CN101361156B - 用于实施放射治疗的设备 - Google Patents
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Abstract
在其它物件之中，加速器(502)安装在台架(504)上以使得加速器能移动通过在患者支撑件上的患者(506)周围的一定的位置范围。加速器配置的以产生具有足以从所述范围内的位置到达患者的任何的任意目标的能级的质子或离子束。质子或者离子束实质上直接从加速器通过到达患者。在一些例子中，同步回旋加速器具有产生至少6特斯拉的场强的超导电磁结构，产生具有至少150兆电子伏的能级的粒子束，具有不大于4.5立方米的体积，并具有小于30吨的重量。
Description
本申请享有于2005年11月18日提交的序列号为60/738,404的美国临时专利申请的提交日的权益，其整个内容在此引入作为参考。
技术领域
本描述涉及带电粒子(例如，质子或者离子)放射治疗。
背景技术
与用于传统的放射疗法的电子束的能量相比，用于治疗的质子或者离子束的能量需要是高的。例如，具有在水中约32厘米的残余射程(residualrange)的质子束被认为是足以治疗人体中的任何肿瘤目标。当允许由于用于扩散束的散射箔所致的残余射程的降低时，需要250兆电子伏的初始质子束能量以获得32厘米的残余射程。
可以使用数种类型的粒子加速器以产生用于治疗的足够束电流(例如，约10nA)的250兆电子伏的质子束，包括直线加速器、同步加速器和回旋加速器。
用于临床环境的质子或者离子放射治疗系统的设计应当考虑整体尺寸、成本和复杂性。可用空间通常受限于拥挤的临床环境。较低的成本允许更多的系统得以应用到更多的患者人群。更低的复杂性降低操作成本并使得系统更可靠以便常规临床使用。
其它的考虑同样与这样的治疗系统的设计有关。通过配置系统以施加治疗到保持在稳定的可再现的位置(例如，仰卧在平台上)的患者，医生可以在每一治疗相对于患者的解剖结构更加精确地再定位意在的目标。对于每一治疗，可靠地再现患者的位置还可以通过使用配合到患者的定制的模型和支架而得以辅助。借助于患者在稳定的固定位置，放射治疗束可以从一系列的角度指向患者，以使得在整个治疗过程中在目标处的放射剂量得以提高，同时外部放射剂量在非目标组织上散布开。
传统地，等心台架(isocentric gantry)围绕仰卧的患者转动以沿着位于公共的垂直面中的一定范围的角度内的相继接连的路径向着患者体内的单一点(称作等心点)定向放射束。通过绕竖直轴转动患者所躺的台，束可以沿着不同路径定向到患者。其它技术已经用于改变患者周围的放射源的位置，包括机器人操作。并且，其它移动或者再定位患者的方法已经使用。
在高能量的X射线束治疗中，X射线束可以向着等心点从安装在台架或者机器人臂上的电子线性加速器定向。
在典型的质子束治疗中，产生束的环形粒子加速器太大而不能安装在台架上。相反，加速器安装在固定位置，而粒子束通过使用磁性波束控制元件再定向通过转动的台架。Blosser已经建议在水平转动轴附近的台架的侧面安装加速器。
发明内容
通常，在一方面，加速器安装在台架上以使得加速器能移动通过位于患者支撑件上的患者周围的一定的位置范围。加速器配置的以产生具有足以从所述范围内的位置到达患者中的任何的任意目标的能级的质子或离子束。质子或者离子束实质上直接从加速器壳体通过到达患者。
