CN111035862A - Medical accelerator and dose monitoring method based on electron beam extraction process - Google Patents
Medical accelerator and dose monitoring method based on electron beam extraction process Download PDFInfo
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- A—HUMAN NECESSITIES
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- A61N5/1071—Monitoring, verifying, controlling systems and methods for verifying the dose delivered by the treatment plan
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- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
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Abstract
The invention relates to the technical field of medical accelerators and discloses a medical accelerator, wherein an accelerating tube, a beam pipeline and a beam needle share a central shaft and are communicated with a straight-line channel, so that an electron beam is transmitted in the straight-line channel; the side surface of the beam pipeline is connected with a beam eduction tube, the first electron beam is transmitted in the beam eduction tube, and the periphery of the beam pipeline is provided with a deflection magnetic field generating device which periodically prompts the electron beam to change the transmission direction and output from the beam eduction tube. The dosage monitoring method of the medical accelerator is also disclosed, before treatment, the dosage of the first electron beam and the dosage of the second electron beam are tested simultaneously to establish a relevant numerical relation, and during treatment, the dosage of the second electron beam is monitored by testing the dosage of the first electron beam. According to the invention, through the beam extraction tube and the deflection magnetic field generating device, few parts of electron beams are extracted for synchronous testing, the step of measuring the dose is simple and convenient, the treatment process is not influenced, the on-line dose monitoring is realized, and the method is feasible and has reliable results.
Description
Technical Field
The invention relates to the technical field of medical accelerators, in particular to a medical accelerator and a dose monitoring method based on an electron beam extraction process.
Background
According to the requirements of the national standard GB9706.5-2008, a dose monitoring system must be included in the medical electronic linear accelerator. The dose monitoring system used by the traditional medical accelerator consists of an ionization chamber detector and an auxiliary circuit thereof. The ionization chamber is positioned in the radiation system, is arranged between the homogenizing filter or the scattering foil and the secondary collimator of the photon line, and consists of a plurality of pole pieces, wherein two pairs of pole pieces are used for monitoring the homogenization degree of two mutually vertical directions in the radiation field, one pole piece is used for monitoring the energy change of radiation, and the other two pole pieces are used for detecting the absorption dose of the radiation. The dose monitoring system of the traditional medical accelerator mostly uses a flat ionization chamber, the size of the flat ionization chamber is required to cover the whole treatment radiation field, and the number of the flat ionization chambers is limited. The function of the dose monitoring system is to monitor the X-ray, the dose rate of the electron beam, the integrated dose and the symmetry and flatness of the field.
The medical accelerator of the invention directly utilizes the electron beam to treat the tumor, the whole process that the electron beam leaves the accelerating tube and reaches the tumor is transmitted in a thin tube (the inner diameter is less than 5mm) and can not directly pass through the ionization chamber, so the ionization chamber is not suitable for the equipment, and no related dose monitoring method is available at home and abroad at present to test the treatment dose of the electron beam in the small field on line.
Disclosure of Invention
In view of the above, the present invention is directed to a small field electron beam medical accelerator and a dose monitoring method of the small field electron beam medical accelerator capable of monitoring the small field electron beam on-line during a treatment process.
In order to achieve the purpose, the invention adopts the following technical scheme:
the invention provides a medical accelerator, which comprises an electron gun control power supply, an electron gun, an accelerating tube, a magnetron, a modulator, a beam pipeline and a beam needle, wherein the electron gun control power supply is connected with the accelerating tube; the electron gun control power supply is used for controlling the electron gun injection voltage; the electron gun is used for outputting electron beams, and the accelerating tube is used for accelerating the electron beams output by the electron gun and then outputting the electron beams through a beam needle; the modulator is used for controlling the magnetron; the magnetron is connected with the accelerating tube through a waveguide chain; the rear end of the beam pipeline is fixedly connected to the center of the front end of the accelerating tube, and the front end of the beam pipeline is connected with the beam needle; the accelerating tube, the beam pipeline and the beam needle share a central shaft and are communicated with a straight-line channel to transmit electron beams in the straight-line channel; the side surface of the beam pipeline is connected with a beam eduction tube, a first electron beam is transmitted in the beam eduction tube, a deflection magnetic field generating device is arranged on the periphery of the beam pipeline, and the electron beam is periodically prompted to change the transmission direction and is output from the beam eduction tube to form the first electron beam; the electron beam output by the beam needle is a second electron beam.
Preferably, the beam needle and the outlet end of the beam eduction tube are sealed ends.
Preferably, the magnetic field direction of the deflecting magnetic field generating device is perpendicular to the plane formed by the beam current lead-out tube and the beam current pipeline, and when the beam current lead-out tube is located at the right side of the accelerating tube, the magnetic field direction of the deflecting magnetic field is directed from the far end to the near end.
Preferably, the front end of the beam pipeline is provided with a first connecting part, the inlet end of the beam needle is provided with a second connecting part, and the first connecting part and the second connecting part are detachably connected.
The invention also provides a dose monitoring method for monitoring the medical accelerator in any technical scheme, which comprises the following steps:
s1: the deflection magnetic field generating device works within the time delta t, so that the electron beam changes the transmission direction and is output from the beam current extraction tube to form the first electron beam;
s2: the first electron beam is shot into the first dose probe, and the first dose probe collects a first signal;
s3: after the first dose probe collects the first signal, the first data processing system processes the first signal to obtain the dose rate H of the first electron beama；
S4: dose H of the first electron beam by the first data processing systemaThe data is further processed to obtain the dose H of the second electron beamb。
Preferably, the dose rate H of the first electron beam in the step S4aAnd a dose rate H of the second electron beambThere is a linear numerical relationship: hb＝KHa。
Preferably, the step of determining K is as follows:
p1: the deflection magnetic field generating device works within the time delta t, so that the electron beam changes the transmission direction and is output from the beam current extraction tube to form the first electron beam; the deflection magnetic field generating device stops working within the time n delta t, the electron beam is transmitted along the linear channel and output from the beam needle to form a second electron beam, and n is a positive integer;
p2: the first electron beam is shot into a first dose probe, and the first dose probe collects a first signal; the second electron beam is emitted into a second dose probe, and the second dose probe collects a second signal;
p3: after the first dose probe collects the first signal, the first data processing system processes the first signal to obtain the dose rate H1 of the first electron beam1(ii) a After the second signal is collected by the second dose probe, the second data processing system processes the second signal to obtain the dose rate H2 of the second electron beam1；
P4: repeating the steps P1-P3 to obtain a series of dose rates H1 (H1) of the first electron beam2,H13,H14,H1i-and the dose rate of said second electron beam H2 (H2)2,H23,H24,H2i，┉)；
P5: dose rate H1 (H1) of the first electron beam1,H12,H13,H14,H1i-and the dose rate of said second electron beam H2 (H2)1,H22,H23,H24,H2i-averaging) to obtain an average dose rate of said first electron beam
And the average dose rate of the second electron beam
A linear numerical relationship is obtained:
the value of K is obtained.
