TWM604092U - Synchrotron accelerating system - Google Patents

Abstract

A synchronous acceleration system includes a main ring, an injection device and an extraction device. The main ring contains four maintenance devices and a radio frequency accelerating cavity. The four maintaining devices are respectively arranged in the four quadrants of the main ring and spaced apart from each other. The maintaining device is used to deflect and focus a particle beam. The radio frequency accelerating cavity is adjacent to the maintaining device, and the radio frequency accelerating cavity is used to accelerate the particle beam. The injection device has an introduction channel located on the same horizontal plane as the main ring. The lead-out device has a spacer magnet, a lead-out spacer magnet and a six-pole magnet respectively arranged on two opposite sides of the maintaining device, and a lead-out channel perpendicular to the main ring. The two ends of the six-pole magnet are respectively connected to the main ring and the lead-out channel. The six-pole magnet is used to make the particle beam form a third-order resonance and enter the lead-out channel.

Description

Synchronous acceleration system

This model relates to an acceleration system, especially a synchronous acceleration system suitable for charged particles.

At present, the synchrotron system is used to accelerate the charged particles and emit high-energy charged particle beams to treat cancer, which can accurately target the target tumor, reduce damage to normal tissues, and effectively reduce the occurrence of side effects. It is one of the medical treatment methods for cancer. For example, proton therapy uses charged protons to destroy the DNA of cancer cells and prevent cell regeneration to kill tumors.

However, the synchrotron system usually has a huge volume. For example, the acceleration track has a circumference of more than 30 meters. Therefore, a large medical field space is required to accommodate the system equipment. For most medical institutions, it will cause space utilization. It is inconvenient and increases the related cost of configuring this medical system.

The synchrotron system for medical use is limited in the field space due to its excessive size, and even affects the scope of application. In view of this, some embodiments of this creation provide a synchronous acceleration system suitable for small spaces.

The synchronization acceleration system of an embodiment of the invention includes a main ring, an injection device, and an extraction device. The main ring contains four maintenance devices and a radio frequency accelerating cavity. The four maintaining devices are respectively arranged in the four quadrants of the main ring and spaced apart from each other. The maintaining device is used to deflect and focus a particle beam. The radio frequency accelerating cavity is adjacent to the maintaining device, and the radio frequency accelerating cavity is used to accelerate the particle beam. The injection device has an introduction channel located on the same horizontal plane as the main ring, wherein the introduction channel is connected to the main ring. The lead-out device has a spacer magnet, a lead-out spacer magnet and a six-pole magnet respectively arranged on two opposite sides of the maintaining device, and a lead-out channel perpendicular to the main ring. The two ends of the six-pole magnet are respectively connected to the main ring and the lead-out channel. The six-pole magnet is used to make the particle beam form a third-order resonance and enter the lead-out channel.

In an embodiment, an included angle between the two-pole magnet of the maintaining device and a ring center of the main ring ranges from 30 degrees to 90 degrees.

In one embodiment, the two-pole magnet of the maintaining device has an edge angle ranging from 15 degrees to 30 degrees.

In one embodiment, the two-pole magnet of the maintaining device has an edge angle of 18.6 degrees.

In one embodiment, the quadrupole magnet of the maintaining device is used to focus the particle beam so that the particle beam is a cluster of elliptical cross-section at any position in the main ring, wherein the width of the cluster in the horizontal direction is greater than that in the vertical direction. height.

In one embodiment, the circumference of the main ring ranges from 15 meters to 100 meters.

In one embodiment, the main ring further includes an annular vacuum tube surrounding the four maintaining devices, the radio frequency accelerating cavity, and the extraction device.

In one embodiment, the injection device includes a linear accelerator.

In one embodiment, the linear accelerator includes an ion source, an accelerator, and a radio frequency quadrupole magnet.

