CN108562928B - Detector for positron emission imaging apparatus and positron emission imaging apparatus - Google Patents
Detector for positron emission imaging apparatus and positron emission imaging apparatus Download PDFInfo
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Abstract
The invention provides a detector and an emission imaging apparatus having the same. The detector includes scintillation crystal module and photoelectric sensor array, and the scintillation crystal module includes a plurality of slice scintillation crystal units, each the slice scintillation crystal unit has the through-hole, and a plurality of slice scintillation crystal unit axial are piled up in order to form the scintillation crystal module piles up and forms the scintillation crystal module has inner wall, outer wall and through-hole, the through-hole is used for holding treating the formation of image object. The photoelectric sensor array is coupled on the inner wall of the scintillation crystal module or/and the outer wall of the scintillation crystal module and is used for detecting visible photons generated by the reaction of gamma photons and the scintillation crystal module, wherein the gamma photons are generated through positron annihilation effect generated in the body of the object to be imaged. The detector has low processing difficulty, simple assembly and higher DOI decoding precision and position decoding capability.
Description
Technical Field
The invention relates to the field of positron emission imaging, in particular to a detector for positron emission imaging equipment and the positron emission imaging equipment.
Background
A medical Positron Emission Tomography (PET) system is a representative product of international advanced medical devices, and is a technology for displaying the internal structure of a human body or an animal body by using a radioactive element tracing method, and is widely applied to early diagnosis, treatment scheme formulation, prognosis effect prediction, drug efficacy evaluation and the like of tumors, cardiovascular and cerebrovascular diseases and neurodegenerative diseases in clinic.
In a conventional medical positron emission tomography system, a detector system generally includes a plurality of square detector modules connected by a mechanical structure to form a cylindrical envelope structure for intercepting and receiving gamma photons released from radioactive substances. Specifically, the square detector module is formed by coupling a scintillation crystal (scintillation crystal array) and a photosensor, and some designs also put a readout circuit into the module; a plurality of square detectors are fixed through a complex mechanical structure and arranged along a cylindrical surface or a spherical surface to form a gamma photon detection layer.
Due to the assembly and splicing of the detectors, the traditional positron emission imaging equipment mostly adopts a discrete crystal design, and the design of the discrete crystal often causes the following problems:
(1) the difficulty of crystal processing is large: the traditional square crystal design often uses a small-sized scintillation crystal unit to improve the system resolution, but the method has strict requirements on crystal processing and high cost;
(2) edge effect: an edge effect may occur in the discrete crystal assembly design, so that the detected photon position information cannot correctly reflect light distribution, the decoding precision is low, and the spatial resolution of imaging equipment is low;
(3) assembly has a position error: positioning errors are easily generated by the detector modules which are assembled together, so that the detection of a coincidence event is deviated, and the spatial resolution of the imaging equipment is further influenced;
(4) detecting a gap: the detection gap comprises a crystal assembly gap: can produce great equipment clearance during discrete crystal concatenation, survey module clearance: when the square detection modules are arranged along the ring shape, a complete detection surface cannot be formed, and both the square detection modules can cause the occurrence of a detection gap, so that the system sensitivity is reduced.
The conventional positron emission imaging device also adopts a flaky continuous crystal design, and the flaky continuous crystal is optically connected to form a semi-continuous crystal, which is a long-standing solution. The method reduces the requirements on the difficulty of the crystal processing technology to a certain extent, but still cannot solve the problems caused by the edge effect.
Therefore, it is necessary to provide a detector for a positron emission tomography apparatus and a positron emission tomography apparatus including the detector to reduce the difficulty of mechanical design, improve the system sensitivity and spatial resolution, improve the decoding accuracy, and further improve the system resolution.
