JP6257994B2 - Neutron generator and medical accelerator system - Google Patents

Description

  Embodiments described herein relate generally to a neutron generator and a medical accelerator system.

  In a neutron generator, a neutron generator particularly for application to neutron therapy is required to obtain a high-intensity neutron flux.

  As such a neutron generator, there is a neutron generator that generates neutrons by irradiating a target with a high-energy proton beam (charged particle beam) accelerated by an accelerator (see, for example, Patent Document 1). Here, in order to generate neutrons, there is an energy threshold. That is, neutrons cannot be generated unless the energy of the charged particle beam is higher than this threshold.

  Non-Patent Document 1 discloses a technique for adjusting the energy of protons when a target is incident by applying a high voltage to the target.

JP 2009-47432 A

Completion of world-class high-performance monochromatic neutron standard irradiation field (Notice) III. Outline of Main Technology Development Japan Atomic Energy Agency Announced October 4, 2010 http://www.jaea.go.jp/02/press2010/p10100401/index.html

  In the neutron generator described in Patent Document 1, it is desirable to set the energy of the charged particle beam from the accelerator to a value that provides a necessary neutron flux near the reaction threshold. Incidentally, this is to suppress heat generation of the target, activation of the structure, and generation of secondary gamma rays.

  However, it has been difficult for the neutron generator to control the energy of the charged particle beam from the accelerator with high responsiveness and high accuracy. In this regard, although the technique described in Non-Patent Document 1 described above can control the energy of the charged particle beam to some extent, it has been desired to control it with higher accuracy.

  The problem to be solved by the embodiments of the present invention is to provide a neutron generator and a medical accelerator system capable of adjusting the amount and energy of generated neutrons with high accuracy.

The neutron generator of the present embodiment includes an accelerator that accelerates a charged particle beam to a predetermined energy, a target that generates neutrons when irradiated with the charged particle beam accelerated by the accelerator, and a voltage applied to the target. A high-voltage power source that applies and adjusts the energy of the charged particle beam when incident on the target; a dose detector that detects a neutron dose generated by irradiating the target with the charged particle beam; and the dose detection A voltage control device that controls a value of a voltage applied to the target from the high-voltage power source based on a neutron dose detected by a detector, an integration unit that integrates the neutron dose detected by the dose detector, and the integration comprising a determining unit neutron dose is accumulated is whether it is above a preset value in parts, and the neutron beam There characterized by stopping the supply of the charged particle beam when it becomes more than a preset value.

The medical accelerator system of this embodiment includes an accelerator that accelerates a charged particle beam to a predetermined energy, a target that irradiates the charged particle beam accelerated by the accelerator to generate neutrons, and a voltage with respect to the target. A high voltage power source for adjusting the energy of the charged particle beam at the time of incidence of the target, a dose detector for detecting a neutron dose generated by the target, and a neutron dose detected by the dose detector A voltage control device that controls the voltage value of the high-voltage power supply, an integration unit that integrates the neutron dose detected by the dose detector, and the neutron dose integrated by the integration unit is greater than or equal to a preset value and a determination unit for determining whether or not now, the target is in use in boron neutron supplemental therapy (BNCT) A BNCT target for releasing the child, irradiating the neutron irradiation target, wherein the neutron dose stops supply of the charged particle beam when it becomes more than a preset value.

  According to this embodiment, the amount and energy of neutrons generated can be adjusted with high accuracy, and controllability and maintainability can be improved.

It is sectional drawing which shows 1st Embodiment of the neutron generator which concerns on this invention. It is sectional drawing which shows 2nd Embodiment of the neutron generator which concerns on this invention. It is explanatory drawing which shows the drive type target of 3rd Embodiment of the neutron generator which concerns on this invention. It is explanatory drawing which shows the rotary target of the modification of 3rd Embodiment. It is explanatory drawing which shows the oblique incidence target of 4th Embodiment of the neutron generator which concerns on this invention. It is sectional drawing which shows the arrangement | positioning aspect of the target of 5th Embodiment of the neutron generator which concerns on this invention.

  Embodiments of a neutron generator and a medical accelerator system according to the present invention will be described below with reference to the drawings.

