CN110389373B - Crystal module, detector and high-degree decoding method thereof - Google Patents
Crystal module, detector and high-degree decoding method thereof Download PDFInfo
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- CN110389373B CN110389373B CN201810366676.0A CN201810366676A CN110389373B CN 110389373 B CN110389373 B CN 110389373B CN 201810366676 A CN201810366676 A CN 201810366676A CN 110389373 B CN110389373 B CN 110389373B
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
- G01T1/164—Scintigraphy
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
- G01T1/164—Scintigraphy
- G01T1/1641—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras
- G01T1/1645—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras using electron optical imaging means, e.g. image intensifier tubes, coordinate photomultiplier tubes, image converter
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/20—Measuring radiation intensity with scintillation detectors
- G01T1/202—Measuring radiation intensity with scintillation detectors the detector being a crystal
Abstract
The invention provides a crystal module, a detector and a high-degree decoding method. The size of a scintillation crystal array of the crystal module is 4 Nx 4N, N is a natural number, except for scintillation crystals in the 1 st and 4 Nth columns, a first light transmission window is arranged on a surface, coupled with the adjacent scintillation crystal in the 2n +1 st column, of the scintillation crystals in the 2N th column, and a second light transmission window is arranged on a surface, coupled with the adjacent scintillation crystal in the 2N +1 nd column, of the scintillation crystals in the rest scintillation crystals; except for the scintillation crystals in the 1 st and 4N rows, the surfaces of the scintillation crystals in the 2N row coupled with the adjacent scintillation crystals in the 2n +1 row in the rest of the scintillation crystals are provided with third light transmission windows, and the surfaces of the scintillation crystals in the 2n +1 row in the rest of the scintillation crystals coupled with the adjacent scintillation crystals in the 2N row are provided with fourth light transmission windows. The detector of the invention has higher DOI decoding precision and position decoding capability.
Description
Technical Field
The present invention relates to emission imaging systems, and in particular, to a crystal module, a detector, and a method of highly decoding a detector.
Background
Positron Emission Tomography (PET) is one of the most sensitive and quantitative measurement methods in functional molecular imaging, and is widely used for detecting early diseases, such as cardiovascular diseases, tumors, cancers and the like. PET front-end detector modules are typically composed of an array of discrete crystal-coupled photosensors, such as PMTs (photodiodes tubes), siPMs (silicon photodiodes). The 511KeV gamma photon and the scintillation crystal generate annihilation reaction and are converted into visible light subgroup, the visible light subgroup is received by the photoelectric sensor, and the energy signal distribution detected by the sensor utilizes a gravity center algorithm (Anger Logic) to decode the position of the reaction crystal. In order to be able to detect metabolic disorders in the human body early and meet the requirements of clinical research, PET systems must simultaneously satisfy the performance of high spatial resolution and sensitivity. As the system edge radius increases, the spatial resolution is severely degraded by visual errors (parallelax errors). PET systems are capable of achieving high sensitivity without degrading the spatial resolution of the system and must have the ability to obtain Depth of Interaction (DOI) information of gamma photons in the scintillation crystal.
Therefore, it is necessary to provide a crystal module, a detector and a highly decoding method of the detector to accurately obtain the reaction depth of the scintillation crystal and improve the spatial resolution of the imaging system.
Disclosure of Invention
According to one aspect of the invention, a crystal module for a detector is provided, which comprises a scintillation crystal array, wherein the crystal module is provided with an upper end surface and a lower end surface, the scintillation crystal array is 4 Nx 4N, N is a natural number, except for scintillation crystals in a 1 st column and a 4 Nth column, a first light-transmitting window is arranged on a surface, coupled with the scintillation crystal in an adjacent 2n +1 st column, of scintillation crystals in the rest scintillation crystals, and a second light-transmitting window is arranged on a surface, coupled with the scintillation crystal in an adjacent 2n N +1 st column, of the rest scintillation crystals; except for the scintillation crystals in the 1 st and 4N rows, the surfaces of the scintillation crystals in the 2N row coupled with the adjacent scintillation crystals in the 2n +1 row in the rest scintillation crystals are provided with third light transmission windows, and the surfaces of the scintillation crystals in the 2n +1 row in the rest scintillation crystals coupled with the adjacent scintillation crystals in the 2N row are provided with fourth light transmission windows; wherein N is a natural number, and 4N-1 ≧ N ≧ 1.