实施例可以包括一个或多个下面的特征。支撑台架以便在患者支撑件两侧的轴承上转动。台架具有从转动轴延伸两条腿和上面安装有加速器的所述两条腿之间的桁架。台架被限制在小于360度，至少有180度大，并且在一些实施例中为从约180度到约330度的位置范围内转动。(180度的转动范围足以提供接近仰卧的患者的所有角度)。辐射防护壁包括与在所述范围内的任何位置中的来自加速器的质子或者离子束不在一条直线的壁；所述壁构造的以用较小的质量提供相同的辐射保护。患者支撑件安装在可通过由台架被限制得不能转动的一定的位置范围限定的空间接近的区域中。患者支撑件可相对于包括绕竖直的患者转动轴转动的台架移动。患者转动轴包含在患者支撑件上的患者周边的等心点。台架转动轴是水平的并包含等心点。加速器重量小于40吨，并且在典型的实施例中在5-30吨范围内，占据小于4.5立方米，典型地在0.7-4.5立方米的体积，并产生具有至少150兆电子伏，并且在150-300兆电子伏，例如250兆电子伏的能级的质子或者离子束。
加速器可以是具有磁体结构的同步回旋加速器，其具有至少6特斯拉的场强，并可以为6-20特斯拉。磁体结构包括由低温冷却器冷却的超导绕组。质子或者离子束直接从加速器通过达到患者台的总体区域。防护室包含患者支撑件、台架和加速器，其包括比所述室的其它壁薄的该室的至少一个壁。一部分室可以嵌入在土内。
通常，在一方面，加速器配置的以产生具有足以到达患者的任何的任意目标的能级的质子或者离子束。加速器足够小并且重量足够轻以安装在允许质子或者离子束实质上直接从加速器壳体通过到达患者的方位的旋转台架上。
通常，在一方面，医疗同步回旋加速器具有超导电磁结构，其产生至少6特斯拉的场强，产生具有至少150兆电子伏的能级的粒子束例如质子束，具有不超过4.5立方米的体积，并具有小于30吨的重量。
通常，在一方面，患者支撑在治疗空间内，质子或者离子束在直线方向从加速器的输出通过到患者体内的任何的任意目标，并且使得该直线方向得以在通过患者周围的一定的方向范围变化。
通常，在一方面，一种结构包括患者支撑件和台架，加速器安装在其上以使得加速器能移动通过位于患者支撑件上的患者周围的一定的位置范围。加速器配置的以产生具有足以从所述范围内的位置到达患者中的任何的任意目标的能级的质子或离子束。壁式包壳包含患者支撑、台架和加速器。在一些例子中，壁式包壳的表面的超过一半嵌入在土中。
其它的方面包括上述方面和特征以及表示为设备、系统、方法、软件产品、商业方法和其它方式的特征的组合。
通过产生大约10特斯拉的磁场，加速器的尺寸接近1.5米，并且质量降低到大约15-20吨。重量将取决于在加速器附近允许的杂散磁场。甚至更小的重量和大小是可能的。这使得回旋加速器能够放置在台架上，具有直接指向等心点的输出束，并围绕患者转动，这样简化质子或者离子束放射治疗的实施。所有的引出束聚集和操纵元件结合到加速器中或者直接与其邻接。加速器在台架上的直接安装消除了否则需要将束从加速器传递到患者的目标位置的束传递部件。质子或者离子束治疗系统的尺寸、复杂性和成本降低并且其性能得以改善。在竖直平面内降低台架的转动范围到小于360度降低必须设置在束决不会指向的位置的防护屏障的厚度。这还允许便于接近患者治疗空间。同步回旋加速器可以比例放大到任意强的场而在加速过程中不影响束聚集。低温液体冷却线圈的消除降低了如果在故障情况例如磁体失超的情况下蒸发的液体冷冻剂释放对操作者和患者的风险。
其它的优点和特征将从下面的描述以及权利要求变得明显。
附图说明
图1是治疗系统的透视图。
图2是同步回旋加速器的部件的分解透视图。
图3、4和5是同步回旋加速器的截面视图。
图6是同步回旋加速器的透视图。
图7是反向线圈架和绕组部分的截面视图。
图8是电缆在通道中的复合导体的截面视图。
图9是离子源的截面视图。
图10是D形板(dee plate)和伪D形件(dummy dee)的透视图。
图11是拱室的透视图。
图12是具有拱室的治疗室的透视图。
图13示出极片(pole piece)和极面(pole face)的对称剖面的一半的剖面。
具体实施方式
如图1所示，带电粒子放射治疗系统500包括束产生粒子加速器502，其具有足够小的重量和尺寸以允许其安装在转动台架504上，其输出直接(也就是，实质上直接)从加速器壳体向着患者506直着定向。治疗系统的尺寸和成本明显降低，并且系统的可靠性精度可得以增加。
