-09-08 | 2021-12-28 | 中国原子能科学研究院 | Positioning method, detecting device and storage medium |
| CN113848580A (en) * | 2021-09-26 | 2021-12-28 | 中国科学院高能物理研究所 | X/gamma ray radiation quantity detection system and detection method |
| WO2023284606A1 (en) * | 2021-07-12 | 2023-01-19 | 同方威视技术股份有限公司 | Radiation imaging system and method |
Citations (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20020109091A1 (en) * | 2001-02-10 | 2002-08-15 | Michael Overdick | X-ray detector having a large dynamic range |
| US20090008564A1 (en) * | 2007-07-05 | 2009-01-08 | Cmt Medical Technologies Ltd. | Modular X-Ray Detector With Single Photon Counting, Energy Sensitivity And Integration Capabilities |
| CN102395901A (en) * | 2009-04-16 | 2012-03-28 | 皇家飞利浦电子股份有限公司 | Spectral imaging |
| US20130010921A1 (en) * | 2011-06-14 | 2013-01-10 | Tomoe Sagoh | X-ray computed tomography apparatus and radiation detector |
| CN103998952A (en) * | 2011-12-19 | 2014-08-20 | 皇家飞利浦有限公司 | X-ray detector |
| US20150223766A1 (en) * | 2012-10-02 | 2015-08-13 | Analogic Corporation | Detector array comprising energy integrating and photon counting cells |
| US20160070005A1 (en) * | 2014-06-16 | 2016-03-10 | Kabushiki Kaisha Toshiba | Photon-counting x-ray ct apparatus and photon-counting x-ray diagnostic apparatus |
| CN106019355A (en) * | 2016-07-07 | 2016-10-12 | 清华大学 | Radiation particle detector readout circuit and radiation particle signal counting method |
| US20170212250A1 (en) * | 2016-01-22 | 2017-07-27 | General Electric Company | Dual-mode radiation detector |
-
2020
- 2020-07-28 CN CN202010735827.2A patent/CN111896991A/en active Pending
Patent Citations (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20020109091A1 (en) * | 2001-02-10 | 2002-08-15 | Michael Overdick | X-ray detector having a large dynamic range |
| US20090008564A1 (en) * | 2007-07-05 | 2009-01-08 | Cmt Medical Technologies Ltd. | Modular X-Ray Detector With Single Photon Counting, Energy Sensitivity And Integration Capabilities |
| CN102395901A (en) * | 2009-04-16 | 2012-03-28 | 皇家飞利浦电子股份有限公司 | Spectral imaging |
| US20130010921A1 (en) * | 2011-06-14 | 2013-01-10 | Tomoe Sagoh | X-ray computed tomography apparatus and radiation detector |
| CN103998952A (en) * | 2011-12-19 | 2014-08-20 | 皇家飞利浦有限公司 | X-ray detector |
| US20150223766A1 (en) * | 2012-10-02 | 2015-08-13 | Analogic Corporation | Detector array comprising energy integrating and photon counting cells |
| US20160070005A1 (en) * | 2014-06-16 | 2016-03-10 | Kabushiki Kaisha Toshiba | Photon-counting x-ray ct apparatus and photon-counting x-ray diagnostic apparatus |
| US20170212250A1 (en) * | 2016-01-22 | 2017-07-27 | General Electric Company | Dual-mode radiation detector |
| CN106019355A (en) * | 2016-07-07 | 2016-10-12 | 清华大学 | Radiation particle detector readout circuit and radiation particle signal counting method |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2023284606A1 (en) * | 2021-07-12 | 2023-01-19 | 同方威视技术股份有限公司 | Radiation imaging system and method |
| CN113850093A (en) * | 2021-09-08 | 2021-12-28 | 中国原子能科学研究院 | Positioning method, detecting device and storage medium |
| CN113848580A (en) * | 2021-09-26 | 2021-12-28 | 中国科学院高能物理研究所 | X/gamma ray radiation quantity detection system and detection method |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US7829860B2 (en) | Photon counting imaging detector system | |
| CN108271415B (en) | Semiconductor X-Ray detector | |
| US7512210B2 (en) | Hybrid energy discriminating charge integrating CT detector | |
| US9759822B2 (en) | Detection device for detecting photons and method therefore | |
| JP5701743B2 (en) | Radiation detector, imaging system, method for detecting photons and computer program for executing the method | |
| US7403589B1 (en) | Photon counting CT detector using solid-state photomultiplier and scintillator | |
| EP2676434B1 (en) | Single photon counting detector system having improved counter architecture | |
| CN111896991A (en) | Radiation imaging detection method and device | |
| US9897707B2 (en) | X-ray detector operable in a mixed photon-counting/analog output mode | |
| JP3961052B2 (en) | Method and device for correction of spectral measurements in gamma photon detection fields | |
| US7851764B2 (en) | Method of high-energy particle imaging by computing a difference between sampled pixel voltages | |
| US8624195B2 (en) | Neutron detector attachment device | |
| WO2018232370A1 (en) | Counting and integrating pixels, detectors, and methods | |
| CN110133710B (en) | Signal correction method and device | |
| US6586743B1 (en) | X-ray detector having sensors and evaluation units | |
| EP2145209A2 (en) | Multi-functional radiation/photon identifying and processing application specific integrated circuit and device | |
| US8450692B2 (en) | Increasing edge sensitivity in a radiation detector | |
| US9086493B2 (en) | High-sensitivity X-ray detector | |
| Tomita et al. | X-ray color scanner with multiple energy discrimination capability | |
| WO2006080004A2 (en) | Method and system for x-ray radiation imaging | |
| Prekas et al. | Direct and indirect detectors for X-ray photon counting systems | |
| Meng et al. | Investigation of the intrinsic spatial resolution of an intensified EMCCD scintillation camera | |
| Perri et al. | Amplitude Measurements with SiPM and ASIC (Citiroc 1A) Front-End Electronics | |
| Meyer et al. | A time-based front end readout system for PET & CT | |
| US20230204799A1 (en) | Radiation detector |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| RJ01 | Rejection of invention patent application after publication |
Application publication date: 20201106 |
|
| RJ01 | Rejection of invention patent application after publication |