CN217091814U - Matrix radiation dose detector - Google Patents
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Abstract
The utility model discloses a matrix radiation dose detector, include: the system comprises a detection module and a back-end processing module; the detection module is used for receiving gamma rays to generate corresponding photocurrent signals and comprises NxM probe units, and each probe unit comprises a front collimator, a high-precision CsI scintillator and a photomultiplier which are sequentially arranged from top to bottom; the probe units are arranged in an NxM matrix form, and N and M are positive integers larger than 1; the back-end processing module comprises: the single-channel pulse amplitude analyzer, the FPGA and the MCU; each photomultiplier is correspondingly connected with one single-channel pulse amplitude analyzer, all the single-channel pulse amplitude analyzers are electrically connected with the FPGA, and the FPGA is electrically connected with the MCU; the utility model discloses can effectively scan receiving interior radiotherapy treatment patient specific organ.
Description
Technical Field
The utility model relates to a nuclear radiation monitoring technology field, more specifically the matrix radiation dose detector that says so relates to.
Background
In recent years, with the development of related technical means in the field of nuclear medicine, radiotherapy technology is becoming one of the common means for clinical treatment of malignant tumor diseases. According to statistics, the number of new tumor diseases in China is about 180 ten thousand every year, and 130 malignant tumor patients need to receive radiotherapy. Although the early common radiotherapy technology can treat most tumors, the early common radiotherapy technology also has great damage to normal tissues around the tumors, and the dose distribution of the control radiation field is not well controlled. As a new radioactive treatment means, the internal radiotherapy technology has the treatment advantages of high targeting property, remarkable treatment effect and good persistence. The internal radiotherapy treatment technology is mainly characterized in that a medicine source with radioactivity is implanted into the body of a patient through an operation or through intravenous injection, ingestion or pill swallowing and other modes, tumor cells are killed through the absorption and enrichment effect of internal organs on the radiopharmaceutical and the short-distance directional irradiation, and the internal radiotherapy treatment technology plays an irreplaceable role in the treatment of thyroid cancer, prostatic cancer, cervical cancer and malignant tumor lymph node metastasis.
Therefore, it is an urgent need to solve the above-mentioned problems by those skilled in the art to provide a detection matrix radiation dose detector capable of scanning a specific organ of a patient undergoing internal radiotherapy.
SUMMERY OF THE UTILITY MODEL
In view of this, the utility model provides a matrix radiation dose detector can effectively scan receiving interior radiotherapy treatment patient specific organ.
In order to achieve the above purpose, the utility model adopts the following technical scheme:
a matrix radiation dose detector comprising: the system comprises a detection module and a back-end processing module;
the detection module is used for receiving gamma rays to generate corresponding photocurrent signals and comprises NxM probe units, and each probe unit comprises a front collimator, a high-precision CsI scintillator and a photomultiplier which are sequentially arranged from top to bottom; the probe units are arranged in an NxM matrix form, and N and M are positive integers larger than 1;
the back-end processing module comprises: a single-channel pulse amplitude analyzer, an FPGA and an MCU; each photomultiplier is correspondingly connected with one single-channel pulse amplitude analyzer, all the single-channel pulse amplitude analyzers are electrically connected with the FPGA, and the FPGA is electrically connected with the MCU;
the single-channel pulse amplitude analyzer is used for classifying the electric pulse signals corresponding to the photocurrent signals according to the amplitude of the signal amplitude and recording the number of each type of signal;
the FPGA is used for completing integration and packaging processing of the independent pulse counting rate;
and the MCU is used for converting each independent pulse counting rate according to a calibrated conversion formula according to an instruction of the upper computer to obtain NxM absorption counting rates and obtaining accurate absorption metering data through an interpolation algorithm.
Preferably, the front collimator is a lead hollow columnar structure with a square cross section, the thickness of the front collimator is 1.5mm, the side length of the cross section is 1cm, and the height of the front collimator is 1.5cm
Preferably, the high-precision CsI scintillator is of a cubic structure, and the side length of the high-precision CsI scintillator is 1 cm.
Preferably, the photomultiplier is a cylindrical structure with a square cross section, the height of the photomultiplier is 3mm, and the side length of the cross section is 1 cm.
