CN102697516B - Method for establishing fault contrastographic image display and computer fault contrastographic system - Google Patents
Method for establishing fault contrastographic image display and computer fault contrastographic system Download PDFInfo
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computerised tomographs
- 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 for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/027—Devices 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 for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/40—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis
- A61B6/4007—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis characterised by using a plurality of source units
- A61B6/4014—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis characterised by using a plurality of source units arranged in multiple source-detector units
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/42—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4208—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
- A61B6/4233—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector using matrix detectors
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/42—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4291—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis the detector being combined with a grid or grating
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5205—Devices using data or image processing specially adapted for radiation diagnosis involving processing of raw data to produce diagnostic data
Abstract
The present invention relates to a method for establishing fault contrastographic image display and a computer fault contrastographic system, and the method is realized through the computer fault contrastographic system (1) provided with at least two radiator-detector systems (2,3;4,5). The method has the following steps, utilizing at least one first radiator-detector system (2,3) with a first modulation transmitting function (MTF 1); utilizing at least one second radiator-detector (4,5) to scan patients (P) with the first modulation transmitting function (MTF 1) and a second modulation transmitting function (MTF 2) different from the first modulation transmitting function (MTF 1); generating at least one fault contrastographic image data group (Bges) with at least direct or indirect results (B(MTF 1),B(MTF 2)) obtained by the different modulation transmitting functions; and outputting or storing the at least one fault contrastographic image data group (Bges).
Description
Technical field
The present invention relates to a kind of utilization at least two irradiator-detector systems to set up method and the computer-tomographic system of computed tomography images display, wherein utilize at least one first and second irradiator-detector system to scan patient simultaneously, produce according to the indirect or direct result of at least twice sweep and store or export the display of at least one computed tomography images.
Background technology
Such CT system is generally known in the concept of Multi-source ct system.Equally, be known according to the method for the data reconstruction tomographic image data group of this Multi-source ct system.
In this CT system and method, user must determine eclectically between definition and noise up to now.At this, the boundary of the possible selection between definition and noise is determined by measuring system, this measuring system is given in advance optional or predetermined focus size, detector grid and pixel size.Usually definition and corresponding noise is regulated by restitution nucleus in this boundary.
For high-contrast, in current prior art, start the strict coupling in the image rebuilding method of iteration between noise and definition at least in part.For the low contrast at noise threshold place and typical case occurs in medical science thus the situation of identifiable design low contrast, alternative manner up to now does not improve.
Summary of the invention
Therefore, the technical problem to be solved in the present invention is, find a kind of utilization at least two irradiator-detector systems to set up method and the computer-tomographic system of computed tomography images display, wherein also mainly can improve the recognizability of detailed structure when low contrast is taken.
Inventor has realized that, the measurement undertaken by two or more measuring systems with different measuring resolution can be combined, and wherein different Measurement Resolution produces different modulation transfer function (MTF)s (=Modulations-Transfer-Funktion=MTF) or contrast transfer function.Obtain following advantage thus, namely the corresponding strength of a measuring system compensates the weak place of another measuring system at least in part.So in the image reconstruction of rear arrangement, complementary information can be bonded to each other, thus generation has good low contrast detection probability and high-resolution total view data simultaneously.
Preferably, the method in conjunction with data for projection or the local oscillation frequency division of view data and weighted blend, iterative approximation subsequently or can be fade-in fade-out simply
data for projection or view data are implemented.
When using two-tube CT scanner, the probability providing combination to have two measuring systems of different physical characteristics and realization scan the probability of (being mostly patient's) object in fact simultaneously.At this, for different focus size, detector grid or the pixel size of corresponding measuring system.At this, different pixel sizes is also advised to the detector using structure identical, wherein implement a kind of measurement without any covering and another kind is partly covered by preposition detector element, be i.e. the measurement of so-called UHR comb.In addition, the different detector kinetics about noise, linear and twilight sunset or different detection principles can also be used, detector that is that such as count or integration.
Namely, the detector system that uses of structure, makes it have the different measuring system MTF of in the scope of local oscillation frequency two like this.This point especially can realize respectively by different Measurement Resolution.
