CN104665859B - Imaging system - Google Patents
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- CN104665859B CN104665859B CN201310628197.9A CN201310628197A CN104665859B CN 104665859 B CN104665859 B CN 104665859B CN 201310628197 A CN201310628197 A CN 201310628197A CN 104665859 B CN104665859 B CN 104665859B
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Abstract
The present invention relates to a kind of imaging system.The imaging system includes：X radiographic sources, for launching X beams；Detector array, including some detectors, the detector produce the initial signal for responding the oblique X beams for being incident upon the detector, and the initial signal includes the parallax crosstalk signal that response is incident to the X beams of the adjacent detector；And correcting module, the detector array is connected to, and revise signal is produced for correcting the parallax crosstalk signal from adjacent detector.The imaging system is modified to parallax crosstalk signal to improve the quality of image.
Description
Technical field
A kind of relevant imaging system of the present invention, more particularly to one kind are used for CT（Computed Tomography, computer
Tomography）Imaging system in imaging.
Background technology
CT scanner is worked by projecting fan-shaped or cone shaped X-ray beams from X-ray source.X-ray source is around quilt
Imaging object such as patient multiple view positions transmitting X-ray, by imaging object allow X-ray beam by when it is declined
Subtract.Light beam after decay is detected by one group of detector, and detector produces the signal for representing incident X-ray beam intensity.Handle the letter
Number produce and to represent the data of line integral of the object attenuation coefficient along X-ray approach.These signals are commonly referred to as " data for projection "
Or it is referred to as " projecting ".Using reconfiguration technique, such as filtered back projection, can from projection formed with image.Then, may be used
So that each image is associated, to form the volume perspective view of regions of interest.Then, medically, can be from reconstruct
Image or the volume of reproduction position or identified various symptom or other structures of concern.It is generally desirable to develop room and time
The good CT scanner of high resolution, picture quality.X-ray beam, which enters multiple detectors, can produce parallax crosstalk signal, parallax string
Disturb be image degradation a major reason, picture noise and artifact can be produced.
Therefore, it is necessary to a kind of imaging system is provided to solve above mentioned technical problem.
The content of the invention
One aspect of the present invention is to provide a kind of imaging system.The imaging system includes：X-ray source, for launching
X-ray beam；Detector array, including some detectors, the detector produce the oblique X- for being incident upon the detector of response and penetrated
The initial signal of wire harness, the initial signal include the parallax crosstalk letter that response is incident to the X-ray beam of the adjacent detector
Number；And correcting module, the detector array is connected to, and produce for correcting the parallax crosstalk signal from adjacent detector
Revise signal.
The imaging system of the present invention is modified to parallax crosstalk signal to improve the quality of image.
Brief description of the drawings
It is described in conjunction with the accompanying drawings for embodiments of the present invention, the present invention may be better understood, in accompanying drawing
In：
Fig. 1 show the schematic diagram of one embodiment of imaging system of the present invention；
Fig. 2 show the X-ray source of the imaging system shown in Fig. 1 and the schematic diagram of one embodiment of detector array；
Fig. 3 show the partial schematic diagram of the flat sheet mould of the detection array of one embodiment；
Fig. 4 show the partial schematic diagram of the flat sheet mould of the detection array of another embodiment；
Fig. 5 show the partial schematic diagram of the flat sheet mould of the detection array of another embodiment.
Embodiment
Unless otherwise defined, technical term or scientific terminology used herein should be in art of the present invention and had
The ordinary meaning that the personage of general technical ability is understood.Used in present patent application specification and claims " the
One " " the second " and similar word are not offered as any order, quantity or importance, and are used only to distinguish different groups
Into part.Either the similar word such as "comprising" means to appear in element or thing before " comprising " or "comprising" to " comprising "
Part, which is covered, appears in the " comprising " either element of "comprising" presented hereinafter or object and its equivalent, it is not excluded that other elements or
Person's object." connection " either the similar word such as " connected " is not limited to physics or mechanical connection, but can wrap
Electrical connection is included, it is either directly or indirect.
