CN1940992A - Image-based artifact reduction in PET/CT imaging - Google Patents
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Abstract
A method for reducing image-based artifacts in combined positron emission tomography and computed tomography (PET/CT) scans. The method includes identifying pixels in a CT image having a large HU value, identifying a region surrounding the pixels, and modifying a value of each pixel within the region.
Description
The cross reference related application
The title that this application requires on June 17th, 2005 to submit to is the U.S. interim series application No.60/691 of " the pseudo-shadow based on image in the PET/CT imaging reduces ", 811 right of priority, and its full content is hereby incorporated by.
Technical field
The invention belongs to the positron emission tomography (PET) of use combination and the medical imaging field of computerized tomography (CT) form.More specifically, the method that reduces based on the pseudo-shadow of image is paid close attention in this invention in PET/CT scanning.
Background technology
In the field of positron emission tomography that makes up and computerized tomography (PET/CT), well-known is usually can meet difficulty in finding the solution the used correction for attenuation factor.Usually this is found the solution as digital operation and carries out at the computing machine that is used for PET/CT.The typical operation that is used to obtain the correction for attenuation factor (ACF) in PET/CT is as follows.
At first, (X, Y is Z) with the attenuation coefficient of representative on the X-heat input to produce the CT image I.These attenuation coefficients are derived from such measurement: wherein the X-wire harness passes health along straight line, surveys to pass completely through the X-line of health and the X-line of being surveyed is used to rebuild the CT image.The CT image is made of data matrix, and wherein these data from a key element in the matrix are a pixel, and its numerical value is relevant with the attenuation coefficient of this position.
The second, in order in PET, to use the more 511keV radiation of high energy, the CT pixel value is converted to pad value (mu map).
At last, the PET tomography carries out it along straight line to be measured, and by the subclass along this straight line mu map integration is produced ACF.
Error appears at the first step, and wherein the CT pixel value is incorrect, makes they accurately to be converted to mu map pixel value.Up to now, also unresolved as this problem of a part of PET processing.Particularly, this problem is not also solved in the step that pixel value is converted to pad value.Like this, just there are the needs that address this problem.
When to the soft-tissue imaging in the person, best execution is designed to medical X-line CT tomography.This material only comprises the lightest chemical element, mainly is hydrogen, carbon, nitrogen and oxygen.Under the situation of medical X-line tomography, the existence of cortex bone needs secondary to pass correction in the visual field, is present in the calcium mechanism of absorption different to the X-line with potassium in the bone with solution.
Sometimes the CT image is damaged by a slice metal in patient's body, for example surgical clips or reparation joint.These objects are not see through ray in many cases, and promptly nearly all X-line that shines them is all absorbed by metal.In the CT image therefore and the mistake that produces is called as metal artifacts.In order to solve the problem of metal artifacts, the medical imaging document has proposed to be used for to have static metal object, when promptly this metal object is not subjected to patient's breathing or blood flow circulating effect, creates out improved CT treatment of picture technology.These methods are to the such knowledge of very little distance based on metal mobile phase during measuring.In a kind of classic method of handling this problem, as people such as G.H.Glover, " An algorithm for the reduction ofmetal clip artifacts in CT reconstructions ", Medical Physics, 8 (6), discussed among the 799-807 (Nov/Dec1981), use interpolation method modified chi-line hole chamber to take a picture, wherein use estimated value to replace known impaired hole chamber photograph numerical value based on the hole chamber photograph numerical value of known essentially no measuring error.Recently, alternative manner has been proposed as improvement to this method.See people " Reduction ofmetal streak artifacts in x-ray computed tomography using a transmission maximum aposteriori algorithm " such as B.De Man, IEEE Transactions on Nuclear Science, the 47th volume, No. 3,977-981 (2000).