(First embodiment)
FIG. 1 is a cross-sectional view showing a first embodiment of a neutron generator according to the present invention.

  The neutron generator of this embodiment is applied to a medical accelerator system, for example. This medical accelerator system is applied to, for example, boron neutron capture therapy (BNCT) in a hospital. This BNCT causes a nuclear reaction with boron by irradiating a boron compound selectively retained inside the tumor with neutrons from outside the body, and locally destroys only the DNA of tumor cells by the fissioned helium and lithium nuclei. This is a treatment method.

  As shown in FIG. 1, the neutron generator of this embodiment includes an ion source 1, a linear accelerator 3, and a target unit 15. The ion source 1 generates a charged particle beam 2a. The ion source 1 is connected to the linear accelerator 3 via the transport system 4a.

  The linear accelerator 3 accelerates the charged particle beam 2a generated by the ion source 1 to a predetermined energy. As the linear accelerator 3, for example, a radio frequency quadrupole (RFQ) is used. Further, the linear accelerator 3 may be connected in multiple stages. In this case, the structure etc. which connected RFQ and the drift tube linear accelerator (DTL: Drift Tube Linac) in multiple stages are applicable.

  The linear accelerator 3 is connected to the target unit 15 via the transport system 4b. The target unit 15 includes a target 5, a gamma shield 10, a moderator (decelerator) 11, a collimator 12, and an irradiation port 13.

  The target 5 is installed in the target storage chamber 15a and, for example, lithium is used. The target 5 is irradiated with the charged particle beam 2 b accelerated by the linear accelerator 3 to generate neutrons 8. The target 5 is electrically insulated from other members by the insulating portion 14. The target 5 is electrically connected to the high voltage power supply 6 through the conductive wire 7. The high voltage power supply 6 applies a high voltage to the target 5 through the conducting wire 7.

  A dose detector 16 is installed in the target storage chamber 15a. The dose detector 16 detects the dose of neutrons generated by irradiating the target 5 with the charged particle beam 2b. The neutron dose is displayed by the neutron dose monitor 17. The neutron dose monitor 17 is electrically connected to the voltage control device 18. The voltage control device 18 controls the value of the high voltage applied from the high voltage power supply 6 to the target 5 based on the neutron dose detected by the dose detector 16.

  The gamma shield 10 shields gamma rays 9 that are secondary generated when the neutron 8 is generated. The moderator 11 guides the neutron 8 generated by irradiating the target 5 with the charged particle beam 2b to the irradiation port 13 while decelerating. This neutron 8 is irradiated to the tumor T of the patient P who is the irradiation target in a hospital or the like.

  Next, the operation of this embodiment will be described.

  First, a charged particle beam 2 a is generated by the ion source 1, and the charged particle beam 2 a is accelerated to a predetermined energy by the linear accelerator 3. The charged particle beam 2b accelerated by the linear accelerator 3 is irradiated to the target 5 in the target storage chamber 15a to generate neutrons 8. This neutron 8 is irradiated to the tumor T of the patient P, who is the subject of irradiation, to be treated.

Here, in this embodiment, lithium is used as the target 5 and a proton beam is used as the charged particle beam 2b. In this case, the threshold value at which the nuclear reaction of ⁷ Li (p, n) ⁷ Be occurs is 1.88 MeV, which is an endothermic reaction.

Incidentally, Li (p, n) in the reaction, proton lithium ^{7 (7} Li) (p) of lithium ⁷ by the collision (7 Li) neutrons in the process of is converted to beryllium ^{7 (7} Be) (n) ( ⁷ Li + p → ⁷ Be + n). The half-life of beryllium 7 ( ⁷ Be) is about 2 months and returns to lithium 7 ( ⁷ Li) by β decay. That is, beryllium 7 ( ⁷ Be) generated by the Li (p, n) reaction is used again for the Li (p, n) reaction by returning to the lithium 7 ( ⁷ Li).

