KR101662067B1 - X-ray tomography system using dual detector and method for the same - Google Patents

X-ray tomography system using dual detector and method for the same Download PDF

Info

Publication number
KR101662067B1
KR101662067B1 KR1020150095165A KR20150095165A KR101662067B1 KR 101662067 B1 KR101662067 B1 KR 101662067B1 KR 1020150095165 A KR1020150095165 A KR 1020150095165A KR 20150095165 A KR20150095165 A KR 20150095165A KR 101662067 B1 KR101662067 B1 KR 101662067B1
Authority
KR
South Korea
Prior art keywords
detector
image
ray
detectors
value
Prior art date
Application number
KR1020150095165A
Other languages
Korean (ko)
Inventor
조승룡
민종환
박미란
조상훈
Original Assignee
한국과학기술원
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by 한국과학기술원 filed Critical 한국과학기술원
Priority to KR1020150095165A priority Critical patent/KR101662067B1/en
Application granted granted Critical
Publication of KR101662067B1 publication Critical patent/KR101662067B1/en

Links

Images

Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N23/00—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00
    • G01N23/02—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material
    • G01N23/04—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material
    • G01N23/046—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material using tomography, e.g. computed tomography [CT]
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N23/00—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00
    • G01N23/02—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material
    • G01N23/04—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material
    • G01N23/043—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material using fluoroscopic examination, with visual observation or video transmission of fluoroscopic images
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N2223/00—Investigating materials by wave or particle radiation
    • G01N2223/10—Different kinds of radiation or particles
    • G01N2223/101—Different kinds of radiation or particles electromagnetic radiation
    • G01N2223/1016—X-ray

Abstract

An X-ray CT apparatus and method using a dual detector are disclosed. A first detector for detecting discontinuous image data on a part of a large body to be positioned corresponding to a part of an entire region of the large body of the large body, A second detector for detecting discontinuous image data on the rest of the large subject placed in the remaining region of the entire region of the specimen, a rotation mechanism for rotating the first and second detectors, And a controller for reconstructing the discontinuous image data detected by the detector into an image without a cutting error.

Description

[0001] The present invention relates to an X-ray tomography system using a dual detector,

The present invention relates to an X-ray CT apparatus, and more particularly, to an X-ray CT apparatus and method using a dual detector.

Currently, the device for retrieving the luggage using x-rays is widely used in airports and ports, but the need for a three-dimensional x-ray tomography apparatus is continuously increasing for accurate analysis of internal structures.

However, the three-dimensional X-ray CT system is limited in its ability to produce a large-area detector for capturing large-size baggage, In order to secure a wide field of view (FOV) under a limited detector area, a method of moving a detector and photographing it or photographing a plurality of detectors connected thereto is utilized.

Even with this effort, there is a problem that direct connection to the housing or the like at the end of the detector is not easy when the plurality of flat panel detectors are continuously connected together with the increase of the photographing time. In order to overcome this problem, it is possible to use a method of arranging the detector vertically or obliquely to align the end of the detector. In this case, the FOV is lost and precise installation is difficult.

Korean Patent Registration No. 10-0718671 discloses a method for reconstructing a two-dimensional sectional image by acquiring information on irregular movement through a reference detector in an X-ray tube in which an X-ray is generated, Dimensional reference detector and a collimator for a reference detector for improving the spatial resolution by reflecting the reflected light.

An object of the present invention is to provide an X-ray tomography apparatus and method using a dual detector that captures a large object such as a large bag of water by ensuring a wide area FOV that is not secured by a single detector.

It is another object of the present invention to provide an X-ray CT apparatus and method using a dual detector for reconstructing an image without discarding the detected data from each of the separated detectors.

In order to achieve the above object,

An X-ray CT apparatus using a dual detector according to the present invention comprises:

A first detector for detecting discontinuous image data of a part of the large subject placed in correspondence with a part of the entire region of the large subject, an X-ray generating unit for irradiating the large subject with X- A second detector for detecting discontinuous image data with respect to the rest of the large subject by being positioned to correspond to the remaining area of the entire area of the large subject, and for rotating the X-ray generator and the first and second detectors And a controller for reconstructing the discontinuous image data detected by the first and second detectors into an image without a cutting error.

The first and second detectors are planar detectors.

The first and second detectors are characterized in that the center position is shifted on the same plane.

And the first detector and the second detector are spaced apart from each other.

