CN104809750B - A kind of linear scanning CT system and image rebuilding method - Google Patents
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Abstract
The present invention relates to a kind of linear scanning CT system and image rebuilding method, belong to CT scan technical field.A kind of linear scanning CT system, the system includes x-ray source, detector, detection object, data collecting system, image reconstruction and shows computer system, control system and mechanical system；The detector is face Array Plate detector；X-ray source does opposite parallel lines around detection object with detector and moved in scanning process；A kind of linear scanning CT system that the present invention is provided does not use the slide ring portion and big visual field multilayer detection system of conventional CT system, have the advantages that simple in construction, inexpensive, removable/portable, for linear scanning CT system, present invention also offers a kind of exact reconstruction algorithm, the data for projection that may be directly applied to the system carries out image reconstruction, with preferable anti-noise ability and arithmetic speed is very fast.
Description
Technical field
The invention belongs to CT scan technical field, it is related to a kind of linear scanning CT system and image rebuilding method.
Background technology
Since being come out from 1970s, and X ray computer tomography (Computed Tomography, referred to as
CT the key technology of medical diagnostic image) is turned into, CT system configuration quantity, the quantity of CT scan imaging are always in growth
Trend.Statistics display in 2007, global in-service CT system is more than 45000 sets, and the U.S. CT of 1 year detects number more than 7000
Ten thousand person-times.
Chinese medicine equipment association provides《Chinese CT Analysis on Market Development report》It has been shown that, China's CT machines possess within 2010
Measure as 11 242, the owning amount per a population of one million CT machines increases to 8.6 in 2010 from 5.5 of 2006.In the world,
Japan possesses CT machines up to 98 per a population of one million within 2006, and Australia is 51.Owning amount of the China per a population of one million CT machines
Although maintaining faster growth level, compared with developed countries, owning amount is still relatively low.Therefore, should《Report》Point out, I
State is huge to CT system potential of demand.Correspondingly, other developing countries and regions, such as India, Africa, Latin America, also there is wide
Big market.
In recent years, research and development input of the CT system in directions such as sweep speed, low dosage, picture qualities is more.Such as
Using multilayer, big fan angle scanning, multiray source system, connected applications high speed rotary slip ring technology, expect meet it is clinically fast
The demand of fast large area scanning.However, existing medical CT system is all based on x-ray source and detector around detection object rotation
Scanning, it is use filtered backprojection image algorithm for reconstructing, it is necessary to (>=180 °) collection numbers of global full angle (360 °) or half angle more
According to.Correspondingly, slip ring turns into critical component indispensable in CT system.And slip ring manufacture is complicated, it is difficult to simplify CT system
Structure.Therefore, modern Medical CT system price is expensive, and use requirement is high, and only developed country or developing country is large-scale
Medical institutions are equipped with, and the CT equipment that many developing country, remote districts etc. are needed badly is difficult to possess.According to newest report
Road, U.S. Department of Defense have subscribed 70,000,000 dollars of removable, new x-ray imaging systems of transmission of wireless signals in January, 2014
System, for solving Military Medical demand, illustrates that the special dimensions such as military affairs, wartime medical treatment also need new CT equipment badly.
Therefore, advanced CT imaging methods are tracked, carry out new CT technical foundation research, so development structure it is simple, it is low into
Originally, removable/portable new CT system is very necessary and urgent.
The content of the invention
In view of this, it is an object of the invention to provide a kind of linear scanning CT system and image rebuilding method, the system
Use conventional CT system slide ring portion and big visual field multilayer detection system, with it is simple in construction, inexpensive, removable/
Portable the advantages of, a kind of exact reconstruction algorithm is additionally provided, the data for projection that may be directly applied to the system carries out image weight
Build, with preferable anti-noise ability and arithmetic speed is very fast.
An object of the present invention is to provide a kind of linear scanning CT system；The second object of the present invention is to provide a kind of straight
The image rebuilding method of line scanning computed tomography.
