CN100443052C - X-ray CT appts. - Google Patents
X-ray CT appts. Download PDFInfo
- Publication number
- CN100443052C CN100443052C CNB2004100881547A CN200410088154A CN100443052C CN 100443052 C CN100443052 C CN 100443052C CN B2004100881547 A CNB2004100881547 A CN B2004100881547A CN 200410088154 A CN200410088154 A CN 200410088154A CN 100443052 C CN100443052 C CN 100443052C
- Authority
- CN
- China
- Prior art keywords
- ray
- mentioned
- data
- hemichannel
- energy
- Prior art date
- Legal status (The legal status 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 status listed.)
- Expired - Fee Related
Links
Images
Abstract
The present invention relates to the subject that tube voltage is not switched and an X-ray detector is used for shooting two tomographic images of different X-ray energies. In order to solve the subject, the present invention makes the energies (150, 160) of the X-rays respectively entering the front-half channel and the back-half channel of a multichannel X-ray detector (106) mutually different, and respective specular point data is generated according to the X-ray detection data of the front-half channel and the X-ray detection data of the back-half channel, which are obtained by the rotation of 360 DEG. The first and the second tomographic images are respectively constructed on the basis of the combination of the X-ray detection data and the specular point data of the front-half channel, and the combination of the X-ray detection data and the specular point data of the back-half channel.
Description
Technical field
(Computed Tomography: computed tomography) device, particularly shooting makes the X ray CT device of 2 kinds of different faultage images of X ray energy (energy) to the present invention relates to X ray CT.
Background technology
In X ray CT device, can take 2 kinds of faultage images that make the X ray energy different.The a kind of of 2 kinds of faultage images is with for example faultage image of the soft tissue (fat etc.) of the shooting of the low-energy X-ray about 80kV, and another kind is with for example faultage image of sclerous tissues's (skeleton etc.) of the shooting of the high-energy X ray about 140kV.
X ray energy differential is to switch to (for example with reference to the patent documentation 1) that 2 stages realize by the tube voltage with X-ray tube.Perhaps, by using (for example with reference to the patent documentation 2) that 2 kinds of X-ray detectors arranged in series, that EAC is different are realized on the direction that see through at X ray.
[patent documentation 1] spy opens 2004-65975 communique (7-9 page or leaf, Fig. 2-3)
[patent documentation 2] spy opens 2004-181017 communique (4-6 page or leaf, Fig. 1-5)
When switching by tube voltage when making the X ray energy differential, owing to must in 1 scanning, alternately switch tube voltage, so just need at a high speed and high-precision control device.When carrying out the tube voltage switching by each scanning,, be subjected to according to amount so just increased owing to need carry out 2 scanning.When use made the different 2 kinds of X-ray detectors of EAC, X-ray detector just needed 2 systems.
Summary of the invention
Therefore, problem of the present invention is exactly to realize not switching tube voltage and using a kind of X-ray detector to take the X ray CT device of 2 kinds of different faultage images of X ray energy.
In order to solve above-mentioned problem, X ray CT device of the present invention, clipping under the mutual opposed state of object to be detected with the isocenter point is that the center makes x-ray source and the rotation of multichannel X-ray detector, collect X ray and detect data, and reconstruct the faultage image of object to be detected based on this, it is characterized in that, possess: differential unit, point of irradiation with the X ray by isocenter point is the boundary, makes different mutually with the energy of the incident X ray of back hemichannel to the preceding hemichannel of above-mentioned multichannel X-ray detector respectively; Data generating unit detects data according to the X ray detection data of the preceding hemichannel that is obtained by 360 ° of rotations and the X ray of back hemichannel, generates mirror point data separately; And reconstructing the unit, the X ray that detects the combination of data and its mirror point data and back hemichannel based on the X ray of preceding hemichannel detects the combination of data and its mirror point data, reconstructs the 1st kind of faultage image and the 2nd kind of faultage image respectively.
Above-mentioned multichannel X-ray detector has a plurality of channel column, the differential pattern of energy before above-mentioned differential unit alternately reverses by each adjacent channel column in hemichannel and the back hemichannel, this is fine for taking 2 kinds of different searching image this point of X ray energy simultaneously.
