CN105759319A - Improved double-energy CT imaging method and apparatus - Google Patents
Improved double-energy CT imaging method and apparatus Download PDFInfo
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Abstract
The invention relates to an improved double-energy CT imaging method and apparatus, and belongs to the field of CT imaging. The apparatus scans a scanning object, the left half portion of a single-layer detector acquires low-energy projection data, the right half portion of the single-layer detector acquires high-energy projection data, according to a conjugation projection principle, equivalent low-energy projection data of the right half portion is obtained through the low-energy projection data of the left half portion of the single-layer detector, the equivalent high-energy projection data of the left half portion is obtained through the high-energy projection data of the right half portion of the single-layer detector, and then data processing and image reconstruction are carried out. The apparatus comprises a radiation source, a radiation source controller, a rotation mechanism, a motion controller, the single-layer detector, a metal filter, a data acquisition controller and a maser control computer. The left half portion of the single-layer detector comprises a low-energy detection element, and the right half portion comprises a high-energy detection element. The method and apparatus provided by the invention decrease the detector cost by nearly 50%.
Description
Technical field
The present invention relates to the dual intensity CT formation method of a kind of improvement and device, belong to CT (ComputedTomography, i.e. CT scan) imaging field, especially safety inspection CT imaging field.
Background technology
At present, dual intensity CT imaging pattern generally has following several: one is switch, by radiogenic high pressure, the data for projection obtaining under two high pressure, and object generally to be scanned twice by this mode.Two is adopt two radiographic sources, two detectors, and two radiographic sources arrange different tube voltages, and this equipment cost is significantly high.Three is that this method is higher to radiogenic requirement by radiogenic quick switching.Above-mentioned three kinds of situations are true dual-energy imaging.Four is adopt double decker detector, i.e. pseudo-dual-energy imaging, and the cost of detector is of a relatively high.Five is adopt photon counting detector, carries out spectral imaging, and this technology is currently also in the laboratory research stage, and the cost of detector is also very high.
Number of patent application be 201410294426.2 patent document disclose a kind of pseudo-dual-energy x-ray linear array imaging system, it adds aluminium foil copper sheet between mental retardation detection chip and high energy detection chip and constitutes pseudo-dual intensity detecting module, its shortcoming is, required detector is many, equipment cost is high, and there is substantial amounts of data redundancy amount when image reconstruction.
Summary of the invention
It is an object of the invention to for the deficiencies in the prior art, it is provided that the dual intensity CT formation method of a kind of improvement and device.
This invention address that the technical scheme of problem is: the dual intensity CT formation method of a kind of improvement is provided, comprises the steps:
(1) with the dual intensity CT imaging device improved, sweep object being scanned, the left-half of single slice detector collects mental retardation data for projection, and the right half part of single slice detector collects high energy data for projection；
(2) the Conjugate Projection principle according to CT scan data for projection, the mental retardation data for projection collected by the left-half of single slice detector obtains the mental retardation data for projection of the right half part of the single slice detector of equivalence, the high energy data for projection collected by the right half part of single slice detector obtains the high energy data for projection of the left-half of the single slice detector of equivalence, thus obtaining high energy data for projection and the mental retardation data for projection of whole single slice detector；
(3) dual intensity image reconstruction, obtains the physical parameter of sweep object.
Further, the method for the dual intensity image reconstruction in described step (3) adopts any one in pretreatment algorithm for reconstructing, post processing algorithm for reconstructing, iterative reconstruction algorithm.
The dual intensity CT imaging device of improvement of the present invention, including radiographic source, radiographic source controller, rotating mechanism, motion controller, single slice detector, metal filtration sheet, data acquisition controller, host computer, described host computer respectively with radiographic source controller, motion controller, data acquisition controller is connected, described radiographic source controller is connected with described radiographic source, described motion controller is connected with described rotating mechanism, described data acquisition controller is connected with described single slice detector, described single slice detector includes left-half and right half part, described metal filtration sheet is between the right half part and described radiographic source of described single slice detector and parallel to each other with the right half part of described single slice detector.