And the control unit separates the first and second detectors using the following equations.

[Mathematical Expression]

Figure 112015064745095-pat00001

here,

Figure 112015064745095-pat00002
Means the center position of the first detector,
Figure 112015064745095-pat00003
Means the center position of the second detector,
Figure 112015064745095-pat00004
Means the center position of the second detector which is symmetrical to the center of the large subject,
Figure 112015064745095-pat00005
Means the transverse length of the first and second detectors,
Figure 112015064745095-pat00006
Quot; means an arbitrary moving displacement value.

Wherein the controller reconfigures the discontinuous data using an inverse projection filtering method.

The control unit calculates the back projection filtering method using the following equation.

[Mathematical Expression]

Figure 112015064745095-pat00007

here,

Figure 112015064745095-pat00008
Denotes an image value on a pi (pi) segment,
Figure 112015064745095-pat00009
,
Figure 112015064745095-pat00010
Represents an arbitrary point on the circular trajectory with respect to the pie line segment,
Figure 112015064745095-pat00011
Represents the vertical coordinate value of the image,
Figure 112015064745095-pat00012
,
Figure 112015064745095-pat00013
Respectively denote the end points of the pie segments,
Figure 112015064745095-pat00014
Denotes an image coordinate to be projected backward,
Figure 112015064745095-pat00015
Means the coordinates of the image value on the pie segment,
Figure 112015064745095-pat00016
Quot; means the pi segment value,
Figure 112015064745095-pat00017
The
Figure 112015064745095-pat00018
Lt; / RTI >
Figure 112015064745095-pat00019
Means the superposition value of the pie line segment.

The control unit may calculate the image coordinates of the backprojection using the following equation.

[Mathematical Expression]

Figure 112015064745095-pat00020

here,

Figure 112015064745095-pat00021
Denotes a weight function,
Figure 112015064745095-pat00022
Means mean converted cone beam projection data,
Figure 112015064745095-pat00023
Quot; means the horizontal coordinate,
Figure 112015064745095-pat00024
Means the vertical coordinate,
Figure 112015064745095-pat00025
Quot; means a converted rotation locus,
Figure 112015064745095-pat00026
Refers to the distance between the X-ray generator and the detector,
Figure 112015064745095-pat00027
Means the distance between the X-ray generating part and the rotation center axis.

The control unit calculates the weight function using the following equation.

[Mathematical Expression]

Figure 112015064745095-pat00028

here,

Figure 112015064745095-pat00029
Means the starting angle of the rotation locus.

An X-ray tomography method using a dual detector according to the present invention,

Placing a first detector in a part of an entire region of the large subject and positioning a second detector in the remaining region, irradiating X-rays toward the large subject, And reconstructing the detected discontinuous image data into an image without a cutoff error by using the first and second detectors and the inverse projection filtering method, respectively.

The step of irradiating X-rays is characterized in that X-rays are irradiated while rotating around the large subject.

According to the X-ray CT apparatus and method using the dual detector according to the present invention, it is possible to capture a large object such as a large hydrate by securing a wide area FOV that is not secured by a single detector.

Also, discontinuous data detected from each detector that is separated from each other can be reconstructed by a reverse projection filtering method, and a tomographic image including a large area FOV can be generated without any errors.

FIG. 1 is a block diagram illustrating an X-ray CT apparatus according to an embodiment of the present invention. Referring to FIG.
FIG. 2 is a view illustrating an irradiation slope of an X-ray CT apparatus according to an embodiment of the present invention.
3 is a view for explaining a discontinuous image detected by an X-ray CT apparatus according to an embodiment of the present invention.
4 is a view for explaining a reconstructed tomographic image in an X-ray CT apparatus according to an embodiment of the present invention.
5 is a flowchart illustrating an X-ray CT method according to an embodiment of the present invention.

Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings. In the drawings, the same reference numerals as used in the appended drawings denote like elements, unless indicated otherwise. In the following description of the present invention, a detailed description of known functions and configurations incorporated herein will be omitted when it may make the subject matter of the present invention rather obvious or understandable to those skilled in the art.

FIG. 1 is a block diagram illustrating an X-ray CT apparatus according to an embodiment of the present invention. Referring to FIG.

Referring to FIG. 1, the X-ray CT apparatus 1 captures a large object, such as a large bag, by ensuring a wide area FOV that can not be secured by a single detector. The X-ray tomography apparatus 1 reconstructs the detected data from each of the separated detectors without corrupted errors.

