TWI836518B - Particle therapy system and gantry therefor - Google Patents

Particle therapy system and gantry therefor Download PDF

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TWI836518B
TWI836518B TW111127195A TW111127195A TWI836518B TW I836518 B TWI836518 B TW I836518B TW 111127195 A TW111127195 A TW 111127195A TW 111127195 A TW111127195 A TW 111127195A TW I836518 B TWI836518 B TW I836518B
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particle
therapy system
particle beam
magnet
magnets
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TW111127195A
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TW202310892A (en
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馬克 Ｒ 瓊斯
吉瑞特 唐塞德 茲瓦特
詹姆斯 顧里
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美商美威高能離子醫療系統公司
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Abstract

An example particle therapy system includes a particle accelerator configured to output a particle beam at a predefined maximum energy and a toroidal gantry comprising magnets in an interior thereof. The magnets include a first magnet proximate to an output of the particle accelerator and second magnets proximate to a treatment position. The first magnet is configured to direct the particle beam to a second magnet. The second magnet is configured to bend the particle at the predefined maximum energy towards the treatment position.

Description

粒子治療系統及用於其之檯座 Particle therapy system and table used therefor

本說明書闡述粒子治療系統及供在該粒子治療系統中使用之檯座之實例。 This specification describes a particle therapy system and an example of a table for use in the particle therapy system.

粒子治療系統使用一粒子加速器來產生一粒子束，用於醫療諸如腫瘤等疾病。粒子治療系統可使用一檯座將粒子束朝向一患者引導。在某些實例中，一檯座包含在醫療期間支撐一輻射遞送裝備之一裝置。 Particle therapy systems use a particle accelerator to generate a particle beam for treating diseases such as tumors. Particle therapy systems may use a pedestal to direct the particle beam toward a patient. In some embodiments, a pedestal includes a device that supports a radiation delivery device during treatment.

一實例性粒子治療系統包含經組態以在一預定義最大能量下輸出一粒子束之一粒子加速器以及一環形檯座，該環形檯座在其一內部中包括磁體。該等磁體包含接近於該粒子加速器之一輸出之一第一磁體以及接近於一醫療位置之第二磁體。該第一磁體經組態以將該粒子束引導至一第二磁體。該第二磁體經組態以將處於該預定義最大能量之粒子束朝向該醫療位置彎曲。該粒子治療系統可單獨地或以組合方式包含以下特徵中之一或多者。 An exemplary particle therapy system includes a particle accelerator configured to output a particle beam at a predetermined maximum energy and an annular pedestal including magnets in an interior thereof. The magnets include a first magnet proximate an output of the particle accelerator and a second magnet proximate a treatment location. The first magnet is configured to direct the particle beam to a second magnet. The second magnet is configured to bend the particle beam at the predetermined maximum energy toward the treatment location. The particle therapy system may include one or more of the following features, either individually or in combination.

該粒子加速器與該環形檯座可係在同一醫療空間內。該粒子加速器可係一固定能量粒子加速器。該粒子治療系統可包含可在該等第 二磁體中之每一者與該醫療位置之間移動之一能量降級器。該能量降級器可經組態以在該粒子束到達該醫療位置之前改變該粒子束之一能量。該等第二磁體可係間隔開的且各自可位於該環形檯座之一不同圓周扇區中。該環形檯座可包含六個與二十個之間的第二磁體。該等第二磁體在該環形檯座上可係靜止的。該等第二磁體可經組態以將該粒子束彎曲至少90°。該粒子治療系統可包含可在該環形檯座之一孔內移動之一醫療床。該醫療床可用於將一患者固持在該醫療位置處。該第二磁體與該醫療位置之間的一距離可係兩米(2m)或更小。該第二磁體與該醫療位置之間的一距離可係一米(1m)或更小。該第二磁體與該醫療位置之間的一距離可係0.5m或更小。 The particle accelerator and the annular pedestal can be attached in the same medical space. The particle accelerator may be a fixed energy particle accelerator. The particle therapy system may include a An energy degrader moves between each of the two magnets and the medical location. The energy degrader may be configured to modify an energy of the particle beam before the particle beam reaches the medical location. The second magnets may be spaced apart and each may be located in a different circumferential sector of the annular base. The annular pedestal may contain between six and twenty second magnets. The second magnets may be stationary on the annular base. The second magnets can be configured to bend the particle beam by at least 90°. The particle therapy system may include a medical bed movable within a hole in the annular base. The medical bed can be used to hold a patient in the medical position. A distance between the second magnet and the medical location may be two meters (2m) or less. A distance between the second magnet and the medical location may be one meter (1m) or less. A distance between the second magnet and the medical location may be 0.5m or less.

該粒子加速器可係或可包含一同步迴旋加速器。該粒子加速器可係或可包含經組態以在兩種能量下操作之一同步迴旋加速器，該兩種能量中之一者大於該兩種能量中之另一者。該粒子加速器可係或可包含一同步加速器。 The particle accelerator may be or may include a synchrocyclotron. The particle accelerator may be or may include a synchrocyclotron configured to operate at two energies, one of the two energies being greater than the other of the two energies. The particle accelerator may be or may include a synchrotron.

該粒子治療系統可包含安裝至該環形檯座之一或多個成像裝置。該一或多個成像裝置可經組態用於圍繞該環形檯座移動。該粒子治療系統可包含經組態用於圍繞該環形檯座移動之一噴嘴。該噴嘴可用於調節該粒子束並將其輸出至該醫療位置。該粒子治療系統可包含經程式化以控制該一或多個成像裝置之移動並控制該噴嘴之移動的一控制系統。該控制系統可經程式化以防止該噴嘴與該一或多個成像裝置之間發生碰撞。該噴嘴可經組態以圍繞該環形檯座中之一第一內部軌道旋轉，並且該一或多個成像裝置可經組態以圍繞該環形檯座中之一第二內部軌道旋轉。該第一內部軌道與該第二內部軌道可位於該環形檯座之不同位置處。 The particle therapy system may include one or more imaging devices mounted to the annular pedestal. The one or more imaging devices may be configured to move about the annular pedestal. The particle therapy system may include a nozzle configured for movement about the annular pedestal. The nozzle can be used to condition and output the particle beam to the medical location. The particle therapy system may include a control system programmed to control movement of the one or more imaging devices and to control movement of the nozzle. The control system can be programmed to prevent collisions between the nozzle and the one or more imaging devices. The nozzle can be configured to rotate about a first inner orbit in the annular pedestal, and the one or more imaging devices can be configured to rotate about a second inner orbit in the annular pedestal. The first inner track and the second inner track may be located at different positions of the annular base.

該等第二磁體可係間隔開的且各自可位於該環形檯座之一不同圓周扇區中。該等扇區中之每一者可包含用於將該粒子束輸出至該醫療位置之一噴嘴。該粒子加速器可包含用以產生用於加速粒子來產生該粒子束之一磁場的主超導線圈。該粒子加速器可包含用以在與該等主超導線圈相反之一方向上傳導電流之主動返回線圈。可在FLASH劑量下將該粒子束遞送給該患者。可在小於五(5)秒之一持續時間內在超過二十(20)戈每秒之一劑量下將該粒子束遞送給該患者。 The second magnets may be spaced apart and each may be located in a different circumferential sector of the annular table. Each of the sectors may include a nozzle for outputting the particle beam to the medical location. The particle accelerator may include a main superconducting coil for generating a magnetic field for accelerating particles to generate the particle beam. The particle accelerator may include an active return coil for conducting current in a direction opposite to the main superconducting coils. The particle beam may be delivered to the patient at a FLASH dose. The particle beam may be delivered to the patient at a dose of more than twenty (20) Ge per second for a duration of less than five (5) seconds.

另一實例性粒子治療系統包含：一多扇區檯座，其中每一扇區經組態以將輻射自該多扇區檯座上之一不同位置遞送給一患者；及一粒子加速器，其連接至該多扇區檯座以將該輻射朝向該多扇區檯座輸出。該多扇區檯座與該粒子加速器可係在同一醫療室中且未被該多扇區檯座或該粒子加速器外部之屏蔽件分隔。該粒子治療系統可單獨地或以組合方式包含以下特徵中之一或多者。 Another exemplary particle therapy system includes: a multi-sector table, wherein each sector is configured to deliver radiation to a patient from a different location on the multi-sector table; and a particle accelerator connected to the multi-sector table to output the radiation toward the multi-sector table. The multi-sector table and the particle accelerator may be in the same medical room and are not separated by shielding external to the multi-sector table or the particle accelerator. The particle therapy system may include one or more of the following features, either individually or in combination.

該多扇區檯座與該粒子加速器可係在同一醫療空間中。每一扇區可包含經組態以將該輻射朝向該患者引導之一磁體。每一磁體可係實質上D形的。每一磁體可經組態以將該粒子束彎曲至少90°。該多扇區檯座在形狀上可係環形的。該多扇區檯座可包含每一扇區中之一第二磁體以及該第二磁體與該粒子加速器之間的一第一磁體。該第一磁體可用於將該粒子束引導至一標靶扇區中之一第二磁體。該第一磁體可經組態以將該粒子束引導至不同扇區。該粒子加速器可係或可包含一同步迴旋加速器。該同步迴旋加速器可經組態以在兩種不同能量中之一者下輸出該粒子束。該粒子加速器可係或可包含一同步加速器。 The multi-sector pedestal and the particle accelerator can be tethered to the same medical space. Each sector may include a magnet configured to direct the radiation toward the patient. Each magnet may be substantially D-shaped. Each magnet can be configured to bend the particle beam by at least 90°. The multi-sector pedestal may be annular in shape. The multi-sector pedestal may include a second magnet in each sector and a first magnet between the second magnet and the particle accelerator. The first magnet may be used to direct the particle beam to a second magnet in a target sector. The first magnet can be configured to direct the particle beam to different sectors. The particle accelerator may be or may include a synchrocyclotron. The synchrocyclotron can be configured to output the particle beam at one of two different energies. The particle accelerator may be or may include a synchrotron.

供在一粒子治療系統中使用之一實例性檯座包含可連接至 一粒子加速器之一環形結構。該環形結構包含圍繞該環形結構圓周配置在一扇區中之第一磁體。該等第一磁體用於將源於該粒子加速器處之一粒子束朝向一醫療位置彎曲至少90°。一外殼將該環形結構連接至該粒子加速器。該外殼包含第二磁體。該等第二磁體用於接收該粒子束並用於將該粒子束朝向該等第一磁體引導。該外殼內之一可旋轉結構經組態用於安裝輻射遞送組件或成像組件中之至少一者。該檯座與該粒子加速器可係在同一醫療空間內。 An exemplary pedestal for use in a particle therapy system includes an annular structure connectable to a particle accelerator. The annular structure includes first magnets arranged in a sector around the circumference of the annular structure. The first magnets are used to bend a particle beam originating at the particle accelerator by at least 90° toward a treatment location. A housing connects the annular structure to the particle accelerator. The housing includes second magnets. The second magnets are used to receive the particle beam and to direct the particle beam toward the first magnets. A rotatable structure within the housing is configured to mount at least one of a radiation delivery assembly or an imaging assembly. The pedestal and the particle accelerator may be in the same treatment space.

