CN102764137B - Static CT (computed tomography) scanner and scattering X-photon correction method thereof - Google Patents
Static CT (computed tomography) scanner and scattering X-photon correction method thereof Download PDFInfo
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Abstract
A static CT (computed tomography) scanner comprises an X-ray source system, a detector system, a data acquisition system, a power system and a computer. The X-ray source system comprises an annular X-ray source and a front annular collimator arranged at an exit of the annular X-ray source. The annular X-ray source comprises a plurality of X-ray source modules, a plurality of collimator slits limiting emitting scope of X rays are distributed on the front annular collimator. The detector system comprises two annular detectors with the slits in between which are arranged on the inner side of the front annular collimator. Each annular detector comprises a plurality of detector modules capable of distinguishing energies for X photons. The front annular collimator can completely cover detection area of the detector modules. The detector system further comprises two rear annular collimators arranged on the inner side of the annular detectors and two annular monitoring detectors. The data acquisition system is connected with the detector system and the monitoring detectors. The computer processes data acquired by the data acquisition system and then reconstructs images.
Description
Technical field
The present invention relates to medical instruments field, relate in particular to a kind of static CT scanner and the bearing calibration of scattering X-ray thereof.
Background technology
Computed tomography (computed tomography, CT) scanner is a kind of powerful medical imaging diagnosis equipment, it utilizes X ray to carry out successively transverse scan to a certain scope of human body, obtains projection information, then carries out date processing and image reconstruction by computer.The imaging process of X ray is mainly: x-ray source produces X-ray, and X-ray is sentenced straight line path in the focus of x-ray source and launched to all directions.Entering in X-ray of imaging object, the atom of a part of object to be imaged directly absorbs; A part of directly penetrate imaging object and arrive the detector relative with x-ray source, this part X-ray is direct projection X-ray, and also imaging is required just for their information.But in real process, some X-ray can bump with the atom of imaging object, and changes the direction of motion, and loses portion of energy, this part X-ray is scattering X-ray.Because this part X-ray does not meet image reconstruction, even if therefore this part X-ray arrives detector, also cannot make contributions to imaging, therefore, if can not reject this part X-ray, will increase the noise of rebuilding image on the contrary.
As shown in Figure 1, for image reconstruction, for obtaining the CT image of better quality, generally all wish that X-ray of being launched by x-ray source 1 only has direct projection part to arrive detector 2, thus, can determine the path of X-ray according to the incidence point on the focus of x-ray source 1 and detector 2; But in actual imaging process, part scattering X-ray also can enter detector, causes being thus difficult to determine exactly the path of X-ray, thereby affects the quality of CT image.
For solving the problem of X-ray scattering, in a kind of conventional CT scans instrument using at present, detector 2 is take the focus of x-ray source 1 as the center of circle, at x-ray source 1 collimator 3 before a side of detector 2 arranges, and the rear collimator 4 of focus that points to described x-ray source 1 is set towards a side of x-ray source 1 at detector 2, detector 2 and x-ray source 1 are around human body rotating scanning, to obtain projection information, as shown in Figure 2.This CT scanner limits the scope of X ray by described front collimator 3, and further absorb and the inconsistent scattering of its direction X-ray by described rear collimator 4, to suppress the interference of scattering X-ray, improve signal to noise ratio, realize tomographic image reconstructing more accurately.
But conventionally there is the shortcomings such as radiation dose is higher, imaging time is long, system structure is complicated, operation cost is high in this conventional CT scans instrument.For this reason, publication No. is that the Chinese invention patent application of CN102379716A discloses a kind of static CT scanner and scan method thereof, this static state CT scanner has proposed to adopt the scheme of the annular x-ray source based on carbon nanotube field emission cathode X-ray tube and the medical static energy resolution CT scanner of annular detector system development based on tellurium zinc cadmium energy resolution detector, for addressing the above problem.But, in this scheme, because curved detector corresponding to each X-ray tube is difficult to take this X-ray tube as the center of circle, therefore, be difficult to adopt traditional collimator to suppress the impact of scattering X-ray on imaging, and then cause CT picture quality poor.