Disclosure of Invention
According to one aspect of the invention, a detector for a positron emission imaging device is provided, which comprises a scintillation crystal module and a photosensor array, wherein the scintillation crystal module comprises a plurality of sheet-shaped scintillation crystal units, each sheet-shaped scintillation crystal unit is provided with a through hole, the plurality of sheet-shaped scintillation crystal units are stacked axially to form the scintillation crystal module, and the scintillation crystal module formed by stacking is provided with an inner wall, an outer wall and a through hole, and the through hole is used for accommodating an object to be imaged. The photoelectric sensor array is coupled on the inner wall of the scintillation crystal module or/and the outer wall of the scintillation crystal module and is used for detecting visible photons generated by the reaction of gamma photons and the scintillation crystal module, wherein the gamma photons are generated through positron annihilation effect generated in the body of the object to be imaged.
Preferably, two adjacent flake-shaped scintillation crystal units are connected through a light reflecting layer.
Preferably, the light reflecting layer is provided with a light transmitting window.
Preferably, one light-transmitting window is arranged on each light reflecting layer and is arranged inside or outside the light reflecting layer; or, the number of the light-transmitting windows on each reflecting layer is two, and the two light-transmitting windows are respectively arranged inside and outside the reflecting layer; or, the light-transmitting windows on each light-reflecting layer are multiple, and the multiple light-transmitting windows are arranged on the light-reflecting layer at intervals in an arrangement mode from inside to outside or from outside to inside.
Preferably, the scintillation crystal module is in a polygonal prism shape or a cylindrical shape as a whole.
Preferably, the through hole is circular or polygonal.
Preferably, the plate-shaped scintillation crystal unit is formed by connecting a plurality of scintillation crystals.
Preferably, the scintillation crystal module comprises an inner layer scintillation crystal module and an outer layer scintillation crystal module, the inner layer scintillation crystal module comprises a plurality of first sheet-shaped scintillation crystal units, each first sheet-shaped scintillation crystal unit is provided with a first through hole, and the plurality of first sheet-shaped scintillation crystal units are axially stacked to form the inner layer scintillation crystal module; the outer layer scintillation crystal module comprises a plurality of second sheet-shaped scintillation crystal units, each second sheet-shaped scintillation crystal unit is provided with a second through hole, and the plurality of second sheet-shaped scintillation crystal units are axially stacked to form the outer layer scintillation crystal module; the first flaky scintillation crystal units can be accommodated in the second through holes, and the first flaky scintillation crystal units of the inner layer scintillation crystal module are arranged in a staggered mode relative to the second flaky scintillation crystal units of the outer layer scintillation crystal module.
Preferably, the photosensor array includes a plurality of photosensors, one of which is coupled with one of the sheet-like scintillation crystal units, respectively.
Preferably, the photosensor array includes a plurality of photosensors, at least one of which is coupled with a plurality of the sheet-like scintillation crystal units, respectively.
Preferably, the photosensor array comprises m × n photosensors, where m and n are positive integers, and the photosensors in the m-th row are arranged in a staggered manner from the photosensors in the m + 1-th row.
Preferably, the photosensor array includes m × n photosensors, where m and n are positive integers, and the photosensor on the nth column is arranged offset from the photosensor on the (n + 1) th column.
According to another aspect of the present invention, there is also provided a positron emission imaging apparatus, including a readout circuit module, a data processing module and the detector as described above, wherein the readout circuit module is connected to the photosensor array, and is configured to receive an electrical signal output by the photosensor array, and output energy information and time information of gamma photons, and the electrical signal is obtained by converting an optical signal of a visible photon detected by the photosensor array. The data processing module is connected with the reading circuit module and is used for carrying out data processing and image reconstruction on the energy information and the time information so as to obtain a scanning image of an object to be imaged.
Because the flaky scintillation crystal units with the through holes are stacked to form the scintillation crystal module, the detector provided by the invention has the following advantages:
1. the crystal processing difficulty is reduced, and the system cost is reduced;
2. the continuous or semi-continuous crystal structure can reduce decoding errors caused by edge effects;
3. the crystal is simple to assemble, and the position error caused by multi-module positioning and splicing can be greatly reduced;
4. and the system sensitivity is fully improved due to extremely small or even no crystal gap.