Preferably, the first light-transmitting window, the second light-transmitting window, the third light-transmitting window and the fourth light-transmitting window are all arranged close to the upper end face, and the upper ends of all the light-transmitting windows are flush with the top face of the scintillation crystal where the light-transmitting windows are located.
Preferably, the first light-transmitting window, the second light-transmitting window, the third light-transmitting window and the fourth light-transmitting window are all arranged close to the lower end face, and the lower ends of all the light-transmitting windows are flush with the bottom face of the scintillation crystal where the light-transmitting windows are located.
Preferably, the first light-transmitting window and the second light-transmitting window are arranged face to face, and the third light-transmitting window and the fourth light-transmitting window are arranged face to face.
According to another aspect of the present invention, there is provided a detector for an emission imaging device, including a crystal module having a light emitting surface, and a photosensor array coupled to the light emitting surface of the crystal module, wherein the crystal module is the above-mentioned crystal module.
Preferably, the light emitting surface is the lower end surface of the crystal module, all the light transmission windows are arranged close to the upper end surface of the crystal module, and the upper ends of all the light transmission windows are flush with the top surface of the scintillation crystal where the light transmission windows are located.
Preferably, the light emitting surface is the upper end surface of the crystal module, all the light transmission windows are arranged close to the lower end surface of the crystal module, and the lower ends of all the light transmission windows are flush with the bottom surface of the scintillation crystal where the light transmission windows are located.
Preferably, the photosensor array includes a plurality of photosensors, one of the plurality of photosensors being coupled to one of the scintillation crystals, respectively.
Preferably, the photosensor array includes a plurality of photosensors, at least one of the plurality of photosensors being respectively coupled with a plurality of the scintillation crystals.
According to still another aspect of the present invention, there is provided a method for highly decoding a detector, which is used for highly decoding the detector, and comprises the following steps:
s1, making a decoding diagram, respectively establishing three-dimensional coordinate axes for the rest of crystals except for the crystals in the 1 st row and the 1 st column, the 1 st row and the 4n column of the 4n row and the 4n column in the decoding diagram, respectively projecting the three-dimensional coordinate axes onto an x axis according to the coordinate axes, and drawing summation in a y direction along the x axis direction, wherein n is a natural number;
s2, summing the y directions with different collimation heights, comparing and calculating the FWHM resolution of the DOI;
s3, drawing a corresponding relation curve of the spot peak position and the DOI height summed in the y direction with different collimation heights, and interpolating or fitting the corresponding relation to obtain a DOI decoding curve;
and S4, obtaining DOI information through light distribution for image reconstruction after obtaining the DOI decoding curve.
The light-transmitting window is reasonably arranged on the scintillation crystal of the crystal module, so that the light distribution of visible light subgroups on the sensor is guided, the position decoding and the depth decoding of high-energy photons are realized by utilizing the signal strength relation of the sensor, the reaction depth of the scintillation crystal can be accurately obtained, and the spatial resolution of an imaging system is improved. The detector provided by the invention has higher improvement on the decoding capability of the discrete crystal, and has the following advantages: (1) the DOI decoding precision is higher; (2) have higher position decoding ability; and (3) the time measurement potential with high performance is achieved.
A series of concepts in a simplified form are introduced in the summary of the invention, which is described in further detail in the detailed description section. This summary is not intended to identify key features or essential features of the claimed subject matter, nor is it intended to be used as an aid in determining the scope of the claimed subject matter.
The advantages and features of the present invention are described in detail below with reference to the accompanying drawings.
