CN104665859A - Imaging system - Google Patents
Imaging system Download PDFInfo
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- CN104665859A CN104665859A CN201310628197.9A CN201310628197A CN104665859A CN 104665859 A CN104665859 A CN 104665859A CN 201310628197 A CN201310628197 A CN 201310628197A CN 104665859 A CN104665859 A CN 104665859A
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Abstract
The invention relates to an imaging system. The imaging system comprises an X-ray source, a detector array, and a correcting module. The X-ray source is used for emitting X-ray beams. The detector array comprises a plurality of detectors. The detectors generate an initial signal responding to the X-ray beams that obliquely enter the detectors. The initial signal comprises a parallax interfere signal responding to the X-ray beams that obliquely enter adjacent detectors. The correcting module is connected with the detector array; and the correcting module is used for correcting the parallax interfere signal coming from the adjacent detectors in order to generator a corrected signal. The imaging system corrects the parallax interfere signal to increase the quality of the image.
Description
Technical field
The present invention, about a kind of imaging system, particularly relates to a kind of for CT(Computed Tomography, computer tomography) imaging system in imaging.
Background technology
CT scanner is by projecting fan-shaped or cone shaped X-ray beams work from X-ray source.X-ray source is launching X-rays around the multiple view position being imaged object such as patient, be imaged object allow X-beam by time make it decay.Light beam after decay is detected by one group of detector, and detector produces the signal representing incident X-ray beam intensity.Process this signal and produce the data of representative object attenuation quotient along the line integral of X-ray path.These signals are commonly referred to as " data for projection " or are just called " projection ".Utilize reconfiguration technique, such as filtered back projection, can from the image be formed that projects.Subsequently, each image can be made to be associated, to form the volume perspective view in the region be concerned about.Then, medically, can locate or identify various condition of illness or other structure be concerned about from the volume of the image of reconstruct or reproduction.General CT scanner of wishing that development room and time resolution is high, picture quality is good.X-beam injects multiple detector can produce parallax crosstalk signal, and parallax crosstalk is the major reason that picture quality reduces, and can produce picture noise and artifact.
Therefore, be necessary to provide a kind of imaging system to solve above mentioned technical problem.
Summary of the invention
One aspect of the present invention is to provide a kind of imaging system.This imaging system comprises: X-ray source, is used for launching X-beam; Detector array, comprises some detectors, and described detector produces the initialize signal of response oblique incidence to the X-beam of described detector, and described initialize signal comprises the parallax crosstalk signal that response is incident to the X-beam of adjacent described detector; And correcting module, be connected to described detector array, and be used for revising the parallax crosstalk signal generation corrected signal from adjacent detector.
Imaging system of the present invention revises the quality improving image to parallax crosstalk signal.
Accompanying drawing explanation
Be described for embodiments of the present invention in conjunction with the drawings, the present invention may be better understood, in the accompanying drawings:
Figure 1 shows that the schematic diagram of an embodiment of imaging system of the present invention;
Figure 2 shows that the schematic diagram of the X-ray source of the imaging system shown in Fig. 1 and an embodiment of detector array;
Figure 3 shows that the partial schematic diagram of the flat sheet mould of the detection arrays of an embodiment;
Figure 4 shows that the partial schematic diagram of the flat sheet mould of the detection arrays of another embodiment;
Figure 5 shows that the partial schematic diagram of the flat sheet mould of the detection arrays of an embodiment again.
Detailed description of the invention
Unless otherwise defined, technical term used herein or scientific terminology should be in field belonging to the present invention the ordinary meaning that the personage with general technical ability understands." first " " second " used in patent application specification of the present invention and claims and similar word do not represent any order, quantity or importance, and are only used to distinguish different ingredients." comprise " or the similar word such as " comprising " mean to appear at " comprising " or " comprising " before element or object contain the element or object that appear at " comprising " or " comprising " presented hereinafter and equivalent, do not get rid of other elements or object." connection " or " being connected " etc. similar word be not defined in physics or the connection of machinery, no matter but can comprise electrical connection, be direct or indirectly.