In this way, the synchrotron system uses a vertical extraction particle mechanism to reduce the number of secondary magnets through structural improvements, which can effectively save the field space required by the system, so as to achieve a miniaturized synchrotron system and avoid too large volume. And limit the scope of application.

The following detailed descriptions are provided with specific embodiments and accompanying drawings, so that it is easier to understand the purpose, technical content, characteristics and effects achieved by this creation.

The embodiments of this creation will be described in detail below, and the drawings will be used as examples. In the description of the specification, in order to enable readers to have a more complete understanding of this creation, many specific details are provided; however, this creation may still be implemented without some or all of the specific details. The same or similar elements in the drawings will be represented by the same or similar symbols. It is particularly important to note that the drawings are for illustrative purposes only, and do not represent the actual size or quantity of the components. Some details may not be completely drawn in order to keep the drawings concise.

Figure 1 is a schematic diagram of a synchronous acceleration system according to an embodiment of the authoring. FIG. 2 is a schematic diagram of the momentum distribution of the particle beam in the embodiment shown in FIG. 1. Please refer to FIG. 1, the synchronous acceleration system of an embodiment of the present creation includes a main ring 1, an injection device 2 and an extraction device 3. The main ring 1 includes four maintaining devices 10 and a radio frequency accelerating cavity 12. Looking down from top to bottom, the four maintaining devices 10 are spatially separated from each other, and are distributed in the four quadrants of the horizontal plane where the main ring 1 is located. Each maintenance device 10 can deflect the movement direction of the particle beam and focus the beam shape of the particle beam through the action of the internal magnetic field. The particle beam can be, but is not limited to, a proton beam.

In one embodiment, the maintaining device 10 includes a plurality of two-pole magnets 100 and a four-pole magnet 102. The two-pole magnet 100 is arranged on two different sides of the four-pole magnet 102. The two-pole magnet 100 is used to deflect the particle beam, and the four-pole magnet 102 is used to focus the particle beam.

The radio frequency acceleration cavity 12 is arranged adjacent to the maintenance device 10. The particle beam moving through the radio frequency acceleration cavity 12 will be accelerated by the action of the electric field and the magnetic field, and finally reach the expected target speed and energy. Through the action of the main ring 1, the particle beam can maintain stable motion and gain acceleration, gradually reaching the required energy.

The injection device 2 has an introduction channel 200 located on the same horizontal plane as the main ring 1, and the introduction channel 200 is connected to the main ring 1. That is, through the horizontal introduction technology, the particle beam is injected into the internal motion track of the main ring 1 in a manner parallel to the horizontal plane where the main ring 1 is located. Compared with the traditional vertical introduction method, there is no need to add additional and large-angle dipole magnets, which can save the field space required by the system. The introduction channel 200 introduces a particle beam of lower energy into the main ring 1, and the main ring 1 performs a synchronous acceleration effect on the particle beam to regulate the movement energy.

Please refer to Figures 1 and 2 together. The lead-out device 3 includes an electric wire septum 30, a Lambertson Septum 32, a six-pole magnet 34 and an lead-out channel 36, of which six The two ends of the pole magnet 34 are respectively connected to the main ring 1 and the lead-out channel 36. In one embodiment, the lead-out spacer magnet 30 divides the passing particle beam into two parts through spacers and semicircular rings that are separately arranged in the vertical direction, and a part of the ion beam is deflected by the spacer magnet 32 It changes the direction of movement through the action of the six-pole magnet 34 to make the particle beam with a preset energy form a third-order resonance, as shown in FIG. 2, to realize a slow extraction mechanism. Furthermore, the lead-out line spacer magnet 30 is used to generate a deflection electric field, the spacer magnet 32 is used to generate a deflection magnetic field, and the six-pole magnet 34 leads the particle beam to the lead-out channel 36 with the beam line trajectory perpendicular to the main ring 1. Then, the particle beam is led out to an external treatment device in a direction perpendicular to the horizontal plane where the main ring 1 is located through the lead-out channel 36 for medical applications such as hitting target tumors.