Yet, have been found that when metal moved during measuring, these methods can not finely play a role.Like this, if there is the automatic cardioverter-defibrillators of embedded type (AICD) in the patient thoracic cavity, then focus is to carry out the PET/CT research of heart.If these device designs are used for recovering the normal rhythm of the heart when potential life-threatening arrhythmia cordis takes place.Fig. 1 has illustrated this equipment.
Similar with pacemaker, AICD follows heartbeat to move together in the thoracic cavity.For the CT machine, there be the difficulty severeer than pacemaker in AICD equipment.It comprises two platinum filaments vibrations coils, and the about 3mm of diameter is enough greatly with obstruction on some response line all or nearly all X-line.One of them coil location is being adjoined the right ventricle wall, near the free wall of septum wall and left and right ventricles, its in heart PET by imaging.Rebuild when having the part of moving coil when the CT machine, metal artifacts appears in the result, and in the zone that surrounds the coil physical location high CT numerical value and the low CT numerical value with vacation.This illustrates with arrow in Fig. 2.
Have two results at least.The first, the CT image is wrong anatomic image.For example, shown in Fig. 2, coil is not presented at correct position.The second, the PET part of PET/CT image may comprise incorrect numerical value.This situation be because combination and ACF that the PET image derives from the PET emission measurement derive from defective CT image.Before PET/CT, do not notice this problem in the generation of PET, because the influence that the ACF that is obtained by the 511-keV emissive source is existed by 3-mm platinum coil hardly.
People's such as J.F.Williamson " Prospects for quantitative computed tomographyimaging in the presence of foreign metal bodies using statistical imagereconstruction ", Medical Physics 29 (10) 2404-18 (2002) have discussed another iterative reconstruction approach that is used to reduce pseudo-shadow.
People's such as A.H.R.Lonn " Evaluation of method to minimize the effect of X-raycontrast in PET/CT attenuation correction ", Proceedings of the 2003 IEEE MedicalImaging Conference, M6-146 (Portland, OR), discussed the method for the simple setting threshold that is used for PET/CT.
The U.S. Patent No. 6,721,387 of authorizing people such as Naidu on April 13rd, 2004 discloses the method that reduces metal artifacts in CT.The method of being somebody's turn to do ' 387 patent comprises step:
A. produce a preliminary image by input data for projection by the CT system acquisition;
B. in this preliminary image, discern metal object;
C. have in final artifact correction image by removal and may cause that object changes the project objects of such feature, by producing second projection in the input data for projection;
D. be extracted in the metal object projection of the identification among the step B from second data for projection that among step C, produces;
E. produce the projection of correction by the projection of removing the metal object that extracts the step D from the input data for projection; With
F. by being reconstituted in the correction projection that produces in the step e, and the metal object that will discern in step B is inserted into final image, produces final image.
Summary of the invention
The present invention is prescribed the deviation that reduces under the situation that is used for having AICD in patient's thoracic cavity among the heart PET/CT.Because invention is simple and firm, so can be applied to other can not accurately obtain ACF from the CT image situation.
Aspect of invention, have the pixel of big HU numerical value in this method regulation identification CT image, identification is surrounded the zone of these pixels and is revised the numerical value of each pixel in this zone.
In another aspect of the present invention, utilize the reallocation function of continuous and level and smooth original HU numerical value, this method regulation is revised the pixel that has big HU numerical value in the CT image.
The invention further aspect, this method is defined in this zone carries out before the described modification each pixel number, be identified in the raw value of each the bone pixel in this zone, and after the numerical value of each pixel in this zone is made amendment, the numerical value that replaces each bone pixel to revise with the raw value of each bone pixel.
Aspect inventing further, after this method is defined in the zone carried out described identification, form is carried out in the zone that surrounds this pixel expand to increase precision.
In another aspect of the invention, this method is defined in carries out the zone that surrounds this pixel being corroded after form expands to this zone.