The X-ray CT apparatus 1 includes an X-ray generating unit 100, a rotation mechanism 200, a first detector 300, a second detector 400, an input unit 500, a control unit 600, an output unit 700 And a storage unit 800.

The X-ray generator 100 irradiates X-rays toward a large object (not shown). Here, a large subject means a subject having a size that makes it difficult to obtain a full-transmitted image of the subject with one detector. The X-ray generator 100 irradiates X-rays to the FOV 10 of the entire large-sized test object. Accordingly, the X-ray generating unit 100 can detect the transmitted image of the entire large-sized object in the future. The X-ray generator 100 is an X-ray source or tube for generating X-rays. Here, the X-ray generator 100 may be an X-ray generator.

The rotating mechanism unit 200 may be a gantry that rotates 360 degrees. The rotation mechanism unit 200 causes the X-ray generation unit 100 to perform circular rotation. Therefore, the X-ray generating unit 100, the first detector 300, and the second detector 400 are formed in the rotating mechanism unit 200. Therefore, when the rotating mechanism unit 200 rotates, the X-ray generating unit 100, the first detector 300, and the second detector 400 also rotate.

The circular rotation can be set according to the shape and size of the large subject, the distance to the large subject, and the point where the X-ray irradiation is performed, and can be set according to the user input received by the input unit 500 described later.

The first detector 300 is positioned corresponding to a part of the entire area of the large subject to detect discontinuous image data on a part of the large subject. The part of the area may refer to one of the half areas of the large subject. Preferably, the first detector 300 is located on the right side with respect to the central axis of the large subject.

The second detector 400 is positioned corresponding to the remaining area of the entire area of the large subject to detect discontinuous image data on the rest of the large subject. And the remaining region may mean the remaining one of the half regions of the large subject. Preferably, the second detector 400 is located on the left side with respect to the central axis of the large subject.

Here, the discontinuous image data means image data of a large-sized test object with respect to a region in which the first and second detectors are located.

Therefore, the first and second detectors 300 and 400 are kept apart from each other, and the setting of the spaced position is described in detail in the control part 600 described later. The first and second detectors 300 and 400 can set positions based on the shape, size, distance from the large subject, and the like of the large subject.

In particular, the first and second detectors 300, 400 are moved in the same plane, whereby the center position A, B (350, 450) of each detector can also be located on the same plane. For this purpose, the first and second detectors 300 and 400 may be planar detectors.

The input unit 500 may receive data on the irradiation intensity of the X-ray generating unit 100 and the point irradiated by the rotation mechanism unit 200. That is, the input unit 500 can receive a set value for a specification desired by the user according to the environment and the large body.

The controller 600 reconfigures the discontinuous image data detected by the first and second detectors 300 and 400 into an image without a cutting error. To this end, the control unit 600 controls the positions of the first and second detectors 300 and 400. The control unit 600 may control the position of the first and second detectors 300 and 400 according to a user input received from the input unit 500 or may automatically control according to a predetermined set value.

In particular, the control unit 600 controls the positions of the first and second detectors 300 and 400 to be spaced apart from each other so as to satisfy the FOV region required for image reconstruction. In addition, the control unit 600 positions the first and second detectors 300 and 400 on the same plane to recombine the data detected by the first and second detectors 300 and 400 as data on the same plane.

The control unit 600 moves the center positions of the first and second detectors 300 and 400 to A and B (350 and 450). The controller 600 controls the positions of the first and second detectors 300 and 400 using Equation (1).

Figure 112015064745095-pat00030

here,

Figure 112015064745095-pat00031
Means the center position of the first detector,
Figure 112015064745095-pat00032
Means the center position of the second detector,
Figure 112015064745095-pat00033
Means the center position of the second detector which is symmetrical to the center of the large subject,
Figure 112015064745095-pat00034
Means the transverse length of the first and second detectors,
Figure 112015064745095-pat00035
Quot; means an arbitrary moving displacement value.

After controlling the positions of the first and second detectors 300 and 400, the control unit 600 reconstructs the image using discontinuous image data detected by X-ray irradiation. The control unit 600 reconstructs the image by using the inverse projection filtering method. The inverse projection filtering method performs image reconstruction without discontinuity error for discontinuous data. That is, the control unit 600 reconstructs a tomographic image of a large subject.

