CN104597061A - Large-field-of-view cone beam CT imaging method based on virtual detector - Google Patents
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Abstract
The invention provides a large-field-of-view cone beam CT imaging method based on a virtual detector. The large-field-of-view cone beam CT imaging method comprises the following steps: (1) calculating the size of a virtual detector required by performing CT imaging on an object, calculating the position in which the detector is arranged, calculating the distance in which a rotating table is translated, and translating the rotating table; (2) performing dark field and gain calibration on the detector on a plane of the virtual detector; (3) arranging the detector in different positions according to the position, which is calculated according to the step (1) on the plane of the virtual detector, of the detector, and acquiring one group of images on each position; (4) splicing the images acquired by the step (3) under the same angle to obtain an image of the virtual detector; and (5) processing the image of the virtual detector so as to solve a truncated problem, wherein processed data is reconstructed by using a reconstructing method of polarizing a cone beam by the rotating table, and the reconstructing speed is increased by using data redundancy in a back projection method adopted in the reconstructing process. According to the large-field-of-view cone beam CT imaging method, an imaging field of view is greater than a field of view scanned by a 3-times standard.
Description
Technical field
The invention belongs to radiography field, be specifically related to a kind of Large visual angle cone-beam CT imaging method based on dummy detector.
Background technology
Cone beam reconstruction method application based on flat panel detector is more and more extensive.Due to the restriction of manufacturing process, current flat panel detector size is limited.At industrial circle, have a lot of objects to need CT to detect, and article diameters is large, exceeds the maximum field of view that standard CT scan can provide.Chinese patent literature (number of patent application CN200610012217.X and number of patent application CN200910091282.X) is rebuild cone-beam Large visual angle respectively and is disclosed.CN200610012217.X discloses a kind of CT formation method that can reach three times of standard scan visual fields, and the method adopts reordering technique that cone beam data is treated to collimated beam data, and reduce the resolution of imaging, computing velocity is slow.CN200910091282.X discloses the biased large view field cone-beam X-ray dip sweeping three-dimension digital imaging method of a kind of detector, and maximum can be the twice of standard scan visual field by field expander." turntable is once biased the ICT reconstruction algorithm scanned, and " provide the method for reconstructing that turntable is biased Large visual angle, be a kind of fan-beam large field of view scan method to the paper of " stereology and graphical analysis " 16 volumes the 3rd phase of China's publication in 2011.The visual field that these technology can provide above is no more than three times of standard field of view, and scanning times is more, performance difficulty.How can obtain Large visual angle cone-beam CT imaging with few scanning times be a problem demanding prompt solution.
Summary of the invention
The technical problem to be solved in the present invention is to provide a kind of Large visual angle cone-beam CT imaging method based on dummy detector.
Large visual angle cone-beam CT imaging method based on dummy detector of the present invention, comprises the steps:
(1) calculate the size of required dummy detector according to scanning object size, dummy detector is placed according to the detector modes of emplacement under CT standard scan; The diverse location that calculating detector should be placed, moves to correct position by turntable;
(2) identical dark field correction is carried out to the detector of diverse location; Diverse location place detector is carried out gain calibration as the region of on dummy detector;
(3) detector is moved to diverse location, recording projection data; Detector is identical at the height of diverse location, has overlapping region in adjacent position;
(4) to gather under same projection angle in step (3) the detector data of diverse location process, the data in the non-coincidence region of adjacent detector do not process; The data value of overlapping region is the weighted sum of adjacent detector overlapping region, left and right data value, two weighting coefficients and be 1, from left to right, the weighting coefficient of left hand detector data becomes 0 from 1 continuous dullness, and the weighting coefficient of the right detector data becomes 1 from 0 continuous dullness;
(5) the CT method for reconstructing adopting rotation center to be once biased is rebuild the data on dummy detector, need before reconstruction to be weighted and zero padding the data of dummy detector, with the intersection point of focus and turntable line and detector for symmetric points, the length of dummy detector zero padding needs to make symmetric points two ends dummy detector length the same, and utilizes data redundancy to accelerate back projection's calculating.
Described dummy detector size is determined according to content below:
r 1 =SOD × (0.5 × W a + OO 1 × SDD/SOD)/Pow (0.25 × W a × W a + SDD × SDD, 0.5), dummy detector width
w a being unique unknown quantity, obtaining by solving this equation,
oO 1 for the distance of rotation center translation,
r 1 for imaging radius,
sODfor light source is to turntable distance,
sDDfor light source is to detector distance;
Described detector placement location is determined according to content below:
w a <
=W b × (N-(N – 1) × S 1 ), the number of detector placement location
nunique unknown quantity,
w b for the width of single detector,
s 1 represent the ratio of adjacent detector overlapping region width and single detector width on Width, requirement
s 1 > 0.1, Nthe request detector that individual position is placed can cover dummy detector.
Described rotation center translation distance is determined according to content below: for the scanning of solid body,
oO 1 projection width is on the detector less than 0.3
w a ; For the scanning of hollow object,
oO 1 projection width is on the detector less than 0.4
w a .