在一些实施例中，钢制的台架具有两条腿508、510，其安装以便在位于患者的相对侧上的两个各自的轴承512、514上转动。加速器由钢桁架516支撑，其足够长以跨越患者所躺的治疗区域518(例如，高个儿的两倍长，以允许人体在空间内全方位转动，患者的任何期望的目标区域保持与束成一直线)并且其在两端稳定地附着到台架的转动腿的两端。
在一些例子中，台架的转动限于小于360度，例如约180度的范围520以允许地板522从将治疗系统罩在患者治疗区域的拱室524的壁延伸。台架的限制的转动范围还降低提供给在治疗区域外的人辐射屏蔽的一些壁(其决不会直接接收束，例如壁530)的要求厚度。180度范围的台架转动足以覆盖所有的治疗接近角，但提供较大的移动范围是有用的。例如，转动范围可以有用地在180-330度之间，并仍提供给治疗地板空间间隙。当移动的范围是大的时，台架可以摆动到对人体或定位在一部分治疗空间内的设备有害的位置。
台架的水平转动轴532通常位于地板以上一米，那里患者和临床医学家与治疗系统交互。该地板定位在治疗系统屏蔽拱室的底板以上约3米。加速器可以在升高地板(raised floor)下面摆动以便治疗束从转动轴下面传送。患者床在平行于台架的转动轴的实质上水平的平面内转动。借助该构型，床可以转动通过水平平面内的大约270度的范围534。自由度和患者转动范围以及台架的结合允许临床医学家为束选择实际上任何的接近角。如果需要，患者可以位于相反方向的床上，然后所有可能的角度都可使用。
在一些实施例中，加速器使用具有非常高的磁场超导电磁结构的同步回旋加速器构型。因为给定动能的带电粒子的偏转半径与施加到其的磁场的增加成正比地降低，所以非常高的磁场超导磁结构允许加速器制造得较小和较轻。
对于大于5特斯拉的平均磁场强度，同步回旋加速器(其中磁体构造的以使得圆周附近的磁场比中心处的强以补偿质量的增加并维持恒定的转动频率)用以获得250兆电子伏的质子是不可行的。这是因为通过使用铁极面成形用于维持同步回旋加速器中的束聚焦的磁场中的角度变化不能足够大。
在此所述的加速器是同步回旋加速器。同步回旋加速器使用随转动角度均匀并随着半径增加而强度降低的磁场。这样的场的形状可以实现，不管磁场的大小如何，因此理论上不存在可用于同步回旋加速度的磁场强度(以及因此所致的在固定半径处的粒子能量)的上限。
某些超导材料在存在非常高的磁场情况下开始失去其超导性。高性能的超导线缆绕组用于允许非常高的磁场得以实现。
超导材料典型地需要冷却到低温以便它们的超导性得以实现。在此所述的一些例子中，低温冷却器用于将超导线圈绕组带到绝对零度附近。使用低温冷却器，而不是在液氦浴中冷却绕组，降低了复杂性和成本。
同步回旋加速器支撑在台架上以使得束直接产生为在与患者成一直线。台架允许回旋加速器绕关于位于患者内或附近的点(等心点540)的水平转动轴转动。平行于转动轴的分开的桁架支撑在两侧的回旋加速器。
因为台架的转动范围受到限制，患者支撑区域可以容纳在等心点周围的宽的区域内。因为地板可以绕等心点广泛地延伸，所有患者支撑台可以定位的以相对于通过等心点的竖直轴542移动并关于其转动，以使得通过台架转动和台的移动和转动的组合，可以实现进入患者任何部位的任何角度的束方向。两台架臂被分隔开超过高的患者高度两倍，从而允许床和患者在升高地板之上的水平平面中转动和平移。
限制台架转动角度允许围绕治疗室的至少一个壁的厚度降低。厚壁，典型地由混凝土建造，提供给治疗室外面的个体辐射防护。阻止质子束的下游壁需要为在室的相对端的壁的两倍厚以提供等效水平的防护。限制台架转动的范围使得治疗室在三个侧面上能位于土地下面，同时允许占用的区域与最薄的壁相邻，从而降低治疗室的建造成本。
在图1所示的示例性的实施例中，超导同步回旋加速器502用8.8特斯拉的同步回旋加速器的极隙中的峰值磁场操作。同步回旋加速器产生具有250兆电子伏能量的质子束。在其它实施例中，场强可以在6-20特斯拉范围内，并且质子能量可以在150-300兆电子伏范围之内。
