CN113450428B - Pseudo-color mapping method of SPECT reconstruction data based on adjustable bi-directional quantity parameters - Google Patents
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Abstract
The invention relates to medical images, in particular to a pseudo-color mapping method of SPECT reconstruction data based on adjustable bidirectional parameters, which provides a pseudo-color mapping method containing the adjustable bidirectional parameters based on a DICOM file of SPECT, creates a multi-level mapping relation, can control the display range of pseudo colors and regulate multi-segment details of dose display, can more clearly and accurately display a dose region and a data range of interest in a SPECT image, can obviously enhance the focus region and the dose distribution layering sense of SPECT-CT after being fused with a CT image, accurately display the particle space and the radiation dose distribution information of focus positions, and provides a reliable basis for judging clinical curative effects; the technical scheme provided by the invention can effectively overcome the defects that the display range of the pseudo-color image cannot be effectively controlled and the multi-level distribution display of the dose cannot be regulated and controlled in the prior art.
Description
Technical Field
The invention relates to medical images, in particular to a pseudo-color mapping method of SPECT reconstruction data based on adjustable bi-directional quantity parameters.
Background
SPECT is an emission imaging that uses implanted radioactive particles accumulated on a diseased tissue as a gamma ray source, and a rotatable detector placed outside the body collects gamma photon information after passing through the human body, and performs tomographic reconstruction based on the information to obtain the dose distribution of gamma rays on the corresponding tissue. SPECT images are mainly used to determine lesion properties and extent, and belong to functional imaging. Because photon data is less, the resolution ratio of the SPECT image is lower, and the SPECT image and the CT image are required to be fused, so that accurate analysis and diagnosis and treatment of information such as lesion positions, functions and the like are realized.
Usually, the reconstructed SPECT image and CT image are both given in the form of gray-scale images, and if image fusion is directly performed, SPECT information is submerged, so that the SPECT image needs to be fused after being processed by using an image enhancement technology. However, since SPECT image quality is significantly degraded, enhancement processing by gray-scale transformation or sharpening is difficult. The pseudo-color enhancement technology utilizes the characteristic that the resolution of human eyes to different brightness and tone can reach more than hundred times of gray resolution, changes gray images into color images, improves the resolution of the images, and is particularly obvious for images with low resolution.
The pseudo-color display technology is widely applied to medical images, for example, the morphological information of the maxillary tumor in the oral cavity image is obviously enhanced, and hidden rice-size focuses in the spiral CT image of the thyroid gland are clearly displayed. The pseudo-color enhancement technology is a technology for converting different gray levels of a gray image into different colors according to a linear or nonlinear mapping function to obtain a color image, and is essentially a technology for constructing a color mapping function, mainly comprising a density segmentation method, a spatial domain gray-color conversion synthesis method and frequency domain pseudo-color enhancement.
Currently, most pseudo color methods are displayed correspondingly through a mapping relationship between gray values and RGB color spaces, so that gray maps display different color intervals. However, the effects of the images produced by the different color mapping relationships are not the same. When the medical SPECT image is subjected to pseudo-color processing, the problems of monotonous display color, unobvious display range and the like can occur, and the accurate judgment of the size and the distribution area of the radiation dose in the SPECT image is influenced.
Disclosure of Invention
(one) solving the technical problems
Aiming at the defects existing in the prior art, the invention provides a pseudo-color mapping method of SPECT reconstruction data based on adjustable bi-directional quantity parameters, which can effectively overcome the defects existing in the prior art that the display range of a pseudo-color image can not be effectively controlled and the multi-stage distribution display of the dose can not be regulated and controlled.
(II) technical scheme
In order to achieve the above purpose, the invention is realized by the following technical scheme:
a pseudo color mapping method of SPECT reconstruction data based on adjustable bi-directional parameters, comprising the steps of:
s1, constructing a reconstruction data pseudo-color mapping function of distance information and color mapping information between adjacent layers;
s2, reading reconstruction data of a corresponding imaging part, and layering the reconstruction data by taking an area where a larger value in a data matrix is located as a center and gradually reducing and diffusing the area to the periphery according to the value;
s3, calibrating the region of interest in the data layering, and regulating and controlling the distance information between adjacent layering;
s4, regulating and controlling the color mapping information by setting layering colors and a color transition mode among layering.