Further, the left-half of described single slice detector includes mental retardation and visits unit and the first data acquisition circuit plate, and the right half part of described single slice detector includes high energy and visits unit and the second data acquisition circuit plate.
Further, described mental retardation is visited unit and is included mental retardation crystal and the first diode, and described high energy is visited unit and included high energy crystal and the second diode.
Further, described first data acquisition circuit plate and the second data acquisition circuit plate are all connected with described data acquisition controller.
Further, described high energy crystal is thicker than mental retardation crystal.
Preferably, described high energy crystal and mental retardation crystal are scintillation crystal Gd2O2S、CsI、CdWO4In any one.
Further, the left-half of described single slice detector and the demarcation line of right half part are positioned at described radiogenic central beam on the straight line of the center of rotation of rotating mechanism.
Further, described metal filtration sheet covers the right half part of described single slice detector under the projection of described radiogenic ray.
Further, the material of described metal filtration sheet is copper or tungsten.
Further, described rotating mechanism is turntable or the frame with slip ring.
Further, described single slice detector is linear type or camber, and the arrangement of described single slice detector is linear array or face battle array.
The dual intensity CT formation method of improvement of the present invention and the principle of device are as follows:
The sinogram data that CT fan-beam 360 degree scanning obtains is redundancy, has following relation in isogonism fan-delta sandbody process between projection:
P (β, γ)=P (β+π-2 γ ,-γ)
Wherein β is the radiogenic anglec of rotation, and γ is projection (angle) address on isogonism detector.P (β, γ), P (β+π-2 γ ,-γ) are referred to as Conjugate Projection.The situation that fan-beam is equidistant can be derived similarly, have:
P (β, s)=P (β+π-2 γ ,-s)
S is the projection address of equidistant detector, and γ is projection address is the ray angle with central beam of s.
Based on the sinogram of fan-delta sandbody and the geometrical relationship of Conjugate Projection it can be seen that the data for projection of fan-delta sandbody not still redundancy, and exactly redundancy half.
Based on above-mentioned analysis, the dual intensity CT imaging device of the improvement designed by the present invention, according to the mental retardation data for projection that the left-half of single slice detector collects, it becomes possible to obtain the mental retardation data for projection of the right half part of equivalence.In like manner, the high energy data for projection collected according to the right half part of single slice detector, it becomes possible to obtain the high energy data for projection of the left-half of equivalence, therefore just obtain complete high mental retardation data for projection.According to the high mental retardation data for projection completed, dual intensity CT image reconstruction just can be carried out.
For dual intensity image reconstruction, mainly there are three class algorithm for reconstructing, including pretreatment algorithm for reconstructing, post processing algorithm for reconstructing, iterative reconstruction algorithm.For post processing algorithm for reconstructing, it is simply that first rebuild the CT tomograph of high mental retardation, further according to the method for high mental retardation cross-sectional image substance for calculation physical parameter.
For iterative reconstruction algorithm, this kind of method process by iteration, obtain unrelated with power spectrum or approximate unrelated CT image, and then suppress the artifact brought by beam hardening effect, improve picture quality.
The following is the principle of pretreatment algorithm for reconstructing:
It is known that within the scope of ray energy within 200keV, the interaction of ray and material is arranged by Compton scattering and photoelectric effect.And for the linear attenuation coefficient of material, have following approximate model to exist:
μ (E)=acfKN(E)+apfp(E)
Wherein E is ray energy, fp(E)、fKN(E) for only with energy about and the decomposition coefficient unrelated with material.And have:
α=E/510.975KeV, apRepresent photoelectric effect coefficient, acFor compton effect,scattering coefficient, ap、acIt is independently of the physical quantity that energy is only relevant with material, and has:
l1、l2Being two constants, ρ is material density, and Z is atomic number, and A is atomic weight；This model representation is within the scope of certain ray energy, and the decay of material can be collectively constituted by photoelectric effect and two kinds of effects of Compton scattering.This model is normally referred to as base effect model (also can claim double; two effect model).
