技术领域technical field
本申请涉及癌症治疗仪器领域，尤其涉及一种医用质子直线加速器。The present application relates to the field of cancer treatment instruments, in particular to a medical proton linear accelerator.
背景技术Background technique
当今世界，癌症已成为主要威胁人类生命的主要病症。近几年全世界癌症发病率正在逐年提高，癌症也已成为影响中国人生命健康的最大威胁。目前，癌症的传统治疗方法有药物治疗和放疗方法。其中传统放疗方法主要有X射线和γ射线，因射线的能量释放随路径递减，这两种放疗方式在杀死癌细胞的同时，路径中的正常组织也会受到损伤，因此术后严重影响到病人的生活质量。In today's world, cancer has become a major disease that mainly threatens human life. In recent years, the incidence of cancer in the world has been increasing year by year, and cancer has become the biggest threat to the life and health of Chinese people. At present, the traditional treatment methods for cancer include drug therapy and radiotherapy. Among them, the traditional radiotherapy methods mainly include X-rays and γ-rays. Because the energy release of the rays decreases with the path, these two radiotherapy methods kill cancer cells and damage normal tissues in the path, so postoperative serious effects on the Patient's quality of life.
近几年，国内兴起质子和重离子技术在治疗癌症时，相比于传统放疗方法有重大优势，质子经由直线加速器加速至约61％的光速时，形成离子射线被引出射入人体，在到达肿瘤病灶前，射线能量释放不多，但是到达病灶后，射线会瞬间释放大量能量，形成Bragg曲线状能量释放轨迹，整个治疗过程好比是针对肿瘤的“立体定向爆破”，能够对肿瘤病灶进行强有力的照射，并大大减少对周围正常组织的照射，实现疗效最大化。因病人身体内肿瘤位置的不同，因此治疗时所需要的质子束流能量要求一般在70-250MeV内连续可调，并且为了达到较大的剂量率和减少照射时间，质子束占空比需要较高。In recent years, the rise of proton and heavy ion technology in China has significant advantages over traditional radiotherapy methods in the treatment of cancer. When protons are accelerated to about 61% of the speed of light by a linear accelerator, the ion rays formed are drawn out and injected into the human body. Before the tumor lesion, the ray energy release is not much, but after reaching the lesion, the ray will release a large amount of energy instantly, forming a Bragg curve energy release trajectory. Powerful irradiation, and greatly reduce the irradiation of surrounding normal tissues to maximize the curative effect. Due to the different positions of the tumor in the patient's body, the proton beam energy required for treatment is generally continuously adjustable within 70-250 MeV, and in order to achieve a higher dose rate and reduce the irradiation time, the proton beam duty cycle needs to be higher. high.
质子加速器主要包括质子回旋加速器、质子同步加速器和质子直线加速器。质子回旋加速器可提供稳定、持续的质子束，束流切断和开启速度很快，但需定期更换内置离子源，而且束流能量不可调，为了实现质子束能量连续可调，回旋加速器后需再接一个能量调制器，利用散射将经回旋加速器加速的质子束的束流能量降低，这种拦截式的质子束能量调节方式会产生大量的辐射，容易造成器件的活化，增加医院的辐射屏蔽成本，而且散射造成的束流能量利用率低，散射后的束流品质差，70MeV通过的效率仅为2％。质子同步加速器可提供70-250MeV范围内可调的质子束，但同步加速器由注入器和环型加速器组成，占地面积大，整个系统架构复杂，而且同步加速器的注入、升能和标准化循环需要占用很长时间，引出平台所对应的有效时间很短，换能时间缓慢，造成无效治疗时间长；即便是改进后的紧凑型同步加速器，仍不能克服只能提供脉冲质子束、平均剂量率低的缺点，无法适应快速、连续治疗的需要。质子直线加速器质子引出和注入容易，可提供稳定、持续的质子束，质子束在加速和传输过程中几乎无损失，具有离子源可长期稳定运行、剂量率高的优点，申请号为201410323833.1的专利中解决了在限制空间区域安装质子直线加速器的问题，但由于采用的耦合腔线性加速器(CCL)为驻波加速器，出射的质子束能量为固定值，仍未能解决直线加速器束流能量无法连续可调的问题。Proton accelerators mainly include proton cyclotrons, proton synchrotrons and proton linear accelerators. The proton cyclotron can provide a stable and continuous proton beam, and the beam can be cut off and on quickly, but the built-in ion source needs to be replaced regularly, and the beam energy cannot be adjusted. An energy modulator is connected to reduce the beam energy of the proton beam accelerated by the cyclotron by using scattering. This interception-type proton beam energy adjustment method will generate a large amount of radiation, which will easily cause the activation of the device and increase the radiation shielding cost of the hospital. , and the beam energy utilization rate caused by scattering is low, the quality of the beam after scattering is poor, and the passing efficiency of 70MeV is only 2%. The proton synchrotron can provide adjustable proton beams in the range of 70-250MeV, but the synchrotron consists of an injector and a ring accelerator, which occupies a large area, and the entire system architecture is