Described dummy detector data weighting method particular content is: the intersection point of focus and turntable line and detector is
p,
pto the distance from its nearest detector edge be
dp, P both sides separately
dpdata in distance range need to be weighted process; The condition of weighting function demand fulfillment is:
sPfor crossing light source
sarrive
pstraight line, if
pboth sides need be weighted two points in the region of process and light source
sthe straight line determined with
sPangle absolute value identical, these two some place weighting function value and be 1; Weighting function is dull decreasing function continuously, and the closer to detector border, weighting function value is less, and at boundary, functional value is zero.
Described data redundancy speed-up computation method particular content is: first to the detector data filtering after zero padding, filtering mode is identical with the filtering mode of FDK method, be that symmetric points are added to symmetric coordinates position by filtered for zero padding region data with point, in ensuing back projection process, the data in zero padding region do not participate in back projection.
Described Cone-Beam CT comprises cone-beam helical CT.By Technique Popularizing presented hereinbefore to cone-beam spiral scan, longitudinal visual field scaling problem can be solved.
This invention solves the problem that object radius of turn to be scanned exceeds standard scan visual field, and under meeting X-ray and can penetrating the condition of object, use tablet detector can obtain large scanning field of view, image quality is high, and image taking speed is fast.
Accompanying drawing explanation
Fig. 1 is the structural representation representing CT standard scan;
Fig. 2 represents the CT turntable once biased structural representation scanned;
Fig. 3 is the schematic diagram of dummy detector zero padding and continuation.
Embodiment
The present invention will be described in detail with reference to accompanying drawing in conjunction with the embodiments, to object of the present invention, feature and advantage carry out more deep understanding.
Fig. 1 is the structural drawing of CT standard scan.Turntable translation
oO 1 distance, obtains Fig. 2 turntable once biased structural drawing scanned.The cone beam reconstruction that turntable is once biased, by the paper of China's publication " stereology and graphical analysis " 16 volumes the 3rd phase in 2011, " turntable is once biased the ICT reconstruction algorithm scanned, and " method of middle introduction is applied to cone-beam scan, and after utilizing zero padding continuation, the redundancy of dummy detector data carries out acceleration process in back projection's process.The present invention uses the data on dummy detector to rebuild, and dummy detector is for convenience of calculating definition, and do not exist in reality, its data are by obtaining the detector data process on multiple position.In the present embodiment, X source adopts 9Mv accelerator, and detector data pickup area size is 40cm × 40cm, detector width
w b =40cm, the sweep radius R that tested object needs
1=60cm.SDD is 412cm, SOD is 320cm.Radius of turn under standard scan
r 0 =SOD
× (0.5 × W b )/Pow (0.25 × W b × W b + SDD × SDD, 0.5)=15.5cm, therefore standard scan can not meet imaging demand
.in order to carry out imaging to tested object, need the radius of turn of standard scan to expand 4 times.
s 1 be set as 0.1,
oO 1 projection width is set as 0.3 on the detector
w a .The dummy detector width being once biased CT imaging needs by calculating turntable is 97.2cm.The data width that detector merges in the data splicing of 3 station acquisition is greater than 97.2, and get the data that width that wherein counterweight builds up effect is the region of 97.2cm, this data area is positioned at dummy detector centre position, is effective dummy detector.The visual field that this layout obtains, more than the visual field of 3 times of standard scan, the angle that radiographic source and effective dummy detector region right boundary are formed is less than 14 degree.At boundary, roentgen dose X significantly reduces, and therefore integrally carries out gain calibration to dummy detector, and 3 position detector dark field correction modes are identical.Use identical dark field correction file and corresponding mutually different gain calibration file image data successively 3 positions, identical at the initial position of rotation of 3 position turntables, turntable scans in a stepwise manner.
After collection completes, get 3 pictures of lower 3 positions of a certain angle, the position arranged adjacent from left to right placed by detector, judges the similar features on adjacent detector, calculates the migration parameter of adjacent detector manually or automatically.The data of Non-overlapping Domain do not process, and adjacent detector lap data weighting calculates the dummy detector data of overlapping region.
p (x, y, j)=a 1 p 1 (x 1 , y 1 , j)+a 2 p 2 (x 2 , y 2 , j),
p (x, y, j)for data on dummy detector,
p 1 (x 1 , y 1 , j)left detector data,
p 2 (x 2 , y 2 , j)right detector data,
a 1 with
a 2 weighting coefficient,
a 1 + a 2 =1,
jfor projection angle,
(x 1 , y 1 )with
(x 2 , y 2 )it is the point on dummy detector
(x, y)the coordinate of respective point on the adjacent detector of left and right.Overlapping region width is
w q , a 1 =L/W q ,
lfor point
(x 1 , y 1 )to the distance of overlapping region right margin.
a 1 with
a 2 change curve also can use other function representation, demand fulfillment monotonicity, continuity and
a 1 rule is from large to small decremented to the rule of zero.