An object of the present invention is achieved through the following technical solutions：A kind of linear scanning CT system, the system
Computer system, control system and machine are shown including x-ray source, detector, detection object, data collecting system, image reconstruction
Tool system；
The x-ray source sends X-ray penetration-detection object, reaches detector, and dampening information is converted to electricity by detector
Signal and through the incoming computer system of data collecting system, shows after carrying out image reconstruction process through computer system；It is described to visit
Survey device is face Array Plate detector；X-ray source does opposite parallel lines with detector around detection object in scanning process
Motion.
Further, the X-ray in the scanning system through visual field is with respect to the projection angle θ of x-axis：
Wherein, SDIt is radiographic source along y-axis and the distance of detector；xDScanning field of view centrally along x-axis and detector cells it
Between distance；xiFor ray source position, projection number when i=1 ..., I, wherein I are radiographic source linear motions.
Further, X-ray and the projection centre ray in the scanning system through visual field are apart from l：
Wherein, xiFor ray source position, projection number when i=1 ..., I, wherein I are radiographic source linear motions；SoTo penetrate
Distance of the line source along y-axis and scanning field of view center；γ is angle of the ray with the ray for being projected through scanning field of view center, γ
=β-θ, β=θ(l=0)To be projected through scanning field of view center O ray and the angle of x-axis；L span is [- R, R], R
For the radius of scanning field of view.
Further, the system is scanned by the way of multiple straight line parallel moving sweep.
Further, the system is scanned by the way of the multiple parallel lines scanning of isogonism, and acquisition is regarded around scanning
Field is not less than 180 ° of data for projection.
Further, the mode of the multiple parallel lines scanning of the isogonism includes 2 orthogonal linear scanning or 3 circumference
Equally distributed linear scanning.
Further, the system by the way of the multiple parallel lines scanning of isogonism when being scanned, by non-equidistant
Radiographic source projection obtain relative to scanning field of view even circumferential data for projection, i.e. isogonism sample mode, and isogonism sampling side
Case is：
Wherein, β=θ(l=0), to be projected through scanning field of view center O ray and the angle of x-axis；SOIt is radiographic source along y-axis
With the distance at scanning field of view center；△ β is the angles between projecting twice, the start position x that △ β are moved according to radiographic source1With
Final position xICalculate；
The second object of the present invention is achieved through the following technical solutions：A kind of linear scanning CT image reconstruction side
Method, this method comprises the following steps：
S1：Fan beam projections data weighting is carried out by below equation：
Pa(xi,xD)=| cos γ | * P (xi,xD)；
Wherein, P (xi,xD) it is the data for projection gathered, Pa(xi,xD) for weighting after data for projection；xiFor radiographic source position
Put；xDBe scanning field of view centrally along the distance between x-axis and detector cells, γ is the ray for being projected through scanning field of view center
With the angle of the ray；
S2：Weighted projection data is filtered by below equation：
Pb(xi,xD)=Pa(xi,xD)*h(xD)；
Wherein,Pb(xi,xD) it is filtered data for projection, h (xD) be spatial domain in slope
Wave filter；
S3：Back projection：
Wherein,For back projection's coefficient, T is linear scanning number of times, η=1 ..., T.
Further, the data for projection is non-equidistant radiographic source projection acquisition relative to scanning field of view even circumferential
Data for projection；It is scanned using the multiple parallel lines scan pattern of isogonism, a linear scanning can obtain I X-ray throwing
Shadow data, one time CT scan is realized by T linear scanning, and the projection number M of a CT scan is evenly distributed on equivalent be not less than
In 180 ° of projection angle, reconstruction image matrix is N × N；Wherein,
The beneficial effects of the present invention are：A kind of linear scanning CT system that the present invention is provided, using radiographic source and face battle array
Row flat panel detector parallel lines moving sweep, simulation radiographic source and detector are not used around the rotation sweep of detection object
The slide ring portion of conventional CT system and big visual field multilayer detection system, can be with simplied system structure and reduction system cost.Straight line
Scanning computed tomography is imaged, and in the case where detector size is constant, its field of detection changes with scanning process, with conventional CT image weight
Build algorithm different, therefore present invention also offers a kind of linear scanning CT image exact reconstruction algorithm, may be directly applied to
The data for projection of the system carries out image reconstruction, with preferable anti-noise ability and arithmetic speed is very fast.