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 block diagram of a detector for a positron emission imaging apparatus in accordance with one embodiment of the present invention;
FIGS. 2 a-2 d are schematic views of a transparent window according to an embodiment of the present invention;
FIG. 3 is a schematic diagram of DOI decoding by a detector according to an embodiment of the invention;
FIG. 4 is a diagram of a windowed DOI decoding principle according to an embodiment of the present invention;
FIGS. 5 a-5 d are block diagrams of a plate-like scintillation crystal cell according to an embodiment of the invention;
FIG. 6 is a block diagram of a scintillation crystal module according to yet another embodiment of the invention;
FIGS. 7 a-7 d are block diagrams of a plate-like scintillation crystal cell according to yet another embodiment of the invention;
FIG. 8 is a block diagram of a detector for a positron emission imaging apparatus in accordance with yet another embodiment of the invention;
FIGS. 9 a-9 c are schematic diagrams of one coupling of a photosensor array of a detector according to an embodiment of the present invention;
FIGS. 10 a-10 d are schematic diagrams of the coupling of photosensors and plate-like scintillation crystal cells on the same light readout side according to an embodiment of the invention;
figure 11 is a schematic diagram of a positron emission imaging apparatus in accordance with one embodiment of the invention.
Wherein the reference symbols are
10-crystal module
11-plate scintillation crystal unit
111-through hole
101-scintillation crystal
102-connecting body
105-through hole
110-inner layer scintillation crystal module
1101-first sheet-like scintillation crystal unit
1111-through hole
120-outer layer scintillation crystal module
1201-second plate-like scintillation crystal unit
1211-through hole
20. 20' -photoelectric sensor array
21-photoelectric sensor
30-light guide
40-light reflecting layer
40' -retroreflective sheeting
50-light-transmitting window
100-detector module
200-readout circuit module
300-data processing module
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 may be practiced without one or more of these specific 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.
A detector for a positron emission imaging apparatus includes a scintillation crystal module and a photosensor array. As shown in fig. 1, the scintillator crystal module 10 includes a plurality of sheet-like scintillator crystal units 11, each sheet-like scintillator crystal unit 11 having a through hole 111, the plurality of sheet-like scintillator crystal units 11 being stacked axially to form the scintillator crystal module 10, the stacked scintillator crystal module having an inner wall 106, an outer wall 108, and a through hole 105. The through hole 105 is used for accommodating an object to be imaged, and a center line of the through hole 105 coincides with a center line of the through hole 111. The photosensor array 20 is coupled to an outer wall 108 of the scintillation crystal module, and a surface of the outer wall 108 is a light readout surface (in the following, an embodiment in which the photosensor array is coupled to an inner wall 106 of the scintillation crystal module, and both the inner wall 106 and the outer wall 108 of the scintillation crystal module) for detecting visible photons generated by a reaction of gamma photons with the scintillation crystal module 10, wherein the gamma photons are generated by a positron annihilation effect occurring in a subject to be imaged.
As can be seen from the above structural description, the detector of the positron emission imaging apparatus of the present invention is assembled into the scintillation crystal module 10 by the plate-shaped scintillation crystal units 11 with the through holes 111, the plate-shaped scintillation crystal units 11 can be connected with each other by the reflective layer 40 (i.e., adjacent two plate-shaped scintillation crystal units are connected with each other by the reflective layer 40), and the plate-shaped scintillation crystal units 11 are stacked axially to meet the requirement of the axial field length. The retroreflective layer 40 can be made from a wide variety of materials, including diffuse reflective materials: BaSO4, plating film, etc., specular reflective material: ESR, plating film, and the like; diffuse emission, specular reflection hybrid material: teflon adhesive tape, titanium oxide coating and the like can ensure that light can pass between adjacent flaky scintillation crystal units 11 by adjusting the thickness of the reflecting layer 40, thereby realizing position decoding.
In the actual assembly process, a plurality of the plate-shaped scintillation crystal units 11 can be assembled into a small scintillation crystal module, and then a plurality of small scintillation crystal modules are axially stacked into the scintillation crystal module 10.
Illustratively, the photosensor array 20 and the scintillation crystal module 10 can be connected through a light guide 30, so that the photosensors can detect the optical signals of the uncoupled crystals, and position decoding is realized. In an embodiment not shown, the scintillation crystal module 10 and the photosensor array 20 can be directly coupled together by means of a coupling agent, such as optical glue, or by means of air coupling, etc.