Adopt above-mentioned processing mode to obtain dummy detector data, dummy detector is at Fig. 3
fDthe data of scope are weighted process to remove gibbs artifact, FD about
psymmetry,
pfor rotation center
o 1 projection coordinate on dummy detector.In the present embodiment, weighting function adopts parker function, also can use other function, and as linear function replaces, the value of weighting function is from 1 to 0 monotone decreasing.The Parker function that the present embodiment adopts is
w (α)=1-(sin ((π α)/(2 θ))+1)/2 ,-θ≤α≤θ.
θfor
sPwith
sDangle,
αfor
sHwith
sPangle,
hfor dummy detector treats any point on weighted area.
Rotation center once biased reconstruction algorithm needs on width, to carry out zero padding to the data for projection processed above, as shown in Figure 3.Original projection width is
cD.By original projection width by continuation extremely, and need meet:
cP=PE.
dEbe the data for projection of continuation, assignment is 0.The data for projection amount obtained after dummy detector zero padding is comparatively large, adds the calculated amount of process of reconstruction.The present invention, in order to maintain legacy data amount, to put as symmetric points are added to symmetric coordinates position by the filtered result of the data for projection after zero padding, then carries out back projection, obtain rebuilding image, in back projection's process, DE data do not participate in back projection, accelerate process of reconstruction, the speed-up ratio of back projection's process
cE/CD.
Claims (6)
1., based on a Large visual angle cone-beam CT imaging method for dummy detector, comprise the steps:
(1) calculate the size of required dummy detector according to scanning object size, dummy detector is placed according to the detector modes of emplacement under CT standard scan; The diverse location that calculating detector should be placed, moves to correct position by turntable;
(2) identical dark field correction is carried out to the detector of diverse location; Diverse location place detector is carried out gain calibration as the region of on dummy detector;
(3) detector is moved to diverse location, recording projection data; Detector is identical at the height of diverse location, has overlapping region in adjacent position;
(4) to gather under same projection angle in step (3) the detector data of diverse location process, the data in the non-coincidence region of adjacent detector do not process; The data value of overlapping region is the weighted sum of adjacent detector overlapping region, left and right data value, two weighting coefficients and be 1, from left to right, the weighting coefficient of left hand detector data becomes 0 from 1 continuous dullness, and the weighting coefficient of the right detector data becomes 1 from 0 continuous dullness;
(5) the CT method for reconstructing adopting rotation center to be once biased is rebuild the data on dummy detector, need before reconstruction to be weighted and zero padding the data of dummy detector, with the intersection point of focus and turntable line and detector for symmetric points, the length of dummy detector zero padding needs to make symmetric points two ends dummy detector length the same, and utilizes data redundancy to accelerate back projection's calculating.
2. the Large visual angle cone-beam CT imaging method based on dummy detector according to claim 1, is characterized in that: described dummy detector size is determined according to content below:
r 1 =SOD × (0.5 × W a + OO 1 × SDD/SOD)/Pow (0.25 × W a × W a + SDD × SDD, 0.5), dummy detector width
w a being unique unknown quantity, obtaining by solving this equation,
oO 1 for the distance of rotation center translation,
r 1 for imaging radius,
sODfor light source is to turntable distance,
sDDfor light source is to detector distance;
Described detector placement location is determined according to content below:
w a <
=W b × (N-(N – 1) × S 1 ), the number of detector placement location
nunique unknown quantity,
w b for the width of single detector,
s 1 represent the ratio of adjacent detector overlapping region width and single detector width on Width, requirement
s 1 > 0.1, Nthe request detector that individual position is placed can cover dummy detector.
3. the Large visual angle cone-beam CT imaging method based on dummy detector according to claim 1, is characterized in that: described rotation center translation distance is determined according to content below: for the scanning of solid body,
oO 1 projection width is on the detector less than 0.3
w a ; For the scanning of hollow object,
oO 1 projection width is on the detector less than 0.4
w a .
4. the Large visual angle cone-beam CT imaging method based on dummy detector according to claim 1, is characterized in that, described dummy detector data weighting method particular content is: the intersection point of focus and turntable line and detector is
p,
pto the distance from its nearest detector edge be
d p ,
pboth sides separately
d p data in distance range need to be weighted process; The condition of weighting function demand fulfillment is:
sPfor crossing light source
sarrive
pstraight line, if
pboth sides need be weighted two points in the region of process and light source
sthe straight line determined with
sPangle absolute value identical, these two some place weighting function value and be 1; Weighting function is dull decreasing function continuously, and the closer to detector border, weighting function value is less, and at boundary, functional value is zero.
5. the Large visual angle cone-beam CT imaging method based on dummy detector according to claim 1, it is characterized in that, described data redundancy speed-up computation method particular content is: first to the detector data filtering after zero padding, filtering mode is identical with the filtering mode of FDK method, be that symmetric points are added to symmetric coordinates position by filtered for zero padding region data with point, in ensuing back projection process, the data in zero padding region do not participate in back projection.
6. the Large visual angle cone-beam CT imaging method based on dummy detector according to claim 1, is characterized in that: described Cone-Beam CT comprises cone-beam helical CT.
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