該檯座可包含可在該等第一磁體中之每一者與該醫療位置之間移動之一能量降級器。該能量降級器可經組態以在該粒子束到達該醫療位置之前改變該粒子束之一能量。該能量降級器可安裝至該可旋轉結構。 The table may include an energy degrader movable between each of the first magnets and the treatment location. The energy degrader may be configured to change an energy of the particle beam before the particle beam reaches the treatment location. The energy degrader may be mounted to the rotatable structure.

該等第一磁體可係間隔開的且各自位於該環形結構之一不同圓周扇區中。該環形結構可包含六個與二十個之間的第一磁體。該等第一磁體在該環形結構上可係靜止的。該等第二磁體可經組態以將該粒子束彎曲至少90°。該等第一磁體中之每一者與該醫療位置之間的一距離可係兩米(2m)或更小。該第二磁體與該醫療位置之間的一距離可係一米(1m)或更小。 The first magnets may be spaced apart and each located in a different circumferential sector of the annular structure. The annular structure may contain between six and twenty first magnets. The first magnets may be stationary on the annular structure. The second magnets can be configured to bend the particle beam by at least 90°. A distance between each of the first magnets and the medical location may be two meters (2m) or less. A distance between the second magnet and the medical location may be one meter (1m) or less.

該檯座可包含安裝至該可旋轉結構之一或多個成像裝置。該一或多個成像裝置可經組態用於圍繞該環形結構移動。該檯座可包含經組態用於圍繞該環形結構移動之一噴嘴。該噴嘴可用於將該粒子束輸出至該醫療位置。該噴嘴可安裝至該可旋轉結構。 The pedestal may include one or more imaging devices mounted to the rotatable structure. The one or more imaging devices may be configured to move about the annular structure. The pedestal may include a nozzle configured to move about the annular structure. The nozzle can be used to output the particle beam to the medical location. The nozzle is mountable to the rotatable structure.

該檯座可包含經組態用於圍繞該環形結構移動之一或多個成像裝置以及經組態用於圍繞該環形結構移動之一噴嘴。該噴嘴可用於將 該粒子束輸出至該醫療位置。該噴嘴及該一或多個成像裝置可安裝至該可旋轉結構。該等第一磁體可係間隔開的且可各自位於該環形結構之一不同圓周扇區中。該等扇區中之每一者可包含用於將該粒子束輸出至該醫療位置之一噴嘴。 The pedestal may include one or more imaging devices configured for movement about the annular structure and a nozzle configured for movement about the annular structure. This nozzle can be used to The particle beam is output to the medical location. The nozzle and the one or more imaging devices may be mounted to the rotatable structure. The first magnets may be spaced apart and may each be located in a different circumferential sector of the annular structure. Each of the sectors may include a nozzle for outputting the particle beam to the medical location.

本說明書中所闡述之特徵中之任何兩者或更多者(包含本發明內容部分中所闡述之特徵)可經組合以形成本說明書中未經具體闡述之實施方案。 Any two or more of the features described in this specification (including the features described in the content section of the present invention) may be combined to form an implementation scheme not specifically described in this specification.

可經由一電腦程式產品來實施對本文中所闡述之各種裝置、系統及/或組件或者其部分之控制，該電腦程式產品包含儲存在一或多個非暫時性機器可讀儲存媒體上且可在一或多個處理裝置(例如，微處理器、特殊應用積體電路、諸如場可程式化閘陣列等程式化邏輯或者諸如此類)上執行之指令。本文中所闡述之裝置、系統及/或組件或者其部分可被實施為一裝備、方法或者可包含一或多個處理裝置及儲存可執行指令以實施對所陳述功能之控制之電腦記憶體的電子系統。本文中所闡述之裝置、系統及/或組件可例如經由設計、構造、配置、放置、程式化、操作、啟動、解除啟動及/或控制來進行組態。 Control of the various devices, systems and/or components described herein, or portions thereof, may be implemented via a computer program product comprising instructions stored on one or more non-transitory machine-readable storage media and executable on one or more processing devices (e.g., microprocessors, application-specific integrated circuits, programmable logic such as field programmable gate arrays, or the like). The devices, systems and/or components described herein, or portions thereof, may be implemented as an apparatus, method, or electronic system that may include one or more processing devices and a computer memory storing executable instructions to implement control of the described functions. The devices, systems and/or components described herein may be configured, for example, by design, construction, configuration, placement, programming, operation, activation, deactivation and/or control.

在附圖及以下闡述中陳述了一或多個實施方案之細節。依據說明書及圖式且依據申請專利範圍，其他特徵及優點將變得顯而易見。 The details of one or more implementations are set forth in the accompanying drawings and the description below. Other features and advantages will become apparent from the description and drawings and from the scope of the patent application.

10:粒子治療系統 10:Particle therapy system

12:加速器/粒子加速器 12:Accelerator/particle accelerator

14:檯座/環形檯座 14: Pedestal/ring pedestal

15:孔 15: Hole

17:醫療床 17: Medical bed

18:外殼 18: Shell

20:向量磁體 20: Vector magnet

22:磁體/彎曲磁體/不同形狀之彎曲磁體 22: Magnet/Bent Magnet/Bent Magnet of Different Shapes

24:醫療位置 24:Medical location

25:粒子束 25:Particle beam

29:線 29: line

30:扇區 30: Sector

31:扇區 31: Sector

32:扇區 32: sector

33:扇區 33: Sector

34:控制系統 34:Control system

37:噴嘴 37: Spray nozzle

38:噴嘴 38:Nozzle

39:噴嘴 39:Nozzle

40:噴嘴 40: Nozzle

41:能量降級器 41:Energy Degrader

42:結構 42: Structure

43:掃描磁體 43: Scanning magnet

44:準直器 44: Collimator

45:環/可旋轉環 45: Ring/rotatable ring

50:總長度 50:Total length

51:醫療空間 51:Medical space

54:臂/機器人臂 54: Arm/Robot Arm

55:第一分段 55: First segment

56:第二分段 56: Second section

57:第三分段 57: The third section

60:隔間 60: Compartment

61:隔間 61: Compartment

70:平面/成像系統 70:Planar/imaging system

71:平面/成像系統 71:Planar/imaging system

73:裝置/成像系統 73: Device/Imaging System

74:成像系統/扇形束診斷品質電腦斷層造影(CT)裝置 74: Imaging systems/fan-beam diagnostic quality computed tomography (CT) units

75:組件 75:Components

77:超導磁體 77:Superconducting magnet

78:超導線圈 78:Superconducting coil

79:超導線圈 79:Superconducting coil

80:磁軛/相對大之鐵磁磁軛 80: Magnetic yoke/relatively large ferromagnetic yoke

81:磁軛/相對大之鐵磁磁軛 81: Magnetic yoke/relatively large ferromagnetic yoke

84:腔 84: cavity

85:粒子源 85: Particle source

圖1係展示一實例性粒子治療系統之一部分剖視、部分透明側視圖，該實例性粒子治療系統具有本文中所闡述之類型之一實例性環形檯座。 Figure 1 shows a partially cutaway, partially transparent side view of an example particle therapy system having an example annular pedestal of the type described herein.

圖2係展示圖1之實例性粒子治療系統之一部分透明俯視圖之一圖 式。 FIG. 2 is a diagram showing a partially transparent top view of the exemplary particle therapy system of FIG. 1 .

圖3係展示圖1及圖2之實例性粒子治療系統之組件之一部分透明透視圖。 FIG. 3 is a partially transparent perspective view showing components of the exemplary particle therapy system of FIG. 1 and FIG. 2 .

圖4係一實例性環形檯座及其扇區之一部分之一前視圖。 Figure 4 is a front view of an exemplary annular pedestal and a portion of its sectors.

圖5係展示粒子束在不同時間自一向量磁體移動至不同彎曲磁體且接著以不同角度自該等彎曲磁體朝向一共同醫療位置移動之一透視圖。 Figure 5 is a perspective view showing a particle beam moving from a vector magnet to different bending magnets at different times and then moving from the bending magnets at different angles toward a common medical location.

圖6係一實例性噴嘴之組件之一方塊圖，該實例性噴嘴經組態以附接至本文中所闡述之類型之一實例性環形檯座。 Figure 6 is a block diagram of the components of an example nozzle configured to be attached to an example annular mount of the type described herein.

圖7係可含納於圖6之噴嘴內之一實例性能量降級器之一透視圖。 FIG. 7 is a perspective view of an example energy reducer that may be contained within the nozzle of FIG. 6 .

圖8係經組態以裝納圖1至圖3之粒子治療系統之一實例性醫療空間之一方塊圖。 Figure 8 is a block diagram of an example medical space configured to house the particle therapy system of Figures 1-3.

圖9係可在圖1至圖3之粒子治療系統中使用之一實例性病床之一透視圖。 FIG. 9 is a perspective view of an exemplary hospital bed that may be used in the particle therapy system of FIGS. 1 to 3 .

圖10係展示圖1及圖2之實例性粒子治療系統之組件之一部分透明透視圖。 FIG. 10 is a partially transparent perspective view showing components of the example particle therapy system of FIGS. 1 and 2 .

圖11係可與本文中所闡述之粒子治療系統搭配使用的一實例性粒子加速器中之組件之一剖視側視圖。 Figure 11 is a cross-sectional side view of components in an example particle accelerator that may be used with the particle therapy system described herein.

不同圖中之相似元件符號指示相似元件。 Similar component symbols in different drawings identify similar components.

本文中闡述可裝納於用於醫療之同一空間中之一實例性粒子治療系統。此一系統包含可係但不限於一同步迴旋加速器之一粒子加速器，該同步迴旋加速器重量輕且小到足以裝配在一標準線性加速器(LINAC)拱頂內。該系統亦包含經組態以遞送一帶電粒子束(諸如自加速 器輸出之質子或離子)來醫療一患者體內之腫瘤或其他病症的一醫用檯座。在此實例中，檯座包含在其一內部中具有磁體之一環形(例如，圓環形)結構。磁體包含接近於粒子加速器之一輸出之一第一/向量磁體以及接近於一醫療位置之第二/彎曲磁體。醫療位置可對應於彎曲磁體之一共同等中心之一位置。向量磁體經組態以將粒子束引導至不同彎曲磁體，並且彎曲磁體經組態以將粒子束朝向醫療位置彎曲。為使得能夠在用於醫療之同一空間中(尤其在相對小之空間中，諸如一標準LINAC拱頂)遞送粒子束，彎曲磁體經組態以將粒子束彎曲成直角或鈍角。舉例而言，彎曲磁體中之每一者可係「D」形的，並且彎曲磁體中之每一者可經組態並經配置以將粒子束彎曲90°或更大。 Described herein is an example particle therapy system that can be housed in the same space used for medical treatment. Such a system includes a particle accelerator which may be, but is not limited to, a synchrocyclotron that is lightweight and small enough to fit within a standard linear accelerator (LINAC) vault. The system also includes a system configured to deliver a charged particle beam, such as a self-accelerating A medical pedestal that uses protons or ions output by a device to treat tumors or other diseases in a patient. In this example, the pedestal includes an annular (eg, donut-shaped) structure with magnets in an interior thereof. The magnets include a first/vector magnet proximate an output of the particle accelerator and a second/bend magnet proximate a medical location. The medical location may correspond to one of the common isocenter locations of the curved magnets. The vector magnets are configured to direct the particle beam to different bend magnets, and the bend magnets are configured to bend the particle beam toward the medical location. To enable delivery of particle beams in the same space used for medical treatment, especially in relatively small spaces such as a standard LINAC vault, bending magnets are configured to bend the particle beam at right or obtuse angles. For example, each of the bending magnets may be "D" shaped, and each of the bending magnets may be configured and configured to bend the particle beam 90° or more.