Preferably, constructing a reconstruction data pseudo color mapping function of the distance information and the color mapping information between adjacent layers in S1 includes:
the pseudo-color mapping function of the reconstructed data is S P ＝P(S O ,L,C)；
Wherein the vector S P SPECT images representing pseudo-colors; vector S O Representing the original reconstructed data, typically twoDimension; vector L represents the number of layers of the reconstructed data hierarchy and distance information between adjacent hierarchies, note l= (n, s) 1 ,s 2 ,…,s n-1 ) Integer variable n represents the number of layering layers, integer variable s 1 ,s 2 ,…,s n-1 Representing the distance between adjacent layers, which may or may not be the same; vector C represents the color mapping information used by the data to be reconstructed, note c= (C) 0 ,c 1 ,c 2 ,…,c n-1 ,c n Inter), color vector c 0 ,c 1 ,c 2 ,…,c n-1 ,c n The character variable inter represents the color transition mode between adjacent layers.
Preferably, the reading of the reconstructed data of the corresponding imaging region in S2 includes:
and reading a data element part in the DICOM file, independently storing the reconstructed data in a dat file, and carrying out feature analysis on a numerical range, numerical distribution and a lesion part.
Preferably, in S2, the area where the larger value in the data matrix is located is taken as the center, the area is gradually reduced and spread to the periphery according to the value, and the layering of the reconstructed data includes:
taking the row coordinates and the column coordinates of the two-dimensional data matrix as x values and y values respectively, taking the numerical value at the corresponding coordinates as z values, establishing a three-dimensional Cartesian coordinate system, and selecting a threshold point z i Let z=z i Layering the reconstruction data as a threshold plane;
wherein the threshold point z i It is desirable to combine the activity, number and clinical experience of the physician with the implant particles.
Preferably, when the reconstruction data is layered, the non-region of interest having a smaller value beyond the lesion area is taken as a layer.
Preferably, in S3, the adjusting and controlling the distance information between adjacent layers by calibrating the region of interest in the data layer includes:
s31, giving the number n of layering layers;
s32, obtaining a maximum value Zmax and a minimum value Zmin in the reconstructed data;
s33, set S 1 ,s 2 ,…,s n-1 ；
S34, giving a data layering mode: zmin, Z 1 ＝Zmin+s 1 ，Z 2 ＝Z 1 +s 2 ，…， Z n-1 ＝Z n-2 +s n-1 ，Zmax。
Preferably, the region of interest is calibrated by segmenting the SPECT image or the corresponding CT image.
Preferably, in S4, the adjusting and controlling the color mapping information by setting a layered color and a color transition manner between layers includes:
s41, given color vector c 0 ,c 1 ,c 2 ,…,c n-1 ,c n And are arranged in sequence;
s42, selecting an adjacent interlayer color transition mode inter;
s43, establishing color mapping information C= (C) 0 ,c 1 ,c 2 ,…,c n-1 ,c n ,inter)。
Preferably, the color vector c 0 ,c 1 ,c 2 ,…,c n-1 ,c n Defining an m multiplied by 3 matrix, wherein 3 numbers in each row are integers between 0 and 255 and respectively represent RGB values of color composition;
the adjacent interlayer color transition mode inter comprises an adjacent interpolation method, a linear interpolation method and other nonlinear processing modes.
(III) beneficial effects
Compared with the prior art, the pseudo-color mapping method based on the SPECT reconstruction data with adjustable bidirectional quantity parameters, provided by the invention, is based on a DICOM file of SPECT, provides a pseudo-color mapping method containing the adjustable bidirectional quantity parameters, creates a multi-level mapping relation, can control the display range of pseudo colors, can regulate multi-segment details of dose display, can display the interested dose region and the data range in a SPECT image more clearly and accurately, can obviously enhance the focus region and the dose distribution layering sense of SPECT-CT after being fused with a CT image, accurately displays the particle space and the radiation dose distribution information of focus positions, and provides a reliable basis for judging clinical curative effects.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly described below. It is evident that the drawings in the following description are only some embodiments of the present invention and that other drawings may be obtained from these drawings without inventive effort for a person of ordinary skill in the art.
FIG. 1 is a schematic flow chart of the present invention;
FIG. 2 is a schematic diagram of a DICOM file according to the present invention;
FIG. 3 is a schematic diagram of the layering of intermediate reconstructed data according to the present invention;
FIG. 4 is a schematic diagram of non-equally spaced reconstructed data layering based on a region of interest in accordance with the present invention;
FIG. 5 is a color mapping table based on a human eye sensitive color design in the present invention;
fig. 6 is a schematic representation of the fusion registration of SPECT images with CT images in the present invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the embodiments of the present invention more clear, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present invention. It will be apparent that the described embodiments are some, but not all, embodiments of the invention. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.