Illustratively, the light-transmitting window 50 may be formed on the light-reflecting layer 40, and the light-transmitting window 50 may be implemented by using a light-reflecting material, air or optical glue.
Referring to fig. 2a to 2d, the light-transmissive windows 50 may be disposed in various manners, for example, one light-transmissive window 50 on each light-reflective layer 40 is disposed in the interior of the light-reflective layer 40 (see fig. 2a), where the interior is closer to the inner wall 106 of the scintillation crystal module than the exterior described later; alternatively, one light-transmissive window 50 on each light-reflective layer 40 is disposed on the exterior of the light-reflective layer 40 (see fig. 2b), where the exterior is closer to the outer wall 108 of the scintillator crystal module than the interior as described above; alternatively, two light-transmitting windows 50 are provided on each light-reflecting layer 40, respectively arranged on the inner and outer sides of the light-reflecting layer 40 (see fig. 2 c); alternatively, there are a plurality of light-transmitting windows 50 on each light-reflecting layer 40, and the light-transmitting windows 50 are arranged on the light-reflecting layer 50 at intervals in an arrangement manner from inside to outside or from outside to inside (see fig. 2 d).
Referring to fig. 3, for the crystal module composed of the plate-shaped scintillation crystal units 11, taking the structure and the transparent window in fig. 1 as an example, the following position decoding method is proposed:
1. height direction decoding: the photoelectric sensor array 20 is used for measuring the light distribution in the height direction to realize decoding in the height direction, and the algorithm can be a gravity center algorithm, a neural network algorithm or other algorithms;
2. decoding the angle direction: the photoelectric sensor array 20 is used for measuring the light distribution in the angle direction to realize the decoding in the angle direction, and the algorithm can be a gravity center algorithm, a neural network algorithm or other algorithms;
3. DOI (radial direction) decoding: measuring the light distribution for decoding the DOI direction by the photoelectric sensor array 20, wherein the algorithm can be a neural network algorithm or other algorithms; as shown in the upper left corner of fig. 3, the photoelectric sensor 21 reads out both ends, reads the half-peak width and peak value of the energy signal, and implements DOI decoding using a neural network algorithm.
As shown in fig. 4, a plurality of plate-shaped scintillation crystal units 11 are stacked axially to form a scintillation crystal module, the photosensor 21 is coupled to an outer wall of the scintillation crystal module, one light-transmitting window 50 is arranged on each light-reflecting layer 40, and the light-transmitting windows are arranged inside the light-reflecting layers 40, that is, by using an internal single-window method, reaction positions at different depths can obtain large-difference light distribution from the single-ended photosensor 21, thereby realizing DOI decoding.
Illustratively, as shown in fig. 5a, the plate-shaped scintillation crystal unit 11 is circular, the through hole 111 is also circular, and the scintillation crystal module 10 formed by stacking a plurality of plate-shaped scintillation crystal units 11 in the axial direction is cylindrical (as shown in fig. 1).
Illustratively, as shown in fig. 5b, the plate-shaped scintillation crystal unit 11 is circular, the through hole 111 is polygonal, and the scintillation crystal module 10 formed by stacking a plurality of plate-shaped scintillation crystal units 11 in the axial direction is cylindrical as a whole.
Illustratively, as shown in fig. 5c, the plate-shaped scintillation crystal unit 11 is polygonal, the through hole 111 is circular, and the scintillation crystal module 10 formed by stacking a plurality of plate-shaped scintillation crystal units 11 in the axial direction is polygonal as a whole.
Illustratively, as shown in fig. 5d, the plate-shaped scintillation crystal unit 11 is polygonal, the through hole 111 is also polygonal, and the scintillation crystal module 10 formed by stacking a plurality of plate-shaped scintillation crystal units 11 in the axial direction is polygonal as a whole. It should be noted that in the case where the sheet-like scintillation crystal unit 11 is polygonal, and the through-holes 111 are also polygonal through-holes, the number of sides of the sheet-like scintillation crystal unit 11 and the number of sides of the through-holes may be the same or may be different.
