CN103251423A - Computed tomography device and method for recording image data of a volume to be imaged - Google Patents
Computed tomography device and method for recording image data of a volume to be imaged Download PDFInfo
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- CN103251423A CN103251423A CN2013100492092A CN201310049209A CN103251423A CN 103251423 A CN103251423 A CN 103251423A CN 2013100492092 A CN2013100492092 A CN 2013100492092A CN 201310049209 A CN201310049209 A CN 201310049209A CN 103251423 A CN103251423 A CN 103251423A
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- 238000002591 computed tomography Methods 0.000 title claims abstract description 36
- 238000000034 method Methods 0.000 title claims abstract description 15
- 238000013170 computed tomography imaging Methods 0.000 claims abstract description 5
- 238000006073 displacement reaction Methods 0.000 description 3
- 238000001514 detection method Methods 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 230000002349 favourable effect Effects 0.000 description 2
- 238000005259 measurement Methods 0.000 description 2
- IHQKEDIOMGYHEB-UHFFFAOYSA-M sodium dimethylarsinate Chemical class [Na+].C[As](C)([O-])=O IHQKEDIOMGYHEB-UHFFFAOYSA-M 0.000 description 2
- 230000003187 abdominal effect Effects 0.000 description 1
- 210000003484 anatomy Anatomy 0.000 description 1
- 230000002596 correlated effect Effects 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 238000005286 illumination Methods 0.000 description 1
- 238000003384 imaging method Methods 0.000 description 1
- 238000005457 optimization Methods 0.000 description 1
- 230000001105 regulatory effect Effects 0.000 description 1
- 239000011800 void material Substances 0.000 description 1
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
- G01T1/2914—Measurement of spatial distribution of radiation
- G01T1/2985—In depth localisation, e.g. using positron emitters; Tomographic imaging (longitudinal and transverse section imaging; apparatus for radiation diagnosis sequentially in different planes, steroscopic radiation diagnosis)
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/027—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis characterised by the use of a particular data acquisition trajectory, e.g. helical or spiral
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computed tomography [CT]
- A61B6/032—Transmission computed tomography [CT]
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4208—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/40—Arrangements for generating radiation specially adapted for radiation diagnosis
- A61B6/4064—Arrangements for generating radiation specially adapted for radiation diagnosis specially adapted for producing a particular type of beam
- A61B6/4085—Cone-beams
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Abstract
The invention relates to a computed tomography device for recording image data of a volume to be imaged, comprising: a rack, a X-ray source, a detector which has a lateral region on at least one wide edge having a width less than the overall width of the detector, wherein the lateral region with regard to the overall width of the detector is arranged alternatively relative to the center. The device has a control device which controls rack rotation and detector feed relative to the imaged volume in such a coordinated manner for spiral CT imaging that a rotational direction of the rack rotation and a feed direction of the detector feed are matched. The invention further relates to a corresponding method for recording image data of a volume to be imaged in a computer tomography device.
Description
Technical field
The present invention relates to a kind of computer-tomography apparatus, and a kind of method that is used for recording image data at computer-tomography apparatus.
Background technology
In current techniques, computer-tomography apparatus (following to CT (computer tomography) machine or computer tomography use abbreviation CT) columniform detector of assembling.At this, cylindrical expression detector is so moulded, and makes it have the part of virtual cylindrical side.
Above-mentioned detector covers 50 centimetres scanning survey zone (English: scan field of view, SFOV, scan vision) usually.
Detector is made up of many rows usually, and it is arranged on the cylinder axis direction continuously, and constitutes the width of detector together.This width is namely represented the extension of detector on the cylinder axis direction.
Summary of the invention
Task of the present invention is, a kind of computer-tomography apparatus and a kind of at the method for computer-tomography apparatus for the view data of record volume to be imaged is provided, and this method can reduce the cost of computer-tomography apparatus and can scan fast the scanning survey field simultaneously.
Task of the present invention will be solved by the related content of independent claims.
Have according to the computer-tomography apparatus for the view data that records volume to be imaged of the present invention:
Frame,
The X ray emitter,
Detector, this detector has side regions at its at least one broadside, and this side regions has the little width of integral width of ratio detection device,
Wherein this side regions is arranged with respect to the center about the integral width of detector with staggering,
Have control device, when the spiral CT imaging, this control device is controlled frame rotation and the detector feeding with respect to volume to be imaged in phase, and the direction of rotation of frame rotation and the direction of feed of detector feeding are coordinated mutually.