A pseudo color mapping method of SPECT reconstruction data based on adjustable bi-directional parameters, as shown in fig. 1, comprising the steps of:
s1, constructing a reconstruction data pseudo-color mapping function of distance information and color mapping information between adjacent layers;
s2, reading reconstruction data of a corresponding imaging part, and layering the reconstruction data by taking an area where a larger value in a data matrix is located as a center and gradually reducing and diffusing the area to the periphery according to the value;
s3, calibrating the region of interest in the data layering, and regulating and controlling the distance information between adjacent layering;
s4, regulating and controlling the color mapping information by setting layering colors and a color transition mode among layering.
S1, constructing a reconstruction data pseudo-color mapping function of distance information and color mapping information between adjacent layers, wherein the reconstruction data pseudo-color mapping function comprises the following steps:
the pseudo-color mapping function of the reconstructed data is S P ＝P(S O ,L,C)；
Wherein the vector S P SPECT images representing pseudo-colors; vector S O Representing the original reconstructed data, typically two-dimensional; vector L represents the number of layers of the reconstructed data hierarchy and distance information between adjacent hierarchies, note l= (n, s) 1 ,s 2 ,…,s n-1 ) Integer variable n represents the number of layering layers, integer variable s 1 ,s 2 ,…,s n-1 Representing the distance between adjacent layers, which may or may not be the same; vector C represents the color mapping information used by the data to be reconstructed, note c= (C) 0 ,c 1 ,c 2 ,…,c n-1 ,c n Inter), color vector c 0 ,c 1 ,c 2 ,…,c n-1 ,c n The character variable inter represents the color transition mode between adjacent layers.
S2, reading reconstruction data of a corresponding imaging part, wherein the method comprises the following steps:
and reading a data element part in the DICOM file, independently storing the reconstructed data in a dat file, and carrying out feature analysis on a numerical range, numerical distribution and a lesion part.
As shown in fig. 2, DICOM storage format is an international standard for medical imaging and related information, and has been widely used in radiology, cardiovascular imaging, and radiodiagnosis equipment. In order to be able to more accurately acquire SPECT imaging information, it is necessary to re-read the information from the original DICOM file acquired by the device. The DICOM file data consists of a file header and a dataset, wherein the first 128 bytes are the introduction information of an acquisition object, an acquisition mode, time and the like, and then all the introduction information is data elements, which correspond to the reconstruction information of an imaging part.
In the S2, taking the area where the larger value in the data matrix is located as the center, the area is gradually reduced and diffused to the periphery according to the value, and layering the reconstructed data, wherein the method comprises the following steps:
taking the row coordinates and the column coordinates of the two-dimensional data matrix as x values and y values respectively, taking the numerical value at the corresponding coordinates as z values, establishing a three-dimensional Cartesian coordinate system, and selecting a threshold point z i Let z=z i Layering the reconstruction data as a threshold plane;
wherein the threshold point z i It is desirable to combine the activity, number and clinical experience of the physician with the implant particles.
When the reconstruction data is layered, the non-interested area with smaller numerical value beyond the focus area is taken as a layering.
As shown in fig. 3 and 4, in S3, by calibrating a region of interest in a data hierarchy, distance information between adjacent hierarchies is regulated and controlled, including:
s31, giving the number n of layering layers;
s32, obtaining a maximum value Zmax and a minimum value Zmin in the reconstructed data;
s33, set S 1 ,s 2 ,…,s n-1 ；
S34, giving a data layering mode: zmin, Z 1 ＝Zmin+s 1 ，Z 2 ＝Z 1 +s 2 ，…， Z n-1 ＝Z n-2 +s n-1 ，Zmax。
The region of interest is calibrated by segmenting the SPECT image or the corresponding CT image.