Fig. 1 show the schematic diagram of the imaging system 100 of one embodiment.Imaging system 100 includes X-ray source 11, inspection
Survey device array 13 and correcting module 15.X-ray source 11 is used for launching X-ray beam 17.Detector array 13 includes some detections
Device 131.Detector 131 produces the initial signal for responding the oblique X-ray beam 17 for being incident upon detector 131.Initial signal includes ringing
The parallax crosstalk signal of the X-ray beam 17 of adjacent detector 131 should be incident to.Correcting module 15 is connected to detector array 13,
And for producing revise signal according to the parallax crosstalk signal from adjacent detector 131.
Imaging system 100 includes image acquisition unit 110, controller 120, processor 130, equipment for reconstructing image 140, number
According to storage device 150, input unit 160 and display device 170.Image acquiring device 110 include gantry 20, X-ray source 11,
Detector array 13, plummer 22 and host cavity 24.Detector 131 includes at least one scintillator（It is not shown）And photoreceptor
（It is not shown）.In certain embodiments, photoreceptor includes photodiode or phototransistor, but not limited to this.X-ray source
11 and detector array 13 be relatively arranged on gantry 20, both are received chamber 24 and separated.Detection object 26 is positioned over plummer 22
On, and can be located at together with plummer 22 in host cavity 24.In one embodiment, X-ray source 11 and detector array 13 are relative
In gantry 20 and the rotary setting of detection object 26.In another embodiment, X-ray source 11 and detector array 13 remain stationary as.
X-ray source 11 launches X-ray beam 17 to detector array 13, and X-ray beam 17 passes through detection object 26.When X- is penetrated
Wire harness 17 passes through detection object 26, and detection object 26 makes X-ray beam 17 decay.The X-ray beam 17 of decay is by detector
131 scintillator absorbs.The X-ray of absorption is converted to visible ray by scintillator.Photoreceptor will be seen that light is converted to electric signal,
To respond the initial signal of X-ray beam 17, it is the signal for representing the intensity of X-ray beam 17.Telecommunications caused by each photoreceptor
Number to scintillator receive decay X-ray beam 17 intensity it is directly proportional.
Controller 120 includes plummer control unit 30, X-ray control unit 32, gantry control unit 34 and amendment mould
Block 15.Plummer control unit 30 controls the motion of plummer 22.X-ray control unit 32 provide power and clock signal to
X-ray source 11.Gantry control unit 34 controls the rotary speed and angle orientation of X-ray source 11.Correcting module 15 receives inspection
Survey initial signal caused by device 131 and initial signal is handled, produce projection signal and be supplied to equipment for reconstructing image 140.
In one embodiment, correcting module 15 can be with plummer control unit 30, X-ray control unit 32 and gantry control unit
34 combine.In another embodiment, correcting module 15 can combine with detector array 13.Image reconstruction fills
Put 140 and processor 130 according to projection signal's reconstruction image.The image of reconstruction is stored in data storage device 150.Implement one
In example, data storage device 150 also stores intermediate processing data during reconstruction image.Input unit 160, which is used for receiving coming from, to be made
The input of user.Display device 170 shows the image of detection object 26.
In certain embodiments, data storage device 150 can be magnetic storage medium or optical storage media, for example, hard disk,
Storage chip etc., but not limited to this.In one embodiment, computer program or instruction etc. can be uploaded by input unit 160
To processor 130.Input unit 160 can include button, audio input, video input etc., but not limited to this.In some implementations
In example, display device 170 may include liquid crystal display apparatus, cathode-ray display, plasma display etc., but not limited to this.
Fig. 2 show the X-ray source 11 of one embodiment and the schematic diagram of detector array 13.Detector array 13 is wrapped
Include one or more flat sheet moulds 133.Flat sheet mould 133 is tabular, and it includes multiple detectors 131.Each flat sheet mould
133 detector 131 arranges in the same plane.In the present embodiment, the center of multiple flat sheet moulds 133 is arranged in an arc
In shape 40, the detector array 13 of approximate arc-shaped is formed.Detector array is formed with the flat sheet mould 133 of multiple separation
13, flat flat sheet mould 133 is compared with easy processing, and the detector 131 that each flat sheet mould 133 includes is relatively fewer, so as to
Its structure is smaller, and yield rate is higher.