Summary of the invention
Technical problem to be solved by this invention is to provide a kind of static CT scanner and the bearing calibration of scattering X-ray thereof, and the signal to noise ratio of data for projection gathering to improve detector reduces the impact of scattering X-ray on CT scanner image quality.
Solving the technical scheme that technical problem of the present invention adopts is: a kind of static CT scanner is provided, and it comprises: x-ray source system, detector system, data collecting system, computer and power-supply system.Described x-ray source system comprises that an annular x-ray source and one are arranged at collimator before the annular in described annular x-ray source exit, described annular x-ray source comprises several x-ray source modules based on CNT, before described annular, on collimator, be distributed with the collimator slit that several limit for the outgoing scope to X ray, the corresponding described collimator slit of each described x-ray source module; Described detector system is for receiving the X-ray beam of described x-ray source system transmitting, described detector system comprises two annular detectors that are positioned at the front collimator of described annular inner side, the crack between described two annular detectors with corresponding described collimator slit, each described annular detector is made up of several detector modules; Described data collecting system connects described detector system, for the data of described detector system output are gathered; Described computer is connected with described data collecting system; Described power-supply system connects respectively described x-ray source system, described detector system and described data collecting system, so that required high pressure and common power to be provided.Each described detector module includes interconnective detecting area and non-detecting area, described detecting area is near described crack, described non-detecting area is away from described crack, before described annular, the range of exposures of collimator covers the detecting area of the described detector module of its inner side completely, to avoid non-detecting area to be irradiated by X-rays, reduce the absorbed dose that scanning object receives; Described detector system further comprises collimator and two annular monitoring detectors after two annulars, after described two annulars, collimator is arranged at the inner side of described two annular detectors, and lay respectively at the junction of detecting area and the non-detecting area of corresponding detector module, limit for scattering X-ray to X ray; Described two annular monitoring detectors are connected with described data collecting system, and after being arranged at accordingly respectively described two annulars, collimator deviates from a side of the detecting area of described detector module; Described computer carries out image reconstruction after the data of described data collecting system collection are processed.
In a preferred embodiment of the present invention, described in each, annular monitoring detector is by several monitoring detector module compositions.
In a preferred embodiment of the present invention, after described several monitoring detector modules are arranged at intervals at corresponding described annular equally spacedly, collimator deviates from a side of the detecting area of described detector module.
In a preferred embodiment of the present invention, described annular monitoring detector adopts the mode of approximate or interpolation to obtain scattered photon counting and the spectral distribution of interval without the region of described monitoring detector module.
In a preferred embodiment of the present invention, described two annular monitoring detectors and described two annular detectors start simultaneously, work asynchronously.
In a preferred embodiment of the present invention, after described two annulars, collimator is perpendicular to described two annular detectors and be parallel to each other.
In a preferred embodiment of the present invention, described several detector modules are the high count rate detector module based on tellurium zinc cadmium that can carry out to X-ray energy resolution.
In a preferred embodiment of the present invention, the spacing of the crack between described two annular detectors is greater than 0 and be less than 5mm.
In a preferred embodiment of the present invention, the diameter range of described annular x-ray source and described two annular detectors is 0.2m to 1.5m.
The present invention provides a kind of scattering X-ray bearing calibration of above-mentioned static CT scanner in addition, and it comprises the steps: that described two annular detectors and described two annular monitoring detectors survey respectively the X-ray beam of described annular x-ray source transmitting simultaneously; Described data collecting system gathers respectively the data for projection of described detector system output and the data of described two annular monitoring detector outputs; Described computer, according to the data for projection of described detector system output, subtracts each other according to the data of preset rules and ratio and described two annular monitoring detector outputs, obtains the data for projection through scatter correction.