Such as realizing in the measuring system of high total MTF with little position resolution, algorithm MTF can compensate little position definition, and this causes adding noise.Following probability is provided: this frequency is represented by algorithm MTF when not having too high in this additional measurements with higher measuring system MTF.But this is along with the following defect of measuring technique: produce quantum loss by demarcation strip (Septen), higher electronic device noise and the less tube power deposit under less focal status.Just have advantage thus, the dose distribution of application is to two measuring systems.Total MTF of CT system can be written as the product of algorithm MTF and measuring system MTF at this.Algorithm MTF by CT convolution kernel and during CT back projection the Fourier transformation of interpolation determine.Measuring system MTF comprises the effective width of the fuzzy of the scanning in the hole by detector channels and x-ray focus.Such as can see publication A.Oppelt, Imaging Systems forMedical Diagnostics in order to define this concept more accurately, Publicis Erlangen, the 2005,423rd page.
Describe corresponding to these, inventor advises that a kind of computer-tomographic system by having at least two irradiator-detector systems sets up the method for computed tomography images display, and it has following method step:
-utilize at least one first irradiator-detector system with the first modulation transfer function (MTF), and
-utilize at least one second irradiator-detector system with second modulation transfer function (MTF) different from the first modulation transfer function (MTF) scan patients simultaneously,
-produce at least one tomographic image data group by the indirect of at least twice sweep carried out with different modulation transfer function (MTF)s or direct result,
-export or store this at least one tomographic image data group.
According to the first embodiment, above-described method can be constructed like this, make to scan to carry out with the first modulation transfer function (MTF) the detector adopting and there is multiple detector element, wherein use each detector element with its complete radiosensitive measuring surface for collection ray, and scan to carry out with at least one second modulation transfer function (MTF) the detector adopting at least one to have multiple detector element, wherein use each detector element with radiosensitive measuring surface that part covers for collection ray.
Alternatively, in this second embodiment, also can implement like this according to method of the present invention, make to scan to carry out with the first modulation transfer function (MTF) the detector adopting and there is multiple detector element, described multiple detector element have for gather ray, the first size of radiosensitive measuring surface, and adopt at least one to have the detector of multiple detector element to carry out with at least one second modulation transfer function (MTF) scanning, described multiple detector element have for gather ray, other size of radiosensitive measuring surface.
According to preceding method preferred embodiment, in order to produce the method step that at least one tomographic image data group can be implemented as follows:
-produce projection data set by the measurement data of the first modulation transfer function (MTF),
-produce the second projection data set by the measurement data of the second modulation transfer function (MTF),
-projection data set is divided into the part projection data set of at least two different local oscillation frequencies,
-mix divided part projection data set weightedly, specific to local oscillation frequency, the component wherein drawn by the measurement data of modulation transfer function (MTF) higher when higher local oscillation frequency obtains higher weight, and the component drawn by the measurement data of modulation transfer function (MTF) lower when lower local oscillation frequency obtains higher weight.Decompose projection data set with namely depending on local oscillation frequency in this embodiment, mix local oscillation frequency component weightedly subsequently.
The another kind of scheme of this method relates to the decomposition depending on local oscillation frequency, and merges the view data of rebuilding subsequently weightedly above.At this, in order to produce the method step that at least one tomographic image data group is implemented as follows:
-rebuild the first tomographic image data group by the projection data set of the first modulation transfer function (MTF),
-rebuild the second image data set by the projection data set of the second modulation transfer function (MTF),
-image data set is divided into the part image data group of at least two different local oscillation frequencies,
-mix divided part projection data set weightedly, specific to local oscillation frequency, the component wherein drawn by the measurement data of modulation transfer function (MTF) higher when higher local oscillation frequency obtains higher weight, and the component drawn by the measurement data of modulation transfer function (MTF) lower when lower local oscillation frequency obtains higher weight.
According to the again different scheme according to method of the present invention, advising implementing iterative approximation to produce at least one tomographic image data group, wherein input picture being similar to final CT image step by step when employing all measurement data provided by iterative approximation.Particularly advantageously the input picture only drawn by the measurement data of the detector with higher modulation transfer function (MTF) can be used as " priori " information (English " prior knowledge ") at this.
In the scope of the image rebuilding method of iteration, the convergence of so-called regularization (regularisierung) one side method of assuring.It is represented for the key mechanism that may be reduced picture noise by iterative approximation on the other hand.Two objects are all realized by smooth correction image in each iterative cycles.At this, preferably use so-called " priori " information, to distinguish pure noise from real picture structure about the contrast edge determined with high-resolution (namely corresponding input image data group).Such as when identifying high-resolution contrast edge along this in esse edge is smoothing in the picture, and can not lose image detail.