就此而言，本文中所闡述之粒子治療系統之某些實施方案採用大孔徑超導彎曲磁體，其經組態以在一短距離內將粒子束彎曲，藉此減小系統之大小。一般而言，一超導體係諸如鈮-錫(Nb3Sn)之一元素或金屬合金，當冷卻至一臨限溫度以下時，該元素或金屬合金會失去大部分(若非全部)電阻。結果，電流實質上不受阻礙地流經超導體。因此，超導線圈在其超導狀態下能夠傳導比相同大小之普通導線大得多之電流。由於超導線圈能夠傳導大量電流，因此在粒子治療系統中特別有用。 In this regard, certain embodiments of the particle therapy systems described herein employ large aperture superconducting bend magnets that are configured to bend a particle beam over a short distance, thereby reducing the size of the system. In general, a superconductor is an element or metal alloy, such as niobium-tin (Nb 3 Sn), that loses most, if not all, of its electrical resistance when cooled below a critical temperature. As a result, electrical current flows through the superconductor virtually unimpeded. Thus, a superconducting coil, in its superconducting state, is capable of conducting much greater currents than a conventional wire of the same size. Superconducting coils are particularly useful in particle therapy systems because they can conduct large amounts of current.

圖1、圖2及圖3分別展示同一粒子治療系統10之側視圖、俯視圖及透視圖。粒子治療系統10係前述段落中所闡述之類型的。如所展示，粒子治療系統10包含一粒子加速器12，該粒子加速器之實例闡述於本文中。在此實例中，粒子加速器12係具有產生3特斯拉(T)或更大之一最大磁場強度之一超導電磁結構之一同步迴旋加速器。實例性同步迴旋加速器產生具有150兆電子伏特(MeV)或更大之一能階之一粒子束，具有4.5立 方米(m3)或更小之一體積，且具有30噸(T)或更小之一重量。然而，在粒子治療系統10中可使用同步迴旋加速器或具有不同於此等重量、尺寸、磁場及/或能階的其他類型之粒子加速器。 Figures 1, 2 and 3 respectively show a side view, a top view and a perspective view of the same particle therapy system 10. Particle therapy system 10 is of the type described in the preceding paragraph. As shown, particle therapy system 10 includes a particle accelerator 12, examples of which are described herein. In this example, the particle accelerator 12 is a synchrocyclotron having a superconducting electromagnetic structure that produces a maximum magnetic field strength of 3 Tesla (T) or greater. An example synchrocyclotron produces a particle beam with an energy level of 150 megaelectronvolts (MeV) or greater, has a volume of 4.5 cubic meters (m 3 ) or less, and has a volume of 30 tons (T) or more Small one weight. However, synchrocyclotrons or other types of particle accelerators having weights, dimensions, magnetic fields, and/or energy levels different from these may be used in particle therapy system 10 .

粒子治療系統10亦包含檯座14。檯座14在結構上至少部分地係環形的，如圖1、圖2及圖3中所展示。一環形包含由一閉合平面曲線圍繞位於與該閉合平面曲線相同之平面上之一線旋轉所產生的表面形成之一圓環形狀。舉例而言，一環形可由以下或類似方程組參數化地定義：x(u,v)=(cos u)(a cos(v)+c) (1) Particle therapy system 10 also includes a pedestal 14 . The base 14 is at least partially annular in structure, as shown in FIGS. 1 , 2 and 3 . A torus includes the shape of a donut formed by the surface resulting from the rotation of a closed planar curve about a line lying on the same plane as the closed planar curve. For example, a ring can be parametrically defined by the following or similar system of equations: x ( u, v ) = (cos u ) ( a cos ( v ) + c ) (1)

y(u,v)=(sin u)(a cos(v)+c) (2) y ( u,v )=(sin u )( a cos( v )+ c ) (2)

z(u,v)=a sin v (3) z ( u,v )=a sin v (3)

針對中心在一原點處之一圓環，一對稱旋轉軸係圍繞一z軸，自一孔之中心至一圓環管或開口之一中心之一半徑係c，且該管或開口之半徑係a。在此實例中，檯座14具有如圖1中所展示之一大致環形形狀，但無需嚴格符合一環形之數學定義。 For a circular ring whose center is at an origin, the axis of symmetrical rotation is around a z-axis, the radius from the center of a hole to the center of a circular tube or opening is c , and the radius of the tube or opening Department a . In this example, the base 14 has a generally annular shape as shown in FIG. 1 , but does not need to strictly conform to the mathematical definition of an annular shape.

因此，檯座14包含一孔15，醫療床17可穿過該孔移動，以將患者放置在一醫療位置中。檯座14之環形結構之內部由外殼18界定(圖1及圖2)。在彼內部內的係一向量磁體20(圖1及圖2)，其亦被稱為一偏踢(kicker)磁體。在某些實施方案中，檯座14可包含多於一個向量磁體。向量磁體20經被組態並可經控制以將源於粒子加速器12處並自粒子加速器12接收之一粒子束朝向彎曲磁體22引導(圖1及圖2)。在操作中，向量磁體20經組態以將自粒子加速器接收之粒子束朝向彎曲磁體22中之一者引導，且將粒子束重新引導至一不同彎曲磁體22。舉例而言，向量磁體20可經控制以根據一醫療計劃之規格在彎曲磁體22之不同彎曲磁體之間或當 中操縱粒子束。如下文所闡述，彎曲磁體經組態以將粒子束朝向醫療位置引導。因此，藉由在彎曲磁體22之間或當中操縱粒子束，向量磁體20能夠控制粒子束到達醫療位置處之一輻照標靶之方向。舉例而言，藉由在彎曲磁體22之間或當中操縱粒子束，向量磁體20能夠控制將粒子束施加至醫療位置處之一輻照標靶之不同角度。 Therefore, the table 14 includes a hole 15 through which a medical bed 17 can be moved to place a patient in a medical position. The interior of the ring structure of the table 14 is defined by a shell 18 (FIG. 1 and FIG. 2). Inside that interior is a vector magnet 20 (FIG. 1 and FIG. 2), which is also referred to as a kicker magnet. In some embodiments, the table 14 may include more than one vector magnet. The vector magnet 20 is configured and can be controlled to guide a particle beam originating from the particle accelerator 12 and received from the particle accelerator 12 toward the bending magnet 22 (FIG. 1 and FIG. 2). In operation, the vector magnet 20 is configured to guide the particle beam received from the particle accelerator toward one of the bending magnets 22, and redirect the particle beam to a different bending magnet 22. For example, the vector magnet 20 can be controlled to steer the particle beam between or among different bending magnets of the bending magnets 22 according to the specifications of a medical plan. As explained below, the bending magnets are configured to direct the particle beam toward the medical location. Therefore, by steering the particle beam between or among the bending magnets 22, the vector magnet 20 is able to control the direction of the particle beam to an irradiation target at the medical location. For example, by steering the particle beam between or among the bending magnets 22, the vector magnet 20 is able to control different angles at which the particle beam is applied to an irradiation target at the medical location.

在某些實施方案中，存在多個向量磁體，其可包含經組態並可經控制以在多個路徑當中切換粒子束之偶極磁體。舉例而言，每一向量磁體可經組態以將粒子束引導至一單個彎曲磁體或引導至獨特的一組彎曲磁體。在操作中，每一向量磁體可經控制以快速地接通，且然後在一預定義時間內維持一穩定磁場。剩餘向量磁體可在此時斷開，使得所接通向量磁體能夠將粒子束朝向一標靶彎曲磁體引導。可接通及/或斷開不同向量磁體來控制粒子束之方向。 In certain embodiments, there are multiple vector magnets, which may include dipole magnets configured and controllable to switch the particle beam among multiple paths. For example, each vector magnet can be configured to direct the particle beam to a single curved magnet or to a unique set of curved magnets. In operation, each vector magnet can be controlled to turn on quickly and then maintain a stable magnetic field for a predefined time. The residual vector magnet can be switched off at this point, allowing the switched vector magnet to direct the particle beam towards a target bending magnet. Different vector magnets can be switched on and/or off to control the direction of the particle beam.

在某些實施方案中，向量磁體可在二維(例如，一平面之笛卡爾XY維度)上進行控制以將粒子束朝向一彎曲磁體引導。在某些實施方案中，一向量磁體包含控制笛卡爾X維度中之粒子束移動之一第一組兩個線圈以及與該第一組兩個線圈正交並控制笛卡爾Y維度中之粒子束移動之一第二組兩個線圈。在某些實施方案中，藉由使流過一組或兩組線圈之電流變化從而使藉此產生之磁場變化來達成控制。藉由使磁場適當地變化，粒子束可在X維度及/或Y維度上朝向一彎曲磁體移動。舉例而言，X及Y維度對應於平行於環形結構之半徑之一平面，並且向量磁體20可將粒子束引導至彼平面中之任何地方。 In certain embodiments, vector magnets can be controlled in two dimensions (eg, the Cartesian XY dimensions of a plane) to direct the particle beam toward a curved magnet. In certain embodiments, a vector magnet includes a first set of two coils that control movement of the particle beam in the Cartesian X dimension and orthogonal to the first set of two coils that controls the Cartesian particle beam in the Y dimension. Move one of the two coils to the second set. In some embodiments, control is achieved by varying the current flowing through one or both sets of coils, thereby varying the magnetic field produced thereby. By appropriately varying the magnetic field, the particle beam can move in the X and/or Y dimensions toward a curved magnet. For example, the X and Y dimensions correspond to a plane parallel to the radius of the annular structure, and the vector magnet 20 can direct the particle beam anywhere in that plane.

如所提及，在某些實施方案中，檯座14包含實體地連接至粒子加速器12之一外殼18。外殼18可環繞及圍封向量磁體20以及由向量 磁體20引導之粒子束。外殼18亦可環繞並圍封彎曲磁體22及本文中所闡述之其他系統組件，包含但不限於噴嘴及其內部組件以及成像裝置。可使用諸如鉛、硼化聚乙烯及/或鋼等材料對外殼18進行電磁屏蔽。 As mentioned, in some embodiments, the pedestal 14 includes a housing 18 physically connected to the particle accelerator 12. The housing 18 can surround and enclose the vector magnet 20 and the particle beam directed by the vector magnet 20. The housing 18 can also surround and enclose the bending magnet 22 and other system components described herein, including but not limited to the nozzle and its internal components and the imaging device. The housing 18 can be electromagnetically shielded using materials such as lead, boronized polyethylene and/or steel.

如圖1至圖3中所展示，彎曲磁體22被周向地配置成圍繞穿過檯座之環形結構之孔15。在此實例中，彎曲磁體22係實質上D形的；然而，可使用具有其他形狀之磁體來替換D形磁體。在此實例中，所有彎曲磁體22具有相同形狀；然而，在其他實施方案中，可存在佔用檯座14之不同扇區的不同形狀之彎曲磁體22。 As shown in Figures 1 to 3, the bending magnets 22 are circumferentially arranged around a hole 15 through the annular structure of the pedestal. In this example, the curved magnets 22 are substantially D-shaped; however, magnets having other shapes may be used in place of the D-shaped magnets. In this example, all curved magnets 22 have the same shape; however, in other embodiments, there may be differently shaped curved magnets 22 occupying different sectors of the pedestal 14 .