Compared with prior art, static CT scanner provided by the invention has the following advantages: one, before described annular, the range of exposures of collimator covers the detecting area of the described detector module of its inner side completely, can effectively reduce the absorbed dose of imaging object by restriction range of exposures, the source of simultaneously reducing scattered photon; They are two years old, collimator after the inner side of two annular detectors arranges two annulars, after described two annulars, collimator lays respectively at the junction of detecting area and the non-detecting area of corresponding detector module, for scattered photon is limited, on the basis with collimator before described annular, further reduce the impact of X scattered photon; They are three years old, utilization is arranged at two annular monitoring detectors that collimator deviates from a side of the detecting area of described detector module after described two annulars, can effectively obtain the data of scattering X-ray, the data of obtaining for tuning detector module, the signal to noise ratio of the data for projection gathering with raising detector module, reduces the impact of scattering X-ray on static CT scanner image quality; Its four, described static CT scanner adopts the x-ray source module based on CNT, can effectively shorten imaging time, and its overall structure is simpler, be easy to safeguard, operation cost is lower.In addition, scattering X-ray provided by the invention bearing calibration is easy to realize the correction to scattering X-ray, the data that tuning detector module is obtained effectively, the signal to noise ratio of the data for projection that raising detector module gathers, reduces the impact of scattering X-ray on static CT scanner image quality.
Accompanying drawing explanation
Below in conjunction with drawings and Examples, the invention will be further described, in accompanying drawing:
Fig. 1 is X-ray subpath schematic diagram.
Fig. 2 is the imaging process schematic diagram of conventional CT scans instrument.
Fig. 3 is the system composition schematic diagram of the static CT scanner that provides of first embodiment of the invention.
Fig. 4 is the composition schematic diagram of the axial section of static CT scanner described in Fig. 3.
Fig. 5 is the schematic perspective view that static CT scanner does not comprise annular monitoring detector described in Fig. 4.
Fig. 6 is the decomposing schematic representation of static CT scanner shown in Fig. 5.
Fig. 7 is that the one of the annular monitoring detector of static CT scanner shown in Fig. 4 arranges schematic diagram.
Fig. 8 is that the another kind of the annular monitoring detector of static CT scanner shown in Fig. 4 arranges schematic diagram.
Fig. 9 is the flow chart of the scattering X-ray bearing calibration of static CT scanner shown in Fig. 3 of providing of second embodiment of the invention.
Figure 10 a is the spectral distribution figure of direct projection region inscattering photon.
Figure 10 b is the spectral distribution figure of reference zone inscattering photon.
The specific embodiment
In order to make object of the present invention, technical scheme and advantage clearer, below in conjunction with drawings and Examples, the present invention is further elaborated.Should be appreciated that specific embodiment described herein, only in order to explain the present invention, is not intended to limit the present invention.
Refer to Fig. 3, first embodiment of the invention provides a kind of static CT scanner 100, and it comprises x-ray source system 10, detector system 20, data collecting system 30, computer 40 and power-supply system 50.
See also Fig. 4 to Fig. 6, described x-ray source system 10 comprises an annular x-ray source 11 and a front collimator 13 of annular, and described annular x-ray source 11 is for launching X ray, and it comprises several x-ray source modules 111 based on CNT; Before described annular, collimator 13 is arranged at the exit of described annular x-ray source 11, before described annular, on collimator 13, is distributed with several collimator slit 131, and described collimator slit 131 limits for the X ray that described annular x-ray source 11 is launched; The all corresponding described collimator slit 131 of x-ray source module 111 described in each.
The X ray that described detector system 20 is launched for receiving described x-ray source system 10, described detector system 20 comprises and is positioned at collimator 23 and two annular monitoring detectors 25 after two annular detectors 21 of the inner side of collimator 13 before described annular, two annulars.