Fig. 3 show the partial schematic diagram of the flat sheet mould 133 of one embodiment.X-ray beam 17 passes through detection object
（It is not shown）The oblique detector 131 for being incident upon flat sheet mould 133.Part X-ray beam 171 through detection object only injects one
Individual detector 131, and pass through the part X-ray beam 173 of detection object to inject the edge of two neighboring detector 131.Detector
The initial signal of response X-ray beam 17 is incident to regarding for the X-ray beam 173 of adjacent detector 131 including response caused by 131
Poor crosstalk（Parallax Cross Talk）Signal and response are incident to the true letter of the X-ray beam 171 of a detector 131
Number.The X-ray beam 173 for injecting the first edge 135 of detector 131 still injects the second edge 137 of adjacent detector 131.
Two neighboring detector 131 produces response through being directly transmitted to first edge 135 and second edge 137 after detection object respectively
X-ray beam 173 parallax crosstalk signal, one group of parallax crosstalk signal can be referred to as.X-ray beam 171 injects detector 131
Core 136, detector 131 produce the true signal for responding the X-ray beam 171.In one embodiment, simulation software is passed through
First, second edge 135,137 and core are divided according to the arrangement of the incident direction of X-ray beam 17 and detector 131
136.After detector 131 produces initial signal, parallax crosstalk signal and true signal are separated using simulation software.Repairing shown in Fig. 1
Positive module 15 is used for producing revise signal according to the parallax crosstalk signal from adjacent detector 131.Correcting module 15 will be corresponding
Parallax crosstalk signal in first edge 135 and the parallax crosstalk signal corresponding to second edge 137 are modified, come eliminate by
In the flaw of the ring caused by parallax crosstalk signal on image and stain etc..Correcting module 15 is to caused by detector 131
True signal carries out processing and produces true projection signal.
In the embodiment shown in fig. 3, detector array 13 includes the detection of some incident directions along X-ray beam 17
Passage 139.In one embodiment, the projection signal according to caused by the initial signal of at least one sense channel 139 includes true throw
Shadow signal.In one embodiment, the projection signal according to caused by the initial signal of at least one sense channel 139 includes true projection
Signal and revise signal.In embodiment shown in Fig. 3, sense channel 139 includes a part for adjacent detector 131.Detection is logical
Road 139 includes the first edge 135 and core 136 of a detector 131, and the second side including adjacent detector 131
Edge 137.The X-ray beam 17 injected in sense channel 139 includes the X-ray beam 171 for injecting a detector 131 and injects phase
The X-ray beam 173 of adjacent two detectors 131.The X-ray beam 17 that correcting module 15 is injected in sense channel 139 to response
Initial signal carries out processing and produces projection signal.The initial signal of each sense channel 139 include one group of parallax crosstalk signal and
True signal.Correcting module 15 produces one group of projection signal according to the initial signal of each sense channel 139.In the present embodiment, often
One group of projection signal includes revise signal and true projection signal.One group of parallax crosstalk signal is only in a sense channel 139.Figure
Equipment for reconstructing image 140 shown in 1 projection signal's reconstruction image according to caused by correcting module 15.
Fig. 4 show the partial schematic diagram of the flat sheet mould 133 of another embodiment.Embodiment shown in Fig. 4 is similar to Fig. 3
Shown embodiment.The main distinction of the embodiment shown in embodiment and Fig. 3 shown in Fig. 4 is：Detection in Fig. 4 embodiments
Passage 141 includes the core 136 of detector 131 and two groups of Hes of first edge 135 positioned at the both sides of core 136
Second edge 137, adjacent sense channel 142 only include the core 136 of a detector 131, are so intervally arranged.Inspection
Surveying the initial signal of passage 141 includes two groups of parallax crosstalk signals and a true signal, the initial signal of adjacent sense channel 142
Only include true signal.
