CN111956254B - High-resolution tomographic method and reconstruction method - Google Patents
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Abstract
The application relates to the technical field of medical imaging equipment, in particular to a high-resolution tomography method and a reconstruction method, which actually increase the number of sampling LORs of a system in three dimensions of XYZ through a physical translation method and secondary scanning of PET, and achieve the purposes of improving the details of scanned objects of the PET system in the same radiation dose through a new reconstruction algorithm.
Description
Technical Field
The application relates to the technical field of medical imaging equipment, in particular to a high-resolution tomography method and a reconstruction method.
Background
PET (positron emission tomography) is a tool that resolves the spatial distribution of the radioactive energy of an object by capturing the high-energy photons of the object. Can clinically give the human body the physiological characteristics of potential lesions and vascular blood flow. The principle of positron emission tomography is to measure gamma photon pairing after positron annihilation and to image with the geometrical direction and time characteristics of the gamma photon pairing.
Since the determination of the geometric direction and position of the motion of the gamma photons is characterized by the coordinates of the detector that absorbs the gamma photons, the actual resolution of detection is actually affected by the number of detector crystals in space and the size of the crystals. The number and size of the spaces themselves are affected by the cost of manufacturing the crystal, and the density of the electronics system. How to improve the resolution of the system under the given detector setting is a key problem for improving the performance of the PET system.
Disclosure of Invention
In order to solve the problems, the application aims to provide a high-resolution tomography method and a reconstruction method, which achieve the effect of improving the resolution of three dimensions of XYZ.
In order to achieve the above object, the technical scheme of the present application is as follows:
a high resolution tomographic method comprising a three-axis movable scan bed, said scan method comprising the steps of:
s1, setting a first scanning time and a second scanning time of a PET scanning module, and moving a scanning bed to a bed to be scanned;
s2, an attenuation information scanning module scans a target to obtain scanning data for obtaining attenuation information;
s3, the PET scanning module performs first scanning and obtains first scanning data;
s4, performing three-dimensional offset on the scanning bed;
and S5, the PET scanning module performs a second scanning and obtains second scanning data.
Further, the first scanning time and the second scanning time are the same.
Further, the data obtained by the two scans of the PET scanning module will form two independent List mode data.
Furthermore, the data obtained by the two scans of the PET scanning module will form a group of List mode data, and the event of the data will be marked which scan of the bed the event belongs to.
A high resolution tomographic reconstruction method comprising the steps of:
s1, scanning the attenuation information scanning module to obtain data, forming an attenuation distribution map Image (x, y, z) for guiding PET attenuation distribution, and defining the attenuation distribution map as Image' (x, y, z) =image (x+dx, y+dy, z+dz) for a scanning target after translation, wherein [ dxdy dz]Offset in three dimensions XYZ for the scan bed; s2, respectively forward projecting the attenuation distribution diagrams before and after the offset to generate attenuation coefficientsAnd attenuation coefficient after offset-> Wherein the subscript i of the image is a one-dimensional linear storage space coordinate; h j，i Is a system matrix reflecting the geometrical correspondence between event j and pixel i;
s3, obtaining a sensitivity matrix s according to attenuation coefficients before and after the offset, wherein a calculation formula of s is as followsLet->Thens1 and s2 are sensitivity matrices before and after offset of the scanning bed, respectively, wherein the superscript m represents the serial number of the subset, and d1 represents the three-dimensional offset [ dxdy dz ]]A one-dimensional linear storage space formed by image space conversion, wherein Lm is a sequence number set of scanning data before and after offset;
s4, according to the attenuation information, the following reconstruction formula is obtained:
wherein, gamma is [ 01 ]]The relaxation constant between the two is f, the upper mark k represents the iteration times, and N is the total number of pixel points of the image;the correction factor formed by combining scattering and random events can be calculated according to all events of the first scanning data and the second scanning data; variable->Wherein L is 1 m represents the event belonging to pre-shift scanning in Lm, i.e. the sequence number set of the first scanning data, L 2 m represents an event belonging to post-offset scanning in Lm, namely a sequence number set of second scanning data;
s5, substituting the data obtained by the two times of scanning of the PET scanning module into a reconstruction formula to reconstruct an image.
The application has the advantages that: the method of physical translation and the secondary scanning of PET actually increase the number of sampling LORs of the system in three dimensions of XYZ, and the purpose of resolving the scanned object details of the PET system in the same radiation dose is achieved through a new reconstruction algorithm.