在该例子中所述的放射治疗系统用于质子放射治疗，但是相同的原理和细节可以应用到用于重离子(离子)治疗系统的模拟系统中。
如图2、3、4、5和6所示，示例性同步回旋加速器10(图1中502)包括磁体系统12，其包含离子源90、射频驱动系统91和束引出系统38。通过使用分开的一对环形超导线圈40、42和一双成形铁磁(例如低碳钢)极面44、46，磁体系统建立的磁场具有适于维持所含质子束聚焦的形状。
二超导磁体线圈定心在公共轴47上并沿着轴间隔开。如图7和8所示，线圈由布置在卢瑟福(Rutherford)电缆在通道中(cable-in-channel)的导体几何形状中的基于Nb3Sn的超导0.6毫米直径的绞线48(其最初包括由铜包皮围绕的铌锡芯)形成。在六根单独的绞线被布置在铜通道50中后，其被加热以导致形成绕组的最终(脆性的)材料的反应。在材料已经反应后，线缆被焊接到铜通道(外尺寸3.02x1.96毫米，内尺寸2.05x1.27毫米)中，并用绝缘体52(在该例子中，编织玻璃纤维材料)覆盖。包含线缆53的铜通道然后绕在具有6.0cmx15.25cm的矩形截面的线圈中，具有30层，每层47匝。绕起来的线圈然后用环氧化合物54真空浸渍。所得的线圈安装在环形不锈钢反向线圈架56上。加热毯55抵着线圈架和绕组的内面保持以在磁体失超的情况下保护组件。在替代的实施方式中，超导线圈可形成为0.8毫米直径的基于Nb3Sn的绞线。这些绞线可以布置为4绞线电缆，热处理以形成超导矩阵并焊接到外尺寸3.19×2.57毫米的铜通道中。通道导体中集成的电缆可以用重叠编织玻璃纤维带绝缘，并然后绕成49匝且26层深的线圈，其具有79.79毫米×180.5毫米的矩形截面，374.65毫米的内径。绕成的线圈然后用环氧化合物真空浸渍。整个线圈然后可以用铜片覆盖以提供导热性和机械稳定性，并然后包含在环氧附加层中。线圈的预压缩可以通过加热不锈钢反向线圈架和将线圈配合在反向线圈架内而提供。选择反向线圈架内径以使得当整个块冷却到4K时，反向线圈架保持与线圈接触并提供一些压缩。这可以通过加热不锈钢反向线圈架到约50摄氏度并在室温(20摄氏度)下将线圈配合而实现。
通过安装线圈在“反向(reverse)”矩形线圈架56中并将预压缩不锈钢囊状物(bladder)结合在每个线圈和线圈架的内面57之间以施加逆着当线圈被激励时产生的变形力作用的恢复力60而维持线圈的几何尺寸。囊状物在线圈和加热毯子组装在线圈架上之后通过将环氧树脂注入囊状物并允许其硬化而被预压缩。设置囊状物的预压缩力以最小化冷却和磁激励的整个所有阶段在脆性的Nb3Sn超导矩阵中的应力。
如图5所示，通过使用一组暖-冷支撑箍带402、404、406，相对于磁轭和低温恒温器维持线圈位置。用细的箍带支撑冷却块最小化刚性支撑系统给予冷却块的热漏失。箍带安置的以承受当磁体在台架上转动时在线圈上不断变化的重力。它们承受当其从非常对称的位置相对磁轭扰动时线圈施加的大的离心力以及重力的综合影响。此外，连杆用以最小化当位置变化时台架加速和减速在线圈上施加的动态力。每一个暖-冷支撑件包括3个S2玻璃纤维连杆。两连杆410、412支撑跨过在暖和的轭和中等温度(50-70K)之间的销，一个连杆408支撑跨过中等温度销，销附着到冷却块。每一个连杆为10.2厘米长(销中心到销中心)，20毫米宽。连杆厚度是1.59毫米。每一个销由不锈钢制成，并且直径为47.7毫米。
如图13所示，作为半径的函数的场强剖面主要由线圈几何形状的选取确定；导磁轭材料的极面44、46可以轮廓适合以很好地调整磁场的形状以确保粒子束在加速过程中保持集中。