Brief description of the drawings
In order that the object, technical solutions and advantages of the present invention are clearer, below in conjunction with accompanying drawing the present invention is made into
The detailed description of one step, wherein：
Fig. 1 is linear scanning CT system model of the present invention；
Fig. 2 for system of the present invention CT scan in phantom two-dimensional geometry model；
Fig. 3 is the multiple parallel lines scan mode schematic diagram of isogonism；
Fig. 4 is the reconstructing parameters figure of fladellum；
The Shepp-Logan models that Fig. 5 (a) uses for experiment 1；
The CT images that Fig. 5 (b) obtains for 2T scan mode FBP image reconstruction algorithms in experiment 1；
The CT images that Fig. 5 (c) obtains for 3T scan mode FBP image reconstruction algorithms in experiment 1；
The newly-designed model 2 that Fig. 6 (a) experiments 2 are used；
The CT images that 2T scan mode FBP image reconstruction algorithms are obtained in Fig. 6 (b) experiments 2；
The CT images that 3T scan mode FBP image reconstruction algorithms are obtained in Fig. 6 (c) experiments 2；
Wherein, 1 is x-ray source, and 2 be detection object, and 3 be detector, and 4 be data collecting system, and 5 be that image reconstruction is shown
Computer system 6 is control system, 7 be mechanical system.
Embodiment
Below in conjunction with accompanying drawing, the preferred embodiments of the present invention are described in detail.
A kind of linear scanning CT system that the present invention is provided, its model are as shown in figure 1, x-ray source 1, detects object 2, spy
Device 3, and data collecting system 4 are surveyed, image reconstruction shows computer system 5, control system 6 and mechanical system 7.
X-ray source sends X-ray penetration-detection object, reaches detector, and detector changes the information after X-ray attenuation
For electric signal and through the incoming computer system of data collecting system, shown after carrying out image reconstruction process through computer system；Visit
Survey device is face Array Plate detector；X-ray source does opposite parallel lines with detector around detection object in scanning process
Motion.
The present invention rebuilds for middle linear array detector fladellum two dimensional image and studied, it is possible to be generalized to three-dimensional
Image reconstruction.As shown in Fig. 2 detector is by being spaced at equal intervals, theory analysis may be assumed that detector column is endless, radiographic source fortune
Moving axis is parallel with detector plane, and detection object is placed between radiographic source and detector, and the central point of xoy coordinate systems is fixed on
On central point of the radius for R scanning field of view.Given ray source position xi(i=1 ..., I), wherein I is radiographic source straight line fortune
Projection number when dynamic, the ray for reaching detector cells by scanning field of view center is called position xiThe central ray at place, θ is should
Certain lower ray of projection is with respect to the projection angle of x-axis, and γ is the angle of central ray and the ray.SOBe radiographic source along y-axis with sweeping
Retouch the distance at object center, SDIt is radiographic source along y-axis and the distance of detector.The linear motion and x-axis of radiographic source and detector
It is parallel.Then, in 2 dimensional planes, the projection angle θ of the relative x-axis of X-ray through visual field is：
xDIt is scanning field of view centrally along the distance between x-axis and detector cells.
If γ=β-θ, to be projected through the ray at scanning field of view center and the angle of the ray, β=θ(l=0)It is logical for projection
Over-scan field of view center O ray and the angle of x-axis；Then X-ray and the projection centre ray through visual field are apart from l：
Parameter l span is [- R, R] in formula (2).
Parallel beam CT structures realize that a necessary condition of CT image Exact Reconstructions is to obtain to surround no less than 180 °
The parallel projection of scanning field of view.However, 1 straight line parallel moving sweep pattern can not substantially obtain no less than 180 ° degree scopes
Data for projection.Therefore, can use the method for multiple straight line parallel moving sweep.For example, being scanned by the multiple parallel lines of isogonism
Mode be scanned.As shown in figure 3, what we can be distributed using 2 orthogonal linear scanning (2T) or 3 even circumferentials
Linear scanning (3T) obtains the data for projection not less than 180 ° around scanning field of view, and wherein Fig. 3 (a) is 2T patterns, and Fig. 3 (b) is
3T patterns.
