CN100447816C - 3D analysis and analog method for CT projection data - Google Patents
3D analysis and analog method for CT projection data Download PDFInfo
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- CN100447816C CN100447816C CNB2005101359277A CN200510135927A CN100447816C CN 100447816 C CN100447816 C CN 100447816C CN B2005101359277 A CNB2005101359277 A CN B2005101359277A CN 200510135927 A CN200510135927 A CN 200510135927A CN 100447816 C CN100447816 C CN 100447816C
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Abstract
The invention relates to the rebuilding method of a CT projecting image. The CT projecting data three dimensional analog method comprises determining the definition method for the module and scanning, setting analog program inside the computer, with the above to generate CT projecting data pjk. Changing the module definition and scanning parameter in an interactive way, it realizes the quick acquisition of analytical analog projecting data.
Description
Technical field
The present invention relates to the method that the CT projected image is rebuild, particularly the analogy method of CT projected image reconstruction.
Background technology
The CT technology is widely used in industrial nondestructive testing (NDT), medical diagnosis and scientific research field.Must use the CT data for projection in the research process of CT reconstruction algorithm.
The source of CT data for projection can have two kinds: 1) from actual CT system acquisition; 2) produce by computer Simulation calculation.
Since actual CT system price costliness, the CT system that most research units are unactual.In addition, for the data for projection of the performance need particular model of studying reconstruction algorithm, must corresponding model customized during recording projection data in actual CT system, expense is very big, and is subjected to the restriction of actual manufacturing capacity, and some model can't create.For these reasons, the computer Simulation calculation data for projection is widely adopted in CT reconstruction algorithm research process.
The method of computer Simulation calculation data for projection has two classes: 1) analysis and analog method; 2) method for numerical simulation.Analysis and analog method directly calculates the acquisition analog projection data by mathematic(al) representation, required model definition directly writes in the computer program code, change model if desired and then must write the simulated projections calculation procedure again, but its analog projection data is desirable, does not contain the discretize noise.Method for numerical simulation is then with the process of aggregation of model as pixel, simulation process is for calculating each pixel and the result being merged to obtain analog projection data, model can be by pixel definition one by one, and the change model need not to change the simulated projections calculation procedure, and is therefore very easy to use.But method for numerical simulation has 2 deficiencies: 1) computing velocity is slow; 2) introduced the discretize noise in the projection process.The method that reduces the discretize noise is to reduce Pixel Dimensions, but then can cause the one-tenth cube multiplication of computing time long like this.For the CT algorithm research, do not wish to have the discretize noise in the analog projection data, the simulated projections computing method of actual selection then need according to compromising between computing time, this three of convenience to the degrees of tolerance of discretize noise, model change, select suitable computing method, at present under the condition computing velocity of analysis and analog method be generally method for numerical simulation tens to hundred times.
Summary of the invention
(1) technical matters that will solve
The purpose of this invention is to provide a kind of computing velocity fast, be convenient to revise the CT data for projection 3 D analysis and analog method of model, thereby can obtain the analog projection data of the no discretize noise of various models easily and quickly.
(2) technical scheme
In order to achieve the above object, the present invention takes following scheme: comprising: 1) determine the model definition method; 2) determine the scan mode define method; 3) the analytic simulation program is set in computing machine; 4) by 1), 2), 3) produce CT data for projection p
Jk
Wherein, described model definition method comprises: A is by a plurality of models of combination definition of the basic body of attenuation coefficient separately of having specified; B establishes a model by i basic body M
iForm, the attenuation coefficient of each basic body is m
iC carries out model definition by the computer interactive interface.
Wherein, described scan mode define method comprises:
The simulated projections process that a is complete is made of j projection;
B specifies the radiographic source center of this projection for each projection
The detector center
C specifies the probe unit of detector to count k and each detector cells center
Relative detector center
Geometric relationship;
Amount of radiation l, each bar ray starting point that d specifies each detector cells to receive
Relative radiographic source center
Geometric relationship and each bar ray and detector intersection point
Relative detector cells center
Geometric relationship, each bar ray to the contribution weight w of the simulated projections numerical value of detector cells
Jkl, weight should be normalized, promptly
E carries out the definition of scan mode by the computer interactive interface.