就此而言，如先前所提及，檯座14被分成多個扇區。圖4概念性地展示具有各自含納本文中所闡述之類型之一彎曲磁體22之四個扇區30至33之一實例性環形檯座。諸如圖1及圖2中所展示之其他實施方案可包含各自含納一對應彎曲磁體之多於四個扇區或少於四個扇區。歸因於含納於每一扇區中之一彎曲磁體之定位及形狀，扇區中之每一者經組態以自一不同角度位置將輻射遞送給患者。就此而言，在某些實施方案中，每一彎曲磁體22之D形形成將來自加速器12之粒子束朝向一醫療位置24彎曲90°之一磁場。舉例而言，此彎曲之一實例展示於圖5中。 In this regard, as mentioned previously, the pedestal 14 is divided into sectors. Figure 4 conceptually shows an example annular pedestal with four sectors 30-33 each containing a curved magnet 22 of the type discussed herein. Other implementations, such as those shown in Figures 1 and 2, may include more than four sectors or less than four sectors each containing a corresponding curved magnet. Due to the positioning and shape of a curved magnet contained in each sector, each of the sectors is configured to deliver radiation to the patient from a different angular position. In this regard, in certain embodiments, the D-shape of each bend magnet 22 creates a magnetic field that bends the particle beam from the accelerator 12 through 90° toward a medical location 24. An example of such a bend is shown in Figure 5, for example.

如圖5中所展示，向量磁體20在不同時間將粒子束25引導至彎曲磁體22中之不同彎曲磁體(圖5中未展示彎曲磁體)。彎曲磁體22將粒子束25朝向醫療位置24彎曲。在某些實施方案中，每一彎曲磁體22或檯座14之扇區可經組態(例如，經塑形)以將粒子束彎曲成在90°至150°或更大之一範圍內，舉例而言，90°、95°、100°、105°、110°、115°、120°、125°、130°、135°、140°、145°或150°。在某些實施方案中，每一彎曲磁體22或檯座14之扇區可經組態(例如，經塑形)以將粒子束彎曲大 於150°或小於90°。因為扇區及彎曲磁體係在檯座周圍不同角度位置處，所以經由不同彎曲磁體施加之粒子束自不同角度並在某些情形中在不同位置處撞擊輻照標靶。圖5中之線29表示環形結構中之磁場。 As shown in Figure 5, the vector magnet 20 directs the particle beam 25 to different ones of the bending magnets 22 at different times (the bending magnets are not shown in Figure 5). The bending magnet 22 bends the particle beam 25 towards the medical site 24 . In certain embodiments, each bend magnet 22 or sector of the pedestal 14 may be configured (e.g., shaped) to bend the particle beam in a range from 90° to 150° or greater, For example, 90°, 95°, 100°, 105°, 110°, 115°, 120°, 125°, 130°, 135°, 140°, 145° or 150°. In certain embodiments, each bend magnet 22 or sector of the pedestal 14 may be configured (eg, shaped) to bend the particle beam over a large area. at 150° or less than 90°. Because the sectors and curved magnet systems are at different angular positions around the pedestal, particle beams applied via different curved magnets strike the irradiation target from different angles and in some cases at different locations. Line 29 in Figure 5 represents the magnetic field in the ring structure.

在某些實施方案中，彎曲磁體22可係大孔徑超導磁體；然而，可單獨使用或者與超導磁體結合使用非超導磁體。在某些實施方案中，可存在圍繞孔15周向地配置之8個至12個彎曲磁體22。在某些實施方案中，可存在圍繞孔15周向地配置之6個至20個彎曲磁體22。對於所有彎曲磁體，毗鄰彎曲磁體之間的分隔距離可係相同的；亦即，毗鄰彎曲磁體可圍繞環形檯座以均勻間隔隔開。位於檯座14內之彎曲磁體22愈多，檯座之精度便愈高。就此而言，在某些實施方案中，檯座14保持靜止且不相對於醫療位置旋轉。在某些實施方案中，檯座14可進行旋轉以達到一所期望角度位置，但在醫療期間不進行旋轉。舉例而言，在某些實施方案中，檯座14包含使得其角能夠旋轉180°或更多之一或多個馬達，此使得彎曲磁體能夠相對於醫療位置進行精確角度放置，例如，以1°或更少之增量。 In some embodiments, the bending magnets 22 may be large aperture superconducting magnets; however, non-superconducting magnets may be used alone or in combination with superconducting magnets. In some embodiments, there may be 8 to 12 bending magnets 22 arranged circumferentially around the aperture 15. In some embodiments, there may be 6 to 20 bending magnets 22 arranged circumferentially around the aperture 15. The separation distance between adjacent bending magnets may be the same for all bending magnets; that is, adjacent bending magnets may be spaced at uniform intervals around the annular table. The more bending magnets 22 are located in the table 14, the higher the accuracy of the table. In this regard, in some embodiments, the table 14 remains stationary and does not rotate relative to the medical position. In some embodiments, the table 14 can be rotated to achieve a desired angular position, but does not rotate during the medical treatment. For example, in some embodiments, the table 14 includes one or more motors that enable its angle to rotate 180° or more, which enables the bending magnet to be precisely angularly positioned relative to the medical position, for example, in increments of 1° or less.

在前述情形中之任一情形中，彎曲磁體22可在醫療期間相對於醫療位置保持靜止。可藉由在彎曲磁體22之不同彎曲磁體當中移動粒子束來實施醫療，以便在醫療位置處相對於一輻照標靶重新定位粒子束。彎曲磁體22愈多，粒子束相對於輻照標靶之定位便愈精確。換言之，額外磁體提供粒子束相對於輻照標靶之更精細角度定位。除了其他事物之外，還可在基於檯座之實體約束之一醫療計劃中設定醫療角度，諸如可用檯座輸出角度之數目(此將係彎曲磁體22之數目之函數)等。 In any of the foregoing scenarios, the bending magnet 22 may remain stationary relative to the treatment location during treatment. Treatment can be performed by moving the particle beam among different bending magnets 22 to reposition the particle beam relative to an irradiation target at the treatment location. The more curved magnets 22 there are, the more precisely the particle beam can be positioned relative to the irradiation target. In other words, the additional magnets provide finer angular positioning of the particle beam relative to the irradiation target. The medical angles can be set in a medical plan based on physical constraints of the pedestal, such as the number of available pedestal output angles (which will be a function of the number of bending magnets 22), among other things.

在某些實施方案中，彎曲磁體中之個別彎曲磁體可經控制以在檯座內移動。舉例而言，附接至磁體之馬達可控制彎曲磁體之內部移 動來改變束輸出。舉例而言，在檯座內朝向或遠離加速器移動彎曲磁體可影響彎曲磁體將粒子束彎曲之角度。舉例而言，在檯座內旋轉或傾斜彎曲磁體可影響彎曲磁體將粒子束彎曲之角度。磁體移動可符合一醫療計劃之要求。 In certain embodiments, individual ones of the bending magnets can be controlled to move within the pedestal. For example, a motor attached to the magnet can control the internal movement of the curved magnet. Move to change the beam output. For example, moving the bending magnet toward or away from the accelerator within the pedestal can affect the angle at which the bending magnet bends the particle beam. For example, rotating or tilting the bending magnet within the pedestal can affect the angle at which the bending magnet bends the particle beam. The magnets can be moved to meet the requirements of a medical plan.

如所解釋，將檯座14分成多個扇區。歸因於含納於每一扇區中之彎曲磁體之定位及形狀，扇區中之每一者經組態以自一不同角度位置將輻射遞送給患者。一噴嘴可位於每一扇區中，或者可移動至每一扇區。舉例而言，在某些實施方案中，檯座14包含安裝在外殼18內之一軌道或環上或者檯座14之一外部部分上的一單個噴嘴。在醫療期間，使用一或多個馬達來控制噴嘴，以移動至檯座之一扇區，並進入一彎曲磁體22之粒子束路徑輸出路徑中。諸如本文中所闡述之一控制系統34可基於醫療計劃來控制噴嘴沿著檯座之移動。在某些實施方案中，噴嘴或多個噴嘴可安裝至可在檯座14內旋轉且經組態用於安裝諸如噴嘴之輻射遞送組件的一環45(圖3)。該環可旋轉以相對於患者定位噴嘴。當粒子束越過並超過彎曲磁體且進入噴嘴時，粒子束可處於其最大能量下。在某些實施方案中，最大能量可係加速器能夠輸出之最大束能量或者在加速器內設定之一預定義束能量。 As explained, the table 14 is divided into a plurality of sectors. Due to the positioning and shape of the bending magnets contained in each sector, each of the sectors is configured to deliver radiation to the patient from a different angular position. A nozzle may be located in each sector, or may be moved to each sector. For example, in some embodiments, the table 14 includes a single nozzle mounted on a track or ring in the housing 18 or on an outer portion of the table 14. During medical treatment, one or more motors are used to control the nozzle to move to a sector of the table and enter the particle beam path output path of a bending magnet 22. A control system 34 as described herein can control the movement of the nozzle along the table based on the medical plan. In some embodiments, the nozzle or nozzles can be mounted to a ring 45 (Figure 3) that can rotate within the table 14 and is configured to mount radiation delivery components such as nozzles. The ring can rotate to position the nozzle relative to the patient. When the particle beam passes over and beyond the bending magnet and enters the nozzle, the particle beam can be at its maximum energy. In some embodiments, the maximum energy can be the maximum beam energy that the accelerator can output or a predetermined beam energy set within the accelerator.

在某些實施方案中，檯座14包含安裝在檯座14內之一或多個軌道或環上或者檯座14之外部部分上的多個噴嘴。舉例而言，圖3展示在檯座14之內部上安裝至之檯座14之四個噴嘴37、38、39及40。可使用馬達來控制噴嘴37、38、39及40，以移動至檯座之一扇區並進入一彎曲磁體22之粒子束路徑輸出中。另一選擇係，環45可經旋轉以成角度地定位噴嘴，或者噴嘴可經組態以圍繞環45移動(例如，旋轉)。 In some embodiments, table 14 includes a plurality of nozzles mounted on one or more tracks or rings within table 14 or on an exterior portion of table 14. For example, FIG. 3 shows four nozzles 37, 38, 39, and 40 mounted to table 14 on the interior of table 14. Motors may be used to control nozzles 37, 38, 39, and 40 to move to a sector of the table and into a particle beam path output of a bending magnet 22. Alternatively, ring 45 may be rotated to angularly position the nozzles, or the nozzles may be configured to move (e.g., rotate) around ring 45.