On width, can save expensive detector area less than the panel detector structure of middle section (width of its side regions thereby less than integral width) by side regions.
Though this will cause the relatively poor scanning of target to be detected, because the less ray that penetrates target volume only is provided.Can be from largely to its compensation by other measure but known, feasible saving to this detector area has feasibility from clinical angle.
The little detector of above-mentioned side regions width ratio detection device integral width is formed under the situation that does not have other measure, requires to reduce feed speed under the spiral duty.This is necessary for also can fully scanning target volume in the bounds of scanning survey field.
If the width of the side regions of detector for example is the detector integral width half, compare the detector that has same widths everywhere, this may cause the maximum feeding of workbench to reduce by half.Otherwise will produce the space in the volume scan of target to be detected.
The feeding of workbench and detector can be by the realizations of moving of for example sick bed relative to the feeding of volume to be imaged.Also can be by realize the feeding of workbench along frame direction of rotation moving frame.Finally, target volume has been conclusive with respect to the relative motion of frame.
Find out that although detector width is littler, the maximum feeding of workbench also can become greatly again at bounds, is not to arrange symmetrically with respect to detector width if having the side regions of littler width, but the words of relatively arranging with staggering.By the layout of off-centre, still can realize bigger table feed, and however still can be implemented in the bounds by X ray target volume also fully scanning.
Find out that also asymmetric detector arrangement only has a favourable table feed direction.That is to say, when when table feed takes place a definite direction, just producing described advantageous effects.In direction of rotation one timing of frame, if target volume should fully be covered by X ray in bounds, table feed maximal rate in the opposite direction obviously reduces again.
Also find out in addition, if change the direction of rotation of frame, can realize same big table feed in the opposite direction.In other words, suitable, favourable table feed is final relevant with the direction of rotation of frame.
Therefore computer-tomography apparatus is so controlled in suggestion, the direction of rotation of frame and table feed direction is coordinated, perhaps conversely.Can select the direction of rotation of frame according to the table feed direction, perhaps conversely, select the table feed direction according to the direction of rotation of frame.
This will cause when the table feed direction changes, and the direction of rotation of CT frame also will change.
The above-mentioned coordination of following realization namely, guarantees that for two table feed directions target volume is fully covered by X ray concerning the imaging of expectation.That is to say that the covering that produces when inharmonious with respect to frame direction of rotation and table feed direction realizes that for two table feed directions target volumes are by the better covering of X ray.
Thus, final optimization pass is for feeding asymmetric, criss-cross detector configuration.
Detector also can so constitute, and makes it respectively have a width less than the side regions of detector integral width on two broadsides.Second side regions also can so be arranged, it is staggeredly arranged with respect to the detector center.Second the relative detector of side regions center stagger can the center of relative detector with first side regions the direction that staggers opposite.Asymmetric detector like this has criss-cross structure, and wherein this cross also is asymmetric generally.
Comprise the view data that records volume to be imaged with computer-tomography apparatus according to method of the present invention.Computer-tomography apparatus comprises detector, and this detector has width less than the side regions of the integral width of detector at its at least one broadside.The side regions of this detector is arranged with respect to the center about the integral width of detector with staggering.Direction of rotation for above-mentioned detector configuration so selects frame to rotate when spiral is taken makes itself and detector coordinate mutually with respect to the direction of feed of the feeding in space to be imaged.
Under situation about not indicating in detail, on address following in to the description of single feature, its advantage and effect both at the device category also at the method category.Here disclosed single feature also can be according to being combined into the invention key element shown in being different from.
Description of drawings
Form of implementation of the present invention and will provide by the following drawings the elaboration of ultimate principle of the present invention, but need not be confined to this.
Fig. 1 provides the cross detector configuration of the side regions with asymmetric layout, and this side regions has littler detector width;
Fig. 2 is according to the demonstration of the conical ray under the parallel geometry, illustrates for the cross detector of the symmetry volume scan on the SFOV border;
Fig. 3 provides with Fig. 2 and illustrates accordingly, wherein, provides the conical ray that is the pitch value greater than shown in Fig. 2 the time herein;
Fig. 4 provides by the volume scan of asymmetric cross detector on the SFOV border, wherein the pitch value equal+ 1;
Fig. 5 provides by the volume scan of asymmetric cross detector on the SFOV border, and wherein pitch equals-1;
Fig. 6 provides and describes the scanning space for the chart of different volume feeding numerical value;
Fig. 7 provides the especially schematically diagram of computer-tomography apparatus.