Figure 1 shows that the schematic diagram of the imaging system 100 of an embodiment.Imaging system 100 comprises X-ray source 11, detector array 13 and correcting module 15.X-ray source 11 is used for launching X-beam 17.Detector array 13 comprises some detectors 131.Detector 131 produces the initialize signal of response oblique incidence to the X-beam 17 of detector 131.Initialize signal comprises the parallax crosstalk signal that response is incident to the X-beam 17 of adjacent detector 131.Correcting module 15 is connected to detector array 13, and is used for producing corrected signal according to the parallax crosstalk signal from adjacent detector 131.
Imaging system 100 comprises image acquisition unit 110, controller 120, processor 130, equipment for reconstructing image 140, data storage device 150, input equipment 160 and display device 170.Image acquiring device 110 comprises gantry 20, X-ray source 11, detector array 13, plummer 22 and host cavity 24.Detector 131 comprises at least one scintillator (not shown) and photoreceptors (not shown).In certain embodiments, photoreceptors comprises photodiode or phototransistor, but is not limited thereto.X-ray source 11 and detector array 13 are relatively arranged on gantry 20, and both are separated by host cavity 24.Detected object 26 is positioned on plummer 22, and can be positioned at host cavity 24 together with plummer 22.In one embodiment, X-ray source 11 and detector array 13 are relative to gantry 20 and detected object 26 rotary setting.In another embodiment, X-ray source 11 and detector array 13 keep motionless.
X-ray source 11 launches X-beam 17, X-beam 17 through detected object 26 to detector array 13.When X-beam 17 is through detected object 26, detected object 26 makes X-beam 17 decay.The X-beam 17 of decay is absorbed by the scintillator of detector 131.The X-ray of absorption is converted to visible ray by scintillator.Visible ray is converted to the signal of telecommunication by photoreceptors, and be the initialize signal of response X-beam 17, it is the signal representing X-beam 17 intensity.The intensity of the X-beam 17 of the decay that the signal of telecommunication that each photoreceptors produces receives to scintillator is directly proportional.
Controller 120 comprises plummer control unit 30, X-ray control unit 32, gantry control unit 34 and correcting module 15.Plummer control unit 30 controls the motion of plummer 22.X-ray control unit 32 provides power and clock signal to X-ray source 11.Gantry control unit 34 controls rotary speed and the angle orientation of X-ray source 11.Correcting module 15 receives the initialize signal of detector 131 generation and processes initialize signal, produces projection signal and is supplied to equipment for reconstructing image 140.In one embodiment, correcting module 15 can combine with plummer control unit 30, X-ray control unit 32 and gantry control unit 34.In another embodiment, correcting module 15 can combine with detector array 13.Equipment for reconstructing image 140 and processor 130 rebuild image according to projection signal.The image rebuild is stored in data storage device 150.In one embodiment, data storage device 150 also stores intermediate processing data when rebuilding image.Input equipment 160 is used for receiving the input from user.Display device 170 shows the image of detected object 26.
In certain embodiments, data storage device 150 can be magnetic storage medium or optical storage media, such as, and hard disk, storage chip etc., but be not limited thereto.In one embodiment, computer program or instruction etc. can be uploaded to processor 130 by input equipment 160.Input equipment 160 can comprise button, audio frequency input, video input etc., but is not limited thereto.In certain embodiments, display device 170 can comprise liquid crystal display apparatus, cathode-ray display, plasma display etc., but is not limited thereto.