According to attenuation quotient decomposition model, remember:
Ac=∫ acdl,Ap=∫ apdl
BEER law when according to wide power spectrum ray has:
SH(E)、SL(E), PH、PLRespectively high low power range system power spectrum and the projection of high mental retardation.Core based on the dual intensity CT pretreatment algorithm for reconstructing of Projective decomposition is solving of above-mentioned equation group, namely solves A according to above equation groupc、Ap, we claim this process to be Projective decomposition process.Due to Ac、ApFor ac、apLine integral projection value, solve Ac、ApAfter, according to the CT principle rebuild, utilize filtered backprojection image algorithm for reconstructing, just can calculate ac、ap, thus can calculate the equivalent atom ordinal sum electron density information of material, to complete the detection identification of material.Computing formula is as follows:
ρe=K2ac
(K1、K2It is two constants, n ≈ 3～4)
The present invention improve dual intensity CT formation method and device have the beneficial effect that modern design of the present invention is ingenious, the right half part of unit is visited by being divided into single slice detector comprising the first left-half of mental retardation spy and comprising high energy, not only the data for projection of redundancy is simplified, and greatly reducing installation cost, the cost of detector reduces nearly 50%.
Accompanying drawing explanation
Fig. 1 is the connection diagram of the dual intensity CT imaging device of improvement of the present invention；
Fig. 2 is the structural representation of the dual intensity CT imaging device of improvement of the present invention；
Fig. 3 is CT fan-delta sandbody principle schematic；
Fig. 4 is that CT fan-delta sandbody sinogram represents principle schematic.
In figure: 1-radiographic source；2-radiographic source controller；31-turntable；32-is with the frame of slip ring；4-motion controller；5-single slice detector, 51-left-half, 52-right half part, 511-mental retardation visit unit, 512-the first data acquisition circuit plate, 521-high energy visit unit, 522-the second data acquisition circuit plate；6-metal filtration sheet；7-data acquisition controller；8-host computer.
Detailed description of the invention
Below in conjunction with accompanying drawing, the present invention is further illustrated.
Embodiment one:
Fig. 1 illustrates the connection diagram of the dual intensity CT imaging device of improvement of the present invention, and the rotating mechanism in figure is turntable.In the present embodiment, device of the present invention is based on the imaging pattern that turntable rotates, and namely sweep object rotates, and radiographic source and single slice detector all do not rotate.
As it is shown in figure 1, the dual intensity CT formation method of improvement of the present invention, comprise the steps:
(1) with the dual intensity CT imaging device improved, sweep object being scanned, the left-half 51 of single slice detector 5 collects mental retardation data for projection, and the right half part 52 of single slice detector 5 collects high energy data for projection；
(2) the Conjugate Projection principle according to CT scan data for projection, the mental retardation data for projection collected by the left-half 51 of single slice detector 5 obtains the mental retardation data for projection of the right half part 52 of the single slice detector 5 of equivalence, the high energy data for projection collected by the right half part 52 of single slice detector 5 obtains the high energy data for projection of the left-half 51 of the single slice detector 5 of equivalence, thus obtaining high energy data for projection and the mental retardation data for projection of whole single slice detector；
(3) dual intensity image reconstruction, obtains the physical parameter of sweep object.
The method of the dual intensity image reconstruction in described step (3) adopts any one in pretreatment algorithm for reconstructing, post processing algorithm for reconstructing, iterative reconstruction algorithm.
The dual intensity CT imaging device of improvement of the present invention, including radiographic source 1, radiographic source controller 2, turntable 31, motion controller 4, single slice detector 5, metal filtration sheet 6, data acquisition controller 7, host computer 8, described host computer 8 respectively with radiographic source controller 2, motion controller 4, data acquisition controller 7 is connected, described radiographic source controller 2 is connected with described radiographic source 1, described motion controller 4 is connected with described turntable 31, described data acquisition controller 7 is connected with described single slice detector 5, described single slice detector 5 includes left-half 51 and right half part 52, described metal filtration sheet 6 is parallel to each other between the right half part 52 and described radiographic source 1 of described single slice detector 5 and with the right half part 52 of described single slice detector 5.