Preferably, the step S1 is preceded by: and enabling the head end of the dose probe to be opposite to the outlet of the beam flow eduction tube and to be positioned on the same central shaft.
Preferably, the dose probe and the data processing system are in data transmission by wireless or wired means. The wireless mode is one of WIFI, cellular network, microwave communication and Bluetooth. The wired mode is one of optical fiber transmission, twisted pair transmission and broadband common cable transmission.
The invention also provides a medical accelerator, which comprises an electron gun control power supply, an electron gun, an accelerating tube, a magnetron, a modulator, a beam pipeline and a beam needle; the electron gun control power supply is used for controlling the electron gun injection voltage; the electron gun is used for outputting electron beams, and the accelerating tube is used for accelerating the electron beams output by the electron gun and then outputting the electron beams through a beam needle; the modulator is used for controlling the magnetron; the magnetron is connected with the accelerating tube through a waveguide chain; the rear end of the beam pipeline is fixedly connected to the center of the front end of the accelerating tube, and the front end of the beam pipeline is connected with the beam needle; the accelerating tube, the beam pipeline and the beam needle share a central shaft and are communicated with a straight-line channel to transmit electron beams in the straight-line channel; the side surface of the beam pipeline is connected with a first beam extraction pipe and a second beam extraction pipe, the first beam extraction pipe and the second beam extraction pipe are arranged symmetrically to the beam pipeline, a first electron beam is transmitted in the first beam extraction pipe, a third electron beam is transmitted in the second beam extraction pipe, a deflection magnetic field generating device is arranged on the periphery of the beam pipeline, the electron beam is periodically prompted to change the transmission direction and output from the first beam extraction pipe to form the first electron beam, and the electron beam is periodically prompted to change the transmission direction and output from the second beam extraction pipe to form the third electron beam; the electron beam output by the beam needle is a second electron beam.
Preferably, the beam needle and the outlet end of the beam eduction tube are sealed ends.
Preferably, the magnetic field direction of the deflecting magnetic field generating device is perpendicular to a plane formed by the first beam extraction pipe and the beam pipeline, when the first electron beam is required to be output from the first beam extraction pipe, the magnetic field direction of the deflecting magnetic field is directed from the far end to the near end, and when the third electron beam is required to be output from the second beam extraction pipe, the magnetic field direction of the deflecting magnetic field is directed from the near end to the far end.
The invention also provides a dose monitoring method for monitoring the medical accelerator in any technical scheme, which is characterized by comprising the following steps:
s1: the deflecting magnetic field generating device works within the time delta t, so that the electron beam changes the transmission direction and is output from the first beam flow extraction pipe to form the first electron beam;
s2: the first electron beam is shot into a first dose probe, and the first dose probe collects a first signal;
s3: after the first dose probe collects the first signal, the first data processing system processes the first signal to obtain the dose rate H of the first electron beama；
S4: dose H of the first electron beam by the first data processing systemaThe data is further processed to obtain the dose H of the second electron beamb。
S5: the deflection magnetic field generating device works within the time delta t, so that the electron beam changes the transmission direction and is output from the second beam extraction tube to form a third electron beam;
s6: the third electron beam is emitted into a third dose probe, which collects a third signal;
s7: after the third signal is collected by the third dosage probe, the third signal is processed by the third data processing system to obtainDose rate H to the third electron beamc；
S8: dose H of the third electron beam by the third data processing systemcThe data were further processed to obtain a dose H 'of a second electron beam'b。
Preferably, the dose rate H of the first electron beam in the step S4aAnd a dose rate H of the second electron beambThere is a linear numerical relationship: hb＝K1Ha。
Preferably, the dose rate H of the third electron beam in the step S8aAnd dose rate H 'of the second electron beam'bThere is a linear numerical relationship: h'b＝K2Hc。
Preferably, said K1The determination steps are as follows:
p1: the deflecting magnetic field generating device works within the time delta t, so that the electron beam changes the transmission direction and is output from the first beam flow extraction pipe to form the first electron beam; the deflection magnetic field generating device stops working within the time n delta t, the electron beam is transmitted along the linear channel and output from the beam needle to form a second electron beam, and n is a positive integer;
p2: the first electron beam is shot into a first dose probe, and the first dose probe collects a first signal; the second electron beam is emitted into a second dose probe, and the second dose probe collects a second signal;
p3: after the first dose probe collects the first signal, the first data processing system processes the first signal to obtain the dose rate H1 of the first electron beam1(ii) a After the second signal is collected by the second dose probe, the second data processing system processes the second signal to obtain the dose rate H2 of the second electron beam1；
P4: repeating the steps P1-P3 to obtain a series of dose rates H1 (H1) of the first electron beam2,H13,H14,H1i-and the dose rate of said second electron beam H2 (H2)2,H23,H24,H2i，┉)；
P5: dose rate H1 (H1) of the first electron beam1,H12,H13,H14,H1i-and the dose rate of said second electron beam H2 (H2)1,H22,H23,H24,H2i-averaging) to obtain an average dose rate of said first electron beam
And the average dose rate of the second electron beam
A linear numerical relationship is obtained:
namely to obtain K1The numerical value of (c).