The shape of described two annular detectors 21 is identical with size and coaxially arrange, and has the crack 211 of corresponding described collimator slit 131 between described two annular detectors 21, and each described annular detector 21 forms by several detector modules 213; Each described detector module 213 includes interconnective detecting area 2131 and non-detecting area 2133, described detecting area 2131 is near described crack 211, described non-detecting area 2133 is away from described crack 211, and before described annular, the range of exposures of collimator 13 covers the detecting area 2131 of the described detector module 213 of its inner side completely.Described several detector modules 213 are energy resolution digital detector module.With respect to conventional detectors, energy resolution digital detector can carry out energy resolution (Detector and data acquisition system is processed the time that X-ray approximately needs hundreds of nanosecond) to each X-ray, not only by establishing threshold value, little noise signal is kept outside of the door, improve signal to noise ratio from suppressing noise aspect, and obtained the energy information of each X-ray, improve signal to noise ratio from information increase aspect.This imaging mode can reduce half by radiation dose.In the present embodiment, preferably adopt the high count rate detector module based on tellurium zinc cadmium.The high count rate detector module of tellurium zinc cadmium belongs to the one of energy resolution digital detector, has higher signal to noise ratio.
Preferably, before described annular, the range of exposures of collimator 13 just in time covers the detecting area 2131 of the described detector module 213 of its inner side completely, thus, both can just avoid non-detecting area 2133 to be irradiated by X-rays, reduce the absorbed dose that receive of scanning object, can avoid again collimator 13 before described annular to limit too much the X ray on the detecting area 2131 of the described detector module 213 that is projected to relative position.
Further, described annular x-ray source 11 is 0.2m to 1.5m, preferably 1m with the diameter range of described two annular detectors 21.
Further, the spacing of the crack 211 between described two annular detectors 21 is preferably greater than 0 and be less than 5mm.
After described two annulars, collimator 23 is arranged at the inner side of described two annular detectors 21, and lays respectively at the junction of detecting area 2131 and the non-detecting area 2133 of corresponding detector module 213, limits for the scattered photon to X ray.
After described two annular monitoring detectors 25 are arranged at respectively described two annulars accordingly, collimator 23 deviates from a side of the detecting area 2131 of described detector module 213, be described two annular monitoring detectors 25 are arranged at respectively described two detector modules 213 outside along axis direction, to obtain the data of scattering X-ray.
Preferably, after described two annulars collimator 23 perpendicular to described two annular detectors 21 and be parallel to each other.In the present embodiment, described several monitoring detector modules 251 are also the high count rate detector module based on tellurium zinc cadmium, and it can carry out energy resolution to X-ray.
As shown in Figure 7, in the present embodiment, described in each, annular monitoring detector 25 forms by several monitoring detector modules 251, and described several monitoring detector modules 251 are joined successively around forming described annular monitoring detector 25.Certainly, the set-up mode of described several monitoring detector modules 251 is not limited to the present embodiment, as long as described two annular monitoring detectors 25 that described several monitoring detector modules 251 form can obtain the data of X scattered photon effectively.As shown in Figure 8, after described several monitoring detector modules 251 are arranged at intervals at corresponding described annular equally spacedly, collimator 23 deviates from a side of the detecting area 2131 of described detector module 213, thus, can reduce the quantity of described monitoring detector module 251.Be understandable that, now, between two adjacent described monitoring detector modules 251, have the clearance space that described monitoring detector module 251 is not set.In such cases, described annular monitoring detector 25 adopts the mode of approximate or interpolation to obtain scattered photon counting and the spectral distribution of interval without the region of described monitoring detector module 251.
Preferably, described two annular monitoring detectors 25 and described two annular detectors 21 start simultaneously, work asynchronously.Thus, can guarantee described two annular monitoring detectors 25 and the concordance of described two 21 working times of annular detector, and then make described two annular monitoring detectors 25 obtain the x-ray photon data that scattering X-ray subdata and described two annular detectors 21 obtain to there is temporal dependency.
Described data collecting system 30 connects described detector system 20 and described two annular monitoring detectors 25, gathers for the signal that described detector system 20 and described two annular monitoring detectors 25 are exported.