Although in fig. 5c and 5d the plate-like scintillation crystal units 11 are shown as hexagonal structures and the axially stacked scintillation crystal module 10 is overall hexagonal prism-like, it should be noted that the number of sides of the plate-like scintillation crystal units 11 can be any suitable number, and the invention is not limited thereto. For example, the plate-shaped scintillation crystal units 11 may be triangular, quadrangular, pentagonal, etc., and correspondingly, the axially stacked scintillation crystal modules may be triangular prism-shaped, quadrangular prism-shaped, pentagonal prism-shaped, etc. Likewise, the through-holes may be quadrilateral through-holes, hexagonal through-holes, twenty-quadrilateral through-holes, and so forth.
FIG. 6 is a block diagram of a scintillation crystal module according to yet another embodiment of the invention. In the present embodiment, the plate-shaped scintillation crystal unit 11 is formed by connecting a plurality of scintillation crystals 101, for example, the sector ring-shaped scintillation crystals 101 are connected by a connector 102 to form an annular plate-shaped scintillation crystal unit 11, the connector may be optical glue, and the two annular plate-shaped scintillation crystal units 11 may be connected by a reflector 40'. The optical glue serves as a connection, and at the same time, light between the fan-shaped scintillation crystals 101 can be transmitted to each other to form a semi-continuous crystal, and the connection body 102 includes, but is not limited to, the optical glue.
Illustratively, as shown in fig. 7a, the scintillation crystals 101 are fan-shaped, the fan-shaped scintillation crystals 101 are connected to each other by the connecting body 102 to form an annular plate-shaped scintillation crystal unit 11, the through hole 111 is circular, and the scintillation crystal module 10 formed by axially stacking a plurality of annular plate-shaped scintillation crystal units 11 is cylindrical (see fig. 6).
Illustratively, as shown in fig. 7b, the outer edge of each scintillator crystal 101 is arc-shaped, the inner edge is linear, every two scintillator crystals 101 are connected by the connecting body 102 to form the plate-shaped scintillator crystal unit 11, the plate-shaped scintillator crystal unit 11 is circular, the through hole 111 is polygonal, and the scintillator crystal module 10 formed by axially stacking a plurality of plate-shaped scintillator crystal units 11 is cylindrical.
Illustratively, as shown in fig. 7c, the inner edge of each of the scintillation crystals 101 is linear, the outer edge of each of the scintillation crystals 101 is linear, every two scintillation crystals 101 are connected by the connecting body 102 to form the plate-shaped scintillation crystal unit 11, the plate-shaped scintillation crystal unit 11 is polygonal as a whole, the through hole 111 is circular, and the scintillation crystal module 10 formed by axially stacking the plurality of plate-shaped scintillation crystal units 11 is polygonal as a whole.
Illustratively, as shown in fig. 7d, the inner edge of each of the scintillation crystals 101 is linear, the outer edge of each of the scintillation crystals 101 is linear, every two scintillation crystals 101 are connected by the connecting body 102 to form the plate-shaped scintillation crystal unit 11, the plate-shaped scintillation crystal unit 11 is polygonal as a whole, the through hole 111 is also polygonal, and the scintillation crystal module 10 formed by axially stacking the plurality of plate-shaped scintillation crystal units 11 is polygonal as a whole. It should be noted that in the case where the sheet-like scintillation crystal unit 11 is polygonal, and the through-holes 111 are also polygonal through-holes, the number of sides of the sheet-like scintillation crystal unit 11 and the number of sides of the through-holes may be the same or may be different.
Although in fig. 7c and 7d the plate-like scintillation crystal units 11 are shown as hexagonal structures and the axially stacked scintillation crystal module 10 is overall hexagonal prism-like structures, it should be noted that the number of sides of the plate-like scintillation crystal units 11 can be any suitable number, and the invention is not limited thereto. For example, the plate-shaped scintillation crystal units 11 may be triangular, quadrangular, pentagonal, etc., and correspondingly, the axially stacked scintillation crystal modules may be triangular prism-shaped, quadrangular prism-shaped, pentagonal prism-shaped, etc. Likewise, the through-holes may be quadrilateral through-holes, hexagonal through-holes, twenty-quadrilateral through-holes, and so forth.