Preferably, said K2The determination steps are as follows:
q1: the deflection magnetic field generating device works within the time delta t, so that the electron beam changes the transmission direction and is output from the second beam extraction tube to form a third electron beam; the deflection magnetic field generating device stops working within the time n delta t, the electron beam is transmitted along the linear channel and output from the beam needle to form a second electron beam, and n is a positive integer;
q2: the third electron beam is emitted into a third dose probe, which collects a third signal; the second electron beam is emitted into a second dose probe, and the second dose probe collects a second signal;
q3: after the third signal is collected by the third dose probe, the third signal is processed by the third data processing system to obtain the dose rate H3 of the third electron beam1(ii) a After the second signal is collected by the second dose probe, the second data processing system processes the second signal to obtain the dose rate H4 of the second electron beam1；
Q4: repeating steps Q1-Q3 to obtain a series of said third e-beam agentsDose rate H3 (H3)2,H33,H34,H3i-and the dose rate of said second electron beam H4 (H4)2,H43,H44,H4i，┉)；
Q5: dose rate H3 (H3) of the third electron beam1,H32,H33,H34,H3i-and the dose rate of said second electron beam H4 (H4)1,H42,H43,H44,H4i-averaging) to obtain the average dose rate of said third electron beam
And the average dose rate of the second electron beam
A linear numerical relationship is obtained:
namely to obtain K2The numerical value of (c).
Preferably, the step S1 is preceded by: the head end of the first dosage probe is opposite to the outlet of the first beam eduction tube and is positioned on the same central axis; and enabling the head end of the third dose probe to be opposite to the outlet of the second beam outlet pipe and to be positioned on the same central shaft.
Compared with the prior art, the invention has the following beneficial effects:
1. the invention is provided with a deflection magnetic field and a beam current eduction tube, extracts partial electrons, is used for realizing the dose test and monitoring of the electron beam, and has novel structure;
2. the extracted electrons are tested and processed by a dose detector to obtain the dose value of the electron beam, the treatment process is not influenced, the dose can be monitored on line, and the convenience and the accuracy of treatment are improved;
3. the continuous and multiple monitoring of the treatment process can be realized only by determining the K value once before treatment, and the operation is convenient;
4. by adopting the double-dose detector, the effectiveness of the dose detector is ensured and the safety of a patient is improved under the condition that one dose detector fails.
Drawings
One or more embodiments are illustrated by way of example in the accompanying drawings, which correspond to the figures in which like reference numerals refer to similar elements and which are not to scale unless otherwise specified.
Fig. 1 is a basic structural block diagram of a medical accelerator according to the present application;
FIG. 2 is a schematic diagram of an accelerator tube, a beam needle and a dose detector in an embodiment of the medical accelerator;
FIG. 3 is a schematic diagram illustrating a position of a deflecting magnetic field generating device according to an embodiment;
FIG. 4 is a diagram of the steps of the dose monitoring method of FIG. 2;
FIG. 5 is a schematic diagram of the placement of dose detectors in determining K-value in one embodiment;
FIG. 6 is a diagram of the steps for determining the value of K;
FIG. 7 is a schematic structural diagram of an accelerating tube, a beam current needle and a dose detector in a medical accelerator according to another embodiment;
FIG. 8 is a schematic diagram of the position of a deflecting magnetic field generating device in another embodiment;
reference numerals: 1-a medical accelerator, 2-an electron gun control power supply, 3-an electron gun, 4-an accelerating tube, 5-a magnetron, 6-a modulator, 7-a beam pipeline, 8-a beam needle, 9-a beam eduction tube, 9 a-a first beam eduction tube, 9 c-a second beam eduction tube, 10-a deflection magnetic field generating device and 11-a first electromagnet, 12-second electromagnet, 13-first connecting part, 14-second connecting part, 15-dose detector, 16-dose probe, 17-data processing system, 16 a-first dose probe, 17 a-first data processing system, 16 b-second dose probe, 17 b-second data processing system, 16 c-third dose probe and 17 c-third data processing system.
Detailed Description
For further understanding of the present invention, the technical solutions in the embodiments of the present invention are clearly and completely described, and it is obvious that the described embodiments are only a part of the embodiments of the present invention, rather than all embodiments, and all other embodiments obtained by those skilled in the art without any inventive work based on the embodiments of the present invention belong to the protection scope of the present invention.
It should be noted that the terms "first", "second" and "third" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implying any number of technical features indicated. Thus, features defined as "first", "second", "third" may explicitly or implicitly include one or more of the features. The term "distal end" refers to the end of the device or apparatus of the present application that is furthest from the reader when the device or apparatus is facing the reader; "proximal" refers to the end of the device or apparatus of the present application that is closest to the reader when the device or apparatus is facing the reader. The term "front end" or "outlet end" refers to the end of the device or apparatus of the present application that is near the tip of the beam or the end from which the beam exits the orifice when the device or apparatus is facing the reader; "rear end" or "inlet end" refers to the end of the device or apparatus of the present application that is distal from the tip of the beam or the end from which the beam exits the orifice when the device or apparatus is facing the reader.
The invention provides a medical accelerator, please refer to fig. 1-3, which comprises an electron gun control power supply 2, an electron gun 3, an accelerating tube 4, a magnetron 5, a modulator 6, a beam pipeline 7 and a beam needle 8; the electron gun control power supply 2 is used for controlling the injection voltage of the electron gun 3; the electron gun 3 is used for outputting electron beams, and the accelerating tube 4 is used for accelerating the electron beams output by the electron gun 3 and then outputting the electron beams through the beam needle 8; the modulator 6 is used for controlling the magnetron 5; the magnetron 5 is connected with the accelerating tube 4 through a waveguide chain; the rear end of the beam pipeline 7 is fixedly connected to the center of the front end of the accelerating tube 4, and the front end of the beam pipeline 7 is connected with the beam needle 8; the accelerating tube 4, the beam pipeline 7 and the beam needle 8 share a central shaft and are communicated with a straight passage, so that an electron beam is transmitted in the straight passage; the side surface of the beam pipeline 7 is connected with a beam eduction tube 9, a first electron beam is transmitted in the beam eduction tube 9, a deflection magnetic field generating device 10 is arranged on the periphery of the beam pipeline 7, and the electron beam is periodically prompted to change the transmission direction and is output from the beam eduction tube 9 to form the first electron beam; the electron beam output by the beam needle 8 is a second electron beam.