The specific embodiment
Fig. 1 provides the example of a detector configuration, and it can be applied to according to computer-tomography apparatus of the present invention.
At this, detector 21 by rows has middle section 23, and detector 21 has Breadth Maximum in this zone, and finally defines the integral width 25 of detector.
In the left and right edges of detector, namely at left and right sides broadside, detector 21 has asymmetric groove.Left field 27 has the width 29 less than integral width 25.Right side area 31 also has the width less than integral width 25.Two side regions 27,31 are arranged on 21 two relative broadsides of detector.
Left field 27 and right side area 31 are arranged on the detector 21 prejudicially.Refer to the location on the bearing of trend shown in the arrow 25 passed through in integral width prejudicially here.
At this moment, along a direction displacement, right side area 31 is along another direction displacement with respect to center 37 for left field 27.
Arrow 33 provides the orientation of these row, and arrow 35 provides the channel direction of detector.
When for example can there be the width of 64 row (64 row CT) in central authorities zone 23, side regions 27,31 had half big or small width, i.e. 32 row.
Detector 21 since shown in particular arrangement can be known as the cross detector.
Fig. 2 provides be used to the chart that is set forth in the borderline volume scan of SFOV, but a cross detector at symmetry.
Given is to be positioned at the borderline conical ray of SFOV, and is according to parallel geometry specifically.Therefore conical ray is positioned at same level, and the direction of illumination of X ray then is offset 180 ° to each other.
The image geometry structure of setting up in the chart is applicable to have 64 row (English: 64row T-detector, 64 row T detectors) at middle section but have only the detector of a half width (32 row) in side regions.Every row has 0.6 millimeter width (English: slicewidth, layer width).
Pitch (Pitch) is 0.74, and symmetrical centre-focal length (Rf) is that 595 millimeters and symmetrical centre-detector distance (Rd) are 490.6 millimeters.250 millimeters p value points out, description be the conical ray that the bounds (500 millimeters altogether) of SFOV is located.
In Fig. 2 as seen, conical ray tight ground coverage goal volume.
Because at the detector height of the borderline minimizing of detector, for the geometry situation of quoting, only guarantee that feeding numerical value is approximately to 0.75 tight volume scan here.
Fig. 3 provides with Fig. 2 and similarly illustrates.Under the similar situation of other parameter value size, the pitch value is 1 here, therefore greater than the pitch value shown in Fig. 2.
As seen conical ray (p=250 millimeter) in the bounds of SFOV no longer is tight ground coverage goal volume.When volume scan, produce significant space.
If reconstructed image may cause the borderline structure of the not correct SFOV of being described in, and image has pseudo-shadow thus.
If for example consider the axial reconstruction that abdominal part is taken, the structure that target volume is determined axial location being arranged in of FOV border can show at the layer of affiliated reconstruction, but also may in adjacent layer, show extraly, although the there does not have and the dependency of target volume on anatomical structure.Under bigger feeding, there is the scanning in space may be under significant z inhomogeneities to cause the image error of can not ignore in picture field edge.
Fig. 4 provides now at the volume scan of the asymmetric cross detector of SFOV boundary on the SFOV border, wherein the pitch value equal+ 1.
Even the pitch value also is+1 and when therefore equaling among Fig. 3 pitch as the basis, by the unsymmetry of detector, on the border, also can almost entirely scan SFOV.
Though still have very little space, these spaces are acceptable based on the picture quality that will reach, and it is significantly littler to compare space shown in Figure 3.By the pitch value is reduced a little from+1, can also make these spaces littler.
On the contrary, Fig. 5 provides by the volume scan of same asymmetric cross detector on the SFOV border, but the pitch value equals-1.
The negative sign of pitch is represented such practical situation, and when the direction of rotation of frame remained unchanged, table feed was carrying out with rightabout shown in Figure 4.Another kind method allows the pitch can be by keeping the table feed direction constant with respect to shown in Figure 4 reaching-1, but the frame direction of rotation is reverse.