complex, and the injection, energy-up and standardized cycles of the synchrotron require It takes a long time, the effective time corresponding to the extraction platform is very short, and the energy conversion time is slow, resulting in a long time for ineffective treatment; even the improved compact synchrotron still cannot overcome the problem of only providing pulsed proton beams and low average dose rate. Shortcomings, unable to adapt to the needs of rapid and continuous treatment. The proton linear accelerator is easy to extract and inject protons, and can provide a stable and continuous proton beam. The proton beam has almost no loss during acceleration and transmission. It has the advantages of long-term stable operation of the ion source and high dose rate. The patent application number is 201410323833.1 solves the problem of installing a proton linear accelerator in a restricted space area, but because the coupled cavity linear accelerator (CCL) is a standing wave accelerator, the energy of the outgoing proton beam is a fixed value, which still fails to solve the problem that the beam energy of the linear accelerator cannot be continuous. Adjustable question.
发明内容Contents of the invention
本申请提供一种医用质子直线加速器，该医用质子直线加速器提供的质子束稳定、持续且束流能量连续可调。The present application provides a medical proton linear accelerator. The proton beam provided by the medical proton linear accelerator is stable and continuous, and the beam energy is continuously adjustable.
本申请提供的一种医用质子直线加速器，包括：离子源、低能加速段从离子源中引出质子的喷射器、中能加速段将质子能量加速至固定能量值的漂移管直线加速器、RF功率源和高能加速段的行波质子加速器，所述RF功率源为所述行波质子加速器提供高频功率，使得所述行波质子加速器腔体内形成高频电磁场；所述行波质子加速器连接于漂移管直线加速器之后，当质子束进入所述行波质子加速器腔体时受到高频电场的作用而加速，通过改变输入的所述高频功率的大小，可改变高频电场的强度，使得经过所述行波质子加速器加速后出射的质子束能量值连续可调节，获得不同能量值的质子束，满足癌症治疗的需要。The application provides a medical proton linear accelerator, including: an ion source, an injector that extracts protons from the ion source in a low-energy acceleration section, a drift tube linear accelerator that accelerates the proton energy to a fixed energy value in a medium-energy acceleration section, and an RF power source and the traveling-wave proton accelerator of the high-energy acceleration section, the RF power source provides high-frequency power for the traveling-wave proton accelerator, so that a high-frequency electromagnetic field is formed in the cavity of the traveling-wave proton accelerator; the traveling-wave proton accelerator is connected to the drift After the tube linear accelerator, when the proton beam enters the cavity of the traveling wave proton accelerator, it is accelerated by the high-frequency electric field. By changing the input high-frequency power, the intensity of the high-frequency electric field can be changed, so that the The energy value of the proton beam emitted by the traveling wave proton accelerator after acceleration can be continuously adjusted to obtain proton beams with different energy values to meet the needs of cancer treatment.
在一些实施例中，所述离子源为电子回旋共振离子源。In some embodiments, the ion source is an electron cyclotron resonance ion source.
在一些实施例中，所述行波质子加速器包括多段依次连接的行波质子加速腔，RF功率源有多个，每个RF功率源单独向每段加速单元提供高频功率，每个RF功率源的高频功率独立可调。In some embodiments, the traveling wave proton accelerator includes a plurality of traveling wave proton accelerating chambers connected in sequence, and there are multiple RF power sources, and each RF power source provides high-frequency power to each accelerating unit independently, and each RF power The high frequency power of the source is independently adjustable.
在一些实施例中，所述行波质子加速器还包括周期性排列的耦合盘片，所述周期性排列的耦合盘片用于降低电磁场的相速度和保证相邻单元的磁场耦合。In some embodiments, the traveling wave proton accelerator further includes periodically arranged coupling disks, and the periodically arranged coupling disks are used to reduce the phase velocity of the electromagnetic field and ensure the magnetic field coupling of adjacent units.