Radiographic source, detector parallel lines motion CT scan pattern, are to move mould by radiographic source, detector parallel lines
Intend the rotary motion that radiographic source-detector surrounds field of detection.Dot in Fig. 3 on each straight line represents a straight line and swept
The projected position of motion radiographic source is retouched, radiographic source projected position is equidistant mode.Obviously, the equidistant projection mode of radiographic source is obtained
The projection relative scanning visual field obtained is circumferentially uneven, unfavorable to image reconstruction.Therefore, we pass through non-equidistant ray
Source projection obtains the data for projection relative to scanning field of view even circumferential, i.e. isogonism sample mode.
For the multiple parallel lines scan pattern of isogonism, linear scanning of setting can obtain I X-ray projection data,
CT scan is realized by T parallel lines scanning, it is assumed that the projection number M of a CT scan is evenly distributed on equivalent 180 °
In projection angle, reconstruction image matrix is N × N, then
If β=θ(l=0), to be projected through scanning field of view center O ray and the angle of the ray.Sampling side can then be obtained
Case：
xi=-Socot[β1+ (i-1) △ β], (8)
Wherein, △ β is the angles between projecting twice, the start position x that △ β are moved according to radiographic source1With final position xI
Calculate.
Present invention also offers a kind of linear scanning CT image rebuilding method.Parallel beam X-ray is through object declining always
Subtracting can be represented by line integral, even work as conversion
Wherein f (x, y) represents object (or attenuation coefficient distribution of X-ray)；Represent that scanning angle is
Projection ray and the data for projection that initial point distance is l；δ () represents carat function either impulse function in Di；Represent the projection line of X-ray.It is by Fourier transformation (FT) Central slice theorem, i.e. projection angleData for projectionFourier transformationEqual to the Fourier transformation of center slice
F (x, y) can by inverse Fourier transform (1FT) if or antithesis come out when transform reconstruction, it is as follows：
WhereinRepresent reconstruction image；| w | it is referred to as " jump " filtering in frequency domain
Device；Ramp filterBe | w | Fourier inversion.
As shown in figure 4, in the case of fladellum, every fan beam projections rayThrown with the parallel beam of equidirectional
Shadow line g (γ, β) is corresponding, and corresponding relation is
Then have
With polar coordinates (r, α) represent cartesian coordinate (x, y), i.e. x=rcos α, y=rsin α, andThen
Replace variable can specific factor beBy formula (12), (13) are obtained
Formula (15) is Fan-beam Reconstruction algorithm.
A kind of linear scanning CT image rebuilding method, comprises the following steps：
S1：Fan beam projections data weighting：
Pa(xi,xD)=| cos γ | * P (xi,xD), (16)
Wherein P (xi,xD) it is the data for projection gathered, Pa(xi,xD) be weighting after data for projection.
S2：Weighted projection data is filtered：
Pb(xi,xD)=Pa(xi,xD)*h(xD), (17)
Wherein Pb(xi,xD) it is filtered data for projection, h (xD) it is ramp filter in spatial domain,
S3：Not less than the back projection in the range of [0, π]：
Wherein,It is back projection's coefficient, T is linear scanning number of times, η=1 ..., T.
Using MATLAB, we simulate the fan beam projections and FBP image reconstructions of parallel lines CT scan, and table 1 is imitative
True sweep parameter.
Experiment 1：
Emulation experiment image uses Shepp-Logan models, shown in such as Fig. 5 (a).The field number of scan image is
256mm, reconstruction image matrix size is 512 × 512.Following result is obtained by simulation scanning and image reconstruction, Fig. 5 (b),
(c) it is respectively CT images that 2T and 3T scan mode FBP image reconstruction algorithms are obtained.
Experiment 2：
Emulation experiment image uses newly-designed model 2, such as shown in Fig. 6 (a), between model image has several width different
The parting bead line circular hole different with several diameters, minimum Circularhole diameter is a pixel.The field number of scan image is 256mm,
Reconstruction image matrix size is 512 × 512.Following result is obtained by simulation scanning and image reconstruction, Fig. 6 (b), (c) are respectively
It is the CT images that 2T and 3T scan mode FBP image reconstruction algorithms are obtained.