Fig. 5 show the partial schematic diagram of the flat sheet mould 133 of another embodiment.Embodiment shown in Fig. 5 is similar to Fig. 3
With the embodiment shown in Fig. 4.Relative to the embodiment shown in Fig. 3 and Fig. 4, in the embodiment shown in Fig. 5, sense channel 143 wraps
Include a part for a detector 131.Sense channel 143 only includes the core 136 of detector 131, the sense channel 143
Initial signal only include true signal.Adjacent sense channel 144 includes the first edge 135 and adjacent detector of detector 131
131 second edge 137, the initial signal of the sense channel 144 only include one group of parallax crosstalk signal.So it is intervally arranged.
Revise signal and true projection signal produce according to the initial signal of different sense channels 143,144 respectively.Each group of parallax string
Disturb signal to separate with true signal, be separately processed and produce revise signal and true projection signal, revise signal and true projection signal
As different groups of projection signal.Parallax crosstalk signal is so kept apart into independent processing, improves sample rate indirectly, so as to improve
The resolution ratio of image.
In one embodiment, true projection signal prep'(n) expression formula such as expression formula（1）It is shown：
Prep'(n)=Log [I'n(air)/I'n(λ)]
=Log[In(air)/In(λ)]+Log[I'n(air)*In(λ)/(In(air)*I'n(λ))] （1）
=prep(n)+f'(prep(n))
Wherein, I'n(air) represent X-ray through air be emitted directly toward detector 131 when detector 131 caused by really believe
Number；I'n(λ) represent X-ray pass through detection object after inject detector 131 when true signal caused by detector 131；In(air)
Represent X-ray through air be emitted directly toward detector 131 when initial signal caused by detector 131；In(λ) represents X-ray
Initial signal caused by detector 131 when detector 131 is injected after through detection object；N represents n-th of detector 131；λ tables
Show the thickness of detection object；Prep (n) represents the initial projections signal that the initial signal according to caused by detector 131 obtains,
Prep (n)=Log [In(air)/In(λ)]；F'(prep (n)) be true projection signal correction function, f'(prep (n))=Log
[I'n(air)*In(λ)/(In(air)*I'n(λ)), I'nAnd I (air)n(air) it is constant, therefore correction function is with detection pair
The thickness lambda of elephant changes and changed.
Similar to true projection signal prep'(n), revise signal prep " (n) expression formula such as expression formula（2）It is shown：
Prep " (n)=Log [I "n(air)/I"n(λ)]
=Log[In(air)/In(λ)]+Log[I"n(air)*In(λ)/(In(air)*I"n(λ))] （2）
=prep(n)+f"(prep(n))
Wherein, I "n(air) represent X-ray through air be emitted directly toward detector 131 when parallax caused by detector 131
Crosstalk signal；I"n(λ) represents X-ray through parallax caused by detector 131 is believed during injection detector 131 after detection object
Number；F " (prep (n)) is the correction function of revise signal, f " (prep (n))=Log [I "n(air)*In(λ)/(In(air)*
I"n(λ)), I "n(air) it is constant, correction function is as the thickness lambda of detection object changes and changes.
True projection signal prep'(n) and revise signal prep " (n) is respectively on the basis of initial projections signal prep (n)
Acquisition is modified, and correction function is relevant with the thickness lambda of detection object.In one embodiment, obtained by experiment simulation
The value of correction function corresponding to the different-thickness of detection object, it can be corrected accordingly by quick obtain of tabling look-up in actually detected
The value of function.In emulation experiment, moisture film analog detection object can be used, but be not limited to moisture film.Can be right according to practical application
Above-mentioned true projection signal prep'(n) and revise signal prep " (n) is further is handled, amendment letter that can respectively to both
Number could be adjusted to adapt to actual application, to obtain more accurately projection signal, so as to obtain apparent accurate image.