在一些实施例中，所述耦合盘片设置于所述行波质子加速腔腔体内侧，耦合盘片呈周期性排列。In some embodiments, the coupling disks are arranged inside the cavity of the traveling wave proton acceleration cavity, and the coupling disks are arranged periodically.
在一些实施例中，所述喷射器为射频四极场加速器。In some embodiments, the injector is a radio frequency quadrupole field accelerator.
在一些实施例中，所述医用质子直线加速器还包括束流低能传输段，设置于所述离子源与射频四极场加速器之间，用于接收所述离子源输出的质子束，将其调整匹配到射频四极场加速器的入口参数。In some embodiments, the medical proton linear accelerator also includes a beam low-energy transmission section, which is arranged between the ion source and the radio frequency quadrupole field accelerator, and is used to receive the proton beam output by the ion source and adjust it Match to the entrance parameters of the RF quadrupole field accelerator.
在一些实施例中，所述漂移管直线加速器为分离型漂移管直线加速器。In some embodiments, the drift tube linear accelerator is a separate drift tube linear accelerator.
在一些实施例中，所述医用质子直线加速器还包括束流中能传输段，设置于所述射频四极场加速器与分离型漂移管直线加速器之间，用于接收所述射频四极场加速器输出的质子束，将其调整匹配到分离型漂移管直线加速器的入口参数。In some embodiments, the medical proton linear accelerator further includes a beam energy transmission section, which is arranged between the radio frequency quadrupole field accelerator and the separated drift tube linear accelerator, and is used to receive the radio frequency quadrupole field accelerator The output proton beam is adjusted to match the inlet parameters of the separated drift tube linac.
在一些实施例中，其特征在于，所述行波质子加速器为圆柱形腔体或方形腔体。In some embodiments, it is characterized in that the traveling wave proton accelerator is a cylindrical cavity or a square cavity.
本申请的有益效果是：The beneficial effect of this application is:
本申请的医用质子直线加速器在中能加速段使用分离型漂移管直线加速器，在高能加速段采用行波质子加速器代替现有技术中的CCL，使得加速器不仅结构更加紧凑、占用空间更小，而且出射的质子束能量在70-250MeV范围内连续可调，可满足肿瘤治疗时因病人身体内肿瘤位置不同束流能量需调节的需要。The medical proton linear accelerator of the present application uses a separate drift tube linear accelerator in the medium-energy acceleration section, and uses a traveling-wave proton accelerator in the high-energy acceleration section to replace the CCL in the prior art, so that the accelerator is not only more compact in structure and takes up less space, but also The energy of the emitted proton beam is continuously adjustable within the range of 70-250MeV, which can meet the needs of beam energy adjustment due to different tumor positions in the patient's body during tumor treatment.
另外，由于分离型漂移管直线加速器和行波质子加速器均为多段依次连接的结构，可以分期分段建造，本申请的医用质子直线加速器可适应不同医院对质子能量的需求，后期也可根据治疗需求进行能量升级。In addition, since the separate drift tube linear accelerator and the traveling wave proton accelerator are multi-segment sequentially connected structures, they can be built in stages and segments. The medical proton linear accelerator of this application can meet the needs of different hospitals for proton energy. Energy upgrades are required.
附图说明Description of drawings
图1为本申请的一种医用质子直线加速器结构框图；Fig. 1 is a structural block diagram of a medical proton linear accelerator of the present application;
图2为本申请提供的一种SDTL结构图；Fig. 2 is a kind of SDTL structural diagram provided by the present application;
图3为本申请提供的行波质子加速器的一段加速腔结构图。Fig. 3 is a structural diagram of a section of the accelerating cavity of the traveling wave proton accelerator provided by the present application.
图4为行波质子加速器加速质子的原理图。Fig. 4 is a schematic diagram of proton acceleration by a traveling wave proton accelerator.
具体实施方式detailed description
下面通过具体实施方式结合附图对本申请作进一步详细说明。The present application will be described in further detail below through specific embodiments in conjunction with the accompanying drawings.
请参考图1，为本申请提供的一种医用质子直线加速器，该医用质子直线加速器包括：依次连接的离子源1、喷射器2、漂移管直线加速器3和行波质子加速器4。Please refer to FIG. 1 , which is a medical proton linear accelerator provided by the present application. The medical proton linear accelerator includes: an ion source 1 , an injector 2 , a drift tube linear accelerator 3 and a traveling wave proton accelerator 4 connected in sequence.