Described computer 40 is connected with described data collecting system 30, processes, and carry out image reconstruction according to the data of processing with the data that described data collecting system 30 is gathered.
In the present embodiment, the data that described computer 40 is exported according to described detector system 20 and described two annular monitoring detectors 25 are carried out scattering X-ray and are proofreaied and correct, to rebuild the image that obtains better quality.
Described power-supply system 50 connects respectively described x-ray source system 10, described detector system 20, described data collecting system 30 and described computer 40, so that required high pressure and common power to be provided.
Be understandable that, X-ray that described annular x-ray source 11 is launched projects on the detecting area 2131 of described detector module 213 of relative position by the crack 211 between collimator slit 131 and described two annular detectors 21 of collimator 13 before described annular successively.
Be understandable that, described " annular " in the present embodiment can be circular, oval etc., and the present invention is not as limit.
Refer to Fig. 9, second embodiment of the invention provides the scattering X-ray bearing calibration of described static CT scanner 100, and it comprises the steps:
S111: described two annular detectors 21 and described two annular monitoring detectors 25 are surveyed respectively the X-ray beam that described annular x-ray source 11 is launched simultaneously.
Be understandable that, the X-ray beam that described two annular detectors 21 are surveyed comprises the direct projection photon that described annular x-ray source 11 is launched and the inner side scattered photon producing by way of imaging object, and described detector system 20 obtains direct projection photon and the data for projection of the inner side scattered photon that produces by way of imaging object thus; The X-ray beam that described two annular monitoring detectors 25 are surveyed comprises that described annular x-ray source 11 launches X-ray at the outside scattered photon producing after imaging object, and described two annular monitoring detectors 25 obtain the data of the outside scattered photon producing by way of imaging object thus.
S113: described data collecting system 30 gathers respectively data for projection and described two data that annular monitoring detector 25 is exported that described detector system 20 is exported.
The data for projection that the described detector system 20 that described data collecting system 30 gathers is exported, be two X-ray beams that annular detector 21 is surveyed in described detector system 20, that is the data for projection of the direct projection photon that obtains of described detector system 20 and the inner side scattered photon that produces by way of imaging object; Described two data that annular monitoring detector 25 is exported that described data collecting system 30 gathers, be described two X-ray beams that annular monitoring detector 25 is surveyed, that is the data of the outside scattered photon producing by way of imaging object that obtains of described two annular monitoring detectors 25.
Adopt the physical process that X-ray that monte carlo method produces 140keV electronic target arrives detector through limit bundle, collimation through the imaging object of different materials to carry out analog computation, obtain direct projection region as shown in Figure 10 a and Figure 10 b difference and scattering X-ray post-depositional spectral distribution in tellurium-zinc-cadmium detector of reference zone.Research is found: scattering X-ray (being the inner side scattered photon producing by way of imaging object that described annular x-ray source 11 is launched) in (1) direct projection region be can not ignore the impact of final image reconstruction; (2) quantity and the spectral distribution of the quantity of scattering X-ray of reference zone (being the outside scattered photon producing by way of imaging object that described annular x-ray source 11 is launched) and scattering X-ray in spectral distribution and direct projection region are very approaching, can mutually be similar to replacement.
Thus, the data for projection that the data that can export by described two annular monitoring detectors 25 are exported described detector system 20 is proofreaied and correct, the data for projection of the direct projection photon that the data of the outside scattered photon by way of imaging object generation that the described annular x-ray source 11 that utilizes described two annular monitoring detectors 25 to obtain is launched are launched described annular x-ray source 11 and the inner side scattered photon producing by way of imaging object is proofreaied and correct, to improve the signal to noise ratio of the data for projection that described detector module 213 gathers, reduce the impact of scattering X-ray on described static CT scanner 100 image quality.
S115: the data for projection that described computer 40 is exported according to described detector system 20, the data of exporting according to preset rules and ratio and described two annular monitoring detectors 25 are subtracted each other, and obtain the data for projection through scatter correction.