Figure 2 shows that the X-ray source 11 of an embodiment and the schematic diagram of detector array 13.Detector array 13 comprises one or more flat sheet mould 133.Flat sheet mould 133 is tabular, and it comprises multiple detector 131.The detector 131 of each flat sheet mould 133 is arranged in same plane.In the present embodiment, the central row of multiple flat sheet mould 133 is listed on an arc 40, forms the detector array 13 of approximate arc-shaped.Form detector array 13 with the flat sheet mould 133 of multiple separation, flat flat sheet mould 133 is more easily processed, and the detector 131 that each flat sheet mould 133 comprises is relatively less, thus its structure is less, and yield rate is higher.
Figure 3 shows that the partial schematic diagram of the flat sheet mould 133 of an embodiment.X-beam 17 passes the detector 131 of detected object (not shown) oblique incidence to flat sheet mould 133.Part X-beam 171 through detected object only injects a detector 131, and the part X-beam 173 passing detected object injects the edge of adjacent two detectors 131.The initialize signal of the response X-beam 17 that detector 131 produces comprises response and is incident to parallax crosstalk (the Parallax Cross Talk) signal of the X-beam 173 of adjacent detector 131 and responds the true signal being incident to the X-beam 171 of a detector 131.The X-beam 173 injecting the first edge 135 of detector 131 still injects the second edge 137 of adjacent detector 131.Adjacent two detectors 131 produce the parallax crosstalk signal responded through the X-beam 173 being directly transmitted to the first edge 135 and the second edge 137 after detected object respectively, can be called one group of parallax crosstalk signal.X-beam 171 injects the core 136 of detector 131, and detector 131 produces the true signal of this X-beam 171 of response.In one embodiment, first, second edge 135,137 and core 136 is divided by simulation software according to the arrangement of the incident direction of X-beam 17 and detector 131.After detector 131 produces initialize signal, simulation software is utilized to be separated parallax crosstalk signal and true signal.Correcting module 15 shown in Fig. 1 is used for producing corrected signal according to the parallax crosstalk signal from adjacent detector 131.Correcting module 15 will correspond to the parallax crosstalk signal at the first edge 135 and correspond to the parallax crosstalk signal at the second edge 137 and revise, and eliminate the flaw of such as ring and the stain etc. on the image that causes due to parallax crosstalk signal.The true signal that correcting module 15 pairs of detectors 131 produce carries out process and produces true projection signal.
In the embodiment shown in fig. 3, detector array 13 comprises the sense channel 139 of some incident directions along X-beam 17.In one embodiment, the projection signal produced according to the initialize signal of at least one sense channel 139 comprises true projection signal.In one embodiment, the projection signal produced according to the initialize signal of at least one sense channel 139 comprises true projection signal and corrected signal.In embodiment shown in Fig. 3, sense channel 139 comprises a part for adjacent detector 131.Sense channel 139 comprises the first edge 135 and the core 136 of a detector 131, and comprises the second edge 137 of adjacent detector 131.The X-beam 17 injected in sense channel 139 comprises the X-beam 171 injecting a detector 131 and the X-beam 173 injecting adjacent two detectors 131.The initialize signal of correcting module 15 to the X-beam 17 that response is injected in sense channel 139 carries out process and produces projection signal.The initialize signal of each sense channel 139 comprises one group of parallax crosstalk signal and true signal.Correcting module 15 produces one group of projection signal according to the initialize signal of each sense channel 139.In the present embodiment, each group projection signal comprises corrected signal and true projection signal.One group of parallax crosstalk signal is only in a sense channel 139.The projection signal that equipment for reconstructing image 140 shown in Fig. 1 produces according to correcting module 15 rebuilds image.
Figure 4 shows that the partial schematic diagram of the flat sheet mould 133 of another embodiment.Embodiment shown in Fig. 4 is similar to the embodiment shown in Fig. 3.The main distinction of the embodiment shown in the embodiment shown in Fig. 4 and Fig. 3 is: the sense channel 141 in Fig. 4 embodiment comprises the core 136 of a detector 131 and is positioned at two group of first edge 135 and second edge 137 of core 136 both sides, adjacent sense channel 142 only comprises the core 136 of a detector 131, is so intervally arranged.The initialize signal of sense channel 141 comprises two groups of parallax crosstalk signals and a true signal, and the initialize signal of adjacent sense channel 142 only comprises true signal.