Above-mentionedly reconstruct half sweep test that the X ray that detects half sweep test of combination of data and its mirror point data and back hemichannel based on the X ray of preceding hemichannel respectively in the unit detects the combination of data and its mirror point data, reconstruct the 1st kind of faultage image and the 2nd kind of faultage image, this is for fine according to minimal data obtain the faultage image this point.
Above-mentioned differential unit has the X ray filter plate, and this is fine for the differential this point of carrying out the X ray energy rightly.
Above-mentioned X ray filter plate is arranged on the X ray emitting side of above-mentioned x-ray source, and this is fine by differential X ray this point for emission.
Above-mentioned X ray filter plate is arranged on the X ray light incident side of above-mentioned multichannel X-ray detector, and this is fine by differential X ray this point for incident.
Above-mentioned X ray filter plate is separately positioned on the X ray emitting side of above-mentioned x-ray source and the X ray light incident side of above-mentioned multichannel X-ray detector, and this is fine for implementing the differential this point of X ray energy.
Above-mentioned X ray filter plate turns to 80kV and 140kV with the energy difference of X ray, and this is fine for the faultage image this point of faultage image that obtains soft tissue respectively and sclerous tissues.
According to the present invention, because X ray CT device possesses: the point of irradiation with the X ray by isocenter point is the boundary, makes respectively the mutual different differential hands section of energy to the preceding hemichannel and the incident X ray of back hemichannel of multichannel X-ray detector; Detect data according to the X ray detection data of the preceding hemichannel that obtains by 360 ° of rotations and the X ray of back hemichannel, generate the data generating means of mirror point data separately; And the combination and the X ray detection data of back hemichannel and the combination of its mirror point data that detect data and its mirror point data based on the X ray of preceding hemichannel, reconstruct the means that reconstruct of the 1st kind of faultage image and the 2nd kind of faultage image respectively, so just tube voltage can not switched and use the X-ray detector of 1 system to take 2 kinds of different faultage images of X ray energy.
Description of drawings
Fig. 1 is the figure of structure of the X ray CT device of an expression example being used for implementing optimal way of the present invention.
Fig. 2 is the figure of the structure of expression x-ray bombardment checkout gear.
Fig. 3 is the figure of the X ray energy of expression irradiation filter plate by characteristic.
Fig. 4 is the figure of the X ray energy of expression incident filter plate by characteristic.
Fig. 5 is the spatial figure of expression display channel.
Fig. 6 is the right figure of mirror point in the expression display channel space.
Fig. 7 is the block diagram of the function of expression operator's console.
Fig. 8 is the figure of the configuration of high-energy portion in the expression incident filter plate and low-yield portion.
Fig. 9 is the figure of the configuration of high-energy portion in the expression irradiation filter plate and low-yield portion.
The specific embodiment
Below, the optimal way that is used for carrying out an invention with reference to description of drawings.In addition, the present invention is not limited to the optimal way that is used for carrying out an invention.Fig. 1 has represented the structure of X ray CT device.This device is an example that is used for implementing optimal way of the present invention.By the structure of this device, represented to be used for implementing an example of the of the present invention optimal way relevant with X ray CT device.
As shown in the drawing, this device has gantry (gantry) 100, workbench 200 and operator's console (operator console) 300.The object to be detected 10 that gantry 100 usefulness x-ray bombardment checkout gears 102 scannings (scan) are moved into by workbench 200 is also collected X ray and is detected data (data).
Gantry 100 condition according to the rules scans, and workbench 200 carries out the location of object to be detected 10 in the photographing space, so that the position of scanning regulation.The location is undertaken by the height of adjusting top board 202 and the distance that moves horizontally of its bracket (cradle) 204 by built-in position adjusting mechanism.
The altitude mixture control of top board 202 is that the center is swung (swing) and realized by making pillar 206 with the installation portion with base (base) 208.By the swing of pillar 206, can make top board 202 at above-below direction and horizontal direction top offset.Carriage 204 carries out the displacement of horizontal direction on top board 202.According to the condition of scanning, in that being tilted, gantry 100 scans under (tilt) states.The inclination of gantry 100 is undertaken by built-in leaning device.