Drawings
FIG. 1 is a schematic diagram of a conventional PET system;
FIG. 2 is a schematic diagram of a three-axis movable scanning bed used in the present embodiment;
FIG. 3 is a schematic front view of FIG. 2;
FIG. 4 is a flowchart of the operation of the PET scanning module in an embodiment;
FIG. 5 is a flow chart of data processing performed by the data processing module in an embodiment;
FIG. 6 is a reconstruction effect diagram, wherein the left diagram is a reconstruction effect diagram adopting the method of the present application, and the right diagram is a reconstruction effect diagram adopting the prior method;
FIG. 7 is a schematic view of the intensity of a region of interest, wherein the left view is a schematic view of the method of the present application and the right view is a schematic view of the conventional method;
description of the reference numerals
The PET system includes a main body holder and housing 101, a detector 102, a scanner 103, a couch board 201, a feed drive support 202, a left-right movement drive support 203, a lift table 204, and a support base 205.
Detailed Description
The present application is described in further detail below with reference to examples.
Description is made of basic concepts that may be involved in the present embodiment:
(1) Response line: the Line between two crystal bars of gamma photons detected by the detector is called a Line of Response (LOR);
(2) Coincidence events: a pair of coincidence events is considered to occur when two 511keV gamma photons are detected within a predetermined time coincidence window (e.g., 0ns-15 ns);
(3) Conforming to a time window: is the time length set for the time difference between the arrival of two gamma photons at the detector;
(4) A crystal: the minimum geometric unit of the PET detector ring, which receives gamma photons at the front end of the detector to generate a front end trigger signal;
(5) The real coincidence is as follows: two gamma photons generated by annihilation radiation move in opposite directions and are respectively received by two crystals within a coincidence time window;
(6) The scattering corresponds to: two gamma photons generated by annihilation radiation, if one were scattered with tissue before arrival, but still coincident with the detected scatter within a coincidence time window;
(7) Random coincidence: is a false coincidence, where two gamma photons have no temporal and spatial correlation, but are falsely detected coincidence events within a coincidence time window.
(8) List mode data: during the scanning process of the PET machine, data conforming to the event is recorded, and the method is characterized in that: each of which includes at least the following information: position information (detector number of two gamma photons detected coincident with an event, or LOR number of the two detectors) and time information (time difference in detection of two photons).
Introduction to background knowledge of conventional reconstruction algorithms:
a common formula for the OSEM (ordered subset maximum likelihood estimation) based reconstruction is as follows,
wherein γ is the relaxation constant between [ 01 ];
f represents an image, a subscript i represents a pixel label of the image, an upper label k represents iteration times, and an upper label m represents a sequence number of the subset;
n is the total number of pixels of the image;
alpha is an attenuation coefficient, and subscript j thereof represents a specific event label;
lm represents the set of event sequence numbers in subset m.
H j,i Is a system matrix reflecting the geometrical correspondence between event j and pixel i;
is a correction factor formed by combining scatter and random events, which is calculated from known scatter estimates and random estimates;
s is a sensitivity matrix, and its calculation formula is
The embodiment comprises a motion control module, a scanning module and a data processing module.
A conventional PET system is schematically shown in fig. 1, which includes a body support and housing 101 of the PET system, a detector assembly 102, a scanner 103, i.e., the motion control module described above, for moving the scanner 103 for positioning a patient scanning position and comfort. In the figure, X is the left-right direction of the scanning bed, Y is the lifting direction of the scanning bed, and Z is the in-out direction of the scanning bed.
In order to implement the scanning method and the reconstruction method of the present application, the scanning bed of the present embodiment employs a scanning bed that is movable in three axes, and as shown in fig. 2 and 3, the scanning bed includes a bed plate 201 for supporting a human body, a feed drive support 202 for controlling the bed plate 201 to enter and exit the bed, a left-right movement drive support 203 for guiding the feed drive support 202 to translate left-right, a lifting rack 204 for supporting the left-right movement drive support 203 to lift, and a support base 205.
The scanning module of the present embodiment includes an attenuation information scanning module and a PET scanning module.
The attenuation information scanning module is used for scanning a target by utilizing a CT (X-ray tomography) or MR (nuclear magnetic resonance) device to obtain CT or MR data before scanning by the PET scanning module, and forming a three-dimensional attenuation distribution map Image (X, y, z) for guiding gamma photon attenuation distribution by carrying out a corresponding CT/MR reconstruction algorithm on the data.
The PET scan module refers to a plurality of radiation detector ring structures outside the imaging region for acquiring information of the emitted radiation events. The detector has different timing delay functions to achieve the segmented scanning of the scanning method of the present embodiment. The calibration phantom may emit a radiation source of a pair of events (coincidence events) of simultaneous but opposite radiation, the interaction paths of the pair of radiation events with the radiation detector being LOR's, the geometric position of each LOR being known after the detector ring is determined.