一控制系統(諸如本文中所闡述之彼等控制系統)可基於醫療計劃來控制噴嘴之移動。每一噴嘴可經組態以服務於檯座14之一或多個扇區。舉例而言，一環形檯座可包含十二個扇區及四個噴嘴。每一噴嘴可經組態並可經控制以服務於三個毗鄰扇區。舉例而言，一第一噴嘴可服務於扇區一、二及三；一第二噴嘴可服務於扇區四、五及六；一第三噴嘴可服務於扇區七、八及九；並且一第四噴嘴可服務於扇區十、十一及十二。可協調或限制噴嘴之移動，以防止在醫療期間在噴嘴之間的碰撞。舉例而言，第一噴嘴可經組態以圍繞檯座在0°至90°之一範圍中移動；第二噴嘴可經組態以圍繞檯座在91°至180°之一範圍中移動；第三噴嘴可經組態以圍繞檯座在181°至270°之一範圍中移動；並且第四噴嘴可經控制以圍繞檯座在279°至359°之一範圍中移動。 A control system, such as those described herein, can control the movement of the nozzle based on the medical plan. Each nozzle may be configured to serve one or more sectors of the pedestal 14 . For example, an annular pedestal may contain twelve sectors and four nozzles. Each nozzle can be configured and controlled to serve three adjacent sectors. For example, a first nozzle can serve sectors one, two, and three; a second nozzle can serve sectors four, five, and six; a third nozzle can serve sectors seven, eight, and nine; and A fourth nozzle can serve sectors ten, eleven and twelve. Nozzle movement can be coordinated or limited to prevent collisions between nozzles during medical treatment. For example, the first nozzle can be configured to move around the base in a range of 0° to 90°; the second nozzle can be configured to move around the base in a range from 91° to 180°; The third nozzle can be configured to move about the pedestal in a range of 181° to 270°; and the fourth nozzle can be controlled to move about the pedestal in a range of 279° to 359°.

如本文中所闡述，在環形檯座架構中，一向量磁體位於加速器出口埠處或其附近，且可藉由在一逐層或逐脈衝基礎上同時自多個角度遞送輻射來快速改變束角度，從而顯著縮短總醫療時間。出於此目的，多個噴嘴(例如，2個、3個、4個或更多個噴嘴)可安裝在檯座14之一內部直徑處之可旋轉環45上。因為環旋轉，所以安裝至其之噴嘴中之一或多者與環一起旋轉，使得噴嘴能夠定位，同時減少與患者或系統組件碰撞之機會。 As explained herein, in a ring-shaped table configuration, a vector magnet is located at or near the accelerator exit port and can rapidly change beam angles by delivering radiation from multiple angles simultaneously on a layer-by-layer or pulse-by-pulse basis, thereby significantly reducing the total treatment time. For this purpose, multiple nozzles (e.g., 2, 3, 4 or more nozzles) can be mounted on a rotatable ring 45 at an inner diameter of the table 14. As the ring rotates, one or more of the nozzles mounted thereto rotate with the ring, allowing the nozzles to be positioned while reducing the chance of collision with the patient or system components.

在某些實施方案中，檯座14上之噴嘴係靜止的；亦即，噴嘴不相對於檯座14移動。舉例而言，在每一扇區中可存在位於彼扇區中之一彎曲磁體之束路徑輸出中之一噴嘴。每扇區具有未移動之一個噴嘴可減少醫療時間，此乃因無需時間來定位及重新定位噴嘴。在某些實施方案中，安裝至檯座14之所有組件並不圍繞檯座旋轉地移動。另外，如所提 及，在某些實施方案中，檯座14本身係靜止的。另外，如所提及，在某些實施方案中，檯座14本身係可旋轉的。 In some embodiments, the nozzles on the table 14 are stationary; that is, the nozzles do not move relative to the table 14. For example, in each sector there may be a nozzle located in the beam path output of a bending magnet in that sector. Having a nozzle per sector that does not move can reduce treatment time because there is no time to position and reposition the nozzles. In some embodiments, all components mounted to the table 14 do not move around the table. In addition, as mentioned, in some embodiments, the table 14 itself is stationary. In addition, as mentioned, in some embodiments, the table 14 itself is rotatable.

在圖3之實例中，噴嘴39位於一扇區中。在某些實施方案中，每一噴嘴可具有相同功能及組態。噴嘴39自一彎曲磁體22接收粒子束，且在某些實施方案中調節粒子束以輸出至醫療位置處之一輻照標靶，諸如一患者體內之一腫瘤。就此而言，如所提及，每一彎曲磁體22將粒子束朝向醫療位置處之一患者彎曲至少90°。因此，粒子束在一磁體22之上彎曲之後被朝向醫療位置引導。 In the example of Figure 3, the nozzles 39 are located in a sector. In certain embodiments, each nozzle may have the same function and configuration. Nozzle 39 receives the particle beam from a curved magnet 22 and in some embodiments modulates the particle beam for output to an irradiation target at a medical location, such as a tumor in a patient. In this regard, as mentioned, each bending magnet 22 bends the particle beam by at least 90° toward a patient at a medical location. The particle beam is therefore guided towards the medical location after being bent over a magnet 22 .

在某些實施方案中，每一彎曲磁體可在其輸出處包含一掃描磁體，或者將掃描磁體功能性併入其磁性結構中。一掃描磁體可在兩個維度(例如，笛卡爾XY維度)上進行控制以在彼等兩個維度上定位粒子束，且移動粒子束跨越一輻照標靶之至少一部分。在某些實施方案中，一掃描磁體包含控制笛卡爾X維度中之粒子束移動之一第一組兩個線圈以及與該第一組兩個線圈正交並控制笛卡爾Y維度中之粒子束移動之一第二組兩個線圈。在某些實施方案中，藉由使流過一組或兩組線圈之電流變化以藉此使藉此產生之磁場變化來達成控制。藉由使磁場適當地變化，粒子束可在X及/或Y維度上移動跨越輻照標靶之層。在某些實施方案中，一或多個掃描磁體可位於每一彎曲磁體之下游(亦即比每一彎曲磁體更靠近醫療位置)但位於能量降級器之上游。舉例而言，一或多個掃描磁體43(圖6)可位於下文所闡述之能量降級器與一彎曲磁體之輸出之間的每一噴嘴中。 In some embodiments, each bending magnet may include a scanning magnet at its output, or a scanning magnet may be functionally incorporated into its magnetic structure. A scanning magnet may be controlled in two dimensions (e.g., Cartesian XY dimensions) to position a particle beam in those two dimensions, and to move the particle beam across at least a portion of an irradiated target. In some embodiments, a scanning magnet includes a first set of two coils that control the movement of the particle beam in the Cartesian X dimension and a second set of two coils that are orthogonal to the first set of two coils and control the movement of the particle beam in the Cartesian Y dimension. In some embodiments, control is achieved by varying the current flowing through one or both sets of coils to thereby vary the magnetic field generated thereby. By varying the magnetic field appropriately, the particle beam can be moved across the layer of the irradiated target in the X and/or Y dimensions. In some embodiments, one or more scanning magnets may be located downstream of each bending magnet (i.e., closer to the treatment site than each bending magnet) but upstream of the energy degrader. For example, one or more scanning magnets 43 (FIG. 6) may be located in each nozzle between the energy degrader described below and the output of a bending magnet.

參考圖6及圖7，每一噴嘴(諸如噴嘴38)亦可包含在粒子束到達患者之前自一彎曲及/或掃描磁體接收粒子束之一能量降級器41。在此實例中，能量降級器41位於一彎曲磁體22與輻照標靶之間。能量降級 器41經組態並可經控制以在粒子束到達輻照標靶之前改變粒子束之一能量。舉例而言，能量降級器可包含可移入或移出粒子束之一路徑之板。舉例而言，能量降級器可包含至少部分地重疊且可在粒子束之一路徑內移動之楔形物。一實例性楔形物係由兩個三角形及三個梯形面定義之一多面體。在任一組態中，可變量之材料可移動至粒子束之路徑中。該材料自粒子束吸收能量，從而導致能量減少之束輸出。粒子束之路徑中之材料愈多，粒子束將具有之能量便愈少。在某些實施方案中，能量吸收結構可移動跨越掃描磁體對其進行掃描或者可在其之上遞送粒子束的束場之全部，或者僅移動跨越束場之一部分。在某些實例中，對於一給定彎曲磁體或掃描磁體，射束場係粒子束可跨越平行於一患者上之醫療區域的一平面移動之最大廣度。 6 and 7, each nozzle (such as nozzle 38) may also include an energy degrader 41 that receives the particle beam from a bending and/or scanning magnet before the particle beam reaches the patient. In this example, the energy degrader 41 is located between a bending magnet 22 and the irradiation target. The energy degrader 41 is configured and controllable to change an energy of the particle beam before the particle beam reaches the irradiation target. For example, the energy degrader may include a plate that can be moved into or out of a path of the particle beam. For example, the energy degrader may include a wedge that is at least partially overlapped and can be moved within a path of the particle beam. An exemplary wedge is a polyhedron defined by two triangular and three trapezoidal faces. In either configuration, a variable amount of material can be moved into the path of the particle beam. The material absorbs energy from the particle beam, resulting in a beam output with reduced energy. The more material in the path of the particle beam, the less energy the particle beam will have. In some embodiments, the energy absorbing structure can move across the entire beam field over which the scanning magnet scans it or over which the particle beam is delivered, or only across a portion of the beam field. In some examples, for a given bending magnet or scanning magnet, the beam field is the maximum extent to which the particle beam can move across a plane parallel to the treatment region on a patient.

在圖7之實例中，能量降級器41係一範圍移位器，其可經控制以將結構42移入並移出粒子束之路徑來改變粒子束之能量，且因此改變粒子束之劑量將沈積在輻照標靶中之深度。此類結構之實例包含但不限於能量吸收板；諸如楔形物之多面體、四面體或環形多面體；以及彎曲之三維形狀，諸如圓柱體、球體或圓錐體。以此方式，能量降級器可致使粒子束在一輻照標靶之內部中沈積輻射劑量，以醫療標靶之層或柱。就此而言，當質子移動穿過組織時，質子使組織之原子離子化並沿其路徑沈積一劑量。因此，能量降級器經組態以在笛卡爾Z維度上使粒子束移動穿過標靶，藉此使得能夠在三個維度上進行掃描。在某些實施方案中，能量降級器可經組態以在粒子束之移動期間進行移動，且在移動期間追蹤或尾隨粒子束。追蹤或尾隨粒子束移動之一實例性能量降級器闡述於標題為「High-Speed Energy Switching」之美國專利第10,675,487(Zwart)中。 美國專利第10,675,487號之內容(尤其與追蹤或尾隨粒子束移動之能量降級器相關之內容(例如，美國專利第10,675,487號之圖36至圖46以及隨附闡述))以引用方式併入本文中。 In the example of Figure 7, energy degrader 41 is a range shifter that can be controlled to move structure 42 into and out of the path of the particle beam to change the energy of the particle beam, and thus change the dose of the particle beam that will be deposited in The depth within the irradiated target. Examples of such structures include, but are not limited to, energy absorbing panels; polyhedrons, tetrahedrons, or annular polyhedrons such as wedges; and curved three-dimensional shapes, such as cylinders, spheres, or cones. In this manner, the energy degrader can cause the particle beam to deposit a radiation dose within the interior of an irradiation target to treat layers or columns of the target. In this regard, as protons move through tissue, they ionize the atoms of the tissue and deposit a dose along their path. Therefore, the energy degrader is configured to move the particle beam across the target in the Cartesian Z dimension, thereby enabling scanning in three dimensions. In certain embodiments, the energy degrader can be configured to move during movement of the particle beam and to track or trail the particle beam during movement. An example energy reducer that tracks or follows the movement of a particle beam is described in U.S. Patent No. 10,675,487 (Zwart) entitled "High-Speed Energy Switching." The contents of U.S. Patent No. 10,675,487, particularly those related to energy degraders that track or trail the movement of a particle beam (e.g., Figures 36-46 of U.S. Patent No. 10,675,487 and the accompanying discussion) are incorporated herein by reference. .