300 pairs of gantrys 100 of operator's console and workbench 200 provide scan plan and scan based on this, detect data from gantry 100 input X ray simultaneously, and carry out image based on this and reconstruct.That is, operator's console 300 has and reconstructs the function of device as the function of main frame (host) and according to what X ray detected the data restructuring image as image with what scan plan was supplied with gantry 100 and workbench 200.
Corresponding to these two functions, operator's console 300 has 2 display (display) 302,304.A display 302 is display that main frame is used, and another display 304 is that image reconstructs the display that device is used.
Fig. 2 has schematically shown the structure of x-ray bombardment checkout gear 102.As shown in the drawing, x-ray bombardment checkout gear 102 detects the X ray 140 that radiates from the focus of X-ray tube 104 by X-ray detector 106.X ray 140 is located to be shaped at not shown collimator (collimator), becomes fan beam (fan beam) X ray.X-ray detector 106 is to become the mode bending of the circular arc corresponding with fan beam X ray 140.
X-ray detector 106 is detectors of multichannel (channel).The angle of representing each passage of looking from x-ray focus with γ.The datum line of channel angle γ is the straight line that the central beam of fan beam X ray 140 promptly links x-ray focus and isocenter point ISO.
X-ray bombardment checkout gear 102 is the center rotation with isocenter point (isocenter) ISO.Represent the anglec of rotation with β.The datum line of anglec of rotation β is x-ray bombardment checkout gear 102 when becoming plumbness as shown in the figure, the straight line that links x-ray focus and isocenter point ISO.
Be provided with irradiation filter plate (filter) 150 in the front of X-ray tube 104.Shine photographing space from the X ray of X-ray tube 104 emissions by irradiation filter plate 150.This filter plate is also referred to as bow tie filter plate (bowtie filter) because of the similarity event of its shape.
It is the boundary that irradiation filter plate 150 constitutes with the central beam, different by characteristic with left side 154 energy at right-hand part 152.Fig. 3 has represented the example of the energy of right-hand part 152 and left side 154 by characteristic.As shown in the drawing, right-hand part 152 has the energy in high relatively territory by characteristic, and the energy that left side 154 has low relatively territory passes through characteristic.Below, right-hand part 152 is called high-energy portion, left side 154 is called low-yield portion.Having the filter plate of such energy by characteristic is made of the material with suitable X ray EAC respectively.Irradiation filter plate 150 is the differential unitary examples among the present invention.
Be provided with incident filter plate 160 in the front of X-ray detector 106.X ray by photographing space comes incides by filter plate 160 on the sensitive surface of X-ray detector 106.The point of irradiation that incident filter plate 160 constitutes with central beam is the boundary, and is different by characteristic with left side 164 energy at right-hand part 162.Fig. 4 has represented the example of the energy of right-hand part 162 and left side 164 by characteristic.As shown in the drawing, right-hand part 162 has the energy in high relatively territory by characteristic, and the energy that left side 164 has low relatively territory passes through characteristic.Below, right-hand part 162 is called high-energy portion, left side 164 is called low-yield portion.Having the filter plate of such energy by characteristic is made of the material with suitable X ray EAC respectively.Incident filter plate 160 is the differential unitary examples among the present invention.
By such irradiation filter plate 150 and incident filter plate 160, just the incidence point with central beam at X-ray detector 106 is the right-hand part and the left side on boundary, respectively the different X ray of projectile energy.That is, at the high-octane relatively X ray of right-hand part incident, at the low-energy relatively X ray of left side incident.The energy of high-energy X ray for example is 140kV, and the energy of low-energy X-ray for example is 80kV.In addition, irradiation filter plate 150 and incident filter plate 160 also can only use one.
When each passage to X-ray detector 106 numbered in order from right to left side, right-hand part just became preceding hemichannel, and the left side just becomes the back hemichannel.Below right-hand part is called preceding hemichannel, with the left side be called the back hemichannel.
Because x-ray bombardment checkout gear 102 becomes such structure, so display channel data (view-channel data) that get according to the scanning of 360 ° of the anglecs of rotation, as shown in Figure 5, with regard to the line that becomes with the spatial γ of display channel=0 is the boundary, different with left-half (back hemichannel) X ray energy at right half part (preceding hemichannel).Right half part is a high-energy, and left-half is low-yield.