The treatment process of the invention is as follows: the beam needle 8 is led into a tumor focus part in a human body through a trocar (not shown) preset on the human body, the electron gun 3 generates electron beams, the electron beams are accelerated through the accelerating tube 4 and are finally output through the beam needle 8, and the electron beams strike the tumor focus part to melt the tumor.
The treatment process of the invention may also be as follows: the tumor focus part is exposed through modes such as operation, the beam needle 8 is introduced into the tumor focus part in a human body, the electron gun 3 generates electron beams, the electron beams are accelerated through the accelerating tube 4 and are finally output through the beam needle 8, and the electron beams strike the tumor focus part to melt the tumor.
The waveguide chain of the embodiment is a flexible waveguide, the flexible waveguide has good flexibility, can bear bending, stretching and compression to a certain degree, and ensures the transmission of electron beams under the condition that the accelerating tube 4 and the magnetron 5 are separately arranged.
In order to enable the electron beams to be smoothly transmitted from the beam current needle 8, the periphery of the connection structure of the accelerating tube 4 and the beam current needle 8 is provided with the focusing coil, so that the moving path of the electron beams is effectively guided, and the electron beams are ensured to be focused on the axis of the beam current needle 8.
Because the dosage of the electron beams must be monitored in the treatment process, few parts of the electron beams are extracted to carry out synchronous test through the beam extraction tube 9 and the deflection magnetic field generating device 10, the treatment process is not influenced, and the online dosage monitoring can be realized.
Further, the outlet ends of the beam needle 8 and the beam eduction tube 9 are sealed ends.
By adopting the technical scheme, the internal environment of the whole accelerator is kept in a vacuum environment, and the electrons realize vacuum low-loss transmission.
In this embodiment, the beam needle 8 and the outlet end of the beam lead-out tube 9 are made of the same material, and the sealed end is a nonmagnetic metal sheet, preferably a titanium sheet or a beryllium sheet. The thickness of the sealed end is below 200 μm. Long-term experiments and research summarization show that the sealing end is too thick, electrons cannot pass through the sealing end, when a titanium sheet or a beryllium sheet is used as the sealing material, the passing condition of the electrons is better, the attenuation degree of the electrons is lower, and at the moment, the effective passing rate of the electrons and the sealing of the space in the tube can be ensured.
Further, referring to fig. 3, the magnetic field direction of the deflecting magnetic field generating device 10 is perpendicular to the plane formed by the beam extraction tube 9 and the beam duct 7, and when the beam extraction tube 9 is located at the right of the accelerating tube 4, the magnetic field direction of the deflecting magnetic field is directed from the far end to the near end.
Specifically, the deflecting magnetic field generating device 10 is a pair of electromagnets. The electromagnet has magnetism when being electrified, and the magnetism disappears along with the electrification after the power is off, so that the deflection of the electron beam can be conveniently and rapidly regulated. Preferably, two identical electromagnets are respectively and equidistantly arranged on two sides of the beam needle 8, the first electromagnet 11 is arranged at the far end, and the second electromagnet 12 is arranged at the near end.
By adopting the technical scheme, the transmission direction of the electron beam is changed from being parallel to the central axis of the beam pipeline 7 to being parallel to the central axis of the beam eduction tube 9, so that a first electron beam is formed and used for detecting the dose rate of the electron beam.
Further, the front end of the beam pipeline 7 is provided with a first connecting part 13, the inlet end of the beam needle 8 is provided with a second connecting part 14, and the first connecting part 13 and the second connecting part 14 are detachably connected.
By adopting the technical scheme, the beam pipeline 7 and the beam needle 8 can be disassembled, and because the beam needle 8 is a thin hollow pipe, the outer diameter is generally 1.5-6mm, if the beam needle is damaged due to some reason, the beam needle 8 can be replaced by disassembling.
The present invention further provides a dose monitoring method for monitoring the medical accelerator according to any of the above embodiments, referring to fig. 4, including the following steps:
s1: the deflecting magnetic field generating device 10 works within the time delta t, so that the transmission direction of the electron beam is changed and the electron beam is output from the beam current extraction pipe 9 to form the first electron beam;
s2: the first electron beam is incident on the first dose probe 16a, and the first dose probe 16a collects a first signal;
s3: after the first dose probe 16a finishes collecting the first signal, the first data processing system 17a processes the first signal to obtain the dose rate H of the first electron beama；
S4: dose H of the first electron beam by the first data processing system 17aaThe data is further processed to obtain the dose H of the second electron beamb；。
Further, the dose rate H of the first electron beam in the step S4aAnd a dose rate H of the second electron beambThere is a linear numerical relationship: hb＝KHa。
FIG. 5 is a schematic diagram of the placement of the dose detector in determining the K value in one embodiment.
Further, the step of determining K is as follows, please refer to fig. 6:
p1: the deflecting magnetic field generating device 10 works within the time delta t, so that the transmission direction of the electron beam is changed and the electron beam is output from the beam current extraction pipe 9 to form the first electron beam; the deflecting magnetic field generating device 10 stops working within time n Δ t, and the electron beam is transmitted along the linear channel and output from the beam needle 8 to form the second electron beam, wherein n is a positive integer;
p2: the first electron beam is incident on a first dose probe 16a, and the first dose probe 16a collects a first signal; the second electron beam is emitted to a second dose probe 16b, and the second dose probe 16b collects a second signal;
p3: after the first dose probe 16a finishes collecting the first signal, the first data processing system 17a processes the first signal to obtain the dose rate H1 of the first electron beam1(ii) a After the second dose probe 16b finishes collecting the second signal, the second data processing system 17b processes the second signal to obtain the second signalDose rate of the electron beam H21；
P4: repeating the steps P1-P3 to obtain a series of dose rates H1 (H1) of the first electron beam2,H13,H14,H1i-and the dose rate of said second electron beam H2 (H2)2,H23,H24,H2i，┉)；
P5: dose rate H1 (H1) of the first electron beam1,H12,H13,H14,H1i-and the dose rate of said second electron beam H2 (H2)1,H22,H23,H24,H2i-averaging) to obtain an average dose rate of said first electron beam
And the average dose rate of the second electron beam
A linear numerical relationship is obtained:
the value of K is obtained.