Finally according to the simple especially embodiment of calculating, also the projection data set of all detector systems with different modulation transfer function (MTF)s can be superposed to a projection data set to produce at least one tomographic image data group, and rebuild at least one final tomographic image data group thus.
As the replacement of superposition projection data set, in order to produce at least one tomographic image data group, can also distinguish reconstructed image data group by the projection data set of the detector system with different modulating transfer function, and this image data set projection data set by different modulating transfer function drawn is superposed at least one tomographic image data group.
Except according to method of the present invention, inventor also advises a kind of computer-tomographic system, in this computer-tomographic system, in frame, arrange at least two irradiator-detector systems with different measuring resolution, for while scanography object, particularly patient.
At this particularly advantageously, previously described computer-tomographic system has the computer system with the memorizer for computer program, and stores the computer program of the method step operationally performed according to method of the present invention in this memorizer.
Accompanying drawing explanation
By accompanying drawing, the invention will be further described below, and the feature in order to understand necessity of the present invention is wherein only shown.Use following Reference numeral: 1: double source CT system; 2: the first X-ray tubes; 3: the first detectors; 3.1: scatter-grid; 3.2: detector element; 4: the second X-ray tubes; 5: the second detectors; 5.1: scatter-grid; 5.2: detector element; 6: frame housing; 7: contrast agent applicator; 8: patient table; 9: system axle; 10: computer system; B
ges: final CT image; B
korr: correcting image; B (MTF (x)): the image data set drawn by reconstruction R (x); B (x): an xth image data set in iteration; FP: forward projection (forward projection); The weighting factor of g (x): P (MTF (x)); IR (1+2): iterative approximation; K (1): edge detection; MTF (x): modulation transfer function (MTF); N: iterations; P: patient; P
ges: by the projection data set of part projection data set weighted array; P ' (x): the projection data set of synthesis; P (MTF (1)): the projection data set with the first modulation transfer function (MTF); P (MTF (2)): the projection data set with the second modulation transfer function (MTF); Prg
1-Prg
n: computer program; P (1+2): by the new projection data set of projection data set P (MTF (x)) weighted array; R (1+2): reconstruction procedures; R (x): rebuild by projection data set P (MTF (x)); Reg: regularization term; SBa: the first beam; SBb: the second beam; TB (H) x: the part image data group with the high local oscillation frequency coming from B (MTF (x)); TB (L) x: the part image data group with the low local oscillation frequency coming from B (MTF (x)); TP (H) x: the part projection data set with the high local oscillation frequency of MTF (x); TP (L) x: the part projection data set with the low local oscillation frequency of MTF (x); Δ: difference image; γ: X-ray.
In accompanying drawing:
Fig. 1 shows double source CT system;
Fig. 2 shows the cross section of the frame of double source CT system;
Fig. 3 shows cross section and the details of the detector element of the detector of Fig. 2;
Fig. 4 shows and carries out specific to the local oscillation frequency ground schematic diagram according to method of the present invention that divides, mix weightedly subsequently and rebuild to the data for projection of different MTF;
The tomographic image data that Fig. 5 shows the data for projection by different MTF forms carries out dividing and the schematic diagram according to method of the present invention mixed weightedly subsequently specific to local oscillation frequency;
Fig. 6 shows the schematic diagram according to method of the present invention of the simple scheme with iterative approximation;
Fig. 7 shows the schematic diagram according to method of the present invention of iterative approximation;
Fig. 8 shows the schematic diagram according to of the present invention method of superposition by the view data of the reconstructs projection data of different MFT.
Detailed description of the invention
Fig. 1 shows the exemplary diagram of the double source CT system CT system of two irradiator-detector systems (=have) 1, this double source CT system has frame housing 6, in this frame be not shown specifically, wherein fix irradiator-detector system that two angles are arranged with staggering.Irradiator-detector system is made up of by the second X-ray tube 4 with the detector 5 that the second X-ray tube is oppositely arranged the first X-ray tube 2 and the detector 3 be oppositely arranged with the first X-ray tube, another aspect on the one hand.Two the irradiator-measurement field of detector system scan setting in central circular openings.Patient P can be moved through this measurement field by patient table 8 along system axle 9.Not only can perform helical scanning in principle also can execution sequence scanning at this point.In order to the imaging improving blood vessel or other structure also can by contrast agent applicator 7 to patient's injection of contrast medium.