In addition, in the display channel space, two coordinates (beta, gamma) and (β+π+2 γ ,-γ) be the relation of mirror point (mirror point).So-called mirror point is to be used to obtain identical but the coordinate that direction is opposite in the path of X-ray beam of its position data.Data in such coordinate are called as the mirror point data.The mirror point data to having identical value.
Fig. 6 has represented the distribution of the mirror point in the display channel space.In the figure, represent that with same pictorial pattern mirror point is mutually the same.As shown in the drawing, the mirror point data of the data of preceding hemichannel side are present in later half channel side, and the mirror point data of the data of later half channel side are present in preceding hemichannel side.
If utilize such relation, then can be with the later half channel side of mirror point data filling of the data of preceding hemichannel side, make the spatial data of display channel all become the data of high-energy X ray, in addition, can also make the spatial data of display channel all become the data of low-energy X-ray with hemichannel side before the mirror point data filling of the data of later half channel side.
Therefore, since for high-energy and low-yield can obtain to one group of group display channel data completely, so reconstruct by utilizing each data set to carry out image, just can obtain the faultage image of high-energy X ray and the faultage image of low-energy X-ray.Therefore, just can not switch tube voltage and use the X-ray detector of 1 system to take 2 kinds of different faultage images of X ray energy.
In addition, as long as reconstruct because there are the display channel data of half sweep test just can carry out image, detect data and the mirror point data are filled the scope shown in the tetragon ABCD so also can become respectively, replace with high-energy and low-yieldly fill up all display channel spaces with X ray.
Fig. 7 has represented to carry out the functional-block diagram of aforesaid mirror point data generation and the reconstituted operator's console 300 of image.As shown in the drawing, operator's console 300 generates its mirror point data in mirror point data generating unit 310 according to the data of preceding hemichannel, generates its mirror point data according to the data of back hemichannel.
And, reconstructing portion 312 by image, the combination based on data He its mirror point data of preceding hemichannel reconstructs the high-energy faultage image.This faultage image is the faultage image of the sclerous tissues of skeleton etc. for example.
In addition, reconstruct portion 314,, reconstruct low-yield faultage image based on the data of back hemichannel and the combination of its mirror point data by image.This faultage image is the faultage image of the soft tissue of fat etc. for example.
For high-energy faultage image and low-yield faultage image, as required, obtain and or poor image.Mirror point data generating unit 310 is examples of the data generating unit among the present invention.Image reconstructs portion the 312, the 314th, reconstructs a unitary example among the present invention.
When X-ray detector 106 had 2 row passages, the structure of incident filter plate 160 as shown in Figure 8.That is, partly be high-energy portion 162 before being configured in of high-energy portion 162 and low-yield 164 become in 1 row, later half is low-yield 164, and in another row, becoming later half on the contrary is high-energy portion 162, and preceding partly is low-yield 164.In addition, for irradiation filter plate 150, as shown in Figure 9, make high-energy portion 152 and low-yield 's 154 configuration consistent with the configuration in incident filter plate 160.When X-ray detector 106 be 3 row more than multiple row the time also be same main points.
By as above-mentioned, just can easily take search (scout) image with 2 kinds of X ray energy of height.Promptly, though by for example the direction of illumination of X ray being fixed as on the vertical direction, on the axon direction, carry object to be detected 10 to take searching image, but, because by the high-energy portion in irradiation filter plate 150 and incident filter plate 160 and the above-mentioned configuration of low-yield portion, alternately take the same part of object to be detected 10, so also just can obtain 2 kinds of different searching images of X ray energy simultaneously with high-energy X ray and low-energy X-ray.For these searching images, as required, obtain and or poor image.