Figure 5 shows that the partial schematic diagram of the flat sheet mould 133 of an embodiment again.Embodiment shown in Fig. 5 is similar to the embodiment shown in Fig. 3 and Fig. 4.Relative to the embodiment shown in Fig. 3 and Fig. 4, in the embodiment shown in Fig. 5, sense channel 143 comprises a part for a detector 131.Sense channel 143 only comprises the core 136 of detector 131, and the initialize signal of this sense channel 143 only comprises true signal.Adjacent sense channel 144 comprises the first edge 135 of detector 131 and the second edge 137 of adjacent detector 131, and the initialize signal of this sense channel 144 only comprises one group of parallax crosstalk signal.So be intervally arranged.Corrected signal and true projection signal produce according to the initialize signal of different sense channels 143,144 respectively.Each group parallax crosstalk signal and true signal are separated, respectively processed generation corrected signal and true projection signal, and corrected signal and true projection signal are as the projection signal of difference group.So parallax crosstalk signal is kept apart individual processing, indirectly improve sample rate, thus improve the resolution of image.
In one embodiment, true projection signal prep'(n) expression formula as shown in expression formula (1):
prep'(n)＝Log[I'
n(air)/I'
n(λ)]
=Log[I
n(air)/I
n(λ)]+Log[I'
n(air)*I
n(λ)/(I
n(air)*I'
n(λ))] （1）
=prep(n)+f'(prep(n))
Wherein, I'
n(air) true signal that when representing that X-ray directly injects detector 131 through air, detector 131 produces; I'
n(λ) true signal that X-ray produces through detector 131 when injecting detector 131 after detected object is represented; I
n(air) initialize signal that when representing that X-ray directly injects detector 131 through air, detector 131 produces; I
n(λ) initialize signal that X-ray produces through detector 131 when injecting detector 131 after detected object is represented; N represents the n-th detector 131; λ represents the thickness of detected object; Prep (n) represents the initial projections signal that the initialize signal produced according to detector 131 obtains, prep (n)=Log [I
n(air)/I
n(λ)]; F'(prep (n)) be the correction function of true projection signal, f'(prep (n))=Log [I'
n(air) * I
n(λ)/(I
n(air) * I'
n(λ)), I'
nand I (air)
n(air) be constant, therefore correction function changes along with the thickness lambda change of detected object.
Be similar to true projection signal prep'(n), corrected signal prep " expression formula of (n) is as shown in expression formula (2):
prep"(n)＝Log[I"
n(air)/I"
n(λ)]
=Log[I
n(air)/I
n(λ)]+Log[I"
n(air)*I
n(λ)/(I
n(air)*I"
n(λ))] （2）
=prep(n)+f"(prep(n))
Wherein, I "
n(air) the parallax crosstalk signal that when representing that X-ray directly injects detector 131 through air, detector 131 produces; I "
n(λ) parallax signals that X-ray produces through detector 131 when injecting detector 131 after detected object is represented; F " correction function that (prep (n)) is corrected signal, f " (prep (n))=Log [I "
n(air) * I
n(λ)/(I
n(air) * I "
n(λ)), I "
n(air) be constant, correction function changes along with the thickness lambda change of detected object.
True projection signal prep'(n) and corrected signal prep " (n) carries out correction respectively and obtains on the basis of initial projections signal prep (n), and correction function is all relevant with the thickness lambda of detected object.In one embodiment, the value of the correction function that the different-thickness of emulation acquisition detected object is corresponding by experiment, can by the value obtaining corresponding correction function fast of tabling look-up in actual detection.In emulation experiment, can moisture film analog detection object be used, but be not limited to moisture film.Can to above-mentioned true projection signal prep'(n according to practical application) and corrected signal prep " (n) does further process; can adapt to actual application to both correction function adjustment respectively; to obtain projection signal more accurately, thus can obtain more clear image accurately.