Wherein, described analytic simulation program comprises:
The analog physical factor for the treatment of that a) will be provided with is divided into to the influence of ray position with to two classes that influence of projection value.According to starting point and the terminal point coordinate of the influence of ray position being adjusted ray, according to projection value influenced the final simulated projections value of adjustment.
B) by coordinate conversion ray starting point, terminal point coordinate are transformed into the solid local coordinate system, in the solid local coordinate system, calculate the intersecting point coordinate of ray and solid.
C),, calculate attenuation coefficient subsequently by the coordinate Calculation intersection length in the solid local coordinate system to direct stack combinations mode.
D) to replacing array mode, intersecting point coordinate is transformed into system coordinate system, in system coordinate system, calculates the distance of two intersection points, calculate attenuation coefficient subsequently to the ray starting point.
Wherein, described CT data for projection p
JkComprise:
A) the simulated projections numerical value p of a ray
JklBe line segment
Go up the integration of all attenuation coefficient m, that is:
B) the simulated projections numerical value p of each detector cells
JkFor:
C) p
JklThe computing method and the attenuation coefficient of model relevant, the attenuation coefficient of model is made up by certain mode by the attenuation coefficient of each solid and obtains, different array modes must use different computing method to calculate p
Jkl
Wherein, described array mode comprises: directly adding up of each solid attenuation coefficient, that is: establish a bit in the model
Be positioned at m solid forming this model, then the attenuation coefficient of this point of model is
P under this array mode
JklComputing method be:
Calculate line segment earlier
Intersection length L with each solid of composition model
Ijkl, calculate simulated projections numerical value p then
Jkl:
Wherein, described array mode comprises: the replacement of each solid attenuation coefficient is made up, and establishes in the model a bit that is:
Be positioned at m solid forming this model, then the attenuation coefficient of this point of model is
P under this array mode
JklComputing method be: establish line segment
There are two intersection points of two intersection points and n solid to be positioned at the n layer with N solid in i the solid of composition model, arrive
Distance be respectively a
JklnAnd b
Jkln, establish a
Jkln<b
Jkln
a
jkl0=0,
m
0=0。The 0th layer is line segment
The line segment of each layer all may be divided into shorter line segment by more high-rise intersection point, and the attenuation coefficient value of each point is the attenuation coefficient value of the solid of the top line segment correspondence under it.Can calculate simulated projections numerical value p thus
Jkl
(3) beneficial effect
1) is used for changing model definition and sweep parameter definition owing to offering with alternant way, be implemented under the situation that need not to write again the simulated projections program and define various models and sweep parameter as required, thereby obtain the analytic simulation data for projection quickly and easily.2) computing velocity is fast, can obtain the analog projection data of the no discretize noise of various models.
Description of drawings
Fig. 1 is the simulated projections value calculation flow chart of replacement when combination ray of each solid attenuation coefficient of the present invention;
Fig. 2 is an analytic simulation projection process synoptic diagram of the present invention;
Fig. 3 is a model definition interactive interface synoptic diagram of the present invention;
Fig. 4 is that simulated projections parameter of the present invention is provided with the interactive interface synoptic diagram.
Fig. 5 is an analytic simulation projection program calculation flow chart of the present invention.
1) embodiment
Following examples are used to illustrate the present invention, but are not used for limiting the scope of the invention.
The present invention adopts when implementing, and comprises step: 1) determine the model definition method; 2) determine the scan mode define method; 3) the analytic simulation program is set in computing machine; 4) by step 1), step 2), step 3) produces CT data for projection p
Jk
As shown in Figure 2, exemplary embodiments of the present invention comprises the disposal route that computer interactive interface and analytic simulation program are imported the user.Use two coordinate systems among the embodiment: system coordinate system and solid local coordinate system.Model center is positioned at the system coordinate system initial point, and radiographic source position, detector position all define in system coordinate system.Solid is centered close to solid local coordinate system initial point, and axis of symmetry overlaps with coordinate axis.
The interactive interface of model definition as shown in Figure 3, the user determines the coordinate (x of solid center in system coordinate system of composition model
i, y
i, z
i) and the angle of inclination a of axis of symmetry in system coordinate system of solid
i, f
i, determine solid attenuation coefficient m simultaneously
iAnd array mode.