The control unit 600 calculates the inverse projection filtering method as shown in the following equation (2).

Figure 112015064745095-pat00036

here,

Figure 112015064745095-pat00037
Denotes an image value on a pi (pi) segment,
Figure 112015064745095-pat00038
,
Figure 112015064745095-pat00039
Represents an arbitrary point on the circular trajectory with respect to the pie line segment,
Figure 112015064745095-pat00040
Represents the vertical coordinate value of the image,
Figure 112015064745095-pat00041
,
Figure 112015064745095-pat00042
Respectively denote the end points of the pie segments,
Figure 112015064745095-pat00043
Denotes an image coordinate to be projected backward,
Figure 112015064745095-pat00044
Means the coordinates of the image value on the pie segment,
Figure 112015064745095-pat00045
Quot; means the pi segment value,
Figure 112015064745095-pat00046
The
Figure 112015064745095-pat00047
Lt; / RTI >
Figure 112015064745095-pat00048
Means the superposition value of the pie line segment.

The control unit 600 controls the image coordinates

Figure 112015064745095-pat00049
) Is calculated as shown in Equation (3).

Figure 112015064745095-pat00050

here,

Figure 112015064745095-pat00051
Denotes a weight function,
Figure 112015064745095-pat00052
Means mean converted cone beam projection data,
Figure 112015064745095-pat00053
Quot; means the horizontal coordinate,
Figure 112015064745095-pat00054
Means the vertical coordinate,
Figure 112015064745095-pat00055
Quot; means a converted rotation locus,
Figure 112015064745095-pat00056
Refers to the distance between the X-ray generator and the detector,
Figure 112015064745095-pat00057
Means the distance between the X-ray generating part and the rotation center axis.

In addition, the controller 600 calculates a weight function

Figure 112015064745095-pat00058
) Is calculated as shown in Equation (4).

Figure 112015064745095-pat00059

here,

Figure 112015064745095-pat00060
Means the starting angle of the rotation locus. That is, it means the position (angle) at which rotation starts first.

The output unit 700 outputs a discontinuous image detected by the first and second detectors 300 and 400. Further, the output unit 700 outputs a reconstructed tomographic image of the large subject in the control unit 600.

The output unit 700 may be a liquid crystal display (LCD), a thin film transistor-liquid crystal display (TFT LCD), an organic light-emitting diode (OLED), a flexible display display, a monitor, a projector, and a printer.

The storage unit 800 stores user inputs received from the input unit 500 and discontinuous images detected by the first and second detectors 300 and 400 are stored. The storage unit 800 stores the reconstructed tomographic image in the control unit 600. FIG.

The storage unit 800 may be a storage medium such as a memory. The storage unit 800 may be a flash memory type, a hard disk type, a multimedia card micro type, a card type memory (for example, SD or XD memory) (Random Access Memory), a static random access memory (SRAM), a read-only memory (ROM), an electrically erasable programmable read-only memory (EEPROM), a programmable read-only memory (PROM) A magnetic disk, and / or an optical disk.

FIG. 2 is a view illustrating an irradiation slope of an X-ray CT apparatus according to an embodiment of the present invention.

FIG. 2 (a) is a view showing a case where the rotating mechanism unit 200 rotates by 30 ° in the counterclockwise direction, FIG. 2 (c) is a view showing a case where the rotating mechanism unit 200 rotates counterclockwise by 60 degrees to irradiate a large-sized test object, and FIG. 2 (d) And the rotating mechanism unit 200 rotates by 90 degrees in the counterclockwise direction to irradiate a large-sized test object.

Referring to FIG. 2, the X-ray CT apparatus 1 irradiates X-rays to a large subject in various directions due to circular rotation of the rotation mechanism 200. Therefore, the X-ray CT apparatus 1 can generate a tomographic image of a large subject in various directions.

The X-ray CT apparatus 1 can detect discontinuous image data for a large subject on the same line by positioning the first and second detectors 300 and 400 formed in a planar shape at various slopes on the same plane. That is, the X-ray CT apparatus 1 can reconstruct an image using discontinuous image data on the same line, thereby generating a precise tomographic image.

FIG. 3 is a view for explaining a discontinuous image detected by an X-ray CT apparatus according to an embodiment of the present invention. FIG. 4 is a view for explaining a discontinuous image detected by an X-ray CT apparatus according to an embodiment of the present invention, Fig.