In the pulsed operation mode, the temporal characteristics of the generation of the electron beam have a pulse characteristic, for example, a repetition frequency of 5Hz, 5 current pulses are generated within 1s, a pulse repetition period of 200ms, and a pulse width of 1 to 4 us.
Further, step S1 is preceded by: the head end of the dosage probe 16 is opposite to the outlet of the beam eduction tube and is positioned on the same central axis.
Referring to fig. 2, the dose detector 15 used in the present invention includes a dose probe 16 and a data processing system 17, wherein the data processing system 17 processes signals monitored by the dose probe 16 to obtain the dose of the electron beam; the head end of the dosage probe 16 is opposite to the outlet of the beam outlet pipe 9 and is positioned on the same central axis.
In particular, the dose probe 16 of the dose detector 15 of the present embodiment comprises a finger ionization chamber, preferably a UNIDOS E dosimeter manufactured by PTW, Germany. The UNIDOS E dosimeter can monitor signals at the outlet of the beam eduction tube 9 and directly obtain the dose of the first electron beam; similarly, the UNIDOS E dosimeter can monitor signals at the outlet of the beam needle 8 and directly obtain the dose of the second electron beam.
Principle of finger ionization chamber measuring absorbed dose: the ionization charge generated by ionizing radiation is first measured and then calculated and converted into the energy deposited by ionizing radiation, i.e. the absorbed dose, using the average ionization energy of air.
When the accelerator performs radiotherapy, ionizing radiation exists, which affects the health of doctors and technicians, in the embodiment, the dose probe 16 and the data processing system 17 perform data transmission in a wireless mode or a wired mode. The doctor or technician can measure and monitor the dosage on line through remote operation.
Specifically, the wireless mode is one of WIFI, cellular network, microwave communication, and bluetooth.
Specifically, the wired mode is one of optical fiber transmission, twisted pair transmission, coaxial cable transmission, and broadband common cable transmission.
According to the invention, through the beam extraction tube 9 and the deflection magnetic field generating device 10, few parts of electron beams are extracted to carry out synchronous testing, the treatment process is not influenced, and the dosage can be monitored on line.
In order to reduce the error of the dose test result, the distance between the first dose probe 16a and the outlet end of the beam outlet pipe 9 and the distance between the second dose probe 16b and the outlet end of the beam needle 8 are equal and are kept constant.
Example 1
Before treatment, the procedure was followed as described above in steps P1-P5, Δ t 1s, and the test data obtained are shown in table 1.
TABLE 1 test results tables for H1 and H2 (units Gy/min)
By processing the test results of H1 and H2, K is determined to be 4.
Example 2
During the treatment, the dose monitoring is performed according to steps S1-S4, Δ t ═ 1S, n ═ 5, and the dose rate H of the first electron beamaThe test value and the dose rate H of the second electron beambThe calculated values are shown in Table 2.
TABLE 2 test results tables for H1 and H2 (units Gy/min)
| Number of tests | HaTest value | HbCalculated value | Number of tests | HaTest value | HbCalculated value |
| 1 | 16.26 | 65.05 | 14 | 16.26 | 65.03 |
| 2 | 16.75 | 66.99 | 15 | 16.47 | 65.89 |
| 3 | 16.56 | 66.22 | 16 | 16.52 | 66.06 |
| 4 | 15.95 | 63.79 | 17 | 16.74 | 66.96 |
| 5 | 16.54 | 66.17 | 18 | 16.30 | 65.18 |
| 6 | 16.77 | 67.07 | 19 | 16.03 | 64.10 |
| 7 | 16.39 | 65.56 | 20 | 16.29 | 65.16 |
| 8 | 16.86 | 67.45 | 21 | 16.55 | 66.19 |
| 9 | 16.65 | 66.58 | 22 | 16.26 | 65.02 |
| 10 | 16.82 | 67.27 | 23 | 16.03 | 64.10 |
| 11 | 16.25 | 64.98 | 24 | 16.27 | 65.08 |
| 12 | 16.13 | 64.52 | 25 | 16.25 | 64.98 |
| 13 | 16.81 | 67.22 |
In this embodiment, the dose rate of the second electron beam (for treatment) is calculated by monitoring the dose rate of the first electron beam, and the dose rate is monitored without affecting the treatment.
For the sake of safety, to avoid the dose detector 15 from malfunctioning, in another technical solution, two sets of the dose detector 15 and two sets of the beam extraction tubes 9 are provided, and the dose rates obtained by the two sets of the dose detector 15 are both set, wherein one set of the dose detector 15 is malfunctioning, the other set is capable of continuing to operate, and in addition, the two sets of dose rate data are also capable of being compared to examine the stability of the data.
In another embodiment, referring to fig. 7-8, a medical accelerator includes an electron gun control power supply 2, an electron gun 3, an accelerating tube 4, a magnetron 5, a modulator 6, a beam conduit 7, and a beam needle 8; the electron gun control power supply 2 is used for controlling the injection voltage of the electron gun 3; the electron gun 3 is used for outputting electron beams, and the accelerating tube 4 is used for accelerating the electron beams output by the electron gun 3 and then outputting the electron beams through the beam needle 8; the modulator 6 is used for controlling the magnetron 5; the magnetron 5 is connected with the accelerating tube 4 through a waveguide chain; the rear end of the beam pipeline 7 is fixedly connected to the center of the front end of the accelerating tube 4, and the front end of the beam pipeline 7 is connected with the beam needle 8; the accelerating tube 4, the beam pipeline 7 and the beam needle 8 share a central shaft and are communicated with a straight passage, so that an electron beam is transmitted in the straight passage; the side surface of the beam pipeline 7 is connected with a first beam extraction pipe 9a and a second beam extraction pipe 9b, the first beam extraction pipe 9a and the second beam extraction pipe 9b are arranged symmetrically to the beam pipeline 7, a first electron beam is transmitted in the first beam extraction pipe 9a, a third electron beam is transmitted in the second beam extraction pipe 9b, a deflection magnetic field generating device 10 is arranged on the periphery of the beam pipeline 7, the electron beams are periodically prompted to change the transmission direction and are output from the first beam extraction pipe 9a to form the first electron beam, and the electron beams are periodically prompted to change the transmission direction and are output from the second beam extraction pipe 9b to form the third electron beam; the electron beam output by the beam needle 8 is a second electron beam.