According to the present invention, two detectors 3 and 5 have scattered-out beam and cover, it only transmits the ray directly arrived from the direction of each irradiator positioned opposite on each detector element, the part that wherein detector element is covered by ray is different to different detectors, and realizes different Measurement Resolution and MTF thus.Such as also can adopt additional UHR comb (UHR=ultra highresolution=ultrahigh resolution) in detector, this UHR combs the covering that (UHR-Kamm) produces the high percentage ratio (such as > 50%) of detector element.
Control to CT system 1 and the analysis to the scanning of patient P are implemented by the computer system 10 be attached thereto, and wherein this computer system 10 has at least one and stored therein computer program Prg
1-Prg
nmemorizer.Also comprise or store the program of like this structure according to the present invention wherein, make it perform different embodiments according to method of the present invention when system cloud gray model.
Figure 2 illustrates the cross section with this frame of two irradiator-detector systems of Fig. 1.First irradiator-detector system is made up of the X-ray tube 2 sending beam SBa there, and this beam SBa aims at detector 3 positioned opposite.Detector 3 has scatter-grid 3.1, and this scatter-grid only causes the little covering of detector and has the Measurement Resolution less than the second detector thus but high quantum efficiency.Stagger 90 ° and show the second irradiator-detector system, it has the X-ray tube 4 that can send beam SBb, and this beam SBb aims at detector 5 positioned opposite.Detector 5 has UHR and the scatter-grid 5.1 of combination, and have the high covering of detector element, this causes high Measurement Resolution while less quantum efficiency.There are two irradiator-detector systems thus, it can simultaneously scan patients P and have different MTF at this.
Again illustrate the details of the Cover treatment of the detector element of two detectors 3 and 5 in figure 3.On the left side illustrates the cross section of the detector 3 in the scope of detector element 3.2 with the scatter-grid 3.1 arranged thereon.The ray arrived from above is capped hardly at this and can arrives detector plane completely.The relevant details of the detector 5 in the scope of detector element 5.2 with the scatter-grid 5.1 arranged can be found out thereon on adjacent the right.Substantially the less part of ray γ only can be registrated to detector element 5.2 by the larger covering corresponding to detector element 5.2, but is wherein reached much trickleer than detector 3 resolution of detector 5 by the less open plane of detector element 5.2 simultaneously.
In the simplest situations, the measurement data obtained from two systems can be combined by each image produced of being fade-in fade-out simply.Be fade-in fade-out described in can being selected according to structure size and contrast by frequency multiband method.
In the method for reconstructing of iteration, the high-resolution information obtained from detector can be used as so-called prior information for the data obtained from two detectors.Can optionally distinguish between noise and real contrast information thus.Therefore when identical radiation dose with compared with unique measuring system this point cause the low contrast improved to detect probability.
Diverse ways schematic diagram based on above-described measuring method has been shown in Fig. 4 to Fig. 8 below.
Fig. 4 shows the first image and produces scheme, wherein utilizes the detector system with different MTF (1) or MTF (2) to produce two projection data set P (MTF (1)) and P (MTF (2)) simultaneously.Then different local oscillation frequency H (=high) and L (=low) is divided into dividually to each projection data set, thus generation four projection data set: the P (H) 1, the P (L) 1 that obtain from P (MTF (1)) and the P (H) 2, the P (L) 2 that obtain from P (MTF (2)).These four projection data set present different weights ground are combined as again unique projection data set P
ges, wherein outstanding introducing has the data for projection of high MTF fine structure information.Then by total projection data set P
gescarry out final CT image B
gesreconstruction R (1+2), then show or store this CT image B
ges.
Figure 5 illustrates similar method scheme, but wherein first implement dividually respectively to rebuild R (1) and R (2) to two projection data set P (MTF (1)) and P (MTF (2)) at this, utilize this reconstruction R (1) and R (2) to calculate image data set B (MTF (1)) based on different MTF and B (MTF (2)).Then these image data set are divided into respectively part image data group TB (H) 1, the TB (L) 1 and TB (H) 2, TB (L) 2 with high and low local oscillation frequency.Then by part image data group different weights to combine be a new CT image B
ges, wherein disproportionately the high-resolution information drawn by the image data set of better MTF is introduced in weighting again.