The left-half 51 of described single slice detector 5 includes mental retardation and visits unit 511 and the first data acquisition circuit plate 512, and the right half part 52 of described single slice detector 5 includes high energy and visits unit 521 and the second data acquisition circuit plate 522.
Described mental retardation is visited unit 511 and is included mental retardation crystal and the first diode, and described high energy is visited unit 521 and included high energy crystal and the second diode.
Described first data acquisition circuit plate 512 is all connected with described data acquisition controller 7 with the second data acquisition circuit plate 522.
Described high energy crystal is thicker than mental retardation crystal.
Described high energy crystal and mental retardation crystal are scintillation crystal Gd2O2S、CsI、CdWO4In any one.
The left-half 51 of described single slice detector 5 and the demarcation line of right half part 52 are positioned at the central beam of described radiographic source 1 on the straight line of the center of rotation of turntable 31.
Described metal filtration sheet 6 covers the right half part 52 of described single slice detector 5 under the projection of the ray of described radiographic source 1.
The material of described metal filtration sheet 6 is copper or tungsten.
Described single slice detector 5 is linear type, and the arrangement of described single slice detector 5 is linear array.
Embodiment two:
Fig. 2 illustrates the structural representation of the dual intensity CT imaging device of improvement of the present invention, and in figure, rotating mechanism is the frame with slip ring.In the present embodiment, device of the present invention is based on the imaging pattern that slip ring rotates, and namely radiographic source and single slice detector rotate with the frame with slip ring, and sweep object then moves in parallel, as shown in Figure 2.
In the present embodiment, the step of the dual intensity CT formation method of described improvement is identical with the step in embodiment one.
nullThe dual intensity CT imaging device of improvement of the present invention，Including radiographic source 1、Radiographic source controller 2、Frame 32 with slip ring、Motion controller 4、Single slice detector 5、Metal filtration sheet 6、Data acquisition controller 7、Host computer 8，Described host computer 8 respectively with radiographic source controller 2、Motion controller 4、Data acquisition controller 7 is connected，Described radiographic source controller 2 is connected with described radiographic source 1，Described motion controller 4 is connected with the described frame 32 with slip ring，Described data acquisition controller 7 is connected with described single slice detector 5，Described single slice detector 5 includes left-half 51 and right half part 52，Described metal filtration sheet 6 is parallel to each other between the right half part 52 and described radiographic source 1 of described single slice detector 5 and with the right half part 52 of described single slice detector 5.
The left-half 51 of described single slice detector 5 includes mental retardation and visits unit's (not shown) and the first data acquisition circuit plate (not shown), and the right half part 52 of described single slice detector 5 includes high energy and visits unit's (not shown) and the second data acquisition circuit plate (not shown).
Described mental retardation is visited unit and is included mental retardation crystal and the first diode, and described high energy is visited unit and included high energy crystal and the second diode.
Described first data acquisition circuit plate and the second data acquisition circuit plate are all connected with described data acquisition controller 7.
Described high energy crystal is thicker than mental retardation crystal.
Described high energy crystal and mental retardation crystal are scintillation crystal Gd2O2S、CsI、CdWO4In any one.
The left-half 51 of described single slice detector 5 and the demarcation line of right half part 52 are positioned at the central beam of described radiographic source 1 on the straight line of the center of rotation of the frame 32 with slip ring.
Described metal filtration sheet 6 covers the right half part 52 of described single slice detector 5 under the projection of the ray of described radiographic source 1.
The material of described metal filtration sheet 6 is copper or tungsten.
Described single slice detector 5 is camber, and the arrangement of described single slice detector 5 is face battle array.
In the present embodiment, described radiographic source 1 is relatively fixed in the frame 32 with slip ring with single slice detector 5, and described radiographic source 1 rotates with the frame 32 with slip ring around a public axle center with single slice detector 5.
In the present embodiment, the transporter of sweep object is also connected with motion controller 4.
Fig. 3-Fig. 4 illustrates the dual intensity CT formation method of improvement of the present invention and the schematic diagram of device, and Fig. 3 and Fig. 4 is all for D fan scanning.