The interactive interface that the simulated projections parameter is provided with as shown in Figure 4, the physical influence factor that the user determines scan mode and will simulate.
The flow process of analytic simulation program to the disposal route of user input is as shown in Figure 5:
1) the physical influence factor that will simulate is decomposed into two classes: to the influence of ray position (as various skews etc.) and to the influence of ray upslide shadow value (as noise etc.).
2) calculate the starting point coordinate of each bar ray according to sweep parameter setting and the physical factor setting that influences ray position
And terminal point coordinate
3) starting point coordinate and terminal point coordinate are obtained the starting point coordinate of each bar ray in the local coordinate system of each solid by coordinate conversion
And terminal point coordinate
4) in the local coordinate system of each solid, calculate the intersecting point coordinate of ray and solid: do not have two intersection points (no intersection point or an intersection point is only arranged); Two intersection points are perhaps arranged
With
If the attenuation coefficient of solid calculates ray and each solid intersection length L by direct accumulate mode combination according to the distance between two points formula
Ijkl, can calculate the projection value p of each bar ray then
Jklp
JklComputing method be:
Calculate line segment earlier
Intersection length L with each solid of composition model
Ijkl, calculate simulated projections numerical value p then
Jkl:
If the attenuation coefficient of solid then obtains its coordinate in system coordinate system with intersecting point coordinate by coordinate conversion by the substitute mode combination
With
Calculate again intersection point to the ray starting point apart from a
IjklAnd b
Ijkl, can calculate the projection value p of each bar ray then
Jkl
The corresponding calculated formula is:
Each bar ray is to the contribution weight w of the simulated projections numerical value of detector cells
JklMay be selected to be:
As shown in Figure 1, under the above-mentioned substitute mode combination, p
JklComputing method be:
If line segment
There are two intersection points of two intersection points and n solid to be positioned at the n layer with N solid in i the solid of composition model, arrive
Distance be respectively a
JklnAnd b
Jkln, establish a
Jkln<b
Jklna
jkl0=0,
m
0=0。The 0th layer is line segment
The line segment of each layer all may be divided into shorter line segment by more high-rise intersection point, and the attenuation coefficient value of each point is the attenuation coefficient value of the solid of the top line segment correspondence under it.Calculate simulated projections numerical value p by method shown in Figure 1 thus
JklWith all intersection points by arriving
Distance series arrangement from small to large, search with this then and be each positioned at top line segment.Use a variable p
JklPreserve the simulated projections value, initial value is changed to 0.Use variable S
c, E
cPreserve current line segment starting point, final position of handling, variable n
cPreserve line segment place layer when pre-treatment.
S
cSince 0, search corresponding E by the following method
cAnd n
cIf: as the line segment starting point S of pre-treatment
cBe a
JklnClass point (i.e. n layer middle distance
Nearer point), then calculate E earlier
c, E
cFor all are higher than as anterior layer n
cAnd greater than S
cA
JklnClass point and as the b of anterior layer correspondence
JklnClass point (i.e. n layer middle distance
Point far away) b
JlncMiddle minimum point recomputates then as anterior layer n
c, with n
cBe changed to E
cThe place layer; If line segment starting point S when pre-treatment
cBe b
JklnThe class point then recomputates earlier as anterior layer n
c, with n
cBe changed to and satisfy corresponding a
JklnClass point is less than S
c, corresponding b
JklnClass point is less than E
c(be the line segment terminal point of preceding single treatment this moment) and the number of plies own are less than n
cAll layers in maximal value, calculate line segment terminal point E then when pre-treatment
c, E
cFor all are higher than as anterior layer n
cAnd greater than S
cA
JklnClass point and as the b of anterior layer correspondence
JklnClass point (i.e. n layer middle distance
Point far away) b
JklncMiddle minimum point.Search subsequently as anterior layer n
cCorresponding attenuation coefficient m
Nc, then with (E
c-S
c) ' m
NcBe added to p
JklIn, so just finished a line segment and handled.The line segment terminal point of single treatment before will working as pre-treatment line segment starting point subsequently and being changed to repeats above line segment processing procedure then, up to starting point arrive the maximal value b in having a few
Jkl0The time finish calculating.