Although with reference to specific embodiment, the present invention is described, it will be appreciated by those skilled in the art that
Can be so that many modifications may be made and modification to the present invention.It is therefore contemplated that claims are intended to cover in the present invention
All such modifications and modification in true spirit and scope.
Claims (9)
1. a kind of imaging system, it is characterised in that it includes：
X-ray source, for launching X-ray beam；
Detector array, including some detectors, the detector are penetrated for producing the oblique X- for being incident upon the detector of response
The initial signal of wire harness, the initial signal include the parallax crosstalk letter that response is incident to the X-ray beam of the adjacent detector
Number；And
Correcting module, the detector array is connected to, and is produced for correcting the parallax crosstalk signal from adjacent detector
Revise signal,
The detector array includes one or more flat sheet moulds, and the flat sheet mould includes the detector, each described
The detector arrangement of flat sheet mould in the same plane, wherein according to the incident direction of X-ray beam and the detector
Arrangement separation parallax crosstalk signal and true signal.
2. imaging system as claimed in claim 1, it is characterised in that：The center of multiple flat sheet moulds is arranged in an arc
In shape.
3. a kind of imaging system, it is characterised in that it includes：
X-ray source, for launching X-ray beam；
Detector array, including some detectors, the detector are penetrated for producing the oblique X- for being incident upon the detector of response
The initial signal of wire harness, the initial signal include the parallax crosstalk letter that response is incident to the X-ray beam of the adjacent detector
Number；And
Correcting module, the detector array is connected to, and is produced for correcting the parallax crosstalk signal from adjacent detector
Revise signal,
The initial signal includes the true signal that response is incident to the X-ray beam of a detector, the detector array
Include the sense channel of some incident directions along the X-ray beam, the correcting module is used for injecting the inspection according to response
Initial signal caused by the X-ray beam surveyed in passage produces projection signal and produces true projection signal according to the true signal.
4. imaging system as claimed in claim 3, it is characterised in that：According to the described initial of at least one sense channel
The projection signal caused by signal includes the true projection signal.
5. the imaging system as described in claim 3 or 4, it is characterised in that：According to the initial of at least one sense channel
The projection signal caused by signal includes the true projection signal and the revise signal.
6. imaging system as claimed in claim 3, it is characterised in that：Produced according to the initial signal of a sense channel
The projection signal include the true projection signal and the revise signal, and according to the initial of the adjacent sense channel
The projection signal caused by signal includes the true projection signal.
7. imaging system as claimed in claim 3, it is characterised in that：The revise signal and true projection signal's difference root
Produced according to the initial signal of the different sense channels.
8. imaging system as claimed in claim 3, it is characterised in that：The sense channel includes the one of a detector
Part.
9. imaging system as claimed in claim 3, it is characterised in that：The sense channel includes the one of the adjacent detector
Part.
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| CN201310628197.9A CN104665859B (en) | 2013-11-29 | 2013-11-29 | Imaging system |
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| CN104665859B true CN104665859B (en) | 2017-12-15 |
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Family Cites Families (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE19714689A1 (en) * | 1997-04-09 | 1998-10-15 | Siemens Ag | X-ray detector |
| CA2445044C (en) * | 2001-04-25 | 2011-02-15 | Amnis Corporation | Method and apparatus for correcting crosstalk and spatial resolution for multichannel imaging |
| JP2004024659A (en) * | 2002-06-27 | 2004-01-29 | Hitachi Medical Corp | X-ray ct apparatus |
| JP4261864B2 (en) * | 2002-10-07 | 2009-04-30 | ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー | Data correction method and X-ray CT apparatus |
| JP4041040B2 (en) * | 2003-09-08 | 2008-01-30 | ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー | Radiation tomography equipment |
| JP3978193B2 (en) * | 2004-03-15 | 2007-09-19 | ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー | Crosstalk correction method and X-ray CT apparatus |
| JP2006068338A (en) * | 2004-09-03 | 2006-03-16 | Ge Medical Systems Global Technology Co Llc | Radiographic equipment |
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