Of the present invention further aspect, the identification of this method regulation has the pixel that approaches to surround the zone with big HU numerical value pixel in the CT image of the HU numerical value that is lower than the threshold value that defines, and the pixel that will have the HU numerical value that is lower than the threshold value that defines is adjusted to new numerical value.
Description of drawings
To the detailed description of invention, will more clearly understand inventive features above-mentioned below reading in conjunction with the accompanying drawings, wherein:
Fig. 1 is a legend that has the automatic cardioverter-defibrillators of embedded type (AICD) according to prior art in the patient thoracic cavity;
Fig. 2 be one according to prior art by the legend that is similar to the pseudo-shadow of typical metal that AICD shown in Figure 1 causes;
Fig. 3 A is illustrated according to before and after the embodiments of the invention by figure to 3D, reduces (IBAR) and has CT image before and after the line contour of indication CT pixel number using pseudo-shadow based on image; With
Fig. 4 is a process flow diagram, has shown according to embodiments of the invention to carry out the processing procedure that typically reduces (IBAR) based on image artifacts.
Embodiment
Based on the exemplary embodiments of image artifacts reduction (IBAR) method, positron emission tomography that is used to make up and computerized tomography (PET/CT) scanning.Under the CT of PET/CT scanning measured by situation about damaging such as pseudo-shadows such as the sheet metals that moves, present embodiment was useful.The situation that reduces metal artifacts separately is known as metal artifacts reduction or MAR.
Typical IBAR method in a series of CT image slices, revise pixel value I (X, Y, Z).Image value is stipulated with Huo Sifeierde (Hounsfield) unit (HU).Appropriate functional CT equipment produces image, and the numerical value of wherein specifying water is zero (0HU), and specifying the numerical value of air is about 1000HU, and the numerical value of appointment bone and metal is greater than zero (0HU).In already used PET/CT process software, use the reorganization program that image at first is reduced to 256 * 256 sizes from the array of 512 * 512 pixel sizes, wherein per four pixels are averaged for one group in 512 * 512 matrixes, and those mean values are placed in 256 * 256 matrixes on the pixel.Typical IBAR method is applied in 256 * 256 image families.Yet typical IBAR does not need specific matrix size, and can be with or without the correction of the program of recombinating as the aforementioned in use.
The many image pixels that are subjected to the metal artifacts influence are rebuild with high HU numerical value.As the set of striped, one group of this high pixel is very outstanding in Fig. 2.
Fig. 4 is a process flow diagram, has shown according to embodiments of the invention to carry out the processing procedure that typically reduces (IBAR) based on the pseudo-shadow of image.In the step 1 of typical IBAR method, identification has all pixels more than or equal to the reconstruction HU numerical value of 900HU.Though numerical value 900HU is a preferred value for the adjustable parameters of IBAR method, what it should be appreciated by those skilled in the art is also can use other numerical value and still belong in the scope of the present invention.This program caused being called as STREAK (X, Y, pattern matrix Z), the numerical value that wherein is equal to or higher than this threshold value is decided to be 1, the numerical value that is lower than it is decided to be 0.(Z) array generally includes some pixels of expression bone to STREAK for X, Y.
In step 2, then create the second pattern matrix NEAR_STREAK (X, Y, Z).By (X, Y Z) use the morphological operations that expands to create this array to STREAK.This pattern matrix identifies all pixels in 2 pixels of the striped of discerning in step 1.Though disclose 2 pixel coverages, those skilled in the art is to be appreciated that and also can uses other numerical value also still to belong in the scope of the present invention.Be associated by the integral width of this pixel coverage of following formula with the nuclear that expands:
Nuclear _ half-breadth=2x nuclear _ width+1
This can also be defined as millimetre-sized distance, and this distance is converted to pixel by conversion formula:
(pel spacing from)=(mm distance)/(mm pixel size)
Other modes that are equal to expansion within the scope of the present invention comprise, and for example level and smooth STREAK_IMAGE (X, Y, Z).It is the set that has the image volume elements of almost spherical based on structure that the nuclear that expands expands on the three-dimensional.In one embodiment of the invention, expanding acts on three dimensions, makes that the striped in the image slices produces " adjacent stripe " in contiguous section.Pixel near this striped is designated as numerical value 1; The pixel that keeps clear of this striped is designated as numerical value 0.