Referring to FIGS. 3 and 4, the X-ray CT apparatus 1 detects a discontinuous image and reconstructs the image based on the discontinuous image to generate a tomographic image.

The X-ray CT apparatus 1 detects a discontinuous image from the first and second detectors 300 and 400. That is, as shown in FIG. 3, an image that is displayed in black and has no projection image is detected. The X-ray CT apparatus 1 detects a discontinuous image of a portion where the first and second detectors 300 and 400 are spaced apart, but reconstructs the image through the control unit 600. Here, the X-ray tomographic imaging apparatus 1 rotates the periphery of the large inspected object 360 degrees to detect the image. Each detected image contains a discontinuous portion.

The X-ray CT apparatus 1 can reconstruct each discontinuous image to be a continuous image using a reverse projection filtering method, and then generate a tomographic image. That is, the X-ray CT apparatus 1 can take tomographic images of small cylinders existing inside a large cylinder as shown in FIG.

5 is a flowchart illustrating an X-ray CT method according to an embodiment of the present invention.

Referring to FIG. 5, the X-ray CT method can capture a large object such as a large hydrate by securing a wide area FOV that is not secured by a single detector. X - ray tomography can generate a tomographic image including a large - area FOV without discontinuity error by reconstructing the image by using the inverse projection filtering technique for discontinuous data detected from each detector that is separated from each detector.

The X-ray tomography method can be performed in the following order.

The X-ray CT apparatus 1 separates the first and second detectors 300 and 400 (S100). The X-ray computed tomography apparatus 1 positions the first detector 300 in a part of the entire area of the subject and the second detector 400 in the remaining area. The X-ray CT apparatus 1 separates the first and second detectors 300 and 400 according to Equation (1).

Here, the spaced apart positions of the first and second detectors 300 and 400 are positions that satisfy the FOV region necessary for the subsequent image reconstruction.

The X-ray computed tomography apparatus 1 irradiates X-rays toward a large subject (S110). The X-ray CT apparatus 1 irradiates X-rays to a large-sized test object through the X-ray generating unit 100. At this time, the X-ray CT apparatus 1 can irradiate the X-ray while rotating circularly through the rotation mechanism unit 200. [ That is, the X-ray CT apparatus 1 can irradiate X-rays with respect to 360 ° of a large subject, and the point to be irradiated can be changed according to predetermined points or user inputs.

The X-ray tomography apparatus 1 detects the discontinuous images irradiated (S120). The X-ray tomography apparatus 1 detects a projected image of a large subject as a discontinuous image from the first and second detectors 300 and 400. Here, the X-ray CT apparatus 1 detects a discontinuous image due to the separation of the first and second detectors 300 and 400.

The X-ray computed tomography apparatus 1 reconstructs the image based on the detected discontinuous image (S130). The X-ray tomography apparatus 1 reconstructs a discontinuous image detected by the first and second detectors 300 and 400 by an inverse projection filtering method. The X-ray CT apparatus 1 can reconstruct an image using Equation (2), thereby generating a tomographic image of the subject.

While the present invention has been particularly shown and described with reference to exemplary embodiments thereof, it is clearly understood that the same is by way of illustration and example only and is not to be taken by way of limitation in the embodiment in which said invention is directed. It will be understood by those skilled in the art that various changes in form and detail may be made therein without departing from the scope of the appended claims.

1: X-ray CT
10: FOV
100: X-ray generator
200:
300: first detector
350: center position (A) of the first detector
400: second detector
450: center position (B) of the second detector
450 ': the center position (B') of the second detector, which is symmetrical to the central axis of the large subject,
500: input unit
600:
700: Output section
800:

Claims (11)