Claims (5)
1, CT data for projection 3 D analysis and analog method is characterized in that comprising:
1) determines the model definition method;
2) determine the scan mode define method, described scan mode define method comprises:
The simulated projections process that a is complete is made of j projection;
B specifies the radiographic source center of this projection for each projection
The detector center
C specifies the probe unit of detector to count k and each detector cells center
Relative detector center
Geometric relationship;
Amount of radiation l, each bar ray starting point that d specifies each detector cells to receive
Relative radiographic source center
Geometric relationship and each bar ray and detector intersection point
Relative detector cells center
Geometric relationship, each bar ray to the contribution weight w of the simulated projections numerical value of detector cells
Jkl, weight should be normalized, promptly
E carries out the definition of scan mode by the computer interactive interface;
3) the analytic simulation program is set in computing machine;
4) by 1), 2), 3) produce CT data for projection p
Jk
2, CT data for projection 3 D analysis and analog method as claimed in claim 1 is characterized in that described model definition method comprises: A is by a plurality of models of combination definition of the basic body of attenuation coefficient separately of having specified; Model of B is by i basic body M
iForm, the attenuation coefficient of each basic body is m
iC carries out model definition by the computer interactive interface.
3, CT data for projection 3 D analysis and analog method as claimed in claim 1 is characterized in that described analytic simulation program comprises:
The analog physical factor for the treatment of that a) will be provided with is divided into to the influence of ray position with to two classes that influence of projection value, according to starting point and the terminal point coordinate of the influence of ray position being adjusted ray, according to projection value influenced the final simulated projections value of adjustment;
B) by coordinate conversion ray starting point, terminal point coordinate are transformed into the solid local coordinate system, in the solid local coordinate system, calculate the intersecting point coordinate of ray and solid;
C),, calculate attenuation coefficient subsequently by the coordinate Calculation intersection length in the solid local coordinate system to direct stack combinations mode;
D) to replacing array mode, intersecting point coordinate is transformed into system coordinate system, in system coordinate system, calculates the distance of two intersection points, calculate attenuation coefficient subsequently to the ray starting point.
4, CT data for projection 3 D analysis and analog method as claimed in claim 2 is characterized in that described array mode comprises: directly the adding up of each solid attenuation coefficient, promptly in the model a bit
Be positioned at m solid forming this model, then the attenuation coefficient of this point of model is
P under this array mode
JklComputing method be:
Calculate line segment earlier
Intersection length L with each solid of composition model
Ijkl, calculate simulated projections numerical value p then
Jkl:
5, CT data for projection 3 D analysis and analog method as claimed in claim 2 is characterized in that described array mode comprises: the replacement combination of each solid attenuation coefficient, i.e. a bit in the model
Be positioned at m solid forming this model, then the attenuation coefficient of this point of model is
P under this array mode
JklComputing method be:
Line segment
There are two intersection points of two intersection points and n solid to be positioned at the n layer with N solid in i the solid of composition model, arrive
Distance be respectively a
JklnAnd b
Jkln, a
Jkln<b
Jkln, a
Jkl0=0,
m
0The=0,0th layer is line segment
The line segment of each layer all is divided into shorter line segment by more high-rise intersection point, and the attenuation coefficient value of each point is the attenuation coefficient value of the solid of the top line segment correspondence under it, calculates simulated projections numerical value p thus
Jkl
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US9453895B2 (en) * | 2012-10-05 | 2016-09-27 | Siemens Aktiengesellschaft | Dynamic image reconstruction with tight frame learning |
CN104856714A (en) * | 2014-02-21 | 2015-08-26 | 上海西门子医疗器械有限公司 | CT scanning parameter indication method and device and CT machine |
CN109102553B (en) * | 2018-06-27 | 2020-05-05 | 中国人民解放军战略支援部队航天工程大学 | Polar coordinate system matrix calculation method and device in two-dimensional reconstruction algorithm |
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US6081577A (en) * | 1998-07-24 | 2000-06-27 | Wake Forest University | Method and system for creating task-dependent three-dimensional images |
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CN1437914A (en) * | 2001-10-25 | 2003-08-27 | 株式会社东芝 | X-ray CT apparatus, 3-D image reproducing method and resetting method |
JP2004188149A (en) * | 2002-12-12 | 2004-07-08 | Terarikon Inc | Three-dimensional image display device for directly making three-dimensional image from projection data of x-ray ct apparatus |
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