Drawings
The following drawings of the invention are included to provide a further understanding of the invention. The drawings illustrate embodiments of the invention and, together with the description, serve to explain the principles of the invention. In the drawings, there is shown in the drawings,
FIG. 1 is a schematic view of an arrangement of light-transmissive windows of a crystal module according to an embodiment of the invention;
FIG. 2 is a schematic diagram of a coupling of a crystal module to a photosensor array according to an embodiment of the present invention;
FIG. 3 is another schematic diagram of coupling a crystal module to a photosensor array according to an embodiment of the present invention;
FIG. 4 is a schematic diagram of a coupling of a crystal module and a photosensor array according to another embodiment of the present invention;
FIG. 5 is another coupling diagram of a crystal module and a photosensor array according to another embodiment of the present invention;
FIG. 6 is a schematic diagram of establishing three-dimensional coordinate axes according to the height decoding method of the present invention.
Detailed Description
In the following description, numerous details are provided to provide a thorough understanding of the present invention. One skilled in the art will recognize, however, that the following description is merely illustrative of a preferred embodiment of the invention and that the invention can be practiced without one or more of these details. In addition, some technical features that are well known in the art are not described in order to avoid confusion with the present invention.
The invention provides a crystal module for a detector, which comprises a plurality of scintillation crystals, wherein the scintillation crystals are arranged in an array mode. The scintillation crystal can be one of an active thallium sodium iodide crystal, a bismuth germanate crystal, a lutetium silicate crystal and a lutetium-yttrium silicate crystal.
The crystal modules arranged in an array mode are provided with upper end faces and lower end faces, the size of the scintillation crystal array is 4 Nx 4N, and N is a natural number.
Take a crystal module composed of a 4 × 4 array of scintillation crystals as an example. As shown in fig. 1, the crystal module 100 is composed of a 4 × 4 array of scintillation crystals, and in order to accurately obtain the reaction depth of the scintillation crystals, a first light-transmitting window 11 is opened on the right side of all 4 scintillation crystals in the 2 nd column, that is, a first light-transmitting window 11 is opened on the surface of all 4 scintillation crystals in the 2 nd column, which is coupled with all 4 scintillation crystals in the 3 rd column; a second light-transmitting window 12 is arranged on the left side of all 4 scintillation crystals in the 3 rd column, namely, the second light-transmitting window 12 is arranged on the surface of all 4 scintillation crystals in the 3 rd column, which is coupled with all 4 scintillation crystals in the 2 nd column; a third light-transmitting window 13 is arranged behind all 4 scintillation crystals in the 2 nd row, namely, the third light-transmitting window 13 is arranged on the surface, coupled with all 4 scintillation crystals in the 3 rd row, of all 4 scintillation crystals in the 2 nd row; and a fourth light-transmitting window 14 is arranged in front of all 4 scintillation crystals in the 3 rd row, namely, the fourth light-transmitting window 14 is arranged on the surface, coupled with all 4 scintillation crystals in the 2 nd row, of all 4 scintillation crystals in the 3 rd row. The heights of the first light-transmitting window 11, the second light-transmitting window 12, the third light-transmitting window 13 and the fourth light-transmitting window 14 can be adjusted, and the first light-transmitting window 11, the second light-transmitting window 12, the third light-transmitting window 13 and the fourth light-transmitting window 14 can be flush with the top surface (the lower surface is a light-emitting surface), however, the positions of the first light-transmitting window 11, the second light-transmitting window 12, the third light-transmitting window 13 and the fourth light-transmitting window 14 in the height direction are not limited in the invention, and in addition, the sizes and the shapes of the light-transmitting windows are not limited by the attached drawings. The first light-transmitting window 11 faces the second light-transmitting window 12, and the third light-transmitting window 13 faces the fourth light-transmitting window 14. Each light-transmitting window is filled with light-transmitting optical glue, so that bubbles are avoided as much as possible.
In the embodiment shown in fig. 1, the first light-transmissive window 11, the second light-transmissive window 12, the third light-transmissive window 13, and the fourth light-transmissive window 14 are all disposed near the upper end surface 101 (see fig. 2), and the upper ends of all the light-transmissive windows are flush with the top surface of the scintillator crystal on which they are disposed.