Fig. 3 illustrates CT fan-delta sandbody principle schematic, in figure, described direction of rotation for turning clockwise, SmFor maximal projection address, under visual angle β and visual angle β+π-2 γ:
Isogonism fan-delta sandbody process there is following relation between projection:
P (β, γ)=P (β+π-2 γ ,-γ)
Wherein β is the radiogenic anglec of rotation, and γ is projection (angle) address on isogonism detector.P (β, γ), P (β+π-2 γ ,-γ) are referred to as Conjugate Projection.Similar can derive the situation that fan-beam is equidistant, has:
P (β, s)=P (β+π-2 γ ,-s)
S is the projection address of equidistant detector, and γ is projection address is the ray angle with central beam of S.
Fig. 4 illustrates that CT fan-delta sandbody sinogram represents principle schematic, and in figure, COR (CenterofRotation) is for measuring projection rotating center, wherein Sl, SrFor maximal projection address, detector both bounded sides, γml,γmrThe respectively sail angle of the beam relative centre beam that detector both bounded sides are corresponding.Geometrical relationship according to Conjugate Projection is it can be seen that dotted portion projection value correspondent equal from top to bottom, dotted portion projection value correspondent equal from top to bottom in trapezoid area B and D in trapezoid area A and C.Therefore region A and C is two regions of data correspondent equal, and region B and D is also two regions of data correspondent equal.Therefore, the data for projection of fan-delta sandbody not still redundancy, and exactly redundancy half.
The work process of the dual intensity CT imaging device of improvement of the present invention is as follows: host computer controls the rotation of rotating mechanism by motion controller, control radiogenic open and close by radiographic source controller simultaneously, gathered the mental retardation data for projection of the left-half of single slice detector and the high energy data for projection of right half part by data acquisition controller；According to Conjugate Projection principle, the mental retardation data for projection collected by the left-half of single slice detector obtains the mental retardation data for projection of the right half part of equivalence, the high energy data for projection collected by the right half part of single slice detector obtains the high energy data for projection of the left-half of equivalence, thus obtaining high energy data for projection and the mental retardation data for projection of whole single slice detector, according to dual intensity CT image reconstruction algorithm, carry out image reconstruction, obtain the physical parameters such as the density of sweep object, atomic number, attenuation quotient.
The present invention is not limited to above-mentioned embodiment, and when without prejudice to the flesh and blood of the present invention, any deformation that it may occur to persons skilled in the art that, improvement, replacement each fall within protection scope of the present invention.
Claims (10)
1. the dual intensity CT formation method improved, it is characterised in that comprise the steps:
(1) with the dual intensity CT imaging device improved, sweep object being scanned, the left-half of single slice detector collects mental retardation data for projection, and the right half part of single slice detector collects high energy data for projection；
(2) the Conjugate Projection principle according to CT scan data for projection, the mental retardation data for projection collected by the left-half of single slice detector obtains the mental retardation data for projection of the right half part of the single slice detector of equivalence, the high energy data for projection collected by the right half part of single slice detector obtains the high energy data for projection of the left-half of the single slice detector of equivalence, thus obtaining high energy data for projection and the mental retardation data for projection of whole single slice detector；
(3) dual intensity image reconstruction, obtains the physical parameter of sweep object.
2. the dual intensity CT formation method of improvement according to claim 1, it is characterised in that the method for the dual intensity image reconstruction in described step (3) adopts any one in pretreatment algorithm for reconstructing, post processing algorithm for reconstructing, iterative reconstruction algorithm.
3. the dual intensity CT imaging device improved, it is characterized in that, including radiographic source, radiographic source controller, rotating mechanism, motion controller, single slice detector, metal filtration sheet, data acquisition controller, host computer, described host computer respectively with radiographic source controller, motion controller, data acquisition controller is connected, described radiographic source controller is connected with described radiographic source, described motion controller is connected with described rotating mechanism, described data acquisition controller is connected with described single slice detector, described single slice detector includes left-half and right half part, described metal filtration sheet is between the right half part and described radiographic source of described single slice detector and parallel to each other with the right half part of described single slice detector.