Preferably, the detection module is including surveying panel and casing, survey be provided with on the panel with the hollow out construction of probe unit looks adaptation, and hollow out construction's quantity with the quantity of probe unit is the same, the probe unit install in on the detection panel, the casing is the cavity structure, survey the panel conduct the roof of casing is installed on the casing, a side of casing is provided with aluminium system upper cover plate and aluminium system lower cover plate, still be provided with binding post and stores pylon on the casing, binding post includes 485 data interface and 220V power source, the stores pylon is used for hanging establishes the detector.
Preferably, the back-end processing module further includes a pulse amplifier, a scaler, and a high-voltage power supply unit, each photomultiplier is respectively and correspondingly connected to one pulse amplifier, the pulse amplifiers are respectively and correspondingly connected to the single-channel pulse amplitude analyzers, the single-channel pulse amplitude analyzers are respectively and correspondingly connected to the scaler, the scaler is electrically connected to the FPGA, and the photomultipliers are electrically connected to the high-voltage power supply unit;
the high-voltage power supply unit supplies power to the photomultiplier, the pulse amplifier converts the photocurrent signals generated by the photomultiplier into electrical pulse signals and performs amplification and shaping processing, and the scaler is used for completing D/A conversion, converting analog quantity into pulse count of recognizable digital quantity and outputting the pulse count to the FPGA.
Preferably, the MCU communicates with the FPGA through a CAN bus.
Can know via foretell technical scheme, compare with prior art, the utility model discloses a matrix radiation dose detector, this matrix radiation dose detector adopts matrix structural design, use CsI scintillation body and photomultiplier as core detector part, can effectively realize receiving the scanning detection of interior radiotherapy treatment patient specific organ, make things convenient for the doctor to accurately master the radiopharmaceutical activity distribution and the dose residual condition of a certain internal organ of patient, and install the interference that leading collimator reduces gamma ray scattering additional at each detector front end, make the detection precision of this detector higher, can assist the accurate treatment of nuclear medicine better.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings required to be used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only embodiments of the present invention, and for those skilled in the art, other drawings can be obtained according to the provided drawings without creative efforts.
Fig. 1 is a schematic overall frame diagram of a matrix radiation dose detector according to an embodiment of the present invention;
fig. 2 is a schematic diagram of a specific structure of a matrix radiation dose detector according to an embodiment of the present invention, in which a cross section of a probe unit is square;
fig. 3 is a schematic diagram of a specific structure of a matrix radiation dose detector according to an embodiment of the present invention when a cross section of a probe unit is circular;
fig. 4 is a schematic diagram of a specific structure of a matrix radiation dose detector according to an embodiment of the present invention;
fig. 5 is a schematic diagram of a specific structure of a matrix radiation dose detector according to an embodiment of the present invention;
fig. 6 is a schematic diagram illustrating an interpolation algorithm partition in a matrix radiation dose detector according to an embodiment of the present invention;
the device comprises a probe unit a, a1 pre-collimator a2 high-precision CsI scintillator a3 photomultiplier, a lower cover plate b, an upper cover plate c, a connecting terminal d and a hanger e.
Detailed Description
The technical solutions in the embodiments of the present invention will be described clearly and completely with reference to the accompanying drawings in the embodiments of the present invention, and it is obvious that the described embodiments are only some embodiments of the present invention, not all embodiments. Based on the embodiments in the present invention, all other embodiments obtained by a person skilled in the art without creative work belong to the protection scope of the present invention.
The embodiment of the utility model discloses matrix radiation dose detector, as shown in figure 1, include: the system comprises a detection module and a back-end processing module;
the detection module is used for receiving gamma rays to generate corresponding photocurrent signals and comprises NxM probe units a, as shown in FIG. 2, each probe unit a comprises a front collimator a1, a high-precision CsI scintillator a2 and a photomultiplier a3 which are sequentially arranged from top to bottom; the probe units a are arranged in an NxM matrix form, and N and M are positive integers larger than 1;
the back-end processing module includes: the single-channel pulse amplitude analyzer, the FPGA and the MCU; each photomultiplier a3 is correspondingly connected with a single-channel pulse amplitude analyzer, all the single-channel pulse amplitude analyzers are electrically connected with the FPGA, and the FPGA is electrically connected with the MCU;
the single-channel pulse amplitude analyzer is used for classifying the electric pulse signals corresponding to the photocurrent signals according to the amplitude of the signal amplitude and recording the number of each type of signal;
the FPGA is used for completing integration and packaging processing of the independent pulse counting rate;
and the MCU is used for converting each independent pulse counting rate according to a calibrated conversion formula according to an instruction of the upper computer to obtain NxM absorption counting rates and obtaining accurate absorption metering data through an interpolation algorithm.