通过将线圈组件(线圈和线圈架)封装在提供线圈结构周围自由空间的抽真空的环形的铝或者不锈钢低温室70内部，超导线圈维持在绝对零度附近的温度(例如大约4开氏度)，除了在有限的一组支撑点71、73处外。在替代的实施方式中，低温保持器的外壁可由低碳钢制成以为磁场提供额外的返回磁通路径。通过使用安置在线圈组件上的不同位置的两个Gifford-McMahon低温冷却器72、74，绝对零度附近的温度得以实现和维持。每个低温冷却器具有与线圈组件接触的冷却端76。从压缩器80供应压缩氦给低温冷却器头78。另外两个Gifford-McMahon低温冷却器77、79安置的以冷却供应电流到超导绕组的高温(例如60-80开)引线81。
线圈组件和低温保持室安装在碉堡形状的磁轭82的两个半体81、83内并完全封闭在其中。在该例子中，线圈组件的内径为约140厘米。铁轭82提供返回磁场磁通84的路径并磁性屏蔽极面44、46之间的体积86以防止外部磁影响扰乱该体积内的磁场形状。轭还用以降低加速器附近的杂散磁场。
如图3和9所示，同步回旋加速器包括位于磁体结构82的几何中心92附近的Penning离子规几何形状的离子源90。离子源从氢源99通过递送气态氢的导管194和气体管线101馈给。电缆94从电流源95传送电流以激励与磁场200对齐的阴极192、194电子放电。
放电电子电离通过小孔从管194出来的气体以产生一阳离子(质子)供给以便通过跨越磁体结构包围的空间的一半的一个半圆的(D形状)的射频板100和一个伪D板102加速。如图10所示，D板是具有包围其中在其围绕磁体结构包围的空间转动的一半的过程中质子被加速的空间107的两个半圆表面103、105的中空金属结构。通向空间107的管道109通过轭延伸到外部位置，从那里真空泵111可以附着以抽空空间107以及真空室119内的剩余空间，其中发生加速。伪D形件102包括矩形金属环，其间隔在D形板的露出的边缘附近。伪D形件接地到真空室和磁轭。D形板100由在射频传输线路末端施加的射频信号驱动以给空间107施加电场。使得射频电场随着加速离子束在离几何中心的距离的增加而及时变化。在2005年7月21日提交的序列号为11/187,633，名称为“A Programmable RadioFrequency Waveform Generator for a Synchrocyclotron”的美国专利申请，以及于2004年7月21日提交的序列号为60/590,089的相同名称的美国临时专利申请描述了对该目的有用的射频波形发生器的例子，二者都被全文引用作为参考。
对于从中心定位的离子源出现以随着其开始向外旋转跳过(clear)离子源结构的束，需要跨过射频板的大电压差。20,000伏被施加跨过射频板。在一些实施方式中，可以跨过射频板施加8,000-20,000伏。为了降低驱动该大电压所需的能量，磁体结构被安置的以减小射频板和地之间的电容。这是通过形成通过外轭和低温保持器壳体的与射频结构具有足够的间隙的孔洞并使得磁体极面之间具有足够的间距而完成的。
驱动D形板的高压交变电势具有在加速周期过程中向下扫描的频率以应对质子不断增加的相对质量和不断降低的磁场。因为伪D形件与真空室壁都具有接地电势，所以其并不需要中空半柱状结构。可以使用其它板状安置例如超过一对的用不同的电相位或者数倍基频驱动的加速电极。通过使用例如具有相互交叉的转动和固定叶片的转动电容器，可以调节RF结构以在需要的扫频过程中保持高Q。在叶片的每次交叉(meshing)过程中，电容增加，这样降低RF结构的谐振频率。叶片可以为形状适合以产生需要的精确扫频。用于转动电容器(condenser)的驱动电机可以锁相到RF发生器以便精确控制。在转动电容器的叶片的每一次交叉过程中，一束粒子被加速。
其中发生加速的真空室119是大致圆柱形的容器，其在中央处较薄，在边缘处较厚。真空室围绕RF板和离子源并通过真空泵111抽真空。维持高真空保证加速离子不会失控与气体分子碰撞并使得RF电压能够保持在较高水平而没有对地电弧放电。