4. the dual intensity CT imaging device of improvement according to claim 3, it is characterized in that, the left-half of described single slice detector includes mental retardation and visits unit and the first data acquisition circuit plate, the right half part of described single slice detector includes high energy and visits unit and the second data acquisition circuit plate, described mental retardation is visited unit and is included mental retardation crystal and the first diode, and described high energy is visited unit and included high energy crystal and the second diode.
5. the dual intensity CT imaging device of improvement according to claim 4, it is characterised in that described first data acquisition circuit plate and the second data acquisition circuit plate are all connected with described data acquisition controller.
6. the dual intensity CT imaging device of improvement according to claim 4, it is characterised in that described high energy crystal is thicker than mental retardation crystal, and described high energy crystal and mental retardation crystal are scintillation crystal Gd2O2S、CsI、CdWO4In any one.
7. the dual intensity CT imaging device of improvement according to claim 3, it is characterised in that the left-half of described single slice detector and the demarcation line of right half part are positioned at described radiogenic central beam on the straight line of the center of rotation of rotating mechanism.
8. the dual intensity CT imaging device of improvement according to claim 3, it is characterised in that described metal filtration sheet covers the right half part of described single slice detector under the projection of described radiogenic ray；The material of described metal filtration sheet is copper or tungsten.
9. the dual intensity CT imaging device of improvement according to claim 3, it is characterised in that described rotating mechanism is turntable or the frame with slip ring.
10. the dual intensity CT imaging device of improvement according to claim 3, it is characterised in that described single slice detector is linear type or camber, the arrangement of described single slice detector is linear array or face battle array.
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Cited By (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106841244A (en) * | 2017-02-23 | 2017-06-13 | 门阔 | The method that material composition is obtained using CBCT spectral imagings |
| CN107356615A (en) * | 2016-05-10 | 2017-11-17 | 清华大学 | A kind of method and system for dual-energy x-ray CT |
| CN107797155A (en) * | 2016-08-31 | 2018-03-13 | 合肥美亚光电技术股份有限公司 | Compton backscattering detection means |
| CN108333204A (en) * | 2017-12-29 | 2018-07-27 | 公安部第三研究所 | X-ray back scattering detecting structure and imaging method |
| CN108535293A (en) * | 2018-02-26 | 2018-09-14 | 奕瑞新材料科技（太仓）有限公司 | Compton scatter imaging method |
| CN109632844A (en) * | 2019-01-09 | 2019-04-16 | 中国人民解放军战略支援部队信息工程大学 | Dual intensity CT imaging system and method based on linear scanning track |
| CN109946747A (en) * | 2019-03-25 | 2019-06-28 | 北京航星机器制造有限公司 | A kind of dual intensity CT detection system based on novel detection device |
| CN110237444A (en) * | 2019-07-01 | 2019-09-17 | 新里程医用加速器(无锡)有限公司 | CBCT device, CBCT apparatus control method and radiotherapy system |
| CN111366982A (en) * | 2020-03-10 | 2020-07-03 | 上海英曼尼安全装备有限公司 | Detector device of dual-energy CT system, dual-energy CT system and image reconstruction method |
Citations (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1759810A (en) * | 2004-10-14 | 2006-04-19 | Ge医疗系统环球技术有限公司 | X-ray CT appts. |
| CN101229063A (en) * | 2006-12-18 | 2008-07-30 | Ge医疗系统环球技术有限公司 | X-ray computed tomography apparatus |