It should be noted that:
the conversion formula is y ═ ax + b, wherein y is absorbed dose, x is pulse count, parameters a and b are obtained by measuring a group (generally 20-40 groups of data) of absorbed dose and corresponding data of pulse count, and then absorbed dose is obtained by predicting other pulse counts through a and b.
In order to further implement the technical scheme, the front collimator a1 is a lead hollow columnar structure with a square section, the thickness is 1.5mm, the side length of the section is 1cm, and the height is 1.5 cm.
It should be noted that:
fig. 2 is a schematic diagram of the structure of a single detector, in which: the pre-collimator a1 is mainly designed by a lead square columnar structure with the thickness of 1.5mm, the length is 1cm, the size can ensure that gamma rays at the corresponding position can be accurately received, and meanwhile, the interference of nearby scattered gamma rays can be filtered.
In order to further implement the technical scheme, the high-precision CsI scintillator a2 is of a cubic structure, and the side length of the CsI scintillator a2 is 1 cm.
In order to further implement the above technical solution, the photomultiplier a3 has a square cross section and a columnar structure, the height of the columnar structure is 3mm, and the side length of the cross section is 1 cm.
It should be noted that:
the pre-collimator a1, the high-precision CsI scintillator a2 and the photomultiplier a3 may be all configured to be cylindrical, i.e., circular in cross-section, as shown in fig. 3, and may be configured as needed in practical applications.
In order to further implement the technical scheme, as shown in fig. 4, the detection module includes a detection panel and a housing, the detection panel is provided with hollow structures adapted to the probe units a, the number of the hollow structures is the same as that of the probe units a, the probe units a are mounted on the detection panel, the housing is of a cavity structure, the detection panel is mounted on the housing as a top plate of the housing, one side surface of the housing is provided with an aluminum upper cover plate c and an aluminum lower cover plate b, the housing is further provided with a connection terminal d and a hanging rack e, the connection terminal d includes a 485 data interface and a 220V power interface, and the hanging rack e is used for hanging the detector.
It should be noted that:
the matrix radiation dose detector can be hung on a three-dimensional motion platform, can be driven by a multi-axis controller to move up and down, back and forth and left and right, realizes the depth three-dimensional scanning detection of a specific organ of a patient receiving internal radiotherapy treatment, and is convenient for a doctor to accurately master the activity distribution and dose residual condition of a radiopharmaceutical in a certain organ of the patient.
And the shell is an aluminum shell and is used for packaging the probe unit a to form a matrix type detector array.
In order to further implement the technical scheme, the back-end processing module further comprises pulse amplifiers, scalers and a high-voltage power supply unit, each photomultiplier a3 is correspondingly connected with one pulse amplifier, the pulse amplifiers are correspondingly connected with single-channel pulse amplitude analyzers one by one, the single-channel pulse amplitude analyzers are correspondingly connected with the scalers one by one, the scalers are electrically connected with the FPGA, and the photomultipliers are electrically connected with the high-voltage power supply unit;
the high-voltage power supply unit supplies power to the photomultiplier a3, the pulse amplifier converts a photocurrent signal generated by the photomultiplier a3 into an electrical pulse signal and performs amplification and shaping processing, and the scaler is used for completing D/A conversion, converting an analog quantity into a pulse count of a recognizable digital quantity and outputting the pulse count to the FPGA.
In order to further implement the technical scheme, the MCU is communicated with the FPGA through a CAN bus.
It should be noted that:
considering the average size of human organs, in this embodiment, N and M are preferably set to 10, i.e., the matrix radiation dose detector is configured with 100 detectors, and the detection width range of the size covers the size of each main organ of the human body; in addition, the matrix type radiation dose detector is provided with 10 probe units a according to the design of each row and each column, so that the effective coverage and the detection precision of detection data can be ensured; after the multi-channel radiation detector finishes one-time human body scanning, 100 grid data which are 10 multiplied by 10 in total can be obtained, and a dose distribution situation graph of a human body organ range can be finally obtained through data interpolation.