An X-ray generation unit for irradiating X-rays toward a large subject;
A first detector positioned corresponding to a part of an entire region of the large subject to detect discontinuous image data for a part of the large subject;
A second detector positioned corresponding to the remaining area of the entire area of the large subject to detect discontinuous image data on the rest of the large subject;
A rotation mechanism for rotating the X-ray generator and the first and second detectors; And
And a controller for reconstructing the discontinuous image data detected by the first and second detectors into an image without a cutting error,
Wherein,
Wherein the discontinuous data is reconstructed using the inverse projection filtering method and the inverse projection filtering method is calculated using the following equation:
[Mathematical Expression]
Figure 112016059793600-pat00095

here,
Figure 112016059793600-pat00096
Denotes an image value on a pi (pi) segment,
Figure 112016059793600-pat00097
,
Figure 112016059793600-pat00098
Represents an arbitrary point on the circular trajectory with respect to the pie line segment,
Figure 112016059793600-pat00099
Represents the vertical coordinate value of the image,
Figure 112016059793600-pat00100
,
Figure 112016059793600-pat00101
Respectively denote the end points of the pie segments,
Figure 112016059793600-pat00102
Denotes an image coordinate to be projected backward,
Figure 112016059793600-pat00103
Means the coordinates of the image value on the pie segment,
Figure 112016059793600-pat00104
Quot; means the pi segment value,
Figure 112016059793600-pat00105
The
Figure 112016059793600-pat00106
Lt; / RTI >
Figure 112016059793600-pat00107
Means the superimposed value of pie line segment.
The method according to claim 1,
Wherein the first and second detectors comprise:
Wherein the detector is a flat-shaped detector.
The method according to claim 1,
Wherein the first and second detectors comprise:
And the center position is moved on the same plane.
The method of claim 3,
Wherein the first and second detectors are spaced apart from each other.
The method according to claim 1,
Wherein,
Wherein the first and second detectors are spaced apart from each other by using the following equation: X-ray tomography apparatus using dual detector:
[Mathematical Expression]
Figure 112015064745095-pat00061

here,
Figure 112015064745095-pat00062
Means the center position of the first detector,
Figure 112015064745095-pat00063
Means the center position of the second detector,
Figure 112015064745095-pat00064
Means the center position of the second detector which is symmetrical to the center of the large subject,
Figure 112015064745095-pat00065
Means the transverse length of the first and second detectors,
Figure 112015064745095-pat00066
Is an arbitrary moving displacement value.
delete delete The method according to claim 1,
Wherein,
And calculating an image coordinate of the backprojected image using the following equation:
[Mathematical Expression]
Figure 112016059793600-pat00080

here,
Figure 112016059793600-pat00081
Denotes a weight function,
Figure 112016059793600-pat00082
Means mean converted cone beam projection data,
Figure 112016059793600-pat00083
Quot; means the horizontal coordinate,
Figure 112016059793600-pat00084
Means the vertical coordinate,
Figure 112016059793600-pat00085
Quot; means a converted rotation locus,
Figure 112016059793600-pat00086
Refers to the distance between the X-ray generator and the detector, Means the distance between the X-ray generating part and the rotation center axis.
9. The method of claim 8,
Wherein,
Wherein the weight function is calculated using the following equation: X-ray tomography apparatus using dual detector:
[Mathematical Expression]
Figure 112015064745095-pat00088

here,
Figure 112015064745095-pat00089
Means the starting angle of the rotation locus.
Positioning a first detector in a portion of an entire region of the large subject and a second detector in a remaining region;
Irradiating the large subject with X-rays;
Detecting discontinuous image data of the inspected large object by the first and second detectors, respectively; And
Reconstructing the detected discontinuous image data into an image with no truncation error using a reverse projection filtering method,
Wherein the inverse projection filtering method is calculated using the following equation.
[Mathematical Expression]
Figure 112016059793600-pat00108

here,
Figure 112016059793600-pat00109
Denotes an image value on a pi (pi) segment,
Figure 112016059793600-pat00110
,
Figure 112016059793600-pat00111
Represents an arbitrary point on the circular trajectory with respect to the pie line segment,
Figure 112016059793600-pat00112
Represents the vertical coordinate value of the image,
Figure 112016059793600-pat00113
,
Figure 112016059793600-pat00114
Respectively denote the end points of the pie segments,
Figure 112016059793600-pat00115
Denotes an image coordinate to be projected backward,
Figure 112016059793600-pat00116
Means the coordinates of the image value on the pie segment,
Figure 112016059793600-pat00117
Quot; means the pi segment value,
Figure 112016059793600-pat00118
The
Figure 112016059793600-pat00119
Lt; / RTI >
Figure 112016059793600-pat00120
Means the superimposed value of pie line segment.
11. The method of claim 10,
The step of irradiating the X-
And irradiating X-rays while rotating around the large object to be examined.