In an embodiment not shown, the first light-transmissive window 11, the second light-transmissive window 12, the third light-transmissive window 13, and the fourth light-transmissive window 14 may also be all disposed near the lower end surface 102 (see fig. 2), and the lower ends of all the light-transmissive windows are flush with the bottom surface of the scintillator crystal on which they are disposed.
Further, the first translucent window 11 and the second translucent window 12 are preferably disposed to face each other, and the third translucent window 13 and the fourth translucent window 14 are preferably disposed to face each other.
As shown in fig. 2, the detector for an emission imaging device according to an embodiment of the present invention includes a crystal module 100 and a photosensor array 200, the crystal module 100 has an upper end surface 101 and a lower end surface 102, wherein the lower end surface 102 is a light emitting surface of the crystal module 100, and the photosensor array 200 is coupled to the light emitting surface of the crystal module. As a modified embodiment, the upper end face 101 may be a light emitting surface of the crystal module 100, and the photosensor array 200 is coupled to the light emitting surface of the crystal module. Illustratively, the crystal module 100 and the photosensor array 200 may be directly coupled together by a coupling agent such as optical glue, or by air coupling, or the like. It should be noted that the upper end surface and the lower end surface herein do not represent physical or absolute upper and lower, but merely serve to distinguish two ends of the crystal module.
There are various ways to couple the photo sensor array 200 and the crystal module 100 on the light emitting surface. As shown in fig. 2, which employs a one-to-one coupling approach, specifically, the photosensor array 200 includes a plurality of photosensors, one photosensor of the plurality of photosensors being coupled with only one scintillation crystal. As shown in fig. 3, which adopts a one-to-many coupling manner, specifically, the photosensor array 200 includes a plurality of photosensors, at least one photosensor of the plurality of photosensors is coupled with a plurality of scintillation crystals, and an embodiment in which one photosensor is coupled with four scintillation crystals is shown in fig. 3.
Referring to fig. 4 and 5 in combination, which show an embodiment that the detector includes a plurality of crystal modules, and referring to fig. 1 to 3, in the present invention, the size of the scintillator crystal array 110 is 4N × 4N, N is a natural number, except for the scintillating crystals in the 1 st column and the 4N th column, a first light-transmitting window 11 (not shown in fig. 4 and 5) is disposed on a surface of the scintillator crystal in the 2N +1 th column coupled with the adjacent scintillating crystal in the 2n +1 th column in the rest of the scintillating crystals, and a second light-transmitting window 12 (not shown in fig. 4 and 5) is disposed on a surface of the scintillator crystal in the 2n +1 th column coupled with the adjacent scintillating crystal in the 2N nd column in the rest of the scintillating crystals; except for the scintillation crystals on the 1 st and 4N rows, a third light-transmitting window 13 is arranged on the surface of the scintillation crystal on the 2N row in the rest scintillation crystals, which is coupled with the scintillation crystal on the 2n +1 adjacent row, and a fourth light-transmitting window 14 is arranged on the surface of the scintillation crystal on the 2n +1 row in the rest scintillation crystals, which is coupled with the scintillation crystal on the 2N adjacent row; wherein N is a natural number, and 4N-1 ≧ N ≧ 1.
Referring to fig. 6 in combination, according to still another aspect of the present invention, there is provided a method for highly decoding a detector, which is used for highly decoding the above-mentioned detector, and includes the following steps:
s1, making a decoding diagram, respectively establishing three-dimensional coordinate axes for the rest of crystals except for the crystals in the 1 st row and the 1 st column, the 1 st row and the 4n column of the 4n row and the 4n column in the decoding diagram, respectively projecting the three-dimensional coordinate axes onto an x axis according to the coordinate axes, and drawing summation in a y direction along the x axis direction, wherein n is a natural number;
s2, summing different collimation heights in the y direction, comparing and calculating the FWHM (Full Width Half Maximum, half-Width of pulse) resolution of the DOI;
s3, drawing a corresponding relation curve of the spot peak position and the DOI height summed in the y direction with different collimation heights, and interpolating or fitting the corresponding relation to be used as a DOI decoding curve;
and S4, obtaining DOI information through light distribution for image reconstruction after obtaining the DOI decoding curve.