Figure 6 illustrates the simple scheme of iterative reconstruction approach.First CT image B (MTF (1)) is calculated as input picture according to projection data set P (MTF (1)) by simply rebuilding R (1) at this.Then by using view data B (MTF (2)) to carry out iterative modification iR (1+2) to this input picture, until produce optimum total image B
ges, this view data B (MTF (2)) comes from from the reconstruction R (2) having the second projection data set P (MTF (2)) of drawing in the measurement data of the detector of the 2nd MTF and carry out.
Figure 7 illustrates better alternative manner.First the projection data set with different resolution P (MTF (1)) and P (MTF (2)) is combined as new projection data set P (1+2) weightedly with weight g (1) and g (2) at this, and first the path illustrated by a dotted line reconstructs a CT image data set B (0) by reconstruction procedures R (1+2) and utilizes B (0) to initialize B (n).Then the projection data set P ' (0) that forward projection draws synthesis is carried out to a CT image data set, this projection data set P ' (0) in comparison step Δ compared with original weighted projection data group P (1+2).Now difference data is flowed to the computation cycles of iteration.The difference data obtained like this (is such as passed through the Convolution sums back projection of weighting in step R (1+2), as it is by publication Stierstorfer et al. " Weighted FBP-a simple approximate 3D FBP algorithm for multislice spiralCT with good dose usage for arbitrary pitch ", disclosed in Phys.Med.Biol.49 (2004) (2209-2218)) rebuild, thus produce correcting image B
korr.Correcting image by this usually weighting is added with image B (n) determined above.Therefrom deduct equally usually weighting, the result of regularization.They with produce improve image B (n+1).
Concurrently, projection data set P (MTF (1)) according to having high-resolution MTF (1) implements image reconstruction R (1), subsequently at the image B (1) rebuild so upper enforcement edge detection K (1).The result of edge detection as " priori " information conveyance to (known in its function itself) regularization term.Regularization step object from image, deducts pure noise component(s) in each iterative step.Especially, in image B (n), the picture noise of minimizing compared with output image B (0) is obtained by nonlinear regularization.In the scope of regularization for this reason must from the image information of reality burbling noise.Play an important role in this " priori " information.The example of nonlinear regularization is comprise edge level and smooth, and wherein noise component(s) comprises level and smooth image B (n) of border land by being formed and do not have the difference of level and smooth image B (n) to estimate in iterative step n.At this, actual edge should be known according to " priori " information, as far as possible accurately because otherwise can lose image information.The additional information drawn at the edge detection K (1) that this comes from high-resolution image B (1) according to the present invention achieves improvement.
Image B (n+1) according to this improvement recalculates the projection data set P ' (n+1) of synthesis at this by forward projection, and it can start next iteration again in comparison step Δ compared with the new projection data set P (1+2) of the original weighting determined.At this, the circular symbol with Reference numeral n should represent the number of times of the iteration of execution.
If determined in comparison step Δ, at the projection data set P (1+2) of weighting and reach value given in advance by improving the difference determined between the projection data set P ' (n+1) of the synthesis that image B (n+1) the draws frequency n lower than value given in advance or iteration, then using the image B (n+1) of improvement that finally determines as final total image B
gesexport.Can successfully prevent from losing trickle picture structure during iteration in the method for reconstructing of known iteration itself thus by projection data set P (MTF (1)) based on " priori " information obtained now according to the present invention.
Finally, Fig. 8 shows the simple especially scheme according to method of the present invention, and it is similar to Fig. 5.At this, implement dividually to rebuild R (1) and R (2) according to two the projection data set P (MTF (1)) of measurement data and P (MTF (2)) that come from the detector with different MTF respectively and calculate image data set B (MTF (1)) and B (MTF (2)) its thus based on the data of different MTF.By with superpose two image data set weightedly with weight g (1) and g (2) and produce the total image B improved
ges.
Be understandable that, feature of the present invention not only according to the combination provided respectively, and according to other combination or be also applicable when arranging separately, and not to depart from the scope of the present invention.