质子穿过开始于离子源的大致螺旋形路径。在螺旋形路径的每一环的一半中，质子随着其通过空间107中的RF电场而获得能量。随着离子获得能量，其螺旋形路径的每个相继的环的有心轨道的半径比先前环的大直到环半径达到极面的最大半径。在该位置，磁场和电场扰动导向离子到磁场快速降低的区域，离子离开高磁场区域并导向通过引出通道38以离开回旋加速器的轭。离开回旋加速器的离子在当其进入存在于回旋加速器周围的空间内的明显降低的磁场区域时将趋于分散。在引出通道38中的束成形元件107、109再导向离子以使得其位于限制的空间程度的直的束中。
在极隙内的磁场需要具有某些属性以随着束的加速维持其在真空室内。磁场指数
N＝-(r/B)dB/dr
必须保持为正以维持该“弱的”聚集。在此，r是束的半径，B是磁场。此外，场指数需要维持在0.2以下，因为在该值，束的径向振荡和竖直振荡的周期重合在vr＝2vz谐振。电子感应加速器频率由vr＝(1-n)1/2和vz＝n1/2限定。铁磁极面设计以整形线圈产生的磁场从而使得在与给定磁场中的250兆电子伏束一致的最小直径中场指数n维持为正并小于0.2。
随着束离开引出通道，其通过可以程序控制以产生束的幅度调制(rangemodulation)和散射角的期望组合的束形成系统125。对该目的有用的束形成系统的例子在2004年9月24日提交的序列号为10/949,734的名称为“AProgrammable Particle Scatterer for Radiation Therapy Beam Formation”的美国专利申请以及于2005年7月21日提交的序列号为60/590,088的美国临时专利申请中描述，其均被全文引用作为参考。
在操作过程中，板吸收来自施加的射频场的能量，其是沿着板的表面的传导阻力的结果。该能量作为热出现并通过使用在热交换器113中释放热的水冷线路108从板去除。
从回旋加速器离开的杂散磁场由碉堡状磁轭(其也作为防护)和分离开的磁防护物114二者限制。分离开的磁防护物包括围绕碉堡状轭的铁磁材料(例如，钢或者铁)的层117，其由空间116间隔开。该构型包括轭、空间、防护物的三层夹心结构，对于给定的漏出磁场以较低重量实现适当的屏蔽。
如所提及的，台架允许同步回旋加速器围绕水平转动轴532转动。桁架结构516具有两个大致平行的跨580、582。同步回旋加速器托架在大致位于腿之间的中间周围的跨度之间。台架通过使用安装在与桁架相对的腿的末端上的平衡物122、124得以平衡以绕轴承转动。
台架通过安装到一个台架腿的电机驱动而转动并通过主动齿轮和带或者链连接到轴承座。台架的转动位置由结合到台架驱动电机和主动齿轮中的轴角编码器提供的信号得出。
在离子束离开回旋加速器的位置，束形成系统125作用在离子束上以给予其适于患者治疗的属性。例如，束可以展开并且其穿透深度改变以提供跨过给定目标体积的均一的放射。束形成系统可以包括无源(passive)散射部件以及有源(active)扫描部件。
同步回旋加速器的所有有源系统(例如，电流驱动超导线圈、RF驱动板、用于真空加速室和用于超导线圈冷却室的真空泵、电流驱动离子源、氢气源和RF板冷却器)由适当的同步回旋加速器控制电子元器件(未示出)控制。
台架、患者支撑件、有源束成形元件和同步回旋加速器的控制以执行治疗环节是通过适当的治疗控制电子元器件(未示出)实现的。
如图1、11和12所示，台架轴承由回旋加速器拱室524的壁支撑。台架使得回旋加速器能摆动通过包括上述位置的180度(或更大)的范围520到患者的侧面和下面。拱室足够高以在其运动的顶部和底部极限处与台架有间隙。两侧为壁148、150的曲径146为临床医学家和患者提供进入和离开的路线。因为至少一个壁152决不会与直接来自回旋加速器的质子束成一直线，所以其可以被制造的相对薄并仍可执行其防护功能。房间的另外三个侧壁154、156、150/148，其会需要更加重型的防护，可以埋设在土山(未示出)内。壁154、156和158的要求厚度可以降低，因为土地自身可以提供一些必要的防护。