Claims (8)
1. X ray CT device, clipping under the mutual opposed state of object to be detected with the isocenter point is that the center makes x-ray source and the rotation of multichannel X-ray detector, collect X ray and detect data, and, it is characterized in that based on this faultage image that reconstructs object to be detected:
Possess: differential unit is the boundary with the point of irradiation of the X ray by isocenter point, makes different mutually with the energy of the incident X ray of back hemichannel to the preceding hemichannel of above-mentioned multichannel X-ray detector respectively;
Data generating unit detects data according to the X ray detection data of the preceding hemichannel that is got by 360 ° of rotations and the X ray of back hemichannel, generates mirror point data separately; And
Reconstruct the unit, the X ray that detects the combination of data and its mirror point data and back hemichannel based on the X ray of preceding hemichannel detects the combination of data and its mirror point data, reconstructs the 1st kind of faultage image and the 2nd kind of faultage image respectively.
2. X ray CT device as claimed in claim 1 is characterized in that:
Above-mentioned multichannel X-ray detector has a plurality of channel column,
The differential pattern of energy before above-mentioned differential unit alternately reverses by each adjacent channel column in hemichannel and the back hemichannel.
3. X ray CT device as claimed in claim 1 or 2 is characterized in that:
Above-mentioned differential unit has the X ray filter plate.
4. X ray CT device as claimed in claim 3 is characterized in that:
Above-mentioned X ray filter plate is arranged on the X ray emitting side of above-mentioned x-ray source.
5. X ray CT device as claimed in claim 3 is characterized in that:
Above-mentioned X ray filter plate is arranged on the X ray light incident side of above-mentioned multichannel X-ray detector.
6. X ray CT device as claimed in claim 3 is characterized in that:
Above-mentioned X ray filter plate is separately positioned on the X ray emitting side of above-mentioned x-ray source and the X ray light incident side of above-mentioned multichannel X-ray detector.
7. X ray CT device as claimed in claim 3 is characterized in that:
Above-mentioned X ray filter plate turns to 80kV and 140kV with the energy difference of X ray.
8. as any one the described X ray CT device in the claim 4～6, it is characterized in that:
Above-mentioned X ray filter plate turns to 80kV and 140kV with the energy difference of X ray.
Priority Applications (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CNB2004100881547A CN100443052C (en) | 2004-10-14 | 2004-10-14 | X-ray CT appts. |
| JP2005123309A JP4464311B2 (en) | 2004-10-14 | 2005-04-21 | X-ray CT system |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CNB2004100881547A CN100443052C (en) | 2004-10-14 | 2004-10-14 | X-ray CT appts. |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN1759810A CN1759810A (en) | 2006-04-19 |
| CN100443052C true CN100443052C (en) | 2008-12-17 |
Family
ID=36379313
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CNB2004100881547A Expired - Fee Related CN100443052C (en) | 2004-10-14 | 2004-10-14 | X-ray CT appts. |
Country Status (2)
| Country | Link |
|---|---|
| JP (1) | JP4464311B2 (en) |
| CN (1) | CN100443052C (en) |
Families Citing this family (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP2049021B1 (en) * | 2006-07-31 | 2016-11-16 | Koninklijke Philips N.V. | Automatic iso-centering for rotational angiography |
| JP5389324B2 (en) * | 2006-12-18 | 2014-01-15 | 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 | X-ray tomography equipment |
| GB0700470D0 (en) | 2007-01-10 | 2007-02-21 | Cambridge Entpr Ltd | Apparatus and method for acquiring sectional images |
| CN101772324B (en) * | 2007-08-06 | 2012-01-11 | 株式会社日立医药 | X-ray ct device |
| JP5220374B2 (en) * | 2007-09-27 | 2013-06-26 | 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 | X-ray CT system |
| US8260023B2 (en) * | 2008-11-26 | 2012-09-04 | General Electric Company | Forward projection for the generation of computed tomography images at arbitrary spectra |
| KR101362723B1 (en) * | 2012-05-15 | 2014-02-13 | (주)포인트닉스 | Dental x-ray imaging system having dual ct mode |