| CN101266216A (en) * | 2007-03-14 | 2008-09-17 | 清华大学 | Method for calibrating dual-energy CT system and image rebuilding method |
| CN102090900A (en) * | 2009-12-11 | 2011-06-15 | 通用电气公司 | System and method of mitigating low signal data for dual energy CT |
| CN102456228A (en) * | 2010-10-29 | 2012-05-16 | Ge医疗系统环球技术有限公司 | Image reconstruction method and device and CT (computed tomography) machine |
| CN102539460A (en) * | 2012-01-06 | 2012-07-04 | 公安部第一研究所 | Projection center-of-rotation positioning method of computerized tomography (CT) system |
| CN103995278A (en) * | 2014-05-07 | 2014-08-20 | 东北大学 | Double-energy linear array detector for X-ray safety check device |
| CN104065889A (en) * | 2014-06-25 | 2014-09-24 | 山东大学 | Pseudo dual energy X-ray line array imaging system |
| CN204422781U (en) * | 2015-03-06 | 2015-06-24 | 公安部第一研究所 | A kind of dual intensity CT imaging device of improvement |
-
2015
- 2015-03-06 CN CN201510100251.1A patent/CN105759319A/en active Pending
Patent Citations (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1759810A (en) * | 2004-10-14 | 2006-04-19 | Ge医疗系统环球技术有限公司 | X-ray CT appts. |
| CN101229063A (en) * | 2006-12-18 | 2008-07-30 | Ge医疗系统环球技术有限公司 | X-ray computed tomography apparatus |
| CN101266216A (en) * | 2007-03-14 | 2008-09-17 | 清华大学 | Method for calibrating dual-energy CT system and image rebuilding method |
| CN102090900A (en) * | 2009-12-11 | 2011-06-15 | 通用电气公司 | System and method of mitigating low signal data for dual energy CT |
| CN102456228A (en) * | 2010-10-29 | 2012-05-16 | Ge医疗系统环球技术有限公司 | Image reconstruction method and device and CT (computed tomography) machine |
| CN102539460A (en) * | 2012-01-06 | 2012-07-04 | 公安部第一研究所 | Projection center-of-rotation positioning method of computerized tomography (CT) system |
| CN103995278A (en) * | 2014-05-07 | 2014-08-20 | 东北大学 | Double-energy linear array detector for X-ray safety check device |
| CN104065889A (en) * | 2014-06-25 | 2014-09-24 | 山东大学 | Pseudo dual energy X-ray line array imaging system |
| CN204422781U (en) * | 2015-03-06 | 2015-06-24 | 公安部第一研究所 | A kind of dual intensity CT imaging device of improvement |
Non-Patent Citations (2)
| Title |
|---|
| 李保磊 等: "工业计算机断层成像系统转台旋转中心的确定", 《航空动力学报》 * |
| 高洋: "双能CT图像重建算法研究", 《中国优秀硕士学位论文全文数据库 信息科技辑》 * |
Cited By (11)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN107356615A (en) * | 2016-05-10 | 2017-11-17 | 清华大学 | A kind of method and system for dual-energy x-ray CT |
| CN107356615B (en) * | 2016-05-10 | 2020-01-21 | 清华大学 | Method and system for dual-energy X-ray CT |
| CN107797155A (en) * | 2016-08-31 | 2018-03-13 | 合肥美亚光电技术股份有限公司 | Compton backscattering detection means |
| CN106841244A (en) * | 2017-02-23 | 2017-06-13 | 门阔 | The method that material composition is obtained using CBCT spectral imagings |
| CN108333204A (en) * | 2017-12-29 | 2018-07-27 | 公安部第三研究所 | X-ray back scattering detecting structure and imaging method |
| CN108535293A (en) * | 2018-02-26 | 2018-09-14 | 奕瑞新材料科技（太仓）有限公司 | Compton scatter imaging method |
| CN108535293B (en) * | 2018-02-26 | 2020-08-25 | 张岚 | Compton scattering imaging method |
| CN109632844A (en) * | 2019-01-09 | 2019-04-16 | 中国人民解放军战略支援部队信息工程大学 | Dual intensity CT imaging system and method based on linear scanning track |
| CN109946747A (en) * | 2019-03-25 | 2019-06-28 | 北京航星机器制造有限公司 | A kind of dual intensity CT detection system based on novel detection device |
| CN110237444A (en) * | 2019-07-01 | 2019-09-17 | 新里程医用加速器(无锡)有限公司 | CBCT device, CBCT apparatus control method and radiotherapy system |
| CN111366982A (en) * | 2020-03-10 | 2020-07-03 | 上海英曼尼安全装备有限公司 | Detector device of dual-energy CT system, dual-energy CT system and image reconstruction method |
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