离子源1优选为连续束流较大、质子比较高的电子回旋共振(ECR)离子源，ECR离子源产生连续稳定的质子束并将其能量加速至30keV，质子束占空比较高。The ion source 1 is preferably an electron cyclotron resonance (ECR) ion source with a large continuous beam current and a high ratio of protons. The ECR ion source generates a continuous and stable proton beam and accelerates its energy to 30keV, and the duty ratio of the proton beam is high.
喷射器2优选为射频四极场(RFQ)加速器，RFQ加速器作为一种强流低能离子直线加速器，它巧妙地将束流的纵向、横向的匹配以及加速与聚焦等作用都用一个加速腔中的单一射频电场予以实现，被广泛用作质子加速器的低能强流注入器，适于加速低能段质子。具体的，能量30keV的质子束从离子源1中引出后，经过RFQ加速器，束流能量被加速至3～5MeV。The injector 2 is preferably a radio frequency quadrupole field (RFQ) accelerator. As a high-current low-energy ion linear accelerator, the RFQ accelerator skillfully combines the longitudinal and lateral matching, acceleration and focusing of the beam in an accelerating chamber. It is realized by a single radio frequency electric field, and is widely used as a low-energy high-current injector for proton accelerators, suitable for accelerating protons in low-energy segments. Specifically, after the proton beam with an energy of 30keV is extracted from the ion source 1, it passes through the RFQ accelerator, and the energy of the beam is accelerated to 3-5 MeV.
在一些实施例中，在离子源1与RFQ加速器之间还设置有束流低能传输段(LEBT)12，用于接收离子源1输出的质子束，将其调整匹配到RFQ加速器的入口参数。In some embodiments, a low-energy beam transfer section (LEBT) 12 is provided between the ion source 1 and the RFQ accelerator, for receiving the proton beam output from the ion source 1 and adjusting it to match the entrance parameters of the RFQ accelerator.
漂移管直线加速器(DLT)3作为中能加速段，适于加速几兆伏到几十兆伏的质子。由于高频工作频率越高，加速腔径向尺寸越小，DLT3内部若安装磁铁聚焦装置，会使得结构比较复杂，尺寸很难缩小。为此，本申请的漂移管直线加速器3采用分离型漂移管直线加速器(SDTL)，参考图2，SDTL包括多个短腔，漂移管31被放置于腔内，漂移管31内不含磁铁聚焦装置33，使得漂移管3外径较小，磁铁聚焦装置33设置在相邻腔之间，相邻腔之间通过真空束流管道32相连通SDTL由于具有多个短腔和磁铁聚焦装置33因而会使得质子束横向得到聚焦。漂移管31的中心是束流通道311，质子束沿束流通道311轴线正向运动，相邻漂移管31之间为加速隙，漂移管与腔之间、加速隙内充满高频场，当质子运动到两漂移管之间时，高频纵向电场使质子加速，而当电场反向时，质子正好运动到漂移管31内，得到屏蔽。在一些实施例中，质子束经过SDTL加速后，束流能量达到70MeV。分离型漂移管直线加速器(SDTL)能够降低功率消耗，加速梯度高、结构紧凑、易加工安装等优点。The drift tube linear accelerator (DLT) 3 is used as a medium-energy acceleration section, which is suitable for accelerating protons from several megavolts to tens of megavolts. Since the higher the high-frequency operating frequency, the smaller the radial size of the acceleration cavity, if a magnet focusing device is installed inside the DLT3, the structure will be more complicated and the size will be difficult to reduce. For this reason, the drift tube linear accelerator 3 of the present application adopts a separate drift tube linear accelerator (SDTL). Referring to FIG. The device 33 makes the outer diameter of the drift tube 3 smaller, and the magnet focusing device 33 is arranged between adjacent cavities, and the adjacent cavities are connected to the SDTL through the vacuum beam flow pipe 32 because there are multiple short cavities and the magnet focusing device 33 This will cause the proton beam to be focused laterally. The center of the drift tube 31 is the beam channel 311, the proton beam moves forward along the axis of the beam channel 311, the acceleration gap is between the adjacent drift tubes 31, and the gap between the drift tube and the cavity is filled with a high-frequency field. When the protons move between the two drift tubes, the high-frequency longitudinal electric field accelerates the protons, and when the electric field reverses, the protons just move into the drift tube 31 and are shielded. In some embodiments, after the proton beam is accelerated by the SDTL, the energy of the beam reaches 70 MeV. The separated drift tube linear accelerator (SDTL) has the advantages of low power consumption, high acceleration gradient, compact structure, and easy processing and installation.