布拉格峰係布拉格曲線上之一顯著峰，該曲線標繪了在輻射行進穿過組織期間將其離子化之能量損失。布拉格峰表示大多數質子沈積在組織內之深度。對於質子而言，布拉格峰正好出現在粒子靜止下來之前。因此，可改變粒子束之能量，以改變其布拉格峰之位置，且因此改變大部分質子劑量將沈積在組織中深處之位置。就此而言，在某些實施方案中，粒子加速器係一固定能量粒子加速器。在一固定能量粒子加速器中，粒子束總是以相同或大致相同(例如，在與一預期或標靶能量之一偏差在5%以內或更小)之能量離開粒子加速器。在一固定能量粒子加速器中，能量降級器係用於使施加至患者體內之一輻照標靶之束之能量變化之主要運載工具。在某些實施方案中，本文中所闡述之粒子加速器經組態以輸出處於約100MeV與約300MeV之間(例如，在115MeV與250MeV之間)的一範圍內之一單個(固定)能量或者處於兩種或更多種能量之粒子束。固定能量輸出可在彼範圍內(例如，250MeV)，或者在某些實例中高於或低於彼範圍。 A Bragg peak is a prominent peak on the Bragg curve that plots the energy lost to ionize tissue as radiation travels through it. The Bragg peak represents the depth within the tissue at which most protons are deposited. For protons, the Bragg peak occurs just before the particles come to rest. Thus, the energy of a particle beam can be varied to change the location of its Bragg peak, and thus change the location at which most of the proton dose will be deposited deep within the tissue. In this regard, in certain embodiments, the particle accelerator is a fixed energy particle accelerator. In a fixed energy particle accelerator, the particle beam always leaves the particle accelerator at the same or approximately the same energy (e.g., within 5% or less of a deviation from an expected or target energy). In a fixed energy particle accelerator, energy degraders are the primary vehicle for varying the energy of the beam applied to an irradiation target within a patient. In some embodiments, the particle accelerators described herein are configured to output a single (fixed) energy within a range between about 100 MeV and about 300 MeV (e.g., between 115 MeV and 250 MeV) or a particle beam at two or more energies. The fixed energy output can be within that range (e.g., 250 MeV), or in some instances, above or below that range.

在某些實施方案中，粒子加速器係一個雙能量加速器。在一個雙能量粒子加速器中，粒子束在兩種不同能階(一高能階及一低能階)中之一者下離開粒子加速器。術語「高」及「低」沒有具體數值含義，而是意欲傳達相對量值。在某些實施方案中，本文中所闡述之粒子加速器經組態以輸出處於約100MeV與約300MeV之間的一範圍內之兩種能量之粒子束。高能量輸出及低能量輸出可係彼範圍內或者在某些實例中高於或低 於彼範圍之值。本文中所闡述之能量降級器可與雙能量粒子加速器搭配使用，以便將粒子束之能量降低至兩個能階中之一者以下及/或精細地調整該兩個能階。 In certain embodiments, the particle accelerator is a dual energy accelerator. In a dual-energy particle accelerator, the particle beam leaves the particle accelerator at one of two different energy levels: a high energy level and a low energy level. The terms "high" and "low" have no specific numerical meaning but are intended to convey relative magnitudes. In certain embodiments, the particle accelerators described herein are configured to output particle beams of two energies in a range between about 100 MeV and about 300 MeV. High energy output and low energy output may be within that range or in some instances higher or lower value within that range. The energy downgraders described herein can be used with dual-energy particle accelerators to reduce the energy of a particle beam below one of two energy levels and/or to finely tune the two energy levels.

噴嘴40亦包含相對於輻照標靶位於能量降級器41下游(即，在能量降級器與標靶之間)之一準直器44(圖6)。在一實例中，一準直器係可經控制以允許某些輻射傳送至一患者並阻止某些輻射傳送至該患者之一裝置。通常，傳送之輻射被引導至待醫療之一輻照標靶，而被阻擋之輻射會以其他方式擊中並潛在地損害健康組織。在操作中，準直器被放置在一彎曲磁體與輻照標靶之間的輻射路徑中，且經控制以產生一適當大小及形狀之一開口，從而允許某些輻射穿過該開口到達輻照標靶，同時該結構之一剩餘部分阻擋某些輻射到達毗鄰組織。可使用之一可組態準直器之一實例闡述於標題為「Adaptive Aperture」之美國專利公開案第2017/0128746(Zwart)號中。美國專利公開案第2017/0128746號之內容(尤其與自適應孔徑之闡述相關之內容(例如，美國專利公開案第2017/0128746號之圖1至圖7以及隨附闡述))以引用方式併入本文中。 The nozzle 40 also includes a collimator 44 located downstream of the energy reducer 41 relative to the irradiated target (ie, between the energy reducer and the target) (Fig. 6). In one example, a collimator is a device that can be controlled to allow certain radiation to be transmitted to a patient and to block certain radiation from being transmitted to the patient. Typically, delivered radiation is directed toward an irradiation target to be treated, while blocked radiation can otherwise hit and potentially damage healthy tissue. In operation, the collimator is placed in the radiation path between a curved magnet and the irradiation target, and is controlled to create an opening of appropriate size and shape to allow some radiation to pass through the opening to the radiation target. The target is illuminated while one remaining portion of the structure blocks some of the radiation from reaching adjacent tissue. An example of a configurable collimator that can be used is described in US Patent Publication No. 2017/0128746 (Zwart) entitled "Adaptive Aperture." The contents of U.S. Patent Publication No. 2017/0128746 (especially those related to the description of adaptive aperture (e.g., Figures 1 to 7 of U.S. Patent Publication No. 2017/0128746 and the accompanying description)) are incorporated by reference. into this article.

如本文中所闡述，一實例性粒子治療系統包含利用數個大孔徑超導磁體之一實例性環形檯座。在此類型之檯座中，遠距離源(SAD)滿足臨床要求，並且檯座之總直徑可減小至小於5米(m)。在一實例中，對於一250MeV實施方案，檯座14之總直徑係3.2m。在此實例中，檯座14之總長度50(圖2)小於5m，例如大約4.3m，並且每一彎曲磁體22之輸出至醫療位置之間的距離係1m或更小。就此而言，在某些實施方案中，每一彎曲磁體22之輸出與醫療位置之間的距離係2m或更小。在某些實施方案中，每一彎曲磁體22之輸出與醫療位置之間的距離係1m或更小。在某 些實施方案中，每一彎曲磁體22之輸出與醫療位置之間的距離係0.5m或更小。在某些實施方案中，檯座重17噸或更輕。 As described herein, an example particle therapy system includes an example annular pedestal utilizing several large aperture superconducting magnets. In this type of pedestal, the source at a distance (SAD) meets clinical requirements and the overall diameter of the pedestal can be reduced to less than 5 meters (m). In one example, for a 250 MeV implementation, the overall diameter of pedestal 14 is 3.2 m. In this example, the total length 50 (Fig. 2) of the pedestal 14 is less than 5 m, such as approximately 4.3 m, and the distance between the output of each curved magnet 22 and the medical location is 1 m or less. In this regard, in certain embodiments, the distance between the output of each curved magnet 22 and the medical location is 2 m or less. In some embodiments, the distance between the output of each curved magnet 22 and the medical location is 1 m or less. in a certain In some embodiments, the distance between the output of each curved magnet 22 and the medical location is 0.5 m or less. In some embodiments, the pedestal weighs 17 tons or less.

其他實施方案可具有不同尺寸，包含但不限於此處所提及之檯座直徑及距離。在某些實施方案中，粒子治療系統可裝配在LINAC拱頂之佔用面積內。舉例而言，圖1至圖6之組件可小到足以裝配在具有以下尺寸之一拱頂內並具有裝配在該拱頂內之尺寸：長度為25英尺(7.62米(m))或更小，寬度為20英尺(6.09m)或更小，並且高度為11英尺(3.35m)或更小。舉例而言，圖1至圖6之組件可小到足以裝配在具有以下尺寸之一拱頂內且具有裝配在該拱頂內之尺寸：長度為25英尺(7.62米(m))或更小，寬度為26英尺(7.92m)或更小，並且高度為10英尺(3.05m)或更小。舉例而言，圖1至圖3之組件可小到足以裝配在具有26.09英尺(11m)×29.62英尺(9m)或更小之一佔用面積、16.40英尺(5m)或更小之一高度的一LINAC拱頂內，且具有裝配在該拱頂內之尺寸。然而，如所提及，粒子治療系統之某些實施方案可具有不同尺寸，包含但不限於直徑、長度、寬度及/或高度。在某些實施方案中，一預先存在之LINAC拱頂之天花板可能不夠高到足以支撐檯座之整個直徑。在此類實施方案中，可在LINAC拱頂之地板下面挖出一凹坑，以使得檯座能夠裝配在該拱頂內。 Other embodiments may have different dimensions, including but not limited to the pedestal diameters and distances mentioned herein. In certain embodiments, the particle therapy system may fit within the footprint of a LINAC vault. For example, the components of Figures 1-6 may be small enough to fit within and have dimensions to fit within a vault having a length of 25 feet (7.62 meters (m)) or less , a width of 20 feet (6.09m) or less, and a height of 11 feet (3.35m) or less. For example, the components of Figures 1-6 may be small enough to fit within and have dimensions to fit within a vault having a length of 25 feet (7.62 meters (m)) or less , a width of 26 feet (7.92m) or less, and a height of 10 feet (3.05m) or less. For example, the components of Figures 1-3 may be small enough to fit in a building with a footprint of 26.09 feet (11 m) by 29.62 feet (9 m) or less and a height of 16.40 feet (5 m) or less. Within a LINAC vault and having dimensions to fit within that vault. However, as mentioned, certain embodiments of particle therapy systems may have different dimensions, including but not limited to diameter, length, width, and/or height. In some embodiments, the ceiling of a pre-existing LINAC vault may not be high enough to support the entire diameter of the pedestal. In such an embodiment, a recess may be dug under the floor of the LINAC vault to allow the pedestal to fit within the vault.

圖8展示其中可實施粒子治療系統10及其變體之一醫療空間51之一實例。在此實例中，醫療空間在一LINAC拱頂中實施，且使用鉛或者諸如混凝土、硼化聚乙烯及/或鋼等其他適當材料進行屏蔽。就此而言，由粒子加速器產生但沒有到達輻照標靶之粒子(諸如質子)透過產生高能量中子來產生二次輻射。在某些實施方案中，本文中所闡述之檯座經組態以即使在低能量下亦能傳輸超過70%之質子束，該檯座包含使用位於束 線下游之一能量降級器之能量選擇。就此而言，在某些實施方案中，粒子束處於加速器之最大能量及固定能量下，直至正好位於等中心之上游(環形之內部直徑處)為止，其中該粒子束被一動態範圍移位器降低能量。亦即，當粒子束進入噴嘴時，粒子束處於加速器之最大能量下。歸因於此直接束系統架構之高束遞送效率(例如，70%至100%)，該束系統架構維持來自加速器之一低雜散輻射及能量調變，加速器可位於醫療室拱頂內，如圖8中所展示。亦即，本文中所闡述之直接束結構達成粒子束之高效轉移，此減少了雜散輻射。因為雜散輻射減少，加速器及患者可位於同一醫療空間中，而不用擔心雜散輻射傷害患者或電子設備。 Figure 8 shows an example of a medical space 51 in which the particle therapy system 10 and variations thereof may be implemented. In this example, the medical space is implemented in a LINAC vault and is shielded using lead or other suitable materials such as concrete, boronized polyethylene and/or steel. In this regard, particles (such as protons) produced by a particle accelerator but that do not reach the irradiation target generate secondary radiation by producing high-energy neutrons. In certain embodiments, a pedestal described herein is configured to transmit more than 70% of a proton beam even at low energies, the pedestal comprising Energy selection for one of the downstream energy downgraders. In this regard, in certain embodiments, the particle beam is at the maximum energy of the accelerator and at a fixed energy until just upstream of the isocenter (at the inner diameter of the annulus), where the particle beam is shifted by a dynamic range shifter Lower energy. That is, when the particle beam enters the nozzle, the particle beam is at the maximum energy of the accelerator. Due to the high beam delivery efficiency (e.g., 70% to 100%) of this direct beam system architecture, the beam system architecture maintains low stray radiation and energy modulation from the accelerator, which can be located within the medical room vault, As shown in Figure 8. That is, the direct beam structure described in this article achieves efficient transfer of the particle beam, which reduces stray radiation. Because stray radiation is reduced, the accelerator and patient can be located in the same medical space without worrying about stray radiation harming the patient or electronic equipment.