Further, the magnetic field direction of the deflecting magnetic field generating device 10 is perpendicular to the plane formed by the first beam outgoing tube 9a and the beam conduit 7, when the first electron beam is required to be output from the first beam outgoing tube 9a, the magnetic field direction of the deflecting magnetic field is directed from the far end to the near end, and when the third electron beam is required to be output from the second beam outgoing tube 9b, the magnetic field direction of the deflecting magnetic field is directed from the near end to the far end.
Specifically, the magnetic field direction of the deflecting magnetic field is changed by changing the current direction of the spiral line.
Another embodiment of a method for monitoring a dose of a medical accelerator, comprising the steps of:
s1: the deflecting magnetic field generating device 10 works within the time delta t, so that the electron beam changes the transmission direction and is output from the first beam eduction tube 9a to form the first electron beam;
s2: the first electron beam is incident on a first dose probe 16a, and the first dose probe 16a collects a first signal;
s3: after the first dose probe 16a finishes collecting the first signal, the first data processing system 17a processes the first signal to obtain the dose rate H of the first electron beama；
S4: dose H of the first electron beam by the first data processing system 17aaThe data is further processed to obtain the dose H of the second electron beamb。
S5: the deflecting magnetic field generating device 10 works within the time delta t, so that the electron beam changes the transmission direction and is output from the first beam eduction tube 9b to form the third electron beam;
s6: the third electron beam is emitted to a third dose probe 16c, and the third dose probe 16c collects a third signal;
s7: after the third dose probe 16c finishes collecting the third signal, the third data processing system 17c processes the third signal to obtain the dose rate H of the third electron beamc；
S8: dose H of the third electron beam by the third data processing system 17ccThe data were further processed to obtain a dose H 'of a second electron beam'b。
Further, the dose rate H of the first electron beam in the step S4aAnd a dose rate H of the second electron beambThere is a linear numerical relationship: hb＝K1Ha。
Further, the dose rate H of the third electron beam in the step S8aAnd dose rate H 'of the second electron beam'bThere is a linear numerical relationship: h'b＝K2Hc。
Further, K is1The determination steps are as follows:
p1: the deflecting magnetic field generating device works within the time delta t, so that the electron beam changes the transmission direction and is output from the first beam eduction tube 9a to form the first electron beam; the deflection magnetic field generating device stops working within the time n delta t, the electron beam is transmitted along the linear channel and output from the beam needle to form a second electron beam, and n is a positive integer;
p2: the first electron beam is incident on a first dose probe 16a, and the first dose probe 16a collects a first signal; the second electron beam is emitted into a second dose probe, and the second dose probe collects a second signal;
p3: after the first dose probe 16a finishes collecting the first signal, the first data processing system 17a processes the first signal to obtain the dose rate H1 of the first electron beam1(ii) a After the second dose probe 16b finishes collecting the second signal, the second data processing system 17b processes the second signal to obtain a dose rate H2 of the second electron beam1；
P4: repeating the steps P1-P3 to obtain a series of dose rates H1 (H1) of the first electron beam2,H13,H14,H1i-and the dose rate of said second electron beam H2 (H2)2,H23,H24,H2i，┉)；
P5: dose rate H1 (H1) of the first electron beam1,H12,H13,H14,H1i-and the dose rate of said second electron beam H2 (H2)1,H22,H23,H24,H2i-averaging) to obtain an average dose rate of said first electron beam
And the average dose rate of the second electron beam
A linear numerical relationship is obtained:
namely to obtain K1The numerical value of (c).
Further, K is2The determination steps are as follows:
q1: the deflecting magnetic field generating device 10 works within the time delta t, so that the electron beam changes the transmission direction and is output from the first beam eduction tube 9b to form the third electron beam; the deflecting magnetic field generating device 10 stops working within time n Δ t, and the electron beam is transmitted along the linear channel and output from the beam needle 8 to form the second electron beam, wherein n is a positive integer;
q2: the third electron beam is emitted to a third dose probe 16c, and the third dose probe 16c collects a third signal; the second electron beam is emitted to a second dose probe 16b, and the second dose probe 16b collects a second signal;
q3: after the third dose probe 16c finishes collecting the third signal, the third data processing system 17c processes the third signal to obtain the dose rate H3 of the third electron beam1(ii) a After the second dose probe 16b finishes collecting the second signal, the second data processing system 17b processes the second signal to obtain a dose rate H4 of the second electron beam1；
Q4: repeating steps Q1-Q3 to obtain a series of dose rates H3 (H3) of the third electron beam2,H33,H34,H3i-and the dose rate of said second electron beam H4 (H4)2,H43,H44,H4i，┉)；
Q5: dose rate H3 (H3) of the third electron beam1,H32,H33,H34,H3i-and the dose rate of said second electron beam H4 (H4)1,H42,H43,H44,H4i-averaging) to obtain the average dose rate of said third electron beam
And the average dose rate of the second electron beam
A linear numerical relationship is obtained:
namely to obtain K2The numerical value of (c).
Further, step S1 is preceded by: the head end of the first dosage probe 16a is opposite to the outlet of the first beam eduction tube 9a and is positioned on the same central axis; the head end of the third dosage probe 16c is opposite to the outlet of the first beam outlet tube 9b and is on the same central axis.
Example 3
Before treatment, the procedure was followed as described above in steps Q1-Q5, Δ t 1s, and the test data obtained are shown in table 3.
TABLE 1 test results tables for H3 and H4 (units Gy/min)
By processing the test results of H3 and H4, K is determined to be 4.
Example 4
During the treatment, the dose monitoring is performed according to steps S1-S8, Δ t ═ 1S, n ═ 5, and the dose rate H of the first electron beamaTest value, dose rate H of the third electron beamcThe test value and the dose rate H of the second electron beamb、，H'bThe calculated values are shown in Table 4.