在一些实施例中，在RFQ加速器与SDTL之间还设置有束流中能传输段(MEBT)12，用于接收RFQ加速器输出的质子束，将其调整匹配到SDTL的入口参数。In some embodiments, a mid energy transport section (MEBT) 12 is set between the RFQ accelerator and the SDTL, for receiving the proton beam output from the RFQ accelerator and adjusting and matching it to the entrance parameters of the SDTL.
上述RFQ加速器、漂移管直线加速器3和行波质子加速器4由RF功率源(未示出)分别提供高频功率，RF功率源有多个，高频功率由RF网络分别传输至上述各个加速器。The RFQ accelerator, the drift tube linear accelerator 3 and the traveling wave proton accelerator 4 are respectively supplied with high-frequency power by RF power sources (not shown). There are multiple RF power sources, and the high-frequency power is transmitted to each of the above-mentioned accelerators by the RF network.
行波质子加速器4连接于漂移管直线加速器3之后，作为高能加速段。由于RF功率源提供了高频功率，使得在行波质子加速器腔体内形成高频电磁场，当质子束进入质子加速器4腔体，将受到高频电场的作用。参考图4，若质子速度Vp与高频电场相速度Vmw不同步或相差太大，随着时间的推移，质子会落入高频电场曲线的负值区，质子得不到有效加速甚至被减速。因此，为了能够正常加速质子，需要使高频电场的相速度与质子速度同步，即两者之间的相对速度非常小。The traveling wave proton accelerator 4 is connected behind the drift tube linear accelerator 3 as a high-energy acceleration section. Since the RF power source provides high-frequency power, a high-frequency electromagnetic field is formed in the cavity of the traveling wave proton accelerator. When the proton beam enters the cavity of the proton accelerator 4, it will be affected by the high-frequency electric field. Referring to Figure 4, if the proton velocity Vp and the phase velocity Vmw of the high-frequency electric field are not synchronized or the difference is too large, as time goes by, the protons will fall into the negative area of the high-frequency electric field curve, and the protons will not be effectively accelerated or even decelerated. . Therefore, in order to accelerate protons normally, it is necessary to synchronize the phase velocity of the high-frequency electric field with the proton velocity, that is, the relative velocity between the two is very small.
在一些实施例中，行波质子加速器4为圆柱形腔体或方形腔体，包括多段依次连通的行波质子加速腔40。参考图3，为本申请提供的一段行波质子加速腔40示意图，行波质子加速腔40腔体内侧设置有呈周期性排列的耦合盘片41，耦合盘片41为金属材料，设置有径向通道，耦合盘片41的径向通道用于保证相邻加速隙间的磁场耦合，作为高频功率传输的通道并可起到增强腔体抗干扰性的作用，耦合盘片41的周期性排列决定了相邻加速隙的高频电场相移。其中，相邻耦合盘片41之间为加速隙，质子束沿着行波质子加速腔40中轴线正向运动时，加速隙内充满正向高频电场对质子束加速，耦合盘片41隔离反向高频电场，使得质子束不被减速。对于耦合盘片41之间的间隔由进入行波质子加速腔40时的能量决定，若想对70MeV能量的质子进行加速，相邻加速隙高频电场相移为5/6π，进入行波质子加速腔的质子速度因子β为0.367，耦合盘片41需间隔0.153c/f的距离(c为光速，f为RF功率源频率)，若入行波质子加速腔的质子能量为80MeV，耦合盘片的间隔41需相应调整。In some embodiments, the traveling wave proton accelerator 4 is a cylindrical cavity or a square cavity, including a plurality of traveling wave proton accelerating cavities 40 connected in sequence. Referring to FIG. 3 , it is a schematic diagram of a traveling wave proton accelerating cavity 40 provided by the present application. The inside of the traveling wave proton accelerating cavity 40 is provided with periodically arranged coupling disks 41. The coupling disks 41 are made of metal materials and are provided with radial The radial channel of the coupling disc 41 is used to ensure the magnetic field coupling between adjacent acceleration gaps, as a channel for high-frequency power transmission and can play a role in enhancing the anti-interference of the cavity, and the periodicity of the coupling disc 41 The alignment determines the phase shift of the high-frequency electric field between adjacent accelerating gaps. Among them, there is an acceleration gap between adjacent coupling disks 41. When the proton beam moves forward along the central axis of the traveling wave proton acceleration cavity 40, the acceleration gap is filled with a positive high-frequency electric field to accelerate the proton beam, and the coupling disks 41 isolate The reverse high-frequency electric field prevents the proton beam from being decelerated. The distance between the coupling disks 41 is determined by the energy when entering the traveling-wave proton acceleration cavity 40. If you want to accelerate protons with 70 MeV energy, the phase shift of the high-frequency electric field in adjacent acceleration gaps is 5/6π, and the protons entering the traveling-wave The proton velocity factor β of the accelerating cavity is 0.367, and the coupling disk 41 needs to be spaced at a distance of 0.153c/f (c is the speed of light, f is the frequency of the RF power source). If the proton energy entering the traveling wave proton accelerating cavity is 80MeV, the coupling disk The interval 41 needs to be adjusted accordingly.