Fig. 8 is a block diagram of a detector according to yet another embodiment of the present invention. In the present embodiment, the scintillation crystal module 10 includes an inner layer scintillation crystal module 110 and an outer layer scintillation crystal module 120, the inner layer scintillation crystal module 110 includes a plurality of first sheet-like scintillation crystal units 1101, each first sheet-like scintillation crystal unit 1101 has a first through hole 1111, the plurality of first sheet-like scintillation crystal units 1101 are stacked axially to form the inner layer scintillation crystal module 110; the outer layer scintillation crystal module 120 comprises a plurality of second plate-shaped scintillation crystal units 1201, each second plate-shaped scintillation crystal unit 1201 has a second through hole 1211, and the plurality of second plate-shaped scintillation crystal units 1211 are axially stacked to form the outer layer scintillation crystal module 120; the first sheet shaped scintillation crystal unit 1101 can be accommodated in the second through hole 1211, and the first sheet shaped scintillation crystal unit 1101 of the inner layer scintillation crystal module 110 is arranged in a staggered manner with respect to the second sheet shaped scintillation crystal unit 1201 of the outer layer scintillation crystal module 120. The detector of the embodiment introduces a staggered double-layer scintillation crystal module, and the detector with the structure can judge the reaction depth through a decoding position.
The photoelectric sensor array is used as an important component of the detector, and factors such as the size, the detection efficiency, the position distribution and the like of the photoelectric sensor array directly influence the position decoding precision and determine the quality of later-stage image reconstruction. And the performance of the photoelectric sensor is determined by the production process. The arrangement of the photo sensor array positions may be in-coupling as shown in fig. 9a, i.e. the photo sensor array 20 is coupled to the inner wall 106 of the scintillator crystal module 10, and the surface where the inner wall 106 is located is the light-reading surface of the scintillator crystal module 10.
The arrangement of the photo sensor arrays may also be in an out-coupling manner as shown in fig. 9b, i.e. the photo sensor array 20 is coupled to the outer wall 108 of the scintillation crystal module 10, the face where the outer wall 108 is located being the light readout face of the scintillation crystal module 10.
The arrangement of the photosensor arrays can also adopt an internal-external double coupling mode as shown in fig. 9c, and the photosensor arrays are coupled to both the inner wall 106 and the outer wall 108 of the scintillation crystal module 10, that is, the photosensor array 20' is coupled to the inner wall 106 of the scintillation crystal module 10, the photosensor array 20 is coupled to the outer wall 108 of the scintillation crystal module 10, and the surface of the inner wall 106 and the surface of the outer wall 108 are both the light-reading surfaces of the scintillation crystal module 10.
There are also various ways of coupling between the photosensor and the plate-like scintillation crystal unit on the same light readout side. As shown in fig. 10a, a one-to-one coupling method is adopted, specifically, the photosensor array 20 includes a plurality of photosensors 21, only one sheet-shaped scintillation crystal unit 11 is coupled to one photosensor 21 of the plurality of photosensors, and the two sheet-shaped scintillation crystal units 11 are connected through a light reflecting layer 40. As shown in fig. 10b, a one-to-many coupling manner is adopted, specifically, the photosensor array 20 includes a plurality of photosensors 21, and at least one photosensor 21 of the plurality of photosensors is coupled with a plurality of sheet-like scintillation crystal units 11. As shown in fig. 10c, a misalignment coupling method is used, specifically, the photosensor array 20 includes m × n photosensors 21, where m and n are positive integers, and the photosensor 21 on the nth column and the photosensor 21 on the (n + 1) th column are misaligned. As shown in fig. 10d, a misalignment coupling method is adopted, specifically, the photosensor array 20 includes m × n photosensors 21, where m and n are positive integers, and the photosensors 21 in the m-th row are misaligned with the photosensors 21 in the m + 1-th row.