Since the synchronization system has the characteristics of adjustable energy and lower radiation, for example, the initial injected particle beam energy is 7 (MeV), and the subsequent acceleration through the main ring 1 reaches the energy range of 70 to 250 (MeV). It is suitable for providing high-energy particle beam for cancer treatment. According to the above structure, the structural design of horizontal introduction and vertical extraction of particle beams can reduce the field space required by the system, and the main ring 1 adopts a smaller number of two-pole magnets 100, which can reduce the system cost and require less energy. Consumption, so as to realize the miniaturization and low-cost synchronization acceleration system, contribute to the popularization of its medical applications. In some embodiments, the circumference of the main ring ranges from 15 to 100 meters. For example, the circumference of the main ring is 22.5 meters, which requires less layout space than the prior art.

Please continue to refer to FIG. 1. In one embodiment, the four holding devices 10 are arranged in mirror symmetry with respect to the center C of the main ring 1. For example, the two-pole magnet 100 of the holding device 10 is opposite to the ring center C of the main ring 1. The angle between the centers C ranges from 30 degrees to 90 degrees; preferably, the angle between the two-pole magnet 100 and the border of the adjacent quadrant is 45 degrees.

In at least one embodiment, the quadrupole magnet 102 of the maintaining device 10 is used to focus the particle beam, whereby the particle beam is a cluster with an elliptical cross-section at any position in the main ring 1, wherein the cluster is along the horizontal direction. The width is greater than the height along the vertical direction, that is, the β _y function curve is always greater than the β _x function curve (Betatron function), where β _x represents the oscillation of the particle beam in the horizontal direction, and the β _y function represents the oscillation of the particle beam in the vertical direction. For example, the maximum value of the β function value is (6.25, 3.94) meters, which shows that the particle beam is an elliptical cluster at any position in the main ring 1.

FIG. 3 is a schematic diagram of a two-pole magnet 100 according to another embodiment of the invention. Referring to FIG. 3, in one embodiment, the two-pole magnet 100 has a dipole edge angle A, which can deflect and weakly focus the particle beam. As shown in FIG. 3, the edge angle A refers to the angle formed by the line 108 between the ring center C and the particle motion track center 106 relative to the magnet boundary 100a. In other words, the edge angle A refers to the angle between the normal direction perpendicular to the direction of movement of the particle beam and the boundary of the exit end of the magnet. For example, the edge angle A ranges from 15 degrees to 30 degrees; preferably, the edge angle A is 18.6 degrees. Through the appropriate edge angle A design, the circumference of the main ring 1 can be reduced to save layout space, which is helpful to realize a miniaturized synchronous acceleration system.

Fig. 4 is a schematic diagram of a synchronous acceleration system according to another embodiment of the authoring. 4, in one embodiment, the main ring 1 also includes a ring-shaped vacuum tube 14, which surrounds the four maintenance devices 10, the radio frequency acceleration chamber 12, and the extraction device 3 and other components, and has a ring-shaped internal vacuum channel through The function of the device 10 and the radio frequency acceleration cavity 12 is maintained for the particle beam to continuously move and accelerate therein. It is connected in series with four maintaining devices 10 to form a vacuum pipeline required for particle beam movement. In another embodiment, the main ring further includes a vacuum pump connected to the main ring 1 for generating the aforementioned vacuum pipeline. In at least one embodiment, the injection device 2 includes a linear accelerator (Linac). For example, the linear accelerator includes an ion source 20, an accelerator 22, and a radio frequency quadrupole magnet 24. In an exemplary embodiment, the ion source 20 has a hydrogen source with an initial energy of about 7 to 70 (MeV) to generate a proton beam; the accelerator 22 is used to accelerate the proton beam, and the radio frequency quadrupole magnet 24 is used to focus the proton beam.