The amount of neutron required for neutron treatment is about 1.0 × 10 ⁹ n / cm ² / s. When the reaction energy is set to 1.90 MeV, for example, so as to slightly exceed the threshold value, the amount of neutrons generated before the proton beam is decelerated to the threshold value of 1.88 MeV due to collision with the target 5 is 1 mA per proton beam. 1.0 × 10 ¹¹ n / s or more, and a neutron sufficient for treatment is expected to be obtained with a proton beam of about 20 mA.

  It is also possible to use liquid lithium as the lithium target. This liquid lithium target is used so as to be circulated from the surface of supply and cooling. In this case, a mechanism capable of applying a high voltage to the entire liquid lithium circulation system may be used.

  In the present embodiment configured as described above, when a high voltage is applied from the high voltage power source 6 to the target 5, the relative energy when the target 5 is irradiated with the charged particle beam 2b changes by the amount corresponding to the high voltage application. Will do. When a proton beam is used as the charged particle beam 2b, the incident energy incident on the target 5 can be increased by applying a negative voltage to the high voltage power source 6.

  Here, if the relative energy during irradiation can be changed, it is not always necessary to insulate only the target 5 as in the present embodiment. That is, it is also possible to insulate the entire structure including the target 5 and apply a high voltage.

  Therefore, in this embodiment, since the irradiation energy of the charged particle beam 2b can be adjusted only by the voltage of the high-voltage power supply 6, the amount and energy of the neutrons 8 generated by the reaction can be controlled with high accuracy.

  Moreover, in this embodiment, since the thermal neutron which can be directly used for irradiation is obtained by setting the relative energy of the charged particle beam 2b with respect to the target 5 so as to slightly exceed the threshold value, the configuration without the moderator It is also possible. In this case, gamma rays 9 generated when the neutron 8 is decelerated can also be reduced. Therefore, when using for a treatment, the unnecessary exposure to the patient P who is irradiation object can be reduced.

  Furthermore, in this embodiment, the dose detector 16 detects the neutron dose generated by irradiating the target 5 with the charged particle beam 2b. The voltage control device 18 controls the value of the high voltage applied from the high voltage power supply 6 to the target 5 based on the neutron dose detected by the dose detector 16. Thus, the relative energy when the target 5 is irradiated with the charged particle beam 2 b can be controlled by the dose detector 16 and the voltage control device 18. As a result, the amount and energy of the neutrons 8 generated by the reaction can be controlled with higher accuracy, and controllability and maintainability can be improved.

  That is, in the present embodiment, if the relative energy when the target 5 is irradiated with the charged particle beam 2b by the high voltage power source 6 is adjusted so as to greatly increase, neutrons up to the epithermal neutron region can be obtained. It is possible to irradiate a tumor T existing in a deep part that cannot be reached by thermal neutrons.

  As described above, in this embodiment, neutron irradiation with variable energy can be realized, and since the system is a simple system that only controls the high voltage of the high voltage power supply 6, the high voltage power supply 6 can be installed near the target 5. Therefore, the responsiveness is very good, which is optimal for feedback control.

  If the thickness of the target 5 is set so that the average energy of the charged particle beam 2b that has passed through the target 5 becomes just a threshold value, the beam can be used effectively. For example, when the proton beam from the linear accelerator 3 is irradiated to the lithium target 5 at 1.90 MeV, it is about 3 μm. When the average energy is set to exactly the threshold value, it is possible to suppress the heat generation of the target 5 and the generation of unnecessary gamma rays 9 due to the proton beam that does not contribute to the neutron production reaction.

(Second Embodiment)
FIG. 2 is a sectional view showing a second embodiment of the neutron generator according to the present invention.

  Each of the following embodiments is a modification of the first embodiment, and the basic configuration and operation are the same as those of the first embodiment. Therefore, different configurations and operations will be described. In the following embodiments, the same or corresponding parts as those in the first embodiment will be described with the same reference numerals.

  As shown in FIG. 2, in this embodiment, the dose detector 16 is installed in the vicinity of the exit of the irradiation port 13. The dose detector 16 may be installed on the downstream side of the target 5 with respect to the traveling direction of the charged particle beam 2b. The dose detector 16 may be installed on the beam axis of the charged particle beam 2b as long as it is a transmission type (non-destructive type) that can transmit neutrons.