Thus, the data for projection that can export from described detector system 20, reject or reduce the data of the scattered photon that described annular x-ray source 11 launches, carry out scatter correction.And then, can make to carry out according to the data for projection after scatter correction the CT image that image reconstruction obtains and there is preferably quality.
Be understandable that, the scattering X-ray bearing calibration of described static CT scanner 100 provided by the invention measures by described two annular monitoring detectors 25 the outside scattered photon producing by way of imaging object that described annular x-ray source 11 is launched, partly or entirely substitute the inner side scattered photon producing by way of imaging object that described in the data that described detector system 20 obtains, annular x-ray source 11 is launched, to obtain the direct light subdata that more annular x-ray source 11 is launched, to carry out successive image reconstruction.
Compared with prior art, static CT scanner 100 provided by the invention has the following advantages: one, before described annular, the range of exposures of collimator 13 covers the detecting area 2131 of the described detector module 213 of its inner side completely, can effectively reduce the absorbed dose of imaging object by restriction range of exposures, the source of simultaneously reducing scattered photon; They are two years old, collimator 23 after the inner side of two annular detectors 21 arranges two annulars, after described two annulars, collimator 23 lays respectively at the junction of detecting area 2131 and the non-detecting area 2133 of corresponding detector module 213, for scattered photon is limited, on the basis with collimator 13 before described annular, further reduce the impact of X scattered photon; They are three years old, utilization is arranged at two annular monitoring detectors 25 that collimator 23 deviates from a side of the detecting area 2131 of described detector module 213 after described two annulars, can effectively obtain the data of scattering X-ray, the data of obtaining for tuning detector module 213, the signal to noise ratio of the data for projection gathering with raising detector module 213, reduces the impact of scattering X-ray on static CT scanner 100 image quality; Its four, described static CT scanner 100 adopts the x-ray source module 111 based on CNT, can effectively shorten imaging time, and its overall structure is simpler, be easy to safeguard, operation cost is lower.In addition, scattering X-ray provided by the invention bearing calibration is easy to realize the correction to scattering X-ray, the data that tuning detector module 213 is obtained effectively, the signal to noise ratio of the data for projection that raising detector module 213 gathers, reduces the impact of scattering X-ray on static CT scanner 100 image quality.
The foregoing is only preferred embodiment of the present invention, not in order to limit the present invention, all any modifications of doing within the spirit and principles in the present invention, be equal to and replace and improvement etc., within all should being included in protection scope of the present invention.
Claims (10)
1. a static CT scanner, it comprises:
X-ray source system, described x-ray source system comprises that an annular x-ray source and one are arranged at collimator before the annular in exit of described annular x-ray source, described annular x-ray source comprises several x-ray source modules based on CNT, before described annular, on collimator, be distributed with the collimator slit that several limit for the outgoing scope to X ray, all corresponding described collimator slit of each described x-ray source module;
Detector system, described detector system is for receiving the X ray of described x-ray source system transmitting, described detector system comprises two annular detectors of the inner side that is positioned at the front collimator of described annular, between described two annular detectors, there is the crack of corresponding described collimator slit, the detector module composition that each described annular detector can carry out to X-ray energy resolution by several;
Data collecting system, described data collecting system connects described detector system, for the signal of described detector system output is gathered;
Computer, described computer is connected with described data collecting system; And
Power-supply system, described power-supply system connects respectively described x-ray source system, described detector system, described data collecting system and described computer, so that required high pressure and common power to be provided;
It is characterized in that:
Each described detector module includes interconnective detecting area and non-detecting area, described detecting area is near described crack, described non-detecting area is away from described crack, before described annular, the range of exposures of collimator covers the detecting area of the described detector module of its inner side completely, to avoid non-detecting area to be irradiated by X-rays, reduce the absorbed dose that scanning object receives; Described detector system further comprises collimator and two annular monitoring detectors after two annulars, after described two annulars, collimator is arranged at the inner side of described two annular detectors, and lay respectively at the junction of detecting area and the non-detecting area of corresponding detector module, limit for scattering X-ray to X ray; Described two annular monitoring detectors are connected with described data collecting system, and after being arranged at accordingly respectively described two annulars, collimator deviates from a side of the detecting area of described detector module; Described computer carries out image reconstruction after the data of described data collecting system collection are processed.