每段行波质子加速腔40分别连接有一个RF功率源，每个RF功率源单独向每段行波质子加速腔40提供高频功率，分别在每段行波质子加速腔40内形成高频电磁场，每个RF功率源的高频功率独立可调。改变行波质子加速腔40对应的RF功率源的功率值，即可改变该段加速腔电场的强度，从而改变质子束经过该段加速腔加速后获得的能量值。每段行波质子加速腔40都具有一定的能量加速区间，质子束进入每一段行波质子加速腔40时，每段行波质子加速腔40中通过的高频电场相速度在周期性排列的耦合盘片41的作用下分别与当时的质子束的速度同步，当质子束经过依次连通的多段行波质子加速腔40的加速后，质子束将获得所期望的肿瘤治疗需要束流能量。一般来讲，根据肿瘤治疗的需要，束流能量需要在70-250MeV范围内连续可调，质子在70-250MeV能量区间时，其速度因子β的变化由0.367增长到0.61。因此，行波质子加速器4需确保其通过的高频电场相速度在0.367-0.61区间，进一步，通过每段行波质子加速腔40的高频电场相速度需在周期性排列的耦合盘片41的作用下，确保在一段更小的区间，该更小的区间与每段行波质子加速腔40的能量加速区间相对应。例如，将70MeV-250MeV能量区间划分为12段，则相速度区间0.367-0.61也被分为12段，每段分别对应一个行波质子加速腔40。Each traveling-wave proton accelerating cavity 40 is respectively connected with an RF power source, and each RF power source provides high-frequency power to each traveling-wave proton accelerating cavity 40 separately, forming a high-frequency electromagnetic field in each traveling-wave proton accelerating cavity 40, and each RF power The high frequency power of the source is independently adjustable. Changing the power value of the RF power source corresponding to the traveling wave proton accelerating cavity 40 can change the intensity of the electric field of this section of the accelerating cavity, thereby changing the energy value of the proton beam obtained after being accelerated by this section of the accelerating cavity. Each section of traveling-wave proton accelerating cavity 40 has a certain energy acceleration range. When proton beams enter each section of traveling-wave proton accelerating cavity 40, the phase velocity of the high-frequency electric field passing through each section of traveling-wave proton accelerating cavity 40 is in the coupling disk 41 arranged periodically. The proton beams are synchronized with the speed of the proton beams at that time. When the proton beams are accelerated by the sequentially connected multi-section traveling-wave proton acceleration cavity 40, the proton beams will obtain the desired beam energy required for tumor treatment. Generally speaking, according to the needs of tumor treatment, the beam energy needs to be continuously adjustable within the range of 70-250MeV. When the proton is in the energy range of 70-250MeV, the change of its velocity factor β increases from 0.367 to 0.61. Therefore, the traveling-wave proton accelerator 4 needs to ensure that the phase velocity of the high-frequency electric field passing through it is in the range of 0.367-0.61. Further, the phase velocity of the high-frequency electric field passing through each section of traveling-wave proton accelerating cavity 40 needs to be controlled by the periodically arranged coupling disks 41. Next, ensure that there is a smaller interval corresponding to the energy acceleration interval of each traveling-wave proton acceleration cavity 40 . For example, if the energy range of 70 MeV-250 MeV is divided into 12 segments, then the phase velocity range of 0.367-0.61 is also divided into 12 segments, and each segment corresponds to a traveling wave proton acceleration cavity 40 .