The light-transmitting window is reasonably arranged on the scintillation crystal of the crystal module, the light distribution of visible light subgroups on the sensor is guided, the position decoding and the depth decoding of high-energy photons are realized by utilizing the signal strength relation of the sensor, the reaction depth of the scintillation crystal can be accurately obtained, and the spatial resolution of an imaging system is improved. The detector provided by the invention has higher improvement on the decoding capability of the discrete crystal, and has the following advantages: (1) has higher DOI decoding precision; (2) have higher position decoding ability; and (3) the method has high-performance time measurement potential.
The present invention has been illustrated by the above embodiments, but it should be understood that the above embodiments are for illustrative and descriptive purposes only and are not intended to limit the invention to the scope of the described embodiments. Furthermore, it will be understood by those skilled in the art that the present invention is not limited to the embodiments described above, and that many variations and modifications may be made in accordance with the teachings of the present invention, which variations and modifications are within the scope of the present invention as claimed. The scope of the invention is defined by the appended claims and equivalents thereof.
Claims (10)
1. A crystal module for a detector is characterized by comprising a scintillation crystal array, wherein the crystal module is provided with an upper end face and a lower end face, the scintillation crystal array is 4N x 4N, N is a natural number, except for scintillation crystals in a 1 st column and a 4N th column, a first light-transmitting window is arranged on a face, coupled with the adjacent scintillation crystal in a 2n +1 st column, of scintillation crystals in a 2N th column in the rest of scintillation crystals, and a second light-transmitting window is arranged on a face, coupled with the adjacent scintillation crystal in a 2N nd column, of scintillation crystals in a 2n +1 st column in the rest of scintillation crystals; except for the scintillation crystals in the 1 st and 4N rows, the surfaces of the scintillation crystals in the 2N row coupled with the adjacent scintillation crystals in the 2n +1 row in the rest scintillation crystals are provided with third light transmission windows, and the surfaces of the scintillation crystals in the 2n +1 row in the rest scintillation crystals coupled with the adjacent scintillation crystals in the 2N row are provided with fourth light transmission windows; wherein N is a natural number, and 4N-1 ≧ N ≧ 1.
2. The crystal module of claim 1, wherein the first, second, third, and fourth light-transmissive windows are disposed proximate to the upper end surface, and wherein the upper ends of all light-transmissive windows are flush with the top surface of the scintillator crystal on which they are disposed.
3. The crystal module of claim 1, wherein the first, second, third, and fourth light-transmissive windows are disposed adjacent to the lower end surface, and the lower ends of all light-transmissive windows are flush with the bottom surface of the scintillation crystal on which they are disposed.
4. A crystal module according to any one of claims 1-3, wherein the first light-transmissive window is disposed in face-to-face relation with the second light-transmissive window, and the third light-transmissive window is disposed in face-to-face relation with the fourth light-transmissive window.
5. A detector for an emission imaging device comprising a crystal module having an exit face and a photosensor array coupled to the exit face of the crystal module, wherein the crystal module is the crystal module of claim 1.
6. The detector of claim 5, wherein the light-emitting surface is a lower end surface of the crystal module, all the light-transmitting windows are disposed near an upper end surface of the crystal module, and upper ends of all the light-transmitting windows are flush with a top surface of the scintillation crystal on which the light-transmitting windows are disposed.
7. The detector of claim 5, wherein the light-emitting surface is an upper end surface of the crystal module, all the light-transmitting windows are disposed near a lower end surface of the crystal module, and lower ends of all the light-transmitting windows are flush with a bottom surface of the scintillation crystal where the light-transmitting windows are located.
8. The detector of claim 5, wherein the photosensor array comprises a plurality of photosensors, one of the plurality of photosensors respectively coupled to one of the scintillation crystals.