2. static CT scanner as claimed in claim 1, is characterized in that, described in each, annular monitoring detector is by several monitoring detector module compositions.
3. static CT scanner as claimed in claim 2, is characterized in that, after described several monitoring detector modules are arranged at intervals at corresponding described annular equally spacedly, collimator deviates from a side of the detecting area of described detector module.
4. static CT scanner as claimed in claim 3, is characterized in that, described annular monitoring detector adopts the mode of approximate or interpolation to obtain scattered photon counting and the spectral distribution of interval without the region of described monitoring detector module.
5. static CT scanner as claimed in claim 1, is characterized in that, described two annular monitoring detectors and described two annular detectors start simultaneously, work asynchronously.
6. static CT scanner as claimed in claim 1, is characterized in that, after described two annulars, collimator is perpendicular to described two annular detectors and be parallel to each other.
7. static CT scanner as claimed in claim 1, is characterized in that: described several detector modules are the high count rate detector module based on tellurium zinc cadmium that can carry out to X-ray energy resolution.
8. static CT scanner as claimed in claim 1, is characterized in that: the spacing of the crack between described two annular detectors is greater than 0 and be less than 5mm.
9. static CT scanner as claimed in claim 1, is characterized in that: the diameter range of described annular x-ray source and described two annular detectors is 0.2m to 1.5m.
10. the scattering X-ray bearing calibration of the static CT scanner as described in claim 1～9 any one, it is characterized in that, comprise the steps: that described two annular detectors and described two annular monitoring detectors survey respectively the X-ray beam of described annular x-ray source transmitting simultaneously; Described data collecting system gathers respectively the data for projection of described detector system output and the data of described two annular monitoring detector outputs; Described computer, according to the data for projection of described detector system output, subtracts each other according to the data of preset rules and ratio and described two annular monitoring detector outputs, obtains the data for projection through scatter correction.
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| CN103340641B (en) * | 2013-04-27 | 2016-06-08 | 中国人民解放军北京军区总医院 | CT scanner Pulse Imageing system and Pulse Imageing method thereof |
| CN103385732A (en) * | 2013-07-25 | 2013-11-13 | 中国科学院苏州生物医学工程技术研究所 | Static CT (Computed Tomography) scanner |
| CN105361900B (en) * | 2014-08-26 | 2019-01-22 | 北京纳米维景科技有限公司 | Static CT imaging system and its image formation control method in real time |
| CN104434163B (en) * | 2014-12-05 | 2017-09-15 | 中国科学院深圳先进技术研究院 | A kind of carbon nanometer CT imaging systems and imaging method |
| CN104991485B (en) * | 2015-05-21 | 2017-11-03 | 明峰医疗系统股份有限公司 | A kind of sensor-based system power supply collator and its method based on positional information |
| CN105427355B (en) * | 2015-11-26 | 2018-04-03 | 上海联影医疗科技有限公司 | The method and device that case, the scattering composition of radioscopic image are calculated, rebuild |
| CN114113173A (en) * | 2021-11-18 | 2022-03-01 | 上海联影医疗科技股份有限公司 | X-ray equipment and scattering correction method applied to X-ray equipment |
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| EP2436013A4 (en) * | 2009-05-26 | 2017-04-12 | Rapiscan Security Products, Inc. | X-ray tomographic inspection system for the idendification of specific target items |
| CN102379716A (en) * | 2011-08-24 | 2012-03-21 | 苏州生物医学工程技术研究所 | Static CT (computed tomography) scanner system and scanning method thereof |
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