As shown in fig. 5, in S4, the color mapping information is adjusted by setting a layered color and a color transition manner between layers, which includes:
s41, given color vector c 0 ,c 1 ,c 2 ,…,c n-1 ,c n And according toSequentially arranged;
s42, selecting an adjacent interlayer color transition mode inter;
s43, establishing color mapping information C= (C) 0 ,c 1 ,c 2 ,…,c n-1 ,c n ,inter)。
Color vector c 0 ,c 1 ,c 2 ,…,c n-1 ,c n Defining an m multiplied by 3 matrix, wherein 3 numbers in each row are integers between 0 and 255 and respectively represent RGB values of color composition;
the adjacent interlayer color transition mode inter comprises an adjacent interpolation method, a linear interpolation method and other nonlinear processing modes.
In the technical scheme of the application, the color vector c 0 ,c 1 ,c 2 ,…,c n-1 ,c n May be defined according to the purpose and need of the pseudo-color mapping. Two color control points are usually taken in a color mapping table, one color is taken in the largest row, one color is taken in the smallest row, the color in the middle row can be obtained by interpolation through the color in the largest row and the color in the smallest row, and adjacent interpolation, linear interpolation or nonlinear interpolation is selected according to the requirement; a plurality of color control points may be set in the color mapping table, and two adjacent colors may be interpolated to calculate the color between them.
Color mapping information c= (C) 0 ,c 1 ,c 2 ,…,c n-1 ,c n Inter) is based primarily on the visual characteristics of the human eye and the needs in the application. For example, the human eye is relatively sensitive to yellow-green, so the interest range that can be judged in connection with the diagnosis and treatment effect of the focus is set to be yellow-green, such as the vicinity of the boundary of the focus or the central region of the focus. In addition, to facilitate later image fusion, the non-region of interest is typically set to black. In fact, the color setting and transition pattern of the three-dimensional color vector may be entirely dependent on the actual needs.
In a SPECT-CT imaging system, the reconstructed SPECT image data and CT image data are selected to be 512 x 512, as shown in fig. 6 (a) and (b), respectively. Because the implantation particles are distributed at the focus part, according to the particle attenuation ruleGamma-ray dose information provided by SPECT image data is mainly focused on focal sites and their periphery, and is also a region of interest for clinical diagnosis and treatment. Therefore, firstly, using morphological information provided by CT image, selecting focus position corresponding to data in SPECT image, setting s 1 Segmenting the data outside the region of interest as density into a first layer z 1 。
In order to provide richer and accurate gamma ray dose distribution, the experiment combines clinical experience to give a pseudo-color mapping function of S P ＝P(S O L, C). Wherein the parameters in the hierarchical vector L are selected to be n=11, s 1 ＝462，s 2 ＝461，s 3 ＝462，s 4 ＝462，s 5 ＝2539，s 6 ＝4617， s 7 ＝2309，s 8 ＝1154，s 9 ＝1847，s 10 =230, and calculate each threshold plane z=z i The method comprises the steps of carrying out a first treatment on the surface of the The parameter in the color vector C is selected as C 0 ＝[0,0,0]，c 1 ＝[10,0,0]，c 2 ＝[0,0,255]， c 3 ＝[0,255,255]，c 4 ＝[84,197,170]，c 5 ＝[253,82,0]，c 6 ＝[253,94,0]， c 7 ＝[15,244,0]，c 8 ＝[0,253,0]，c 9 ＝[253,253,0]，c 10 ＝[253,253,28]， c 11 ＝[255,255,255]The adjacent interlayer color transition mode inter adopts linear interpolation.
For the original reconstructed data S corresponding to (b) in FIG. 6 O Using a defined pseudo-colour mapping function S P A pseudo-color SPECT image is obtained as shown in fig. 6 (c). The pseudo-colored image can fully reflect the dose distribution condition, and the adjacent interlayer color transition mode adopts linear interpolation, so that the color is excessive and not smooth enough, but the difference between different dose areas can be clearly displayed. The fusion effect of the SPECT image and the CT image after pseudo-color mapping is shown in fig. 6 (d), and it is obvious that the method provided by the invention can give out more abundant dose distribution detail information of the focus part, and the white and yellow regions of the center part are the regions with the largest dose and gradually decrease outwards.
The above embodiments are only for illustrating the technical solution of the present invention, and are not limiting; although the invention has been described in detail with reference to the foregoing embodiments, it will be understood by those of ordinary skill in the art that: the technical scheme described in the foregoing embodiments can be modified or some technical features thereof can be replaced by equivalents; such modifications and substitutions do not depart from the spirit and scope of the technical solutions of the embodiments of the present invention.