TABLE 2Ha、Hc、HbAnd H'bTest result table (Unit Gy/min)
As can be seen from Table 4, the dose rate H of the second electron beam monitored by the first electron beam from the first beam extractor 9abDose rate H 'of the second electron beam monitored by the third electron beam passing through the second beam extractor 9 b'bThe results are approximate, which shows that the dosage monitoring method of the application is feasible and reliable.
According to the invention, through the beam extraction tube 9 and the deflection magnetic field generating device 10, few parts of electron beams are extracted for synchronous testing, and only calibration is needed before treatment.
The embodiments shall be considered as exemplary and not restrictive for the person skilled in the art, and any combination of the features of the above-described embodiments may be made, and for the sake of brevity of description, all possible combinations of the features of the above-described embodiments are not described, however, as long as there is no contradiction between these combinations of features, the scope of the present description shall be considered as being described in the present specification, and therefore all variations falling within the meaning and scope of the equivalents of the claims are intended to be embraced by the present invention.
Claims (18)
1. A medical accelerator is characterized by comprising an electron gun control power supply, an electron gun, an accelerating tube, a magnetron, a modulator, a beam pipeline and a beam needle; the electron gun control power supply is used for controlling the electron gun injection voltage; the electron gun is used for outputting electron beams, and the accelerating tube is used for accelerating the electron beams output by the electron gun and then outputting the electron beams through a beam needle; the modulator is used for controlling the magnetron; the magnetron is connected with the accelerating tube through a waveguide chain; the rear end of the beam pipeline is fixedly connected to the center of the front end of the accelerating tube, and the front end of the beam pipeline is connected with the beam needle; the accelerating tube, the beam pipeline and the beam needle share a central shaft and are communicated with a straight-line channel to transmit electron beams in the straight-line channel; the side surface of the beam pipeline is connected with a beam eduction tube, a first electron beam is transmitted in the beam eduction tube, a deflection magnetic field generating device is arranged on the periphery of the beam pipeline, and the electron beam is periodically prompted to change the transmission direction and is output from the beam eduction tube to form the first electron beam; the electron beam output by the beam needle is a second electron beam.
2. The medical accelerator according to claim 1, wherein the beam needle and the exit end of the beam exit tube are sealed ends.
3. The medical accelerator according to claim 1, wherein the magnetic field direction of the magnetic deflection field generating device is perpendicular to the plane formed by the beam extraction tube and the beam conduit, and when the beam extraction tube is located at the right of the accelerator tube, the direction of the magnetic deflection field is from the far end to the near end.
4. The medical accelerator according to claim 1, wherein a first connecting portion is provided at a front end of the beam line, a second connecting portion is provided at an inlet end of the beam needle, and the first connecting portion and the second connecting portion are detachably connected.
5. A dose monitoring method of monitoring a medical accelerator according to any one of claims 1 to 4, comprising the steps of:
s1: the deflection magnetic field generating device works within the time delta t, so that the electron beam changes the transmission direction and is output from the beam current extraction tube to form the first electron beam;
s2: the first electron beam is shot into a first dose probe, and the first dose probe collects a first signal;
s3: after the first dose probe collects the first signal, the first data processing system processes the first signal to obtain the dose rate H of the first electron beama；
S4: dose H of the first electron beam by the first data processing systemaThe data is further processed to obtain the dose H of the second electron beamb。
6. The dose monitoring method as claimed in claim 5, wherein the dose rate H of the first electron beam in the step S4aAnd a dose rate H of the second electron beambThere is a linear numerical relationship: hb＝KHa。
7. Dose monitoring method according to claim 6, characterized in that the K is determined as follows:
p1: the deflection magnetic field generating device works within the time delta t, so that the electron beam changes the transmission direction and is output from the beam current extraction tube to form the first electron beam; the deflection magnetic field generating device stops working within the time n delta t, the electron beam is transmitted along the linear channel and output from the beam needle to form a second electron beam, and n is a positive integer;
p2: the first electron beam is shot into a first dose probe, and the first dose probe collects a first signal; the second electron beam is emitted into a second dose probe, and the second dose probe collects a second signal;
p3: after the first dose probe collects the first signal, the first data processing system processes the first signal to obtain the dose rate H1 of the first electron beam1(ii) a After the second signal is collected by the second dose probe, the second data processing system processes the second signal to obtain the dose rate H2 of the second electron beam1；
P4: repeating the steps P1-P3 to obtain a series of dose rates H1 (H1) of the first electron beam2,H13,H14,H1i-and the dose rate of said second electron beam H2 (H2)2,H23,H24,H2i，┉)；
P5: dose rate H1 (H1) of the first electron beam1,H12,H13,H14,H1i-and the dose rate of said second electron beam H2 (H2)1,H22,H23,H24,H2i-averaging) to obtain an average dose rate of said first electron beam
And the average dose rate of the second electron beam
A linear numerical relationship is obtained:
the value of K is obtained.
8. The dose monitoring method according to claim 5, further comprising, before said step S1: and enabling the head end of the dose probe to be opposite to the outlet of the beam flow eduction tube and to be positioned on the same central shaft.
9. The dose monitoring method of claim 5, wherein the dose probe and data processing system are in data communication by wireless or wired means.
10. A medical accelerator is characterized by comprising an electron gun control power supply, an electron gun, an accelerating tube, a magnetron, a modulator, a beam pipeline and a beam needle; the electron gun control power supply is used for controlling the electron gun injection voltage; the electron gun is used for outputting electron beams, and the accelerating tube is used for accelerating the electron beams output by the electron gun and then outputting the electron beams through a beam needle; the modulator is used for controlling the magnetron; the magnetron is connected with the accelerating tube through a waveguide chain; the rear end of the beam pipeline is fixedly connected to the center of the front end of the accelerating tube, and the front end of the beam pipeline is connected with the beam needle; the accelerating tube, the beam pipeline and the beam needle share a central shaft and are communicated with a straight-line channel to transmit electron beams in the straight-line channel; the side surface of the beam pipeline is connected with a first beam extraction pipe and a second beam extraction pipe, the first beam extraction pipe and the second beam extraction pipe are arranged symmetrically to the beam pipeline, a first electron beam is transmitted in the first beam extraction pipe, a third electron beam is transmitted in the second beam extraction pipe, a deflection magnetic field generating device is arranged on the periphery of the beam pipeline, the electron beam is periodically prompted to change the transmission direction and output from the first beam extraction pipe to form the first electron beam, and the electron beam is periodically prompted to change the transmission direction and output from the second beam extraction pipe to form the third electron beam; the electron beam output by the beam needle is a second electron beam.