As seen the advantage of detector unsymmetry is transformed into shortcoming now.Compare among Fig. 4 and can scan whole SFOV under abundance covers, shown in Fig. 5, only the change of pitch symbol causes significantly having the scanning in space now.Bigger shown in this void ratio Fig. 3.
Therefore, only have one for the preferred orientations of table feed when detector is asymmetric, this preferred orientations depends on the direction of rotation of frame and causes the maximum of possible pitch numerical value is taken full advantage of.
Therefore, when the spiral CT imaging, on purpose coordinate mutually the rotation of frame and detector.
Coordination to frame direction of rotation and table feed direction when the spiral CT imaging also can be described according to the helix of the relative target volume motion of expression detector.This helix can be by describing along the helix direction of feed of spiral axis and the direction of rotation of helix.
Such side regions on the direction that is arranged in the helix feeding prejudicially of detector is positioned at the front in the helix direction of rotation simultaneously; Perhaps opposite when considering, detector prejudicially with the helix direction of feed on the contrary with respect to such side regions of detector center displacement, then be positioned at the back in the helix direction of rotation.
Fig. 6 provides chart, under the situation based on the cross detector of the symmetry of Fig. 2 and image shown in Figure 3, size (English: gap at edge of FOV in the borderline scanning of SFOV space, the space on FOV border) is correlated with maximum feeding numerical value (English: maximum pitch, maximum pitch) separately.The y axle on right side provides middle section (the T detector with respect to the cross detector, the T detector) pitch, the y axle in left side provides the pitch of the side regions (z-truncated T detector, the T detector that z shortens) with respect to the cross detector.Because zone, detector side have relative middle section half height (here: 32 the row to 64 the row), there is coefficient 2 in the scale between the y in right side and left side axle.
Fig. 7 provides the schematic diagram of computer-tomography apparatus 1.
It comprises the frame 2 of the rotating part 4 with standing part 3 and system for winding axle 5.In described inventive embodiment, rotating part 4 has x-ray system, and it is included in x-ray source 6 and the X-ray detector 7 that is opposite from one another in the rotating part 4.This X-ray detector 7 can have for example asymmetric cross panel detector structure shown in Fig. 1.
When computer-tomography apparatus 1 operation, 7 direction is emitted X ray 8 from x-ray source 6 to X-ray detector, and X ray 8 penetrates object to be measured and by the form collection of X-ray detector 7 with measurement data or measuring-signal.
In addition, computer-tomography apparatus 1 has the sick bed 9 for fixing patient 15 to be detected.This sick bed 9 comprises bed foundation 10, has arranged above it in fact settling the patient support plate 11 of patient's 15 designs.
This patient support plate 11 can so be regulated on the direction of system's axle 5 with respect to bed foundation 10, and the shooting (for example helical scanning) for patient 15 X ray projection makes patient support plate 11 and patient 15 can enter the opening portion 12 of frame 2 jointly.
The Computer Processing of the two-dimensional x-ray projection of taking with x-ray system or rebuild tomographic image, 3-D view or three-dimensional data group based on the measurement data of two-dimensional x-ray projection or measuring-signal and can realize that described tomographic image or 3-D view can be depicted in the display device 14 by the image computer 13 of computer-tomography apparatus 1.
The record of control computer 16 control survey data.Especially, it controls computer-tomography apparatus 1, make the direction of rotation of rotating part 4 of frame 2 and sick bed 9 direction of feed such as above-mentioned in coordinate mutually.
Claims (10)
1. be used for the computer-tomography apparatus (11) of the view data of record volume to be imaged (15), have:
Frame (2,3,4),
X ray emitter (6),
Detector (7,21), this detector (7,21) has side regions (27) at its at least one broadside, the width of this side regions (29) is less than the integral width (25) of detector (7,21), wherein side regions (27) is arranged with respect to center (37) about the integral width (29) of detector (7,21) with staggering
Has control device (16), when the spiral CT imaging, this control device (16) is controlled frame rotation and the detector feeding with respect to volume to be imaged (15) in phase, thereby the direction of rotation of frame rotation and the direction of feed of detector feeding are coordinated mutually.
2. according to the computer-tomography apparatus (11) of claim 1, wherein, detector (7,21) has second side regions (31) on relative broadside, and it has the width less than the integral width (25) of detector (7,21).