Claims (5)
1. A pseudo-color mapping method of SPECT reconstruction data based on adjustable bi-directional parameters, characterized by: the method comprises the following steps:
s1, constructing a reconstruction data pseudo-color mapping function of distance information and color mapping information between adjacent layers;
s2, reading reconstruction data of a corresponding imaging part, and layering the reconstruction data by taking an area where a larger value in a data matrix is located as a center and gradually reducing and diffusing the area to the periphery according to the value;
s3, calibrating the region of interest in the data layering, and regulating and controlling the distance information between adjacent layering;
s4, regulating and controlling the color mapping information by setting a layered color and a color transition mode among layers;
s3, calibrating the region of interest in the data layering, regulating and controlling the distance information between adjacent layering, wherein the method comprises the following steps:
s31, giving the number n of layering layers;
s32, obtaining a maximum value Zmax and a minimum value Zmin in the reconstructed data;
s33, set S 1 ,s 2 ,…,s n-1 ；
S34, giving a data layering mode: zmin, Z 1 ＝Zmin+s 1 ，Z 2 ＝Z 1 +s 2 ，…，
Z n-1 ＝Z n-2 +s n-1 ，Zmax；
The region of interest is calibrated after the SPECT image or the corresponding CT image is segmented;
s4, regulating and controlling the color mapping information by setting a layered color and a color transition mode among layers, wherein the method comprises the following steps:
s41, given color vector c 0 ,c 1 ,c 2 ,…,c n-1 ,c n And are arranged in sequence;
s42, selecting an adjacent interlayer color transition mode inter;
s43, establishing color mapping information C= (C) 0 ,c 1 ,c 2 ,…,c n-1 ,c n ,inter)；
The color vector c 0 ,c 1 ,c 2 ,…,c n-1 ,c n Defining an m multiplied by 3 matrix, wherein 3 numbers in each row are integers between 0 and 255 and respectively represent RGB values of color composition;
the adjacent interlayer color transition mode inter comprises an adjacent interpolation method, a linear interpolation method and other nonlinear processing modes.
2. The method of pseudo color mapping of SPECT reconstruction data based on adjustable bi-directional parameters of claim 1 wherein: s1, constructing a reconstruction data pseudo-color mapping function of distance information and color mapping information between adjacent layers, wherein the reconstruction data pseudo-color mapping function comprises the following steps:
the pseudo-color mapping function of the reconstructed data is S P ＝P(S O ,L,C)；
Wherein the vector S P SPECT images representing pseudo-colors; vector S O Representing the original reconstructed data, typically two-dimensional; vector L represents the number of layers of the reconstructed data hierarchy and distance information between adjacent hierarchies, note l= (n, s) 1 ,s 2 ,…,s n-1 ) Integer variable n represents the number of layering layers, integer variable s 1 ,s 2 ,…,s n-1 Representing the distance between adjacent layers, which may or may not be the same; vector C represents the color mapping information used by the data to be reconstructed, note c= (C) 0 ,c 1 ,c 2 ,…,c n-1 ,c n Inter), color vector c 0 ,c 1 ,c 2 ,…,c n-1 ,c n Colors representing interlayer usageThe color, character variable inter represents the color transition pattern between adjacent layers.
3. The method of pseudo color mapping of SPECT reconstruction data based on adjustable bi-directional parameters of claim 2 wherein: s2, reading reconstruction data of a corresponding imaging part, wherein the method comprises the following steps:
and reading a data element part in the DICOM file, independently storing the reconstructed data in a dat file, and carrying out feature analysis on a numerical range, numerical distribution and a lesion part.
4. A method of pseudo color mapping of SPECT reconstruction data based on adjustable bi-directional parameters according to claim 3, characterized in that: in the S2, taking the area where the larger value in the data matrix is located as the center, the area is gradually reduced and diffused to the periphery according to the value, and layering the reconstructed data, wherein the method comprises the following steps:
taking the row coordinates and the column coordinates of the two-dimensional data matrix as x values and y values respectively, taking the numerical value at the corresponding coordinates as z values, establishing a three-dimensional Cartesian coordinate system, and selecting a threshold point z i Let z=z i Layering the reconstruction data as a threshold plane;
wherein the threshold point z i It is desirable to combine the activity, number and clinical experience of the physician with the implant particles.
5. The method of pseudo color mapping of SPECT reconstruction data based on adjustable bi-directional parameters of claim 4 wherein: when the reconstruction data is layered, the non-interested area with smaller numerical value beyond the focus area is taken as a layering.
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