The detector of the invention adopts the sheet-shaped scintillation crystal units with the through holes to form the scintillation crystal module, and has the following advantages in terms of single-position decoding:
1. angular direction resolution: the continuous or semi-continuous crystal has no edge effect and has great advantages in decoding in the angle direction;
2. axial resolution: similar to conventional crystal assembly, axial resolution depends on the thickness of the assembled crystal slices;
3. DOI resolution: by applying an internal and external double coupling method or a window method, high DOI resolution can be obtained by comparing light distribution;
4. many-to-one coupling can reduce system cost, and dislocation coupling can achieve special position decoding effect.
According to another aspect of the present invention, a positron emission imaging apparatus is provided. As shown in fig. 11, the positron emission imaging apparatus includes a readout circuit module 200, a data processing module 300, and the above-mentioned detector (shown as the detector module 100 in fig. 11), wherein the readout circuit module 200 is connected to a photosensor array in the detector, and is configured to receive an electrical signal output by the photosensor array, and output energy information and time information of gamma photons, where the electrical signal is obtained by converting an optical signal of a visible photon detected by the photosensor array. The data processing module 300 is connected to the readout circuit module 200, and is configured to perform data processing and image reconstruction on the energy information and the time information to obtain a scanned image of the object to be imaged. The readout circuit module 200 and the data processing module 300 may be implemented using any suitable hardware, software and/or firmware. Illustratively, the data processing module 300 may be implemented using a Field Programmable Gate Array (FPGA), a Digital Signal Processor (DSP), a Complex Programmable Logic Device (CPLD), a Micro Control Unit (MCU), or a Central Processing Unit (CPU), etc.
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 (12)
1. A detector for a positron emission imaging apparatus, comprising:
the scintillation crystal module comprises a plurality of sheet scintillation crystal units, each sheet scintillation crystal unit is provided with a through hole, the plurality of sheet scintillation crystal units are axially stacked to form the scintillation crystal module, the stacked scintillation crystal module is provided with an inner wall, an outer wall and a through hole, and the through hole is used for accommodating an object to be imaged; and
the photoelectric sensor array is coupled on the inner wall of the scintillation crystal module or/and the outer wall of the scintillation crystal module and is used for detecting visible photons generated by the reaction of gamma photons and the scintillation crystal module, wherein the gamma photons are generated through positron annihilation effect generated in the object to be imaged;
the scintillation crystal module comprises an inner layer scintillation crystal module and an outer layer scintillation crystal module, the inner layer scintillation crystal module comprises a plurality of first sheet-shaped scintillation crystal units, each first sheet-shaped scintillation crystal unit is provided with a first through hole, and the plurality of first sheet-shaped scintillation crystal units are axially stacked to form the inner layer scintillation crystal module; the outer layer scintillation crystal module comprises a plurality of second sheet-shaped scintillation crystal units, each second sheet-shaped scintillation crystal unit is provided with a second through hole, and the plurality of second sheet-shaped scintillation crystal units are axially stacked to form the outer layer scintillation crystal module; the first flaky scintillation crystal units can be accommodated in the second through holes, and the first flaky scintillation crystal units of the inner layer scintillation crystal module are arranged in a staggered mode relative to the second flaky scintillation crystal units of the outer layer scintillation crystal module.
2. The detector of claim 1, wherein adjacent two of the plate-like scintillation crystal units are connected by a light reflecting layer.
3. The detector of claim 2, wherein the light-reflecting layer has a light-transmissive window formed therein.
4. The detector of claim 3, wherein one of said light-transmissive windows in each of said light-reflective layers is disposed in or outside of said light-reflective layer; or, the number of the light-transmitting windows on each reflecting layer is two, and the two light-transmitting windows are respectively arranged inside and outside the reflecting layer; or, the light-transmitting windows on each light-reflecting layer are multiple, and the multiple light-transmitting windows are arranged on the light-reflecting layer at intervals in an arrangement mode from inside to outside or from outside to inside.
5. The detector of claim 1, wherein the scintillation crystal module is generally polygonal or cylindrical in shape.
6. The detector of claim 1, wherein the through-hole is circular or polygonal.
7. The detector of claim 1, wherein the plate-like scintillation crystal unit is formed by a plurality of scintillation crystals connected together.