Claims (9)
1. one kind by having at least two irradiator-detector systems (2,3; 4,5) computer-tomographic system (1) sets up the method for computed tomography images display, has following method step:
1.1. utilize at least one first irradiator-detector system (2,3) with the first modulation transfer function (MTF) (MTF (1)), and
1.2. at least one second irradiator-detector system (4 is utilized, 5) with second modulation transfer function (MTF) (MTF (2)) different from the first modulation transfer function (MTF) (MTF (1)) scan patients (P) simultaneously
1.3. by the indirect of at least twice sweep carried out with different modulation transfer function (MTF)s or direct result (B (MTF (1)), B (MTF (2)), P (MTF (1)), P (MTF (2))) produce at least one tomographic image data group (B
ges),
1.4. export or store described at least one tomographic image data group (B
ges),
It is characterized in that, in order to produce at least one tomographic image data group (B
ges) method step that is implemented as follows:
1.5. projection data set (P (MTF (1))) is produced by the measurement data of the first modulation transfer function (MTF) (MTF (1)),
1.6. the second projection data set (P (MTF (2))) is produced by the measurement data of the second modulation transfer function (MTF) (MTF (2)),
1.7. by projection data set (P (MTF (1)), P (MTF (2))) be divided into the part projection data set (TP (H) 1 of at least two different local oscillation frequencies, TP (L) 1, TP (H) 2, TP (L) 2)
1.8. divided part projection data set (TP (H) 1 is mixed specific to local oscillation frequency weightedly, TP (L) 1, TP (H) 2, TP (L) 2), the component wherein drawn by the measurement data of higher modulation transfer function (MTF) (MTF (1)) when higher local oscillation frequency obtains higher weight, and the component drawn by the measurement data of lower modulation transfer function (MTF) (MTF (2)) when lower local oscillation frequency obtains higher weight.
2. one kind by having at least two irradiator-detector systems (2,3; 4,5) computer-tomographic system (1) sets up the method for computed tomography images display, has following method step:
2.1. utilize at least one first irradiator-detector system (2,3) with the first modulation transfer function (MTF) (MTF (1)), and
2.2. at least one second irradiator-detector system (4 is utilized, 5) with second modulation transfer function (MTF) (MTF (2)) different from the first modulation transfer function (MTF) (MTF (1)) scan patients (P) simultaneously
2.3. by the indirect of at least twice sweep carried out with different modulation transfer function (MTF)s or direct result (B (MTF (1)), B (MTF (2)), P (MTF (1)), P (MTF (2))) produce at least one tomographic image data group (B
ges),
2.4. export or store described at least one tomographic image data group (B
ges),
It is characterized in that, in order to produce at least one tomographic image data group (B
ges) method step that is implemented as follows:
2.5. the first tomographic image data group (B (MTF (1))) is rebuild by the projection data set (P (MTF (1))) of the first modulation transfer function (MTF) (MTF (1))
2.6. the second image data set (B (MTF (2))) is rebuild by the projection data set (P (MTF (2))) of the second modulation transfer function (MTF) (MTF (2)),
2.7. by image data set (B (MTF (1)), B (MTF (2))) be divided into the part image data group (TB (H) 1 of at least two different local oscillation frequencies, TB (L) 1, TB (H) 2, TB (L) 2)
2.8. divided part image data group (TB (H) 1 is mixed specific to local oscillation frequency weightedly, TB (L) 1, TB (H) 2, TB (L) 2), the component wherein drawn by the measurement data of higher modulation transfer function (MTF) (MTF (1)) when higher local oscillation frequency obtains higher weight, and the component drawn by the measurement data of lower modulation transfer function (MTF) (MTF (2)) when lower local oscillation frequency obtains higher weight.