The scanning method of the present embodiment includes the steps of:
s1, setting total scanning time, first scanning time and second scanning time of a PET scanning module, wherein the two scanning times are 1/2 of the total scanning time (for example, a certain bed needs to acquire data for 5 minutes, and the PET scanning module can independently scan for 2.5 minutes) and moving the scanning bed to the bed needing to be scanned;
s2, scanning a target by using a CT or MR device to obtain scanning data for obtaining attenuation information;
s3, the PET scanning module performs first scanning and obtains first scanning data;
s4, performing three-dimensional offset on the scanning bed; because the detector has different timing delay functions, a period of delay can be set between two scans of PET for waiting for the offset adjustment of the sickbed;
and S5, the PET scanning module performs a second scanning and obtains second scanning data.
Under each bed, the PET scanning module can scan the target twice, the List data acquired by the PET scanning module before and after twice are respectively recorded as L1 and L2, and the two scans of the PET can form two independent groups of List mode data, or a group of List mode data and an event of the data can mark which scan of the bed the event belongs to.
The reconstruction method in the data processing module comprises the following steps:
s1, scanning data obtained by scanning a patient by a CT or MR device to form an attenuation distribution map Image (x, y, z) for guiding PET attenuation distribution, wherein the attenuation distribution map is defined as Image' (x, y, z) =image (x+dx, y+dy, z+dz) for a scanning target after translation, and [ dx dy dz ] is the offset of a scanning bed in three dimensions of XYZ;
s2, respectively forward projecting the attenuation distribution diagrams before and after the offset to generate attenuation coefficientsAnd attenuation coefficient after offset-> Where the subscript i of image is a one-dimensional linear memory space coordinate (in contrast to conventional reconstruction algorithms, α is no longer used as attenuation in the present application, but +.>And->Such two attenuation coefficients);
s3, obtaining a sensitivity matrix s according to attenuation coefficients before and after the offset, wherein a calculation formula of s is as followsLet->Thens1 and s2 are sensitivity matrices before and after offset of the scanning bed respectively, and compared with a conventional reconstruction algorithm, the sensitivity matrix s of the embodiment simultaneously comprises two sets of attenuation information before and after offset, and d1 represents three-dimensional offset [ dxdy dz ]]A one-dimensional linear storage space formed by image space conversion; lm is a sequence number set of scanning data before and after offset;
s4, according to the attenuation information, a reconstruction formula suitable for the reconstruction method can be obtained: the method can be calculated according to all events of the first scanning data and the second scanning data; variable->Wherein L is 1 m represents the event belonging to the pre-shift scan in Lm, i.e. the sequence number set of the first scan data L1 in the foregoing, L 2 m represents an event belonging to post-offset scanning in Lm, namely, a sequence number set of the second scanning data L2 in the foregoing;
s5, substituting the data obtained by the two times of scanning of the PET scanning module into a reconstruction formula to reconstruct an image.
The image shift amount d1 mentioned in step S3 of the reconstruction method is explained as follows:
in a certain bed, the first scanning object coordinates of the PET are [ x, y and z ], after the scanning bed is shifted, the second scanning object coordinates of the PET are [ x ', y ', z ' ], the three-dimensional offset of a defined pixel is d [ dx dy dz ], and the pixel is converted into a one-dimensional linear storage space through an image space, wherein d can also be directly represented by d 1;
for example, data is stored in x, y, z order for a three-dimensional spatial image, where x ' =x+dx, y ' =y+dy, z ' =z+dz, dxdy dz is the offset of three dimensions;
defining one-dimensional coordinates vid=x+y offsetx+z Offsetx Offsety, offsetx and Offsetxy being the widths of the x and y dimensions, respectively, d1=vid '-vid=x' +y '×offsetx+z' ×offsetx Offsetx Offsety- (x+y×offsetx+z) Offsetx) =dx+dy×offsetx+dz.
The scanning method and the reconstruction method of the present embodiment are verified:
the verification uses a 4.2mm LYSO crystal detector ring as an acquisition module, and a Jaszczak scanning die body specially used for measuring the resolution of the system is selected to verify the resolution effect.
As shown in fig. 6, the left graph is a graph of the reconstruction effect of the present application, with a total scan time of 5 minutes (divided into a normal scan of 2.5 minutes and a three-dimensional translation of 2.5 minutes [2.1mm 2.1mm 2.1mm ] post-scan); the right graph is a graph of the reconstruction effect of scanning 5 minutes of data directly without translation.