在某些實施方案中，由加速器輸出之粒子束可係單能的，並且能量降級器係在一輻照標靶之醫療期間用於改變束能量之僅有/唯一或主要運載工具。一單能粒子束包含具有一單個固定能階(諸如100MeV、150MeV、200MeV、250MeV等等)之一粒子束。一單能粒子束可偏離固定能階一預定量，諸如±10%、±5%、±2%或±1%，並且若該單能粒子束之能量沒有主動改變，則該單能粒子束仍被認為係單能的。加速器在醫療期間之切換操作(如在醫療期間切換粒子束能量所需要)可產生過量雜散中子，從而導致需要增加屏蔽並降低束線效率。中子可由粒子加速器及/或沿著束線之磁性產生。藉由使用在醫療期間係單能的之一粒子束並依賴於能量降級器來改變束能量，可減少或最小化雜散中子之產生，且可增加粒子束輸出之效率。 In certain embodiments, the particle beam output by the accelerator may be monoenergetic, and the energy degrader is the sole or primary vehicle used to modify the beam energy during medical treatment of an irradiated target. A monoenergetic particle beam includes a particle beam with a single fixed energy level (such as 100 MeV, 150 MeV, 200 MeV, 250 MeV, etc.). A monoenergetic particle beam can deviate from a fixed energy level by a predetermined amount, such as ±10%, ±5%, ±2%, or ±1%, and if the energy of the monoenergetic particle beam does not actively change, then the monoenergetic particle beam Still considered monoenergetic. Switching operations of accelerators during medical treatments, such as those required to switch particle beam energies during medical treatments, can generate excess stray neutrons, resulting in the need for increased shielding and reduced beamline efficiency. Neutrons can be produced by particle accelerators and/or magnetism along beam lines. By using a particle beam that is monoenergetic during medical treatment and relying on an energy degrader to vary the beam energy, the production of stray neutrons can be reduced or minimized, and the efficiency of the particle beam output can be increased.

使用一單能粒子束、使用檯座外部之一能量降級器以及使用如本文中所闡述的具有向量及彎曲磁體之一環形檯座使得能夠有效地引導粒子束。更具體而言，束能量之改變增加了雜散中子之產生，並因此增 加了粒子束之損失，藉此降低了其效率。本文中所闡述之系統之實施方案中所使用之單能粒子束與具有向量及彎曲磁體之一環形檯座組合可導致效率提高。在某些情形中，本文中所闡述之直接束架構產生10%或更高、20%或更高、30%或更高、40%或更高、50%或更高、60%或更高、70%或更高、80%或更高或者90%或更高之一效率。在某些實例中，效率係自粒子加速器輸出之粒子與自彎曲磁體輸出之粒子的百分比之一量測。因此，10%或更高之一效率包含自彎曲磁體輸出來自粒子加速器之10%或更多之粒子輸出；20%或更高之一效率包含自彎曲磁體輸出來自粒子加速器之20%或更多之粒子輸出；30%或更高之一效率包含自彎曲磁體輸出來自粒子加速器之30%或更多之粒子輸出；40%或更高之一效率包含自彎曲磁體輸出來自粒子加速器之40%或更多之粒子輸出；50%或更高之一效率包含自彎曲磁體輸出來自粒子加速器之50%或更多之粒子輸出；60%或更高之一效率包含自彎曲磁體輸出來自粒子加速器之60%或更多之粒子輸出；70%或更高之一效率包含自彎曲磁體輸出來自粒子加速器之70%或更多之粒子輸出；80%或更高之一效率包含自彎曲磁體輸出來自粒子加速器之80%或更多之粒子輸出；並且90%或更高之一效率包含自彎曲磁體輸出來自粒子加速器之90%或更多之粒子輸出。在一實例中，即使在加速器之較低範圍中之能量下，本文中所闡述之粒子加速器及檯座亦將超過70%之一質子束傳輸給一患者。本文中所闡述之類型之直接束架構達成一「單個室」解決方案，其中粒子加速器、檯座及患者皆駐留在一單個室或拱頂內。 The use of a monoenergetic particle beam, the use of an energy degrader external to the pedestal, and the use of a toroidal pedestal with vector and bending magnets as described herein enables efficient guidance of the particle beam. More specifically, changes in beam energy increase the generation of stray neutrons and thus increase the loss of the particle beam, thereby reducing its efficiency. The monoenergetic particle beam used in embodiments of the system described herein in combination with a toroidal pedestal with vector and bending magnets can result in increased efficiency. In some cases, the direct beam architecture described herein produces an efficiency of 10% or more, 20% or more, 30% or more, 40% or more, 50% or more, 60% or more, 70% or more, 80% or more, or 90% or more. In some embodiments, the efficiency is a measure of the percentage of particles output from the particle accelerator to particles output from the bending magnet. Thus, an efficiency of 10% or more includes 10% or more of the particle output from the particle accelerator being output from the bending magnet; an efficiency of 20% or more includes 20% or more of the particle output from the particle accelerator being output from the bending magnet; an efficiency of 30% or more includes 30% or more of the particle output from the particle accelerator being output from the bending magnet; an efficiency of 40% or more includes 40% or more of the particle output from the particle accelerator being output from the bending magnet; an efficiency of 50% or more includes 50% or more of the particle output from the bending magnet. 50% or more of the particle output from the particle accelerator; an efficiency of 60% or more includes 60% or more of the particle output from the particle accelerator outputted from the bending magnet; an efficiency of 70% or more includes 70% or more of the particle output from the particle accelerator outputted from the bending magnet; an efficiency of 80% or more includes 80% or more of the particle output from the particle accelerator outputted from the bending magnet; and an efficiency of 90% or more includes 90% or more of the particle output from the particle accelerator outputted from the bending magnet. In one example, the particle accelerator and pedestal described herein delivers more than 70% of a proton beam to a patient even at energies in the lower range of the accelerator. A direct beam architecture of the type described herein achieves a "single room" solution, where the particle accelerator, table, and patient all reside within a single room or vault.

相比而言，某些粒子治療系統所採用之能量選擇系統導致高能量中子之顯著產生，且在摒棄超過99%之處於較低能量之質子束。本 文中所闡述之類型之束線效率可達成一「單個室」解決方案，該解決方案將粒子加速器、束線及患者皆放在一單個拱頂內部。在此拱頂內，粒子加速器可包含屏蔽件，但分別含納患者及粒子加速器之拱頂中之分隔隔間60及61無需彼此屏蔽。換言之，在某些實施方案中，在粒子加速器及檯座之外部不存在將粒子加速器與患者分隔之屏蔽件。亦即，在某些實例中，將粒子加速器與患者分隔之僅有屏蔽件係在粒子加速器本身內或在檯座本身內。在圖8中，檯座14之各部分位於分隔之隔間60及61之壁58內。 In comparison, the energy-selective systems used in some particle therapy systems result in significant production of high-energy neutrons, while rejecting more than 99% of the proton beam at lower energies. Book Beamline efficiencies of the type described in this article enable a "single chamber" solution that places the particle accelerator, beamline, and patient within a single vault. Within the vault, the particle accelerator may contain shielding, but the separate compartments 60 and 61 in the vault containing the patient and the particle accelerator respectively need not be shielded from each other. In other words, in certain embodiments, there is no shield external to the particle accelerator and the pedestal that separates the particle accelerator from the patient. That is, in some instances, the only shielding separating the particle accelerator from the patient is within the particle accelerator itself or within the pedestal itself. In Figure 8, parts of the pedestal 14 are located within the walls 58 of separate compartments 60 and 61.

在某些實施方案中，為了能夠在一現有拱頂中安裝一質子治療系統，拱頂能夠提供必要屏蔽件，此可能需要添加屏蔽件。在一環形檯座不旋轉之情形中，可沿著束平面在環形之局部添加屏蔽件。屏蔽件可由諸如混凝土、硼化聚乙烯及鋼之典型屏蔽材料製成。 In some embodiments, in order to be able to install a proton therapy system in an existing vault, the vault can provide the necessary shielding, which may require the addition of shielding. In the case of an annular pedestal that does not rotate, shielding can be added to parts of the annular shape along the beam plane. The shield can be made from typical shielding materials such as concrete, borated polyethylene and steel.

參考圖1、圖2、圖3、圖8及圖9，粒子治療系統10包含一醫療床17。醫療床17經組態以相對於環形檯座14中或穿過環形檯座14之孔15移動並在該孔內移動。在此實例中，醫療床17可安裝至一機器人臂54。臂54包含一第一分段55、一第二分段56及一第三分段57。第一分段55可旋轉地連接至第二分段56，並且第二分段56可旋轉地連接至第三分段57。如圖中所展示，醫療床17連接至第三分段57。臂54可經控制以將醫療床17移入並穿過孔15，從而定位躺在用於醫療之床上之一患者；亦即，將患者移動至醫療位置中。 Referring to FIGS. 1 , 2 , 3 , 8 and 9 , the particle therapy system 10 includes a medical bed 17 . The medical couch 17 is configured to move relative to and within a hole 15 in or through the annular base 14 . In this example, medical bed 17 may be mounted to a robotic arm 54. The arm 54 includes a first section 55 , a second section 56 and a third section 57 . The first section 55 is rotatably connected to the second section 56 , and the second section 56 is rotatably connected to the third section 57 . As shown in the figure, the medical bed 17 is connected to the third segment 57 . The arm 54 can be controlled to move the medical bed 17 into and through the aperture 15 to position a patient lying on the bed for medical treatment; that is, to move the patient into a medical position.