In the actual application process, N and M may be further set as required. For example, N may be set to 1 and M may be set to 13, as shown in fig. 5.
In the embodiment, the silicon photomultiplier a3 is adopted to realize the above operation, and the FPGA mainly adopts a Stratix series chip produced by Altera, which has high processing performance and can ensure the real-time performance of data processing and conversion; the MCU adopts STM32F407 series single-chip microcomputer produced by ST Micro electronics.
The overall working principle of the embodiment is as follows:
the matrix radiation dose detector detects rays, gamma rays firstly pass through a front collimator a1 of each probe unit a to filter the interference of nearby scattered rays, the rays entering the probe units a are ensured to be from ray beams in front of the probe units a, the gamma rays enter a CsI scintillator and react with doping substances in the scintillator to generate fluorescence, and the fluorescence is converted, multiplied and amplified by a photomultiplier tube a3 to generate a photocurrent signal and then is transmitted to a rear-end processing module for further amplification and signal processing. 100 high-voltage power supply modules in the rear-end processing module respectively provide high-voltage supply for a photomultiplier a3 of the 100 probes, so that the normal operation of the photomultiplier a3 is ensured; the current signal generated by the photomultiplier a3 is converted into an electric pulse signal through a pulse amplifier, and the electric pulse signal is amplified and shaped; the converted electric pulse signals are processed by a single-channel pulse amplitude analyzer, classified according to the amplitude of the pulse signals and the number of each type of signals is recorded; then, the scaler completes D/A conversion, and converts the analog quantity into recognizable digital quantity, namely pulse count; and then the FPGA carries out comprehensive processing to complete the integration and the packaging processing of 100 paths of independent pulse counting rates, the MCU is an interactive medium of the detector and an upper computer control system to realize the interaction with an upper computer instruction and the data transmission, the MCU communicates with the FPGA through a CAN bus after receiving an upper computer data acquisition instruction, the 100 paths of pulse counting rates are converted according to a conversion formula calibrated by each independent probe data respectively and are converted into corresponding absorption dose rates, the packaging processing is carried out simultaneously, and the pulse counting rates are uniformly packaged and sent to the upper computer for comprehensive analysis and display processing.
In order to further implement the above technical solution, the interpolation algorithm includes the following:
s1, establishing a coordinate system, dividing P multiplied by P grids, taking any point (x, y) as a point to be interpolated, and taking a corresponding absorbed dose value as D x，y ；
S2, taking parallel lines parallel to an x axis by passing through a point (x, y) to be interpolated, wherein the coordinates of projection points on the parallel lines and the two diagonal lines are (y, y) and (P-y, y) respectively;
s3, respectively calculating the absorbed dose values of the coordinates of the projection points through a linear interpolation formula:
s4, calculating the absorbed dose of the point (x, y) to be interpolated through a linear interpolation formula according to the absorbed dose value;
for the first zone, where the parallel lines parallel to the x-axis pass through the point (x, y) to be interpolated, the absorbed dose scores are:
the absorbed dose is:
for the second zone, where the parallel lines parallel to the y-axis pass through the point (x, y) to be interpolated, the absorbed dose scores are:
the absorbed dose is:
for the third zone, where the parallel lines parallel to the y-axis are taken through the point (x, y) to be interpolated, the absorbed dose score is:
the absorbed dose is:
for the fourth zone, where the parallel lines parallel to the x-axis pass through the point (x, y) to be interpolated, the absorbed dose scores are:
the absorbed dose is:
it should be noted that:
in the above embodiment, the multi-channel radiation dose detection with N set to 10 can obtain 100-shot dose data in total of 10 × 10 per scanning, but since the monitored data on the 10 × 10 grid is mainly discrete points, only centimeter-level resolution efficiency can be achieved, and the fineness of millimeter level cannot be achieved, in order to better reflect the gradient effect of radiation dose distribution of a certain organ of a human body, the embodiment further adopts a four-region secondary linear interpolation algorithm, and obtains corresponding values through value production operation of values of four adjacent points to be interpolated, upper, lower, left, and right.