3. one kind by having at least two irradiator-detector systems (2,3; 4,5) computer-tomographic system (1) sets up the method for computed tomography images display, has following method step:
3.1. utilize at least one first irradiator-detector system (2,3) with the first modulation transfer function (MTF) (MTF (1)), and
3.2. at least one second irradiator-detector system (4 is utilized, 5) with second modulation transfer function (MTF) (MTF (2)) different from the first modulation transfer function (MTF) (MTF (1)) scan patients (P) simultaneously
3.3. by the indirect of at least twice sweep carried out with different modulation transfer function (MTF)s or direct result (B (MTF (1)), B (MTF (2)), P (MTF (1)), P (MTF (2))) produce at least one tomographic image data group (B
ges),
3.4. export or store described at least one tomographic image data group (B
ges),
It is characterized in that,
3.5. by projection data set (P (MTF (1)), P (MTF (2))) be divided into the part projection data set (TP (H) 1 of at least two different local oscillation frequencies, TP (L) 1, TP (H) 2, TP (L) 2)
3.6. divided part projection data set (TP (H) 1 is mixed specific to local oscillation frequency weightedly, TP (L) 1, TP (H) 2, TP (L) 2), the component wherein drawn by the measurement data of higher modulation transfer function (MTF) (MTF (1)) when higher local oscillation frequency obtains higher weight, and the component drawn by the measurement data of lower modulation transfer function (MTF) (MTF (2)) when lower local oscillation frequency obtains higher weight
3.7. in order to produce at least one tomographic image data group (B
ges) implement iterative approximation (iR (1+2)), wherein input picture (B (MTF (1))) is similar to final CT image (B when employing all measurement data provided step by step by iterative approximation
ges).
4. according to the method described in the claims 3, it is characterized in that, the input picture only drawn by the measurement data of the detector with higher modulation transfer function (MTF) (MTF (1)) is used for the image rebuilding method (iR (1+2)) of iteration as additional " priori " information.
5. the method according to any one of the claims 1-4, is characterized in that,
5.1. scan to carry out with the first modulation transfer function (MTF) (MTF (1)) detector (3) that employing has multiple detector element (3.2), wherein use each detector element (3.2) with its complete radiosensitive measuring surface for collection ray, and
5.2. scanning to carry out with at least one second modulation transfer function (MTF) (MTF (2)) detector (5) adopting at least one to have multiple detector element (5.2), wherein using each detector element (5.2) with radiosensitive measuring surface that part covers for collection ray.
6. the method according to any one of the claims 1-4, is characterized in that,
6.1. scan to carry out with the first modulation transfer function (MTF) (MTF (1)) detector (3) that employing has multiple detector element (3.2), wherein use the detector element (3.2) with the first size of radiosensitive measuring surface for collection ray, and
6.2. scanning to carry out with at least one second modulation transfer function (MTF) (MTF (2)) detector (5) adopting at least one to have multiple detector element (5.2), wherein using the detector element (5.2) with other size of radiosensitive measuring surface for collection ray.
7. one kind for set up computed tomography images display there are at least two irradiator-detector systems (2,3; 4,5) computer-tomographic system (1), has:
7.1. for utilizing at least one first irradiator-detector system (2,3) with the parts of the first modulation transfer function (MTF) (MTF (1)), and
7.2. for utilizing at least one second irradiator-detector system (4,5) with the parts of scan patients (P) while of the second modulation transfer function (MTF) (MTF (2)) different from the first modulation transfer function (MTF) (MTF (1))
7.3. for by the indirect of at least twice sweep carried out with different modulation transfer function (MTF)s or direct result (B (MTF (1)), B (MTF (2)), P (MTF (1)), P (MTF (2))) produce at least one tomographic image data group (B
ges) parts,
7.4. for exporting or store described at least one tomographic image data group (B
ges) parts,
It is characterized in that, in order to produce at least one tomographic image data group (B
ges), have:
7.5. for being produced the parts of projection data set (P (MTF (1))) by the measurement data of the first modulation transfer function (MTF) (MTF (1)),
7.6. for being produced the parts of the second projection data set (P (MTF (2))) by the measurement data of the second modulation transfer function (MTF) (MTF (2)),
7.7. for by projection data set (P (MTF (1)), P (MTF (2))) be divided into the part projection data set (TP (H) 1 of at least two different local oscillation frequencies, TP (L) 1, TP (H) 2, TP (L) 2) parts
7.8. for mixing divided part projection data set (TP (H) 1 specific to local oscillation frequency weightedly, TP (L) 1, TP (H) 2, TP (L) 2) parts, the component wherein drawn by the measurement data of higher modulation transfer function (MTF) (MTF (1)) when higher local oscillation frequency obtains higher weight, and the component drawn by the measurement data of lower modulation transfer function (MTF) (MTF (2)) when lower local oscillation frequency obtains higher weight.