8. The detector of any of claims 1-7, wherein the photosensor array comprises a plurality of photosensors, one of the plurality of photosensors respectively coupled to one of the sheet-like scintillation crystal cells.
9. The detector of any of claims 1-7, wherein the photosensor array comprises a plurality of photosensors, at least one of the plurality of photosensors respectively coupled with a plurality of the sheet-like scintillation crystal cells.
10. The detector of any of claims 1-7, wherein the photosensor array comprises m x n photosensors, where m and n are positive integers, and the photosensors in the m-th row are misaligned with the photosensors in the m + 1-th row.
11. The detector of any one of claims 1-7, wherein the photosensor array comprises m x n photosensors, where m and n are positive integers, and the photosensors in the nth column are offset from the photosensors in the (n + 1) th column.
12. A positron emission imaging apparatus, characterized in that it comprises a readout circuitry module, a data processing module and a detector according to any one of claims 1-11,
the readout circuit module is connected with the photoelectric sensor array and used for receiving the electric signal output by the photoelectric sensor array and outputting the energy information and time information of gamma photons, wherein the electric signal is obtained by converting the optical signal of the visible photons detected by the photoelectric sensor array;
the data processing module is connected with the reading circuit module and is used for carrying out data processing and image reconstruction on the energy information and the time information so as to obtain a scanning image of an object to be imaged.
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| CN201711361772.8A CN108562928B (en) | 2017-12-18 | 2017-12-18 | Detector for positron emission imaging apparatus and positron emission imaging apparatus |
| PCT/CN2018/119268 WO2019120078A1 (en) | 2017-12-18 | 2018-12-05 | Detector for positron emission tomography device, and positron emission tomography device |
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| CN201711361772.8A CN108562928B (en) | 2017-12-18 | 2017-12-18 | Detector for positron emission imaging apparatus and positron emission imaging apparatus |
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| CN108562928B (en) * | 2017-12-18 | 2022-01-21 | 中派科技（深圳）有限责任公司 | Detector for positron emission imaging apparatus and positron emission imaging apparatus |
| CN109846504B (en) * | 2018-05-07 | 2021-06-01 | 山东麦德盈华科技有限公司 | Full-angle PET (positron emission tomography) detector |
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| US4755680A (en) * | 1984-04-27 | 1988-07-05 | The Curators Of The University Of Missouri | Radiation imaging apparatus and methods |
| EP2360493A1 (en) * | 2010-02-15 | 2011-08-24 | Bergen Teknologioverføring AS | Detector arrangement for a tomographic imaging apparatus, particularly for a positron emission tomograph |
| CN105361901A (en) * | 2015-12-19 | 2016-03-02 | 山西锦地裕成医疗设备有限公司 | Method and system for correcting depth effect of positron emission tomography |
| 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 |
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| US10234572B2 (en) * | 2014-07-25 | 2019-03-19 | The Regents Of The University Of California | Multiple spatial resolution scintillation detectors |
| CN106597518A (en) * | 2016-12-21 | 2017-04-26 | 中国科学院深圳先进技术研究院 | PET detector, PET imaging system and PET tester |
| CN106725574A (en) * | 2017-01-17 | 2017-05-31 | 孙红岩 | A kind of positron emission computerized tomography imaging system bimorph crystal detector |
| CN107272043B (en) * | 2017-06-05 | 2019-06-04 | 中派科技（深圳）有限责任公司 | Detector and transmitting imaging device with the detector |
| CN108562928B (en) * | 2017-12-18 | 2022-01-21 | 中派科技（深圳）有限责任公司 | Detector for positron emission imaging apparatus and positron emission imaging apparatus |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4755680A (en) * | 1984-04-27 | 1988-07-05 | The Curators Of The University Of Missouri | Radiation imaging apparatus and methods |
| EP2360493A1 (en) * | 2010-02-15 | 2011-08-24 | Bergen Teknologioverføring AS | Detector arrangement for a tomographic imaging apparatus, particularly for a positron emission tomograph |
| CN105361901A (en) * | 2015-12-19 | 2016-03-02 | 山西锦地裕成医疗设备有限公司 | Method and system for correcting depth effect of positron emission tomography |
| 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 |
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