The left plot of fig. 7 is an intensity extraction for the region of interest in the left plot of fig. 5, and shows intensity pixel by pixel in the lateral direction of the region of interest; the right graph of fig. 7 is an intensity extraction for the region of interest in the right graph of fig. 5, and shows the intensity pixel by pixel in the lateral direction of the region of interest; as can be seen from fig. 7, the contrast of the detail of the method of the present application (left panel) is significantly enhanced relative to that of the conventional method (right panel), thus demonstrating the improved resolution of the scanning system relative to that of the conventional method.
The above embodiments are only for illustrating the concept of the present application and not for limiting the protection of the claims of the present application, and all the insubstantial modifications of the present application using the concept shall fall within the protection scope of the present application.
Claims (4)
1. A high-resolution fault scanning method and a reconstruction method are characterized by comprising a scanning bed capable of moving along three axes;
the scanning method comprises the following steps:
s1, setting a first scanning time and a second scanning time of a PET scanning module, and moving a scanning bed to a bed to be scanned;
s2, an attenuation information scanning module scans a target to obtain scanning data for obtaining attenuation information;
s3, the PET scanning module performs first scanning and obtains first scanning data;
s4, performing three-dimensional offset on the scanning bed;
s5, the PET scanning module performs second scanning and obtains second scanning data;
the reconstruction method comprises the following steps:
s1, scanning an attenuation information scanning module to obtain data, forming an attenuation distribution map Image (x, y, z) for guiding PET attenuation distribution, and defining the attenuation distribution map as Image' (x, y, z) =image (x+dx, y+dy, z+dz) for a scanning target after translation, wherein [ dxdy dz ] is the offset of a scanning bed in three dimensions of XYZ;
s2, respectively forward projecting the attenuation distribution diagrams before and after the offset to generate attenuation coefficientsAnd post-offset attenuation coefficientWherein the subscript i of the image is a one-dimensional linear storage space coordinate; h j，i Is a system matrix reflecting the geometrical correspondence between event j and pixel i;
s3, obtaining a sensitivity matrix s according to attenuation coefficients before and after the offset, wherein a calculation formula of s is as followsLet->Thens1 and s2 are sensitivity matrices before and after offset of the scanning bed, respectively, wherein the superscript m represents the serial number of the subset, and d1 represents the three-dimensional offset [ dxdy dz ]]A one-dimensional linear storage space formed by image space conversion, wherein Lm is a sequence number set of scanning data before and after offset;
s4, according to the attenuation information, the following reconstruction formula is obtained:
wherein, gamma is [ 01 ]]The relaxation constant between the two is f, the upper mark k represents the iteration times, and N is the total number of pixel points of the image;the correction factor formed by combining scattering and random events can be calculated according to all events of the first scanning data and the second scanning data; variable->Wherein L is 1 m representsEvents belonging to pre-shift scanning in Lm, i.e. sequence number set of first scanning data, L 2 m represents an event belonging to post-offset scanning in Lm, namely a sequence number set of second scanning data;
s5, substituting the data obtained by the two times of scanning of the PET scanning module into a reconstruction formula to reconstruct an image.
2. A high resolution tomographic method and reconstruction method according to claim 1 wherein: the first scanning time is the same as the second scanning time.
3. A high resolution tomographic method and reconstruction method according to claim 1 wherein: the data obtained by the two scans of the PET scanning module can form two independent List mode data.
4. A high resolution tomographic method and reconstruction method according to claim 1 wherein: the data obtained by the two scans of the PET scanning module can form a group of List mode data, and the event of the data marks which scan of the bed the event belongs to.
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| WO2016197127A1 (en) * | 2015-06-04 | 2016-12-08 | Rensselaer Polytechnic Institute | Attenuation map reconstruction from tof pet data |
| CN108553121A (en) * | 2018-02-12 | 2018-09-21 | 沈阳东软医疗系统有限公司 | A kind of method and apparatus of PET delayed sweeps |
| CN110443866A (en) * | 2019-07-31 | 2019-11-12 | 东软医疗系统股份有限公司 | Image rebuilding method, device, terminal device and PET system |
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| CN108553121A (en) * | 2018-02-12 | 2018-09-21 | 沈阳东软医疗系统有限公司 | A kind of method and apparatus of PET delayed sweeps |
| CN110443866A (en) * | 2019-07-31 | 2019-11-12 | 东软医疗系统股份有限公司 | Image rebuilding method, device, terminal device and PET system |
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