The above algorithm will be exemplified in detail below:
s1, setting grids where interpolation points are located, and respectively extending a horizontal axis and a vertical axis along the right direction and the left side upward direction of the bottom edge, wherein the horizontal axis is an x axis, and the vertical axis is a y axis. The grid (hereinafter referred to as grid) with the interpolation points is equally divided into 100 parts on four sides, that is, M is set to 100, a 100 × 100 cell matrix can be formed, the scale of each cell is 1, and the actual size represented by the grid is 50 mm/100-0.5 mm.
The point where the x axis and the y axis meet is the origin of coordinates, and the minimum value of the coordinate axes is 0; along the transverse x-axis, the maximum is 100 because the grid is divided into 100 equal parts; along the longitudinal y-axis, it is likewise divided into 100 equal parts, so that the maximum value is also 100.
The projection values of each point in a 100 × 100 cell (hereinafter referred to as a cell) on the horizontal axis and the vertical axis are defined as the coordinates of the point, for example, the coordinates of four vertices of the grid in the clockwise direction from the upper left are (0, 100), (100, 0) and (0, 0), and the coordinate of the center point is (50, 50).
If the coordinate of a certain point is (x, y), the absorbed dose value is D x，y (ii) a The absorbed dose values of four vertexes on the grid are respectively marked as D from the upper left along the clockwise direction 0,100 、D 100,100 、D 100，0 And D 0,0 The absorbed dose at the center point is
Dividing the grid into four areas, connecting two vertexes of the diagonal angle by straight lines along the diagonal line respectively by four vertexes of the grid, and dividing the grid into four isosceles triangle areas, wherein the range of the four areas is shown in fig. 6:
the 1 st area coordinate value range is as follows: x is more than or equal to 0 and less than 50, and y is more than or equal to 0 and less than or equal to x; x is more than 50 and less than or equal to 100, y is more than or equal to 0 and less than or equal to 100-x
The 2 nd area coordinate value range: x is more than or equal to 0 and less than or equal to 50, x is less than or equal to 100-x
The value range of the 3 rd zone coordinate is as follows: x is more than 50 and less than or equal to 100, y is more than 100-x and less than x
The value range of the 4 th area coordinate is as follows: x is more than or equal to 0 and less than 50, and y is more than or equal to 100-x and less than or equal to 100; x is more than 50 and less than or equal to 100, and y is more than or equal to x and less than or equal to 100
Wherein, the 1 st area is used as a point D to be interpolated x,y For example, the algorithm calculation process is described, and the interpolation calculation process of other regions is the same as that of region 1.
S2, parallel lines parallel to the x axis are made to pass through a point (x, y) to be interpolated, and coordinates of projection points on the parallel lines and the two diagonal lines are (y, y) and (100-y, y) respectively;
s3, calculating absorbed dose values D of coordinates (y, y) and (100-y, y) through a linear interpolation formula (y ， y) And D (100-y，y) Since three sets of coordinates (0, 0), (100 ), (100, 0) form a right isosceles triangle, and the other three sets of coordinates (0, 0), (y, y), (y, 0) also form a triangle with the vertex of the previous right isosceles triangle. According to the geometric theorem of similar triangles, the distance from the coordinate origin (0, 0) to (x, y) is proportional to the projection distance of the two points on the x axis, and the distance from the coordinate origin (0, 0) to (100 ) is also proportional to the projection distance of the two points on the x axis. Therefore, the projection distance of each point on the x axis can be directly substituted by calculating the data of each length on the diagonal without calculating the data of each length on the diagonal, and the following can be obtained:
s4, borrowing calculated D y，y And D 100-y，y Calculating the absorbed dose of the point (x, y) to be interpolated by a linear interpolation formula
S2-S4 may be re-executed as necessary to sequentially calculate the absorbed dose values of the interpolation points belonging to the 1 st region. Finally, the absorbed dose values generated by interpolation of the obtained 4 regions can be calculated and summarized so as to generate a radiation dose thermodynamic diagram.