8. one kind by having at least two irradiator-detector systems (2,3; 4,5) computer-tomographic system (1) sets up the device of computed tomography images display, has:
8.1. for utilizing at least one first irradiator-detector system (2,3) with the parts of the first modulation transfer function (MTF) (MTF (1)), and
8.2. for utilizing at least one second irradiator-detector system (4,5) with the parts of scan patients (P) while of the second modulation transfer function (MTF) (MTF (2)) different from the first modulation transfer function (MTF) (MTF (1))
8.3. for by the indirect of at least twice sweep carried out with different modulation transfer function (MTF)s or direct result (B (MTF (1)), B (MTF (2)), P (MTF (1)), P (MTF (2))) produce at least one tomographic image data group (B
ges) parts,
8.4. for exporting or store described at least one tomographic image data group (B
ges) parts,
It is characterized in that, in order to produce at least one tomographic image data group (B
ges), have:
8.5. for being rebuild the parts of the first tomographic image data group (B (MTF (1))) by the projection data set (P (MTF (1))) of the first modulation transfer function (MTF) (MTF (1))
8.6. for being rebuild the parts of the second image data set (B (MTF (2))) by the projection data set (P (MTF (2))) of the second modulation transfer function (MTF) (MTF (2))
8.7. for by image data set (B (MTF (1)), B (MTF (2))) be divided into the part image data group (TB (H) 1 of at least two different local oscillation frequencies, TB (L) 1, TB (H) 2, TB (L) 2) parts
8.8. for mixing divided part image data group (TB (H) 1 specific to local oscillation frequency weightedly, TB (L) 1, TB (H) 2, TB (L) 2) parts, the component wherein drawn by the measurement data of higher modulation transfer function (MTF) (MTF (1)) when higher local oscillation frequency obtains higher weight, and the component drawn by the measurement data of lower modulation transfer function (MTF) (MTF (2)) when lower local oscillation frequency obtains higher weight.
9. one kind by having at least two irradiator-detector systems (2,3; 4,5) computer-tomographic system (1) sets up the device of computed tomography images display, has:
9.1. for utilizing at least one first irradiator-detector system (2,3) with the parts of the first modulation transfer function (MTF) (MTF (1)), and
9.2. for utilizing at least one second irradiator-detector system (4,5) with the parts of scan patients (P) while of the second modulation transfer function (MTF) (MTF (2)) different from the first modulation transfer function (MTF) (MTF (1))
9.3. for by the indirect of at least twice sweep carried out with different modulation transfer function (MTF)s or direct result (B (MTF (1)), B (MTF (2)), P (MTF (1)), P (MTF (2))) produce at least one tomographic image data group (B
ges) parts,
9.4. for exporting or store described at least one tomographic image data group (B
ges) parts, it is characterized in that having
9.5. for by projection data set (P (MTF (1)), P (MTF (2))) be divided into the part projection data set (TP (H) 1 of at least two different local oscillation frequencies, TP (L) 1, TP (H) 2, TP (L) 2) parts
9.6. for mixing divided part projection data set (TP (H) 1 specific to local oscillation frequency weightedly, TP (L) 1, TP (H) 2, TP (L) 2) parts, the component wherein drawn by the measurement data of higher modulation transfer function (MTF) (MTF (1)) when higher local oscillation frequency obtains higher weight, and the component drawn by the measurement data of lower modulation transfer function (MTF) (MTF (2)) when lower local oscillation frequency obtains higher weight
9.7. in order to produce at least one tomographic image data group (B
ges) implement iterative approximation (iR (1+2)) parts, wherein input picture (B (MTF (1))) is similar to final CT image (B when employing all measurement data provided step by step by iterative approximation
ges).
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| CN102988076B (en) * | 2012-12-11 | 2015-05-13 | 苏州生物医学工程技术研究所 | CT (Computed Tomography) scanner |
| CN104287757A (en) * | 2013-07-15 | 2015-01-21 | Ge医疗系统环球技术有限公司 | Method and system for reconstructing computer X-ray tomography imaging of object image |
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| CN106510747B (en) * | 2016-12-21 | 2024-02-09 | 北京朗视仪器股份有限公司 | Double-source double-detector cone beam CT system |
| CN107374658B (en) * | 2017-07-01 | 2023-10-03 | 广东顺德中山大学卡内基梅隆大学国际联合研究院 | Shooting system and shooting method for positive side dual-energy image |
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