  The neutron dose monitor 17 includes an integrating unit 21 and a determining unit 22. The integrating unit 21 integrates the neutron dose detected by the dose detector 16. The determination unit 22 determines whether or not the neutron dose accumulated by the accumulation unit 21 is equal to or greater than a preset value. In the present embodiment, the supply of the charged particle beam 2b is stopped when it is determined that the neutron dose integrated by the integration unit 21 is equal to or greater than a preset value.

  The means for stopping the supply of the charged particle beam 2b will be described below.

  As means for stopping the supply of the charged particle beam 2b, for example, there are the following three means. That is, there are means for controlling the voltage control device 18, means for controlling the ion source 1, and means for controlling the transport system 4a. In order to stop the supply of the charged particle beam 2b, at least one of the three means may be provided.

  The means for controlling the voltage control device 18 sets the voltage applied from the high voltage power supply 6 to the target 5 by the voltage control device 18 to zero when the neutron dose accumulated by the accumulation unit 21 becomes a preset value or more. To do.

  The ion source 1 is provided with an ion source control device 25. The ion source control device 25 controls ions generated by the ion source 1. The ion source control device 25 performs control so as to stop the generation of ions when the neutron dose accumulated by the accumulating unit 21 becomes equal to or greater than a preset value.

  A beam chopper 23 is installed in the transport system 4a. The beam chopper 23 bends the charged particle beam 2 a by an electric field so that the charged particle beam 2 a does not enter the linear accelerator 3. The beam chopper 23 is controlled by the transport system control device 24, and this transport system control device 24 operates the beam chopper 23 when the neutron dose accumulated by the accumulating unit 21 becomes a preset value or more. To prevent the charged particle beam 2a from entering the linear accelerator 3.

  As described above, according to the present embodiment, when the neutron dose exceeds a preset value, the supply of the charged particle beam 2b is stopped, so that the patient who is the irradiation target when the neutron is used for medical purposes. Irradiation of P with more than necessary neutrons is eliminated. As a result, unnecessary exposure to the patient P can be reduced.

  Further, according to the present embodiment, the reliability can be improved by using three means as means for stopping the supply of the charged particle beam 2b.

  In this embodiment, three means are used as means for stopping the supply of the charged particle beam 2b. However, the present invention is not limited to this, and the supply of the charged particle beam 2b is automatically stopped when a preset time has elapsed. You may control to do.

(Third embodiment)
FIG. 3 is an explanatory view showing a drive target of a third embodiment of the neutron generator according to the present invention. Each of the following embodiments is a modification of the target of the first embodiment, and the basic configuration and operation thereof are the same as those of the first embodiment. Therefore, different configurations and operations will be described.

  As shown in FIG. 3, the target 5 of this embodiment is provided with a drive mechanism (not shown). Thereby, the target 5 can be moved vertically and horizontally within a plane perpendicular to the beam axis of the charged particle beam 2b.

  As described above, according to the present embodiment, the target 5 is provided with a drive mechanism so that the target 5 can be moved vertically and horizontally within a plane perpendicular to the beam axis of the charged particle beam 2b. The irradiation position 20 of 2b can be changed. Therefore, consumption or damage of the target 5 due to heat generation of the target 5 due to irradiation of the charged particle beam 2b can be suppressed.

  FIG. 4 is an explanatory view showing a rotary target according to a modification of the third embodiment.

  As shown in FIG. 4, the target 5 of this modification is formed in a circular shape. The target 5 is provided with a rotational drive mechanism that rotationally drives the target 5. The rotational axis of this rotational drive mechanism is fixed at a position shifted from the beam axis of the charged particle beam 2 b in the target 5.

  As described above, according to the present modification, the target 5 is provided with the rotation drive mechanism, and the circular target 5 whose rotational axis is shifted with respect to the beam axis of the charged particle beam 2b is rotated. The irradiation position 20 can be changed. As a result, the same effect as in the second embodiment can be obtained.

  In addition, in order to apply a high voltage to the target 5 which is a rotary body in this modification, the restriction | limiting of a rotation range can be eliminated by using a brush.

(Fourth embodiment)
FIG. 5 is an explanatory view showing an oblique incidence target of the fourth embodiment of the neutron generator according to the present invention.