当漂移管直线加速器3出射的质子束进入行波质子加速器4腔体后将受到高频电场的作用而加速，通过改变输入的RF功率源输入的高频功率，即可改变高频电场的强度，使得经过加速后出射的质子束能量值连续可调，获得不同能量值的质子束，满足肿瘤治疗的需要。When the proton beam emitted by the drift tube linear accelerator 3 enters the cavity of the traveling wave proton accelerator 4, it will be accelerated by the high-frequency electric field, and the intensity of the high-frequency electric field can be changed by changing the high-frequency power input by the input RF power source , so that the energy value of the proton beam emitted after acceleration can be continuously adjusted, and proton beams with different energy values can be obtained to meet the needs of tumor treatment.
具体地，当能量为70MeV的质子束进入行波质子加速器4后，由于耦合盘片41的作用，质子束进入每段行波质子加速腔40，行波质子加速腔40中高频电场的相速度与质子速度相当，质子束沿行波质子加速器4腔体中轴线运动，经过各个行波质子加速腔40内高频电场的作用得到不断加速。根据实际需要，将各个行波质子加速腔40对应的RF功率源的高频功率设置为不同的功率值或零，使质子束获得期望的肿瘤治疗需要的不同束流能量，实现质子束能量值连续可调。Specifically, when the proton beam with an energy of 70 MeV enters the traveling wave proton accelerator 4, due to the effect of the coupling disk 41, the proton beam enters each segment of the traveling wave proton accelerating cavity 40, and the phase velocity of the high frequency electric field in the traveling wave proton accelerating cavity 40 is related to the proton The speeds are equal, and the proton beam moves along the central axis of the cavity of the traveling wave proton accelerator 4, and is continuously accelerated by the action of the high frequency electric field in each traveling wave proton accelerating cavity 40. According to actual needs, the high-frequency power of the RF power source corresponding to each traveling wave proton accelerating cavity 40 is set to a different power value or zero, so that the proton beam can obtain different beam energies required for the desired tumor treatment, and realize the proton beam energy value Continuously adjustable.
例如，将70MeV-250MeV能量区间划分为12段，每段分别对应一个行波质子加速腔40，并且由12台独立可调的RF功率源提供功率，每个行波质子加速腔40可提供的质子能量增长区间为0-15MeV。如果需要150MeV能量的质子，只需开启前6个行波质子加速器即可，其他能量可以此类推。For example, the 70MeV-250MeV energy range is divided into 12 sections, each corresponding to a traveling wave proton accelerating cavity 40, and powered by 12 independently adjustable RF power sources, each traveling wave proton accelerating cavity 40 can provide The proton energy growth range is 0-15MeV. If you need protons with 150MeV energy, you only need to turn on the first 6 traveling wave proton accelerators, and so on for other energies.
由此可见，经本申请的医用质子直线加速器获得的质子束能量大小可通过调整RF功率源来改变，不同的RF功率源功率值对应不同的束流能量等级，具体的对应关系以查找表或索引表的形式存储。It can be seen that the proton beam energy obtained by the medical proton linear accelerator of the present application can be changed by adjusting the RF power source. Different RF power source power values correspond to different beam energy levels. The specific correspondence can be found in a lookup table or Stored in the form of an index table.