KR1020150095165A 2015-07-03 2015-07-03 X-ray tomography system using dual detector and method for the same KR101662067B1 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
KR1020150095165A KR101662067B1 (en) 2015-07-03 2015-07-03 X-ray tomography system using dual detector and method for the same

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
KR1020150095165A KR101662067B1 (en) 2015-07-03 2015-07-03 X-ray tomography system using dual detector and method for the same

Publications (1)

Publication Number Publication Date
KR101662067B1 true KR101662067B1 (en) 2016-10-05

Family

ID=57153991

Family Applications (1)

Application Number Title Priority Date Filing Date
KR1020150095165A KR101662067B1 (en) 2015-07-03 2015-07-03 X-ray tomography system using dual detector and method for the same

Country Status (1)

Country Link
KR (1) KR101662067B1 (en)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR20190118870A (en) 2018-04-11 2019-10-21 한국원자력연구원 Apparatus for non-destructive inspection

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2012511950A (en) * 2008-12-15 2012-05-31 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ Semi-circular reverse offset scan for enlarged 3D field of view
JP2013526953A (en) * 2010-05-27 2013-06-27 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ Improved reconstruction for cone-beam computed tomography imaging with an eccentric flat panel detector
KR20140122407A (en) * 2013-04-10 2014-10-20 (주)제노레이 X-ray Imaging Device And Imaging Method Thereof
KR20150039272A (en) * 2013-10-01 2015-04-10 삼성전자주식회사 X-ray detector and Computed tomography system comprising the same

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2012511950A (en) * 2008-12-15 2012-05-31 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ Semi-circular reverse offset scan for enlarged 3D field of view
JP2013526953A (en) * 2010-05-27 2013-06-27 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ Improved reconstruction for cone-beam computed tomography imaging with an eccentric flat panel detector
KR20140122407A (en) * 2013-04-10 2014-10-20 (주)제노레이 X-ray Imaging Device And Imaging Method Thereof
KR20150039272A (en) * 2013-10-01 2015-04-10 삼성전자주식회사 X-ray detector and Computed tomography system comprising the same

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR20190118870A (en) 2018-04-11 2019-10-21 한국원자력연구원 Apparatus for non-destructive inspection

Similar Documents

Publication Publication Date Title
US10492755B2 (en) Calibration phantom comprising a reflectance calibration target and a plurality of radio-opaque markers
JP5209979B2 (en) Method and system for three-dimensional imaging in an uncalibrated geometric configuration
US7561659B2 (en) Method for reconstructing a local high resolution X-ray CT image and apparatus for reconstructing a local high resolution X-ray CT image
US10772576B2 (en) X-ray imaging apparatus and control method thereof
JP5736427B2 (en) Device and method for localizing objects in CT imaging
US11090017B2 (en) Generating synthesized projection images for 3D breast tomosynthesis or multi-mode x-ray breast imaging
US9204854B2 (en) Medical imaging system and method
US10695145B2 (en) Tomographic scan
CN104545969A (en) Determining value of recording parameter by use of anatomic landmark
JP2008012319A (en) Method and system for reducing artifact in tomosynthesis/imaging/system
CN101133962A (en) Method for reconstructing a three-dimensional image volume and x-ray devices
BRPI0719616A2 (en) METHOD AND SYSTEM FOR BINOCULAR STEROSCOPIC RADIOGRAPHIC IMAGE FORMATION
JP2016022095A5 (en)
US20160199012A1 (en) X-ray imaging device
JP2005021675A (en) Tomograph apparatus
JP2007007255A (en) X-ray ct apparatus
US20130235970A1 (en) Image Processing Device of a Computer Tomography System
US20120057671A1 (en) Data acquisition and visualization mode for low dose intervention guidance in computed tomography
US8600000B2 (en) Device and method for a mammography apparatus
KR101662067B1 (en) X-ray tomography system using dual detector and method for the same
JP2008029846A (en) X-ray imaging apparatus and adjustment method of its rotary surface
JP2007143954A (en) Tomographic image reconstructing apparatus and x-ray imaging apparatus using it
US7860211B1 (en) Method of producing a laminography image with a rotating object, fixed x-ray source, and fixed detector columns
US11096639B2 (en) Projection data acquisition apparatus and subject support device
JP2006326175A (en) Digital x-ray tomography system

Legal Events

Date Code Title Description
GRNT Written decision to grant
FPAY Annual fee payment

Payment date: 20190826

Year of fee payment: 4