In summary, some embodiments of this creation provide a synchrotron system, which mainly utilizes the structural design of horizontal introduction and vertical extraction of particle beams, which can reduce the field space required by the system. For example, the circumference of the vacuum tube is only 22.5 meters. , And the use of a smaller number of magnets can reduce system costs and require less energy consumption, so as to achieve a miniaturized and low-cost synchrotron system, which helps to popularize its medical applications and avoids the size of the synchrotron system. And restrict the application field.

The above-mentioned embodiments are only to illustrate the technical ideas and characteristics of this creation, and their purpose is to enable those who are familiar with the art to understand the content of this creation and implement them accordingly. If the patent scope of this creation cannot be limited by this, That is to say, all equal changes or modifications made in accordance with the spirit of this creation should still be covered by the scope of the patent of this creation.

A: Edge angle C: ring center 1: main ring 10: Maintain the device 12: RF acceleration cavity 14: Ring vacuum tube 100: Two-pole magnet 102: Quadrupole magnet 106: Orbit Center 108: connection 100a: Magnet boundary 2: injection device 20: ion source 22: accelerator 24: RF quadrupole magnet 200: introduction channel 3: Leading device 30: Lead wire spacer magnet 32: spacer magnet 34: Six pole magnet 36: lead channel

Figure 1 is a schematic diagram of a synchronous acceleration system according to an embodiment of the authoring. FIG. 2 is a schematic diagram of the momentum distribution of the particle beam in the embodiment shown in FIG. 1. Fig. 3 is a schematic diagram of a two-pole magnet according to another embodiment of the creation. Fig. 4 is a schematic diagram of a synchronous acceleration system according to another embodiment of the authoring.

C: ring center

1: main ring

10: Maintain the device

12: RF acceleration cavity

100: Two-pole magnet

102: Quadrupole magnet

2: injection device

200: introduction channel

3: Leading device

30: Lead wire spacer magnet

32: spacer magnet

34: Six pole magnet

36: lead channel

Claims (9)

A synchronous acceleration system including: One main ring, including: Four maintaining devices, respectively located in the four quadrants of the main ring and spaced apart from each other, are used to deflect and focus a particle beam; and A radio frequency accelerating cavity, adjacent to the maintaining device, for accelerating the particle beam; An injection device having an introduction channel located on the same horizontal plane as the main ring, wherein the introduction channel is connected to the main ring; and A lead-out device having a spacer magnet, a lead-out spacer magnet and a six-pole magnet respectively arranged on two opposite sides of the maintaining device, and a lead-out channel perpendicular to the main ring, wherein the six-pole magnet The two ends are respectively connected to the main ring and the extraction channel, and the six-pole magnet is used to make the particle beam form a third-order resonance and enter the extraction channel. The synchro-acceleration system according to claim 1, wherein an included angle between the two-pole magnet of the maintaining device and a ring center of the main ring ranges from 30 degrees to 90 degrees. The synchronous acceleration system according to claim 1, wherein the two-pole magnet of the maintaining device has an edge angle ranging from 15 degrees to 30 degrees. The synchronous acceleration system according to claim 1, wherein the two-pole magnet of the maintaining device has an edge angle of 18.6 degrees. The synchrotron system according to claim 1, wherein the quadrupole magnet of the maintaining device is used to focus the particle beam so that the particle beam is a bunch of elliptical cross-sections at any position in the main ring, wherein the beam The width of the group in the horizontal direction is greater than the height in the vertical direction. The synchronous acceleration system according to claim 1, wherein the circumference of the main ring is 22.5 meters. The synchrotron acceleration system according to claim 1, wherein the main ring includes a ring-shaped vacuum tube surrounding the four maintaining devices, the radio frequency acceleration cavity and the extraction device. The synchronous acceleration system according to claim 1, wherein the injection device includes a linear accelerator. The synchrotron system according to claim 8, wherein the linear accelerator includes an ion source, an accelerator, and a radio frequency quadrupole magnet.

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