现有的质子直线加速器常采用的是RFQ-DTL-CCL结构，其高能加速段采用的CCL将质子加速至设计能量，如250MeV，但CCL这样的驻波加速器带来的问题是出射质子束的能量不可连续调节，其能量为固定值。行波质子加速器4的优点是，(1)具有很高的加速梯度，如平均加速梯度可达50MV/m，远大于常规CCL的30MV/m，因此行波质子加速器可做到很紧凑；(2)可通过改变输入的高频功率来调节加速后质子束的能量，从而满足肿瘤治疗时不同能量的需求。需要说明的是，本方案采用的行波质子加速器4假如作为基础科学研究的工具可能不符合基础科学研究高流强、高束流品质的要求(高流强的束流加速过程中存在空间电荷效应，比低流强束流加速时要复杂很多)，如中国散裂中子源项目中的直线加速器采用的是DTL，运用驻波加速方式，不需要能量可调节，束流脉冲流强约为30mA，束流占空比约为1.05％，但医用质子直线加速器并不需要高流强，一般医疗使用的质子束流最大约为几十nA到几百nA量级，此量级的束流加速时空间电荷效应基本可以忽略，行波质子加速器4作为可连续调节出射束流能量的加速器很好的满足了治癌对束流能量的需求。Existing proton linear accelerators often use the RFQ-DTL-CCL structure, and the CCL used in the high-energy acceleration section accelerates protons to the design energy, such as 250MeV. However, the problem caused by standing wave accelerators such as CCL is the The energy cannot be adjusted continuously, and its energy is a fixed value. The advantage of the traveling wave proton accelerator 4 is that (1) it has a very high acceleration gradient, such as the average acceleration gradient can reach 50MV/m, which is far greater than the 30MV/m of conventional CCL, so the traveling wave proton accelerator can be made very compact;( 2) The energy of the accelerated proton beam can be adjusted by changing the input high-frequency power, so as to meet the needs of different energy in tumor treatment. It should be noted that if the traveling wave proton accelerator 4 used in this program is used as a tool for basic scientific research, it may not meet the requirements of high current intensity and high beam quality for basic scientific research (there is a space charge effect in the process of beam acceleration with high current intensity, and the ratio of low beam acceleration is much more complicated), for example, the linear accelerator in the China Spallation Neutron Source Project uses DTL, uses standing wave acceleration mode, does not require energy to be adjusted, and the beam pulse current intensity is about 30mA. The current duty cycle is about 1.05%, but the medical proton linear accelerator does not need high current intensity. The proton beam current used in general medical treatment is at most tens of nA to hundreds of nA. It can basically be ignored, and the traveling wave proton accelerator 4, as an accelerator that can continuously adjust the energy of the outgoing beam, satisfies the demand for beam energy for cancer treatment.
综上所述，本申请的要点在于在中能加速段使用了分离型漂移管直线加速器(SDTL)，并高能加速段采用行波质子加速器代替现有技术中的CCL，使得整个医用质子直线加速器不仅结构更加紧凑、占用空间更小，而且出射的质子束能量在70-250MeV范围内连续可调，满足肿瘤治疗时因病人身体内肿瘤位置不同束流能量需调节的需要。另外，本申请的医用质子直线加速器质子注入和引出容易，由于分离型漂移管直线加速器和行波质子加速器均为多段依次连接的结构，可以分期分段建造，可适应不同医院对质子能量的需求，后期也可根据治疗需求进行能量升级。In summary, the gist of this application is to use a separate drift tube linear accelerator (SDTL) in the medium-energy acceleration section, and to replace the CCL in the prior art with a traveling-wave proton accelerator in the high-energy acceleration section, so that the entire medical proton linear accelerator Not only is the structure more compact and the space occupied is smaller, but the energy of the emitted proton beam is continuously adjustable within the range of 70-250 MeV, which meets the needs of adjusting the energy of the beam due to different tumor positions in the patient's body during tumor treatment. In addition, the medical proton linear accelerator of the present application is easy to inject and extract protons. Since the separate drift tube linear accelerator and the traveling wave proton accelerator are multi-stage sequentially connected structures, they can be built in stages and sections, and can adapt to the needs of different hospitals for proton energy. , and the energy can be upgraded according to the treatment needs in the later stage.
以上内容是结合具体的实施方式对本申请所作的进一步详细说明，不能认定本申请的具体实施只局限于这些说明。对于本申请所属技术领域的普通技术人员来说，在不脱离本申请发明构思的前提下，还可以做出若干简单推演或替换。The above content is a further detailed description of the present application in conjunction with specific implementation modes, and it cannot be considered that the specific implementation of the present application is limited to these descriptions. For those of ordinary skill in the technical field to which the present application belongs, some simple deduction or replacement can also be made without departing from the inventive concept of the present application.
| Application Number | Priority Date | Filing Date | Title |
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| CN201710157738.2ACN106879158B (en) | 2017-03-16 | 2017-03-16 | Medical proton linear accelerator |
| Application Number | Priority Date | Filing Date | Title |
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| CN201710157738.2ACN106879158B (en) | 2017-03-16 | 2017-03-16 | Medical proton linear accelerator |
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| CN106879158Atrue CN106879158A (en) | 2017-06-20 |
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| CN201710157738.2AActiveCN106879158B (en) | 2017-03-16 | 2017-03-16 | Medical proton linear accelerator |
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