Then, in step 3, revise high CT image values.This program is similar to setting threshold on mathematics,, big pixel value is set at limits value that is.It can be realized by multiple mode.Typical IBAR method is used following steps.
The pixel value that is lower than threshold value 1 is not revised.IBAR method operation parameter value " threshold value 1=0HU ".Yet those skilled in the art should be able to recognize can use other numerical value and still belonging in the scope of the present invention.
Pixel value between threshold value 1 and (2x threshold value 2-threshold value 1) is used the quadratic interpolation method.Those numerical value I (X, Y Z) are replaced by numerical value:
IBAR method operation parameter value " threshold value 2=100HU ".Yet those skilled in the art should be able to recognize can use other numerical value and still belonging in the scope of the present invention.
Pixel value greater than (2x threshold value 2-threshold value 1) is set as numerical threshold 2.In an embodiment of the present invention, parameter threshold 1 and threshold value 2 are adjustable.
As the result of this reallocation technology, new pixel value and original pixel value are associated by continuous and level and smooth relational expression.Hinting that smoothly the function derivative of reallocating is the continuous function of original HU numerical value.
This step also produce array SOFT_TISSUE (X, Y, Z).In this array, all pixels that are equal to or greater than threshold value 1 at first are set as 1, and other pixels are set as 0.This array is carried out form expand, as in step 2.Though allow expansion texture that other sizes are arranged, in one embodiment of the invention, its same with in the step 2.After the expansion, it is corroded, corrosion is used and the same structure that expands with the morphological operations that corrodes.Dilation dimension and corrosion structure are adjustable parameters of the present invention.Consequent array identifies those parts of the CT image of representing soft tissue or bone density, and has got rid of the zone beyond lung tissue and the patient.Separate little and the technology of irregular area as one, expand and Flame Image Process circle that is combined in of corrosion is known.
At last, in step 5, handle image with the level and smooth CT map of revising.In this step, uneven border is smoothed in the three dimensional CT image.Utilization has 3-pixel ductility on athwartship plane, and also is that the three-dimensional medium filtering of 3-section ductility can be realized it on the direction between the plane.Variable medium filtering only is wherein a kind of possible method of the CT image that is used for smoothly revising on this space.3 * 3 * 3 sizes of the nuclear of its use also are to carry out the selected parameter of this typical case IBAR method.Usually, pixel peace interplanar distance is stipulated and in commission converted to those sizes according to millimeter.Though big or small identical when keeping nuclear size and measurement on millimeter, 3D medium filtering step calculating strength is very high, and if image have more pixel, for example 512 * 512 can be higher.Medium filtering only is used in SOFT_TISSUE, and (Z) array numerical value is 1 place for X, Y., can quicken to finish to using the 3D median filter near the soft tissue place as mentioned above by only.In other another embodiment of typical IBAR method, median filter is applied in the zone that is identified as soft tissue, then expand, but corrode as yet.In the ending of this step, in a conventional manner the CT image is used for the PET/CT processing procedure.
The contrast of the CT image before and after the typical IBAR method of application and the profile of whole metal artifacts are presented among Fig. 3.The data diagram of figure illustrates in the original image and revises the HU numerical value in the image.Below corresponding image is presented at.Image graph 3B and curve map 3A according to the modification of the embodiment of the invention have described distincter image, and the image 3C of this image and prior art and the curve map 3D of prior art compare on picture more level and smooth.
Will be understood that typical method of the present invention negative striped not being carried out threshold setting and handling under the step of this image with level and smooth CT map, has reduced metal artifacts.Yet these steps can be used for providing higher-quality image.