To above-mentioned four district secondary linear interpolation algorithm, the utility model discloses in utilize two diagonals to fall into four regions with the net, every region is by the isosceles triangle that the net central point and two adjacent net summits constitute, through the gradient change law of two oblique sides of triangle-shaped and the horizontal gradient change law parallel with the triangle-shaped base confirm actual interpolation numerical value, eliminated the uncertainty of four summits to interpolation point influence.
The embodiments in the present description are described in a progressive manner, each embodiment focuses on differences from other embodiments, and the same and similar parts among the embodiments are referred to each other. The device disclosed by the embodiment corresponds to the method disclosed by the embodiment, so that the description is simple, and the relevant points can be referred to the method part for description.
The previous description of the disclosed embodiments is provided to enable any person skilled in the art to make or use the present invention. Various modifications to these embodiments will be readily apparent to those skilled in the art, and the generic principles defined herein may be applied to other embodiments without departing from the spirit or scope of the invention. Thus, the present invention is not intended to be limited to the embodiments shown herein but is to be accorded the widest scope consistent with the principles and novel features disclosed herein.
Claims (7)
1. A matrix radiation dose detector, comprising: the system comprises a detection module and a back-end processing module;
the detection module is used for receiving gamma rays to generate corresponding photocurrent signals and comprises NxM probe units, and each probe unit comprises a front collimator, a high-precision CsI scintillator and a photomultiplier which are sequentially arranged from top to bottom; the probe units are arranged in an NxM matrix form, and N and M are positive integers larger than 1;
the back-end processing module comprises: the single-channel pulse amplitude analyzer, the FPGA and the MCU; each photomultiplier is correspondingly connected with one single-channel pulse amplitude analyzer, all the single-channel pulse amplitude analyzers are electrically connected with the FPGA, and the FPGA is electrically connected with the MCU;
the single-channel pulse amplitude analyzer is used for classifying the electric pulse signals corresponding to the photocurrent signals according to the amplitude of the signal amplitude and recording the number of each type of signal;
the FPGA is used for completing integration and packaging processing of the independent pulse counting rate;
and the MCU is used for converting each independent pulse counting rate according to a calibrated conversion formula according to an instruction of the upper computer to obtain NxM absorption dose rates, and acquiring accurate absorption metering data through an interpolation algorithm.
2. A matrix radiation dose detector as claimed in claim 1, wherein said pre-collimator is a lead hollow cylinder with a square cross-section and a thickness of 1.5mm, and the cross-section has a side length of 1cm and a height of 1.5 cm.
3. A matrix radiation dose detector according to claim 1, characterized in that said high accuracy CsI scintillator is of a cubic structure with 1cm side length.
4. The matrix type radiation dose detector as claimed in claim 1, wherein said photomultiplier tube has a square cross section and a cylindrical shape with a height of 3mm and a side length of 1 cm.
5. The matrix radiation dose detector according to claim 1, wherein said detection module comprises a detection panel and a housing, said detection panel has a plurality of hollowed-out structures matching said probe units, said hollowed-out structures are equal in number to said probe units, said probe units are mounted on said detection panel, said housing has a cavity structure, said detection panel is mounted on said housing as a top plate of said housing, one side surface of said housing is provided with an aluminum upper cover plate and an aluminum lower cover plate, said housing is further provided with a connection terminal and a hanging rack, said connection terminal comprises a 485 data interface and a 220V power interface, and said hanging rack is used for hanging said detector.
6. The matrix radiation dose detector according to claim 1, wherein said back-end processing module further comprises pulse amplifiers, scalers and high voltage power supply units, each of said photomultiplier tubes is connected with a corresponding one of said pulse amplifiers, each of said pulse amplifiers is connected with a corresponding one of said single pulse amplitude analyzers, each of said single pulse amplitude analyzers is connected with a corresponding one of said scalers, each of said scalers is electrically connected with said FPGA, and each of said photomultiplier tubes is electrically connected with said high voltage power supply unit;
the high-voltage power supply unit supplies power to the photomultiplier, the pulse amplifier converts the photocurrent signals generated by the photomultiplier into electrical pulse signals and performs amplification and shaping processing, and the scaler is used for completing D/A conversion, converting analog quantity into pulse count of recognizable digital quantity and outputting the pulse count to the FPGA.
7. A matrix-type radiation dose detector according to claim 1, wherein said MCU communicates with said FPGA via a CAN bus.
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