11. The medical accelerator of claim 10, wherein the beam needle and the exit end of the beam exit tube are sealed ends.
12. The medical accelerator according to claim 10, wherein the magnetic field direction of the magnetic deflection field generator is perpendicular to the plane formed by the first beam exit tube and the beam conduit, and the magnetic field direction of the magnetic deflection field is from the distal end to the proximal end when the first electron beam is required to be output from the first beam exit tube, and the magnetic field direction of the magnetic deflection field is from the proximal end to the distal end when the third electron beam is required to be output from the second beam exit tube.
13. A dose monitoring method of monitoring a medical accelerator according to any one of claims 10 to 12, comprising the steps of:
s1: the deflecting magnetic field generating device works within the time delta t, so that the electron beam changes the transmission direction and is output from the first beam flow extraction pipe to form the first electron beam;
s2: the first electron beam is shot into a first dose probe, and the first dose probe collects a first signal;
s3: after the first dose probe collects the first signal, the first data processing system processes the first signal to obtain the dose rate H of the first electron beama；
S4: dose H of the first electron beam by the first data processing systemaThe data is further processed to obtain the dose H of the second electron beamb。
S5: the deflection magnetic field generating device works within the time delta t, so that the electron beam changes the transmission direction and is output from the second beam extraction tube to form a third electron beam;
s6: the third electron beam is emitted into a third dose probe, which collects a third signal;
s7: after the third signal is collected by the third dose probe, the third signal is processed by the third data processing system to obtain the dose rate H of the third electron beamc；
S8: dose H of the third electron beam by the third data processing systemcThe data were further processed to obtain a dose H 'of a second electron beam'b。
14. The dose monitoring method as claimed in claim 13, wherein the dose rate H of the first electron beam in the step S4aAgent with the second electron beamRate HbThere is a linear numerical relationship: hb＝K1Ha。
15. The dose monitoring method as claimed in claim 13, wherein the dose rate H of the third electron beam in the step S8aAnd dose rate H 'of the second electron beam'bThere is a linear numerical relationship: h'b＝K2Hc。
16. The dose monitoring method of claim 14, wherein K is1The determination steps are as follows:
p1: the deflecting magnetic field generating device works within the time delta t, so that the electron beam changes the transmission direction and is output from the first beam flow extraction pipe to form the first electron beam; the deflection magnetic field generating device stops working within the time n delta t, the electron beam is transmitted along the linear channel and output from the beam needle to form a second electron beam, and n is a positive integer;
p2: the first electron beam is shot into a first dose probe, and the first dose probe collects a first signal; the second electron beam is emitted into a second dose probe, and the second dose probe collects a second signal;
p3: after the first dose probe collects the first signal, the first data processing system processes the first signal to obtain the dose rate H1 of the first electron beam1(ii) a After the second signal is collected by the second dose probe, the second data processing system processes the second signal to obtain the dose rate H2 of the second electron beam1；
P4: repeating the steps P1-P3 to obtain a series of dose rates H1 (H1) of the first electron beam2,H13,H14,H1i-and the dose rate of said second electron beam H2 (H2)2,H23,H24,H2i，┉)；
P5: dose rate H1 (H1) of the first electron beam1,H12,H13,H14,H1i-and the dose rate of said second electron beam H2 (H2)1,H22,H23,H24,H2i-averaging) to obtain an average dose rate of said first electron beam
And the average dose rate of the second electron beam
A linear numerical relationship is obtained:
namely to obtain K1The numerical value of (c).
17. The dose monitoring method of claim 15, wherein K is2The determination steps are as follows:
q1: the deflection magnetic field generating device works within the time delta t, so that the electron beam changes the transmission direction and is output from the second beam extraction tube to form a third electron beam; the deflection magnetic field generating device stops working within the time n delta t, the electron beam is transmitted along the linear channel and output from the beam needle to form a second electron beam, and n is a positive integer;
q2: the third electron beam is emitted into a third dose probe, which collects a third signal; the second electron beam is emitted into a second dose probe, and the second dose probe collects a second signal;
q3: after the third signal is collected by the third dose probe, the third signal is processed by the third data processing system to obtain the dose rate H3 of the third electron beam1(ii) a After the second signal is collected by the second dose probe, the second data processing system processes the second signal to obtain the dose rate H4 of the second electron beam1；
Q4: repeating steps Q1-Q3 to obtain a series of dose rates H3 (H3) of the third electron beam2,H33,H34,H3i-and the dose rate of said second electron beam H4 (H4)2,H43,H44,H4i，┉)；
Q5: dose rate H3 (H3) of the third electron beam1,H32,H33,H34,H3i-and the dose rate of said second electron beam H4 (H4)1,H42,H43,H44,H4i-averaging) to obtain the average dose rate of said third electron beam
And the average dose rate of the second electron beam
A linear numerical relationship is obtained:
namely to obtain K2The numerical value of (c).
18. The dose monitoring method according to claim 13, further comprising, before said step S1: the head end of the first dosage probe is opposite to the outlet of the first beam eduction tube and is positioned on the same central axis; and enabling the head end of the third dose probe to be opposite to the outlet of the second beam outlet pipe and to be positioned on the same central shaft.
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| CN111642055A (en) * | 2020-06-04 | 2020-09-08 | 中国科学院近代物理研究所 | Current waveform control system and method of digital pulse power supply of ion synchrotron |
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| CN111642055A (en) * | 2020-06-04 | 2020-09-08 | 中国科学院近代物理研究所 | Current waveform control system and method of digital pulse power supply of ion synchrotron |
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