  As shown in FIG. 5, in this embodiment, the target 5 is provided with a tilt driving mechanism (not shown) that tilts the surface of the target 5 with respect to the beam axis 30. Thereby, in the present embodiment, the surface of the target 5 can be inclined with respect to the beam axis 30. That is, the surface of the target 5 can be adjusted with respect to the incident angle of the beam axis 30.

  Therefore, in the present embodiment, by tilting the target 5 with respect to the beam axis 30, the thickness of the target 5 through which the beam passes changes. Thereby, the production amount of neutrons can be controlled. Further, by changing the thickness of the target 5, it becomes possible to compensate for the consumption of the target 5 due to irradiation.

  In addition, this embodiment can also be set as the structure combined with the said 2nd Embodiment and its modification.

(Fifth embodiment)
FIG. 6 is a cross-sectional view showing an arrangement of targets in the fifth embodiment of the neutron generator according to the present invention.

  As shown in FIG. 6, in this embodiment, two targets used in the first embodiment are arranged as targets 5a and 5b with respect to the beam axis direction of the charged particle beam 2b. The target 5a is installed on the upstream side with respect to the traveling direction of the charged particle beam 2b, and the target 5b is installed on the downstream side with respect to the traveling direction of the charged particle beam 2b. In this case, the high voltage may be applied to either one of the targets 5a and 5b. Hereinafter, when the targets 5a and 5b are distinguished, the target 5a is assumed to be the upstream target 5a, and the target 5b is assumed to be the downstream target 5b.

  Therefore, in this embodiment, most of the charged particle beam 2b irradiated to the upstream target 5a loses the energy depending on the thickness of the upstream target 5a on the average, and then the downstream target. It will enter into 5b. If the energy at this time is higher than the threshold value of the neutron production reaction, the neutron 8 is obtained from the downstream target 5b.

  In this embodiment, if the total thickness of the two targets 5a and 5b is the same as the thickness of the target 5 of the first embodiment, the amount of neutrons 8 obtained is the same as that of the first embodiment. It becomes the same level. On the other hand, the thermal load can be dispersed by dividing the target into two. In this case, the voltage applied to the upstream target 5 a and the downstream target 5 b can also be adjusted by the resistance divider 40.

  Further, in the present embodiment, if the potential of the downstream target 5b is reduced to an amount corresponding to the average energy lost in the upstream target 5a, the downstream target 5b also has neutrons that are substantially equivalent to the upstream target 5a. 8 is obtained, and it becomes possible to efficiently generate the neutron 8 by reusing the charged particle beam 2b after passing through the upstream target 5a.

(Other embodiments)
Although several embodiments of the present invention have been described, these embodiments are presented by way of example and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, replacements, changes, and combinations can be made without departing from the scope of the invention. These embodiments and their modifications are included in the scope and gist of the invention, and are also included in the invention described in the claims and the equivalents thereof.

  For example, in the above-described embodiment, an example in which the medical accelerator system is applied to BNCT has been described. However, the present invention is not limited thereto, and is applied to manufacture a radioisotope element for positron emission tomography (PET). be able to.

  In the above embodiment, the charged particle beam 2a is accelerated to a predetermined energy using the linear accelerator 3, but a cyclotron or a FFAG (Fixed Field Alternating Gradient) accelerator may be used as the other accelerator. .

  Furthermore, in the above embodiment, it is also possible to generate an electric field or magnetic field for deflecting the charged particle beam 2b upstream of the target 5 with respect to the beam traveling direction of the charged particle beam 2b. Thereby, the irradiation position of the charged particle beam 2b to the target 5 can be changed.

  In the embodiment described above, it is also possible to generate a quadrupole electric field or magnetic field for focusing or diverging the charged particle beam 2b upstream of the target 5 with respect to the beam traveling direction of the charged particle beam 2b. Thereby, the irradiation area of the charged particle beam 2b to the target 5 can be changed.