Although describe the present invention in conjunction with specific embodiment, those skilled in the art will appreciate that and can make many amendments and modification to the present invention.Therefore, recognize, the intention of claims is to be encompassed in all such modifications in true spirit of the present invention and scope and modification.
Claims (10)
1. an imaging system, is characterized in that, it comprises:
X-ray source, is used for launching X-beam;
Detector array, comprises some detectors, and described detector is used for producing the initialize signal of response oblique incidence to the X-beam of described detector, and described initialize signal comprises the parallax crosstalk signal that response is incident to the X-beam of adjacent described detector; And
Correcting module, is connected to described detector array, and is used for revising the parallax crosstalk signal generation corrected signal from adjacent detector.
2. imaging system as claimed in claim 1, it is characterized in that: described detector array comprises one or more flat sheet mould, described flat sheet mould comprises described detector, and the described detector of flat sheet mould described in each is arranged in same plane.
3. imaging system as claimed in claim 2, is characterized in that: the central row of multiple described flat sheet mould is listed on an arc.
4. imaging system as claimed in claim 1, it is characterized in that: described initialize signal comprises the true signal that response is incident to the X-beam of a described detector, described detector array comprises the sense channel of some incident directions along described X-beam, and described correcting module is used for producing projection signal according to the initialize signal that the X-beam that response is injected in described sense channel produces and producing true projection signal according to described true signal.
5. imaging system as claimed in claim 4, is characterized in that: comprise described true projection signal according to the described projection signal that the described initialize signal of sense channel described at least one produces.
6. the imaging system as described in claim 4 or 5, is characterized in that: comprise described true projection signal and described corrected signal according to the described projection signal that the initialize signal of sense channel described at least one produces.
7. imaging system as claimed in claim 4, it is characterized in that: comprise described true projection signal and described corrected signal according to the described projection signal that the initialize signal of a described sense channel produces, and comprise described true projection signal according to the described projection signal that the initialize signal of adjacent described sense channel produces.
8. imaging system as claimed in claim 4, is characterized in that: described corrected signal and described true projection signal produce according to the described initialize signal of different described sense channels respectively.
9. imaging system as claimed in claim 4, is characterized in that: described sense channel comprises a part for a described detector.
10. imaging system as claimed in claim 4, is characterized in that: described sense channel comprises a part for adjacent described detector.
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| CN1593341A (en) * | 2003-09-08 | 2005-03-16 | Ge医疗系统环球技术有限公司 | Radiation tomograph apparatus and radiation tomography method thereof |
| CN1669529A (en) * | 2004-03-15 | 2005-09-21 | Ge医疗系统环球技术有限公司 | Cross-talk correction method and x-ray ct apparatus |
| JP2006068338A (en) * | 2004-09-03 | 2006-03-16 | Ge Medical Systems Global Technology Co Llc | Radiographic equipment |
| US7286719B2 (en) * | 2001-04-25 | 2007-10-23 | Amnis Corporation | Method and apparatus for correcting crosstalk and spatial resolution for multichannel imaging |
| 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 |
-
2013
- 2013-11-29 CN CN201310628197.9A patent/CN104665859B/en active Active
Patent Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1195787A (en) * | 1997-04-09 | 1998-10-14 | 西门子公司 | Computerized tomograph camera |
| US7286719B2 (en) * | 2001-04-25 | 2007-10-23 | 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 |
| CN1593341A (en) * | 2003-09-08 | 2005-03-16 | Ge医疗系统环球技术有限公司 | Radiation tomograph apparatus and radiation tomography method thereof |
| CN1669529A (en) * | 2004-03-15 | 2005-09-21 | Ge医疗系统环球技术有限公司 | Cross-talk 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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