9. The detector of claim 5, wherein the photosensor array comprises a plurality of photosensors, at least one of the plurality of photosensors respectively coupled with a plurality of the scintillation crystals.
10. A method for highly decoding a detector according to claim 5, comprising the steps of:
s1, making a decoding diagram, respectively establishing three-dimensional coordinate axes for the rest of crystals except for the crystals in the 1 st row and the 1 st column, the 1 st row and the 4n column of the 4n row and the 4n column in the decoding diagram, respectively projecting the three-dimensional coordinate axes onto an x axis according to the coordinate axes, and drawing summation in a y direction along the x axis direction, wherein n is a natural number;
s2, summing different collimation heights in the y direction, comparing and calculating the FWHM resolution of the DOI;
s3, drawing a corresponding relation curve of the spot peak position and the DOI height summed in the y direction with different collimation heights, and interpolating or fitting the corresponding relation to be used as a DOI decoding curve;
and S4, after obtaining the DOI decoding curve, obtaining DOI information through light distribution for image reconstruction.
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| CN201810366676.0A CN110389373B (en) | 2018-04-23 | 2018-04-23 | Crystal module, detector and high-degree decoding method thereof |
| PCT/CN2019/080296 WO2019205885A1 (en) | 2018-04-23 | 2019-03-29 | Crystal module, detector, and height decoding method therefor |
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| CN201810366676.0A CN110389373B (en) | 2018-04-23 | 2018-04-23 | Crystal module, detector and high-degree decoding method thereof |
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|---|---|---|---|---|
| EP0821247A2 (en) * | 1996-07-16 | 1998-01-28 | Saint-Gobain Industrial Ceramics, Inc. | Scintillation crystal modules and methods of making the same |
| CN106562799A (en) * | 2016-10-19 | 2017-04-19 | 武汉中派科技有限责任公司 | Detector for positron emission imaging equipment, and positron emission imaging equipment |
| CN107121692A (en) * | 2017-06-05 | 2017-09-01 | 中派科技（深圳）有限责任公司 | Detector and the transmitting imaging device with the detector |
| CN107272043A (en) * | 2017-06-05 | 2017-10-20 | 中派科技（深圳）有限责任公司 | Detector and the transmitting imaging device with the detector |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| JP2003240857A (en) * | 2002-02-19 | 2003-08-27 | Shimadzu Corp | Radiation detector |
| US7956331B2 (en) * | 2007-10-26 | 2011-06-07 | Zecotek Imaging Systems Pte. Ltd | Scintillation detector for positron emission tomography |
| US8399843B2 (en) * | 2008-12-17 | 2013-03-19 | Saint-Gobain Ceramics & Plastics, Inc. | Scintillation array method and apparatus |
| CN103393434B (en) * | 2013-08-09 | 2015-04-08 | 中国科学院高能物理研究所 | Method for obtaining system response model of positron emission tomography and method for image reconstruction |
| CN104237924B (en) * | 2014-08-20 | 2017-07-28 | 许剑锋 | Grid mould includes the detector and transmitting imaging device of the grid mould |
| CN107110981A (en) * | 2014-10-23 | 2017-08-29 | 派西斯电子医疗Pet探测仪股份公司 | For X-ray or the detector assembly of gamma-ray detector |
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Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0821247A2 (en) * | 1996-07-16 | 1998-01-28 | Saint-Gobain Industrial Ceramics, Inc. | Scintillation crystal modules and methods of making the same |
| CN106562799A (en) * | 2016-10-19 | 2017-04-19 | 武汉中派科技有限责任公司 | Detector for positron emission imaging equipment, and positron emission imaging equipment |
| CN107121692A (en) * | 2017-06-05 | 2017-09-01 | 中派科技（深圳）有限责任公司 | Detector and the transmitting imaging device with the detector |
| CN107272043A (en) * | 2017-06-05 | 2017-10-20 | 中派科技（深圳）有限责任公司 | Detector and the transmitting imaging device with the detector |
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| WO2019205885A1 (en) | 2019-10-31 |
| CN110389373A (en) | 2019-10-29 |
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