3. according to the computer-tomography apparatus (11) of claim 2, wherein, second side regions (31) arranged with respect to center (37) about integral width (25) with staggering.
4. each described computer-tomography apparatus (11) in requiring according to aforesaid right, wherein, so design this computer-tomography apparatus (11), that is, the translation of the sick bed (9) that is positioned at by volume to be imaged (15) realizes the detector feeding with respect to volume to be imaged (15).
5. each described computer-tomography apparatus (11) in requiring according to aforesaid right, wherein, so design this computer-tomography apparatus (11), that is, by realize the detector feeding with respect to volume to be imaged (15) along rotating shaft (5) moving frame (2,3,4) of frame (2,3,4).
6. the corresponding method of view data of a record volume to be imaged (15) in computer-tomography apparatus (1),
Wherein, this computer-tomography apparatus (1) comprises detector (7,21), this detector (7,21) has side regions (27) at its at least one broadside, the width of this side regions (29) is less than the integral width (25) of detector (7,21), wherein side regions (27) is arranged with respect to center (37) about the integral width (29) of detector (7,21) with staggering
Wherein, so select the direction of rotation of frame rotation, itself and the direction of feed with respect to the detector feeding of volume to be imaged (15) are coordinated.
7. according to the method for claim 6, wherein, detector (7,21) has second side regions (31) on relative broadside, and it has the width less than the integral width (25) of detector (7,21).
8. according to the method for claim 7, wherein, second side regions (31) arranged with respect to center (37) about integral width (25) with staggering.
9. according to each described method in the claim 6 to 8, wherein, the translation of the sick bed (9) that is positioned at by volume to be imaged (15) realizes the detector feeding with respect to volume to be imaged (15).
10. according to each described method in the claim 6 to 9, wherein, by realize the detector feeding with respect to volume to be imaged (15) along rotating shaft (5) moving frame (2,3,4) of frame (2,3,4).
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| DE201210202499 DE102012202499A1 (en) | 2012-02-17 | 2012-02-17 | Computer tomograph for recording image data of volume to be imaged, has control device to control gantry rotation during spiral computer tomograph imaging, and controls detector feed relative to volume to be imaged |
| DE102012202499.9 | 2012-02-17 |
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| Publication Number | Publication Date |
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| CN103251423A true CN103251423A (en) | 2013-08-21 |
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| CN2013100492092A Pending CN103251423A (en) | 2012-02-17 | 2013-02-07 | Computed tomography device and method for recording image data of a volume to be imaged |
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| DE (1) | DE102012202499A1 (en) |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| DE102012217888A1 (en) | 2012-10-01 | 2014-04-03 | Siemens Aktiengesellschaft | Tomographic imaging with asymmetric detection |
Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1346980A (en) * | 2000-09-26 | 2002-05-01 | 株式会社岛津制作所 | CT device |
| CN1945630A (en) * | 2005-10-07 | 2007-04-11 | Ge医疗***环球技术有限公司 | Image reconstructing method and x-ray ct apparatus |
| CN101683271A (en) * | 2008-09-28 | 2010-03-31 | 清华大学 | X-ray CT equipment, image reconstructing method and X-ray imaging method |
| US20120014502A1 (en) * | 2010-07-15 | 2012-01-19 | Bruno Kristiaan Bernard De Man | Asymmetric de-populated detector for computed tomography and method of making same |
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2012
- 2012-02-17 DE DE201210202499 patent/DE102012202499A1/en not_active Withdrawn
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- 2013-02-07 CN CN2013100492092A patent/CN103251423A/en active Pending
Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1346980A (en) * | 2000-09-26 | 2002-05-01 | 株式会社岛津制作所 | CT device |
| CN1945630A (en) * | 2005-10-07 | 2007-04-11 | Ge医疗***环球技术有限公司 | Image reconstructing method and x-ray ct apparatus |
| CN101683271A (en) * | 2008-09-28 | 2010-03-31 | 清华大学 | X-ray CT equipment, image reconstructing method and X-ray imaging method |
| US20120014502A1 (en) * | 2010-07-15 | 2012-01-19 | Bruno Kristiaan Bernard De Man | Asymmetric de-populated detector for computed tomography and method of making same |
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| DE102012202499A1 (en) | 2013-08-22 |
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Application publication date: 20130821 |