  DESCRIPTION OF SYMBOLS 1 ... Ion source, 2a, 2b ... Charged particle beam, 3 ... Linear accelerator, 4a ... Transport system, 4b ... Transport system, 5 ... Target, 5a ... Upstream target, 5b ... Downstream target, 6 ... High voltage Power source, 7 ... conductive wire, 8 ... neutron, 9 ... gamma ray, 10 ... gamma ray shield, 11 ... moderator, 12 ... collimator, 13 ... irradiation port, 14 ... insulating part, 15 ... target part, 15a ... target storage room, 16 ... Dose detector, 17 ... Neutron dose monitor, 18 ... Voltage control device, 20 ... Irradiation position, 21 ... Integration unit, 22 ... Determination unit, 23 ... Beam chopper, 24 ... Transport system control device, 25 ... Ion source control device, 30 ... Beam axis, 40 ... Resistance dividing part, P ... Patient, T ... Tumor

Claims (10)

An accelerator for accelerating a charged particle beam to a predetermined energy;
A target that emits neutrons when irradiated with the charged particle beam accelerated by the accelerator;
A high voltage power source that applies a voltage to the target and adjusts the energy of the charged particle beam when incident on the target;
A dose detector for detecting a neutron dose generated by irradiating the target with the charged particle beam;
A voltage control device that controls a value of a voltage applied to the target from the high-voltage power source based on a neutron dose detected by the dose detector;
An accumulator for accumulating the neutron dose detected by the dose detector;
A determination unit that determines whether or not the neutron dose accumulated in the accumulation unit is equal to or greater than a preset value;
Equipped with a,
The neutron generator , wherein the supply of the charged particle beam is stopped when the neutron dose becomes a preset value or more . The voltage control device stops application of a voltage from the high-voltage power source to the target when a neutron dose accumulated by the accumulation unit becomes equal to or higher than a preset value. The neutron generator described in 1. An ion source for generating the charged particle beam;
An ion source control device for controlling the generation of ions of the ion source,
2. The neutron generator according to claim 1 , wherein the ion source control device stops the generation of the ions when a neutron dose accumulated by the accumulation unit becomes a preset value or more . An ion source for generating the charged particle beam;
A transport system provided between the ion source and the accelerator;
A beam chopper installed in the transport system and bending the traveling direction so that the charged particle beam generated by the ion source does not enter the accelerator;
A transport system control device for controlling the operation of the beam chopper,
The transport system control device controls the charged particle beam so that the charged particle beam does not enter the accelerator by operating the beam chopper when the neutron dose exceeds a preset value. Or the neutron generator of 2 . The neutron generator according to any one of claims 1 to 4, wherein the target has a drive mechanism that moves in a plane perpendicular to a beam axis of the charged particle beam . 5. The target according to claim 1, wherein the target is formed in a circular shape and has a rotation drive mechanism that rotates with a rotation axis shifted from a beam axis of the charged particle beam . Neutron generator. The neutron generator according to any one of claims 1 to 6 , wherein the target has a tilt driving mechanism that allows a surface of the target to tilt with respect to a beam axis of the charged particle beam . The neutron generator according to claim 1 , wherein a plurality of the targets are arranged in a beam axis direction of the charged particle beam . The target is disposed on the upstream side and the downstream side with respect to the traveling direction of the charged particle beam, and the potential of the target on the downstream side is reduced to an amount corresponding to the average energy lost in the target on the upstream side. The neutron generator according to claim 8 . An accelerator for accelerating a charged particle beam to a predetermined energy;
A target for generating neutrons by irradiating the charged particle beam accelerated by the accelerator;
A high-voltage power source that applies a voltage to the target and adjusts the energy of the charged particle beam when the target is incident;
A dose detector for detecting a neutron dose generated by the target;
A voltage control device for controlling the voltage value of the high-voltage power supply based on the neutron dose detected by the dose detector;
An accumulator for accumulating the neutron dose detected by the dose detector;
A determination unit that determines whether or not the neutron dose accumulated in the accumulation unit is equal to or greater than a preset value;
With
The target is a target for BNCT that emits neutrons used for boron neutron supplement therapy (BNCT), and irradiates the irradiation target with the neutrons.
A medical accelerator system , wherein the supply of the charged particle beam is stopped when the neutron dose exceeds a preset value.

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