Emulation experiment confirms FBP image reconstruction feasibilities.
The simulation scanning parameter of table 1.
Finally illustrate, preferred embodiment above is merely illustrative of the technical solution of the present invention and unrestricted, although logical
Cross above preferred embodiment the present invention is described in detail, it is to be understood by those skilled in the art that can be
Various changes are made to it in form and in details, without departing from claims of the present invention limited range.
Claims (2)
1. a kind of linear scanning CT image rebuilding method, it is characterised in that：This method comprises the following steps：
S1：Fan beam projections data weighting is carried out by below equation：
Pa(xi,xD)=| cos γ | * P (xi,xD)；
Wherein, P (xi,xD) it is the data for projection gathered, Pa(xi,xD) for weighting after data for projection；xiFor ray source position, i
Projection number when=1 ..., I, wherein I are radiographic source linear motions；xDFor scanning field of view centrally along x-axis and detector cells it
Between distance, γ is the angle for being projected through the ray at scanning field of view center and the ray；
S2：Weighted projection data is filtered by below equation：
Pb(xi,xD)=Pa(xi,xD)*h(xD)；
Wherein,Pb(xi,xD) it is filtered data for projection, h (xD) filtered for the slope in spatial domain
Device；
S3：Back projection：
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Wherein,For back projection's coefficient, T is linear scanning number of times, η=1 ..., T；SOTo penetrate
Distance of the line source along y-axis and scanning field of view center；The start position of angle Δ beta ray source movement between projecting twice is x1、
Final position is xI, projection number when wherein I is radiographic source linear motion.
2. a kind of linear scanning CT according to claim 1 image rebuilding method, it is characterised in that：The data for projection
The data for projection relative to scanning field of view even circumferential obtained for non-equidistant radiographic source projection；It is repeatedly parallel using isogonism
Linear scan pattern is scanned, and X-ray, which is once projected, can obtain I detection data, and one time CT scan passes through T parallel lines
Scanning realizes, the projection number M of a CT scan be evenly distributed on it is equivalent be not less than in 180 ° of projection angle, reconstruction image matrix
For N × N；Wherein,
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| US10327624B2 (en) * | 2016-03-11 | 2019-06-25 | Sony Corporation | System and method for image processing to generate three-dimensional (3D) view of an anatomical portion |
| CN106097411B (en) * | 2016-06-29 | 2019-07-05 | 沈阳开普医疗影像技术有限公司 | CT machine image rebuilding method and high resolution ct scanning machine |
| CN106447740B (en) * | 2016-10-08 | 2019-04-02 | 重庆大学 | Opposite parallel lines CT area-of-interest image rebuilding method |
| CN107328798B (en) * | 2017-06-21 | 2020-02-11 | 重庆大学 | Novel ICL system and implementation method |
| CN107796834B (en) * | 2017-10-20 | 2020-03-13 | 重庆大学 | Orthogonal electronic linear scanning CL imaging system and method |
| CN109685867B (en) * | 2018-12-29 | 2023-05-30 | 上海联影医疗科技股份有限公司 | CT system, image reconstruction method, device, equipment and medium |
| CN109991251A (en) * | 2019-04-08 | 2019-07-09 | 中国工程物理研究院应用电子学研究所 | A kind of industrial CT scanning method based on multilayer fan-delta sandbody |
| CN110664419B (en) * | 2019-09-12 | 2023-05-02 | 东软医疗***股份有限公司 | Method and device for determining scanning field of view, terminal equipment and CT system |
| CN111707687A (en) * | 2020-03-26 | 2020-09-25 | 国网河南省电力公司电力科学研究院 | Linear track scanning CT detection method and device |
| CN111839568B (en) * | 2020-07-22 | 2023-12-12 | 重庆大学 | Novel large-view-field linear scanning CT system and image reconstruction method |
| CN111982939B (en) * | 2020-07-27 | 2024-03-22 | 清华大学 | Movable multi-section linear light source CT imaging system and method |
| CN113476067B (en) * | 2021-06-30 | 2024-05-31 | 同济大学 | CSXI wheel disc type coding aperture design method based on calculation coding |
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