Typical method of the present invention further provides the recognition methods of bone pixel.In this typical method, the raw value of bone pixel is identified and is substituted after aforesaid processing.
From aforementioned description, one skilled in the art will appreciate that to provide to be used in the illustrative methods of PET/CT scanning minimizing based on the pseudo-shadow of image.
Though the present invention describes by some embodiment and though illustrated embodiment is described with a large amount of details, applicant's intention and unconfinement or by any way the scope of appended claim is restricted to such details.Additional advantage and modification are obviously for a person skilled in the art.Therefore the present invention is not limited to concrete details, representational apparatus and method and illustrative example shown and that describe at it aspect more wide in range.Therefore, under the situation of the spirit and scope that do not break away from applicant's invention upperseat concept, can from such details, break away from and come.
Claims (20)
1, a kind of in the method that computer tomography (CT) image is reduced in as the tomographic scan of a part based on the pseudo-shadow of image, described method comprises step:
(i) discern the pixel that has big Huo Sifeierde unit (HU) numerical value in the CT image;
(ii) the zone of described pixel is surrounded in identification; With
(iii) revise the value of each pixel in the described zone.
2, the method for claim 1 further comprises the reallocation function that utilizes continuous and level and smooth original HU numerical value, the step that the described pixel that has big HU numerical value in the CT image is made amendment.
3, the method for claim 2 wherein uses described method to produce the correction for attenuation factor in PET/CT.
4, the method for claim 3, in revising described zone before the described step of each pixel value, the step that further comprises the raw value of each bone pixel in the described zone of identification, after the described step of each pixel value in revising described zone, further comprise step with each numerical value of revising of alternative each the bone pixel of raw value of each bone pixel.
5, the method for claim 1 after the described step of identified region, further is included as the described zone that surrounds described pixel and carries out the form expansion to increase the step of precision.
6, the method for claim 5 after the described step of described zone being carried out the form expansion, further comprises the step that the described zone that surrounds described pixel is corroded.
7, the process of claim 1 wherein and use described method to produce the correction for attenuation factor one of them of PET and CT.
8, the method for claim 7 further comprises the step of discerning the raw value of each bone pixel in the described zone and the step that substitutes each numerical value of revising of each bone pixel with the raw value of each bone pixel.
9, the method for claim 7 further comprises the reallocation function that utilizes continuous and level and smooth original HU numerical value, revises the step that has the described pixel of big HU numerical value in the CT image.
10, the method for claim 9 further comprises step:
(i) be identified in pixel in the CT image, this pixel has the HU numerical value lower than defined threshold value, and the contiguous described zone that surrounds the described pixel with big HU numerical value; With
The described pixel that (ii) will have the HU numerical value lower than defined threshold value is adjusted to a new numerical value.
11, the method for claim 10 further comprises the step of utilizing the level and smooth image that obtains of spatial filter from the pixel of described adjustment.
12, the method for claim 11, wherein said spatial filter are three-dimensional median filters.
13, the method for claim 1 comprises that further form is carried out in the described zone that surrounds described pixel to expand to increase the step of precision.
14, the method for claim 13 further comprises the step that the described zone that surrounds described pixel is corroded.
15, the process of claim 1 wherein that described pseudo-shadow comprises a pseudo-shadow based on metal.
16, the method for claim 12, wherein said three-dimensional filter are included in 3 pixel ductilities on the athwartship plane.
17, the method for claim 12 further is included in the zone that is identified as soft tissue and uses described three-dimensional filter.
18, the method for claim 1 further comprises the step that pixel value is converted to decay numerical value.
19, the method for claim 18, wherein radioactivity level is about 511keV.
20, the process of claim 1 wherein that described pseudo-shadow is the result of one of them at least of artificial or electronic heart pacemaker and the automatic cardioverter-defibrillators of embedded type.
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