| JP5677543B2 (en) * | 2013-10-03 | 2015-02-25 | キヤノン株式会社 | X-ray CT imaging apparatus, X-ray CT imaging method, X-ray sensor, and reconstruction apparatus |
| JP6165826B2 (en) * | 2014-11-28 | 2017-07-19 | 株式会社モリタ製作所 | X-ray imaging apparatus, image processing apparatus, and X-ray imaging method |
| US9962131B2 (en) | 2014-11-28 | 2018-05-08 | J. Morita Manufacturing Corporation | X-ray photography apparatus, image processing device, and X-ray photography method |
| CN105759319A (en) * | 2015-03-06 | 2016-07-13 | 公安部第研究所 | Improved double-energy CT imaging method and apparatus |
| CN107797155A (en) * | 2016-08-31 | 2018-03-13 | 合肥美亚光电技术股份有限公司 | Compton backscattering detection means |
| CN109632844B (en) * | 2019-01-09 | 2021-08-17 | 中国人民解放军战略支援部队信息工程大学 | Dual-energy CT imaging system and method based on linear scanning track |
Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4780897A (en) * | 1986-05-06 | 1988-10-25 | General Electric Company | Dual energy imaging with kinestatic charge detector |
| CN1041237C (en) * | 1993-04-05 | 1998-12-16 | 卡迪亚航海者公司 | X-ray detector for a low dosage scanning beam digital X-ray imaging system |
-
2004
- 2004-10-14 CN CNB2004100881547A patent/CN100443052C/en not_active Expired - Fee Related
-
2005
- 2005-04-21 JP JP2005123309A patent/JP4464311B2/en not_active Expired - Fee Related
Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4780897A (en) * | 1986-05-06 | 1988-10-25 | General Electric Company | Dual energy imaging with kinestatic charge detector |
| CN1041237C (en) * | 1993-04-05 | 1998-12-16 | 卡迪亚航海者公司 | X-ray detector for a low dosage scanning beam digital X-ray imaging system |
Non-Patent Citations (2)
| Title |
|---|
| 一种螺旋CT的非线性插值算法. 占志刚，冯焕清.生物医学工程研究，第23卷第2期. 2004 |
| 一种螺旋CT的非线性插值算法. 占志刚，冯焕清.生物医学工程研究，第23卷第2期. 2004 * |
Also Published As
| Publication number | Publication date |
|---|---|
| JP4464311B2 (en) | 2010-05-19 |
| JP2006110324A (en) | 2006-04-27 |
| CN1759810A (en) | 2006-04-19 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN100443052C (en) | X-ray CT appts. | |
| JP3909048B2 (en) | X-ray CT apparatus and X-ray tube | |
| EP1216662B1 (en) | Radiation tomographic imaging apparatus and method | |
| US6760399B2 (en) | CT scanner for time-coherent large coverage | |
| CN100441146C (en) | Computerized tomographic imaging system | |
| CN101902965B (en) | Stereo tube attenuation filter | |
| US7502445B2 (en) | Radiographing plan assisting method and X-ray CT system | |
| US5982846A (en) | Methods and apparatus for dose reduction in a computed tomograph | |
| EP0981998B1 (en) | Methods and apparatus for automatic image noise reduction | |
| US20050226371A1 (en) | Stationary Tomographic Mammography System | |
| US6178223B1 (en) | Image reconstruction method and apparatus | |
| CN105828719B (en) | X-ray imaging device | |
| JP2000279404A (en) | Method for forming image of object and imaging system | |
| KR20070057055A (en) | X-ray ct apparatus and method of controlling the same | |
| US6560308B1 (en) | Method and system for approximating missing data in cone beam x-ray CT reconstruction | |
| KR101825107B1 (en) | X-ray Computerized Tomography System Having Scanner Function | |
| CN101111192A (en) | Tomography equipment comprising a variable reproduction geometry | |
| CN102271587A (en) | Method and apparatus to filter x-ray beams generated using a CT apparatus with displaced geometry | |
| US20140247917A1 (en) | X-ray ct scanning and dual-source ct system | |
| US6341152B1 (en) | X-ray computerized tomography apparatus | |
| CN103284745A (en) | X-ray CT system and control program | |
| CN102711616B (en) | Radiation tomography device | |
| EP2506772B1 (en) | Method and system for high resolution nutated slice reconstruction using quarter detector offset | |
| US7058156B2 (en) | Imaging method for a multi-slice spiral CT scan with 3D reconstruction, and a computed tomography unit for carrying out this method | |
| CN102440798A (en) | Method for scanning a heart with a dual-source ct device and embodiment of a dual-source ct device |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| CF01 | Termination of patent right due to non-payment of annual fee | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20081217 Termination date: 20211014 |