出于安全和美学的原因，治疗室160构造在拱室内。治疗室由以与摇摆台架具有间隙并且还最大化治疗室的地板空间164的范围的方式从包含空间的底座162、壁154、156和150到台架腿之间的空间悬臂支撑。加速器的周期性保养可以在升高地板下面的空间内完成。当加速器转动到台架上的下位置时，在与治疗区域分隔开的空间内可以实现全方位接近加速器。电源、冷却设备、真空泵以及其它支撑设备可以位于该分隔开的空间内的升高地板下面。
在治疗室内，患者支撑件170可以以多种方法安装，其允许支撑件升高和降低以及患者转动和移动到多个位置和方向。
关于加速器设计的其它信息可以在于2006年8月9日提交的序列号为No.60/760,788，名称为“HIGH-FIELD SUPERCONDUCTINGSYNCHROCYCLOTRON(T.Antaya)”的美国专利申请，于2006年8月9日提交的序列号为11/463,402，名称为“MAGNET STRUCTURE FORPARTICLE ACCELERATION(T.Antaya等人)”的美国专利申请，以及于2006年10月10日提交的序列号为No.60/850,565，名称为“CRYOGENICVACUUM BREAK PNEUMATIC THERMAL COUPLER(Radovinsky等人)”的美国临时申请中找到，其全部在此全文引用作为参考。
其它实施例是在权利要求的范围内。
Claims (36)
1.一种用于实施放射治疗的设备，包括：
患者支撑件，和
台架，加速器安装在其上以使得所述加速器能移动通过在所述患者支撑件上的患者周围的一定的位置范围，
所述加速器配置的以产生具有足以从所述范围内的位置到达患者内的任意目标的能级的质子或者离子束，
所述质子或者离子束实质上直接从所述加速器壳体通过到达患者，
其中，所述台架包括从所述台架的转动轴延伸的两个臂和所述加速器安装在其上的所述两个臂之间的桁架，并且所述台架被支撑为以便在所述患者支撑件的两侧转动。
2.如权利要求1所述的设备，其中，
所述台架被支撑为以便在所述患者支撑件的两侧的轴承上转动。
3.如权利要求1所述的设备，其中，所述台架限制在小于360度的位置范围内转动。
4.如权利要求3所述的设备，其中，所述范围为至少180度大。
5.如权利要求3所述的设备，其中，所述范围是从180度到330度。
6.如权利要求3所述的设备，还包括辐射防护壁，其中至少一个壁在所述范围内的任何位置与来自所述加速器的所述质子或者离子束不在一条直线上，所述一个壁构造的比其它壁用较少的质量提供相同的辐射防护。
7.如权利要求3所述的设备，其中，所述患者支撑件安装在患者支撑区域，该区域可通过所述台架限制转动的位置范围限定的空间接近。
8.如权利要求1所述的设备，其中，所述患者支撑件可相对所述台架移动。
9.如权利要求8所述的设备，其中，所述患者支撑件配置的以便关于患者转动轴转动。
10.如权利要求9所述的设备，其中，所述患者转动轴是竖直的。
11.如权利要求9所述的设备，其中，所述患者转动轴包含在所述患者支撑件上的患者中的等心点。
12.如权利要求1所述的设备，其中，所述台架配置的以便所述加速器关于台架转动轴转动。
13.如权利要求12所述的设备，其中，所述台架转动轴是水平的。
14.如权利要求12所述的设备，其中，所述转动轴包含在所述患者支撑件上的患者中的等心点。
15.如权利要求1所述的设备，其中，所述加速器重量小于40吨。
16.如权利要求15所述的设备，其中，所述加速器重量在5-30吨范围内。
17.如权利要求1所述的设备，其中，所述加速器占据小于4.5立方米的体积。
18.如权利要求1所述的设备，其中，所述加速器占据的体积是在0.7-4.5立方米范围内。
19.如权利要求1所述的设备，其中，所述加速器产生具有至少150兆电子伏能级的质子或者离子束。
20.如权利要求19所述的设备，其中，所述能级是在150-300兆电子伏的范围内。
21.如权利要求1所述的设备，其中，所述加速器包括同步回旋加速器。
22.如权利要求1所述的设备，其中，所述加速器包括具有至少6特斯拉的场强的磁体结构。
23.如权利要求22所述的设备，其中，场强是在6-20特斯拉范围内。
24.如权利要求22所述的设备，其中，所述磁体结构包括超导绕组。
25.如权利要求1所述的设备，其中，所述质子或者离子束直接从所述加速器通过到达所述患者支撑件的整个区域。
26.如权利要求1所述的设备，还包括防护室，其包括所述患者支撑件、所述台架和所述加速器，所述室的至少一个壁比所述室的其它壁更薄。
27.如权利要求26所述的设备，其中，所述室的至少一部分嵌入在土中。
28.一种用于实施放射治疗的设备，包括：
患者支撑件，和
台架，加速器安装在其上，所述台架支撑在所述患者支撑件的两侧上以便(a)绕包含患者中的等心点的水平台架轴以及(b)通过超过180度的位置范围转动，
所述患者支撑件可关于包含所述等心点的竖直患者支撑轴转动，
所述加速器包括同步回旋加速器，其配置的以产生具有至少150兆电子伏的能级的质子或者离子束以直接从所述范围内的位置到达患者内的任何的任意目标，所述同步回旋加速器具有超导绕组，
其中，所述台架包括从所述台架的水平台架轴延伸的两个臂和所述加速器安装在其上的所述两个臂之间的桁架。
29.一种用于实施放射治疗的设备，包括：
加速器，其配置的以产生带电粒子束并安装在台架上使得所述加速器能移动通过在患者支撑件上的患者周围的超过180度的位置范围，
所述加速器配置的以产生具有足以从所述范围内的位置到达患者内的任何的任意目标的能级的粒子束，
其中，所述台架包括从所述台架的转动轴延伸的两个臂和所述加速器安装在其上的所述两个臂之间的桁架，并且所述台架被支撑为以便在所述患者支撑件的两侧转动。
30.一种用于实施放射治疗的设备，包括：
台架，其配置的以固持加速器并使得所述加速器能移动通过在患者支撑件上的患者周围的超过180度的位置范围，
所述加速器配置的以产生具有足以从所述范围内的位置到达患者内的任何的任意目标的能级的质子或者离子束，
其中，所述台架包括从所述台架的转动轴延伸的两个臂和所述加速器安装在其上的所述两个臂之间的桁架，并且所述台架被支撑为以便在所述患者支撑件的两侧转动。
31.一种用于实施放射治疗的设备，包括：
患者支撑件，
台架，加速器安装在其上以使得所述加速器能移动通过在所述患者支撑件上的患者周围的超过180度的位置范围，
所述加速器配置的以产生具有足以从所述范围内的位置到达患者的任何的任意目标的能级的质子或者离子束，和
壁式包壳，其包含所述患者支撑件、所述台架和所述加速器，
其中，所述台架包括从所述台架的转动轴延伸的两个臂和所述加速器安装在其上的所述两个臂之间的桁架，并且所述台架被支撑为以便在所述患者支撑件的两侧转动。
32.如权利要求31所述的设备，其中，所述壁式包壳的表面的超过一半嵌入在土内。
33.一种用于实施放射治疗的设备，包括：
加速器，其配置的以产生具有足以到达患者内的任何的任意目标的能级的质子或者离子束，所述加速器足够小并且重量足够轻以安装在一定方向的可转动的台架上以允许所述质子或者离子束实质上直接从所述加速器通过到达患者，
其中，所述台架包括从所述台架的转动轴延伸的两个臂和所述加速器安装在其上的所述两个臂之间的桁架，并且所述台架被支撑为以便在所述患者支撑件的两侧转动。
34.如权利要求33所述的设备，其中，所述加速器包括超导同步回旋加速器。
35.如权利要求34所述的设备，其中，所述超导同步回旋加速器的磁场是在6-20特斯拉范围。
36.如权利要求33所述的设备，其中，所述加速器产生至少6特斯拉的场强，产生用于递送到患者的具有至少150兆电子伏的能级的带电粒子束，具有不大于4.5立方米的体积，并具有小于30吨的重量。
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