在某些實施方案中，臂54可以兩個自由度、三個自由度、四個自由度、五個自由度或六個自由度定位患者。兩個自由度之一實例係前後移動及左右移動；三個自由度之一實例係前後移動、左右移動及上下移動；四個自由度之一實例係前後移動、左右移動、上下移動以及縱傾移 動、側傾移動或側滾移動中之一者；五個自由度之一實例係前後移動、左右移動、上下移動以及縱傾移動、側傾移動或側滾移動中之兩者；並且六個自由度之一實例係前後移動、左右移動、上下移動、縱傾移動、側傾移動及側滾移動。在某些實施方案中，醫療床可被至少部分地傾斜之一床或一椅替換，該床或該椅中之任一者皆可以兩個、三個、四個、五個或六個自由度進行控制以定位患者進行醫療。在某些實施方案中，臂54可具有與圖9中所展示的不同之一組態。舉例而言，臂54可具有兩個分段或多於三個分段。液壓、機器人或兩者皆可控制或實施醫療床之非平坦化移動。 In certain embodiments, the arm 54 can position the patient in two degrees of freedom, three degrees of freedom, four degrees of freedom, five degrees of freedom, or six degrees of freedom. One example of two degrees of freedom is forward and backward movement and left and right movement; one example of three degrees of freedom is forward and backward movement, left and right movement and up and down movement; one example of four degrees of freedom is forward and backward movement, left and right movement, up and down movement and pitch. shift One of motion, roll motion or roll motion; one example of the five degrees of freedom is forward and backward motion, left and right motion, up and down motion and two of pitch motion, roll motion or roll motion; and six Examples of degrees of freedom are forward and backward movement, left and right movement, up and down movement, pitch movement, roll movement and roll movement. In certain embodiments, the medical bed may be replaced by an at least partially tilted bed or a chair, either of which may be two, three, four, five, or six free degree of control to position the patient for medical treatment. In certain embodiments, arm 54 may have a different configuration than that shown in FIG. 9 . For example, arm 54 may have two segments or more than three segments. Hydraulics, robotics, or both can control or implement non-flat movements of medical beds.

在某些實施方案中，醫療床或其他座椅經組態以在醫療期間相對於粒子束移動。對於檯座不相對於患者移動之系統而言尤其如此。在某些實施方案中，可使用束移動與醫療床(或其他座椅)移動之一組合來實施醫療。舉例而言，可對檯座進行定位(例如，旋轉)，並且可臨時固定束，在此期間，醫療床移動以實施醫療。此後，可重新定位檯座，以將束臨時固定在一新位置處。可透過床移動在新位置處實施醫療。可按如由供與粒子治療系統搭配使用而起草之一醫療計劃所定義地重複此等操作。 In certain embodiments, a medical couch or other seat is configured to move relative to the particle beam during medical treatment. This is especially true for systems where the pedestal does not move relative to the patient. In certain embodiments, medical treatment may be performed using a combination of beam movement and medical couch (or other chair) movement. For example, the pedestal can be positioned (eg, rotated) and the bundle can be temporarily fixed while the medical couch is moved to perform the treatment. Thereafter, the pedestal can be repositioned to temporarily secure the bundle in a new location. The bed can be moved to perform medical treatment in a new location. These operations may be repeated as defined by a medical plan drafted for use with the particle therapy system.

粒子治療系統10可係一經強度調變質子治療(IMPT)系統。IMPT系統能夠對可具有可變能量及/或強度之受限制質子束進行空間控制。IMPT利用帶電粒子布拉格峰(如所提及，粒子之遞送範圍之端處之劑量特徵峰)結合粒子束變數之調變來建立標靶局部劑量調變，以達成一預定義醫療計劃中所陳述之目標。IMPT可涉及以不同角度且以不同強度將粒子束朝向輻照標靶引導以醫療標靶。此可藉由控制向量磁體將粒子束引導至兩個或更多個不同彎曲磁體來完成。在某些實施方案中，粒子束可跨越輻照標靶之層進行掃描(例如，移動)，其中自相同或不同角度一或多次 對每一層進行治療。可使用本文中所闡述之掃描磁體來執行跨越輻照標靶之移動以實施掃描。 The particle therapy system 10 can be an intensity modulated proton therapy (IMPT) system. An IMPT system is capable of spatially controlling a confined proton beam that can have variable energy and/or intensity. IMPT utilizes charged particle Bragg peaks (as mentioned, dose characteristic peaks at the ends of the particle's delivery range) combined with modulation of particle beam variables to establish targeted local dose modulation to achieve the goals stated in a predefined treatment plan. IMPT can involve directing a particle beam toward an irradiated target at different angles and at different intensities to treat the target. This can be accomplished by directing the particle beam to two or more different bending magnets by controlling a vector magnet. In some embodiments, the particle beam can be scanned (e.g., moved) across layers of an irradiation target, wherein each layer is treated one or more times from the same or different angles. The movement across the irradiation target to perform the scan can be performed using a scanning magnet as described herein.

參考圖10，一或多個成像裝置可在檯座14內部內(如所展示)或檯座14外部上(未展示)安裝至檯座14。可在醫療之前及/或期間進行成像，以識別患者體內之一標靶位置並控制檯座及掃描之操作，以便將粒子束引導至患者體內之輻照標靶。 Referring to FIG. 10 , one or more imaging devices may be mounted to the pedestal 14 within the interior of the pedestal 14 (as shown) or on the exterior of the pedestal 14 (not shown). Imaging can be performed before and/or during medical treatment to identify the location of a target within the patient's body and to control the operation of the stand and scan to direct the particle beam to the irradiation target within the patient's body.

成像裝置可包含但不限於一或多個電腦斷層造影(CT)系統、一或多個扇形束CT系統、一或多個放射照相系統及諸如此類。成像系統可經組態並經控制以圍繞檯座14旋轉或者隨著檯座14之旋轉而旋轉。就此而言，如所提及，一或多個噴嘴可在位於檯座之內部直徑處之一環45上旋轉。各種二維(2D)及/或三維(3D)成像裝置亦可安裝在環45上，以與其一起旋轉。在某些實施方案中，噴嘴及成像裝置可安裝至檯座內之不同內部圓周軌道。舉例而言，噴嘴可在環形結構之一第一半徑處圍繞一圓周軌道旋轉，並且成像裝置可在環形結構的不同於該第一半徑之一第二半徑處圍繞一不同圓周軌道旋轉。在某些實施方案中，檯座可包含不同可旋轉內環，其之一者安裝用於旋轉之噴嘴，且其之一者安裝用於旋轉之成像裝置或系統。 Imaging devices may include, but are not limited to, one or more computed tomography (CT) systems, one or more fan-beam CT systems, one or more radiography systems, and the like. The imaging system may be configured and controlled to rotate about or as the pedestal 14 rotates. In this regard, as mentioned, one or more nozzles may rotate on a ring 45 located at the inner diameter of the pedestal. Various two-dimensional (2D) and/or three-dimensional (3D) imaging devices may also be mounted on ring 45 for rotation therewith. In certain embodiments, the nozzle and imaging device can be mounted to different internal circumferential tracks within the pedestal. For example, the nozzle may rotate about a circular orbit at a first radius of the annular structure, and the imaging device may rotate about a different circular orbit at a second radius of the annular structure that is different from the first radius. In certain embodiments, the pedestal may include different rotatable inner rings, one of which is mounted for rotating the nozzle and one of which is mounted for rotating the imaging device or system.

在圖10之實例中，正交2D成像之兩個平面70、71經展示供用於2D影像導引之放射治療(IGRT)，或者可經旋轉用於錐形束電腦斷層造影系統(CBCT)獲取，包含同時獲取之雙能量成像。就此而言，IGRT包含在輻射醫療期間使用成像來改良醫療遞送之精度及準確度。IGRT可用於醫療身體之活動區域之腫瘤，諸如肺。成像裝置亦可或另一選擇係包含一X射線源以及用於CBCT獲取裝置73或一扇形束診斷品質電腦斷層造影 (CT)裝置74之一影像面板。另一選擇係，一個平面可包含一CBCT，並且另一平面可包含扇形束診斷品質CT。 In the example of FIG. 10 , two planes 70, 71 of orthogonal 2D imaging are shown for use in 2D image guided radiation therapy (IGRT) or may be rotated for cone beam computed tomography (CBCT) acquisition, including dual energy imaging acquired simultaneously. In this regard, IGRT includes the use of imaging during radiation therapy to improve the precision and accuracy of therapy delivery. IGRT may be used to treat tumors in active areas of the body, such as the lungs. The imaging device may also or alternatively include an x-ray source and an image panel for a CBCT acquisition device 73 or a fan beam diagnostic quality computed tomography (CT) device 74. Alternatively, one plane may contain a CBCT and the other plane may contain a fan beam diagnostic quality CT.

在某些實施方案中，控制系統34可協調噴嘴38以及成像系統70、71、73、74之旋轉，使得成像系統在醫療期間不妨礙噴嘴及輸出通道，並且使得噴嘴及輸出通道在醫療期間不妨礙成像系統。在某些實施方案中，成像系統可安裝至檯座14上與噴嘴分隔之軌道。分隔安裝可減少噴嘴與成像裝置或系統之間干涉或碰撞之機會。在某些實施方案中，成像系統可安裝至與噴嘴相同之可旋轉環45。此種安裝可減少噴嘴與成像裝置或系統之間干涉或碰撞之機會。 In some embodiments, the control system 34 can coordinate the rotation of the nozzle 38 and the imaging system 70, 71, 73, 74 so that the imaging system does not interfere with the nozzle and output channel during medical treatment, and the nozzle and output channel do not interfere with the imaging system during medical treatment. In some embodiments, the imaging system can be mounted to a track on the table 14 that is separated from the nozzle. The separated mounting can reduce the chance of interference or collision between the nozzle and the imaging device or system. In some embodiments, the imaging system can be mounted to the same rotatable ring 45 as the nozzle. Such mounting can reduce the chance of interference or collision between the nozzle and the imaging device or system.

如先前所解釋，本文中所闡述之噴嘴中之每一者及成像裝置或系統中之某些可位於環形檯座之外殼內。安裝在外殼內可使得彼等裝置能夠以比外部安裝大之速度旋轉。此乃因內部安裝之裝置比外部安裝之裝置對患者及周圍設備之危險更小。舉例而言，某些外部安裝之裝置被限制在每分鐘一(1)轉(RPM)之旋轉速度。然而，內部安裝之組件可以諸如高達240RPM之更大速率旋轉。 As previously explained, each of the nozzles and certain of the imaging devices or systems described herein may be located within a housing outside of the annular stand. Mounting within the housing allows the devices to rotate at greater speeds than external mounting. This is because internally mounted devices are less dangerous to the patient and surrounding equipment than externally mounted devices. For example, certain externally mounted devices are limited to a rotational speed of one (1) revolution per minute (RPM). However, internally mounted components may rotate at greater rates, such as up to 240 RPM.

如本文中所闡述，一實例性質子治療系統使一質子束在三個維度上跨越一輻照標靶而進行掃描，以便破壞惡性組織。圖11展示可用於在質子治療系統中提供質子束之一實例性超導同步迴旋加速器之組件75之一橫截面。在此實例中，組件75包含一超導磁體77。超導磁體包含超導線圈78及79。超導線圈由多個積體導體形成，其之每一者包含纏繞在一中心絞合線周圍之超導絞合線，諸如四個絞合線或六個絞合線，該中心絞合線本身可係超導或非超導的。超導線圈78、79中之每一者用於傳導產生一磁場(B)之一電流。磁軛80、81或更小磁極片在粒子被加速之一腔 84中對彼磁場進行塑形。在一實例中，一低溫恒溫器(未展示)使用液氦(He)將每一線圈傳導地冷卻至超導溫度，例如，大約4克耳文(K)。 As described herein, one example proton therapy system scans a proton beam in three dimensions across an irradiation target to destroy malignant tissue. Figure 11 shows a cross-section of an assembly 75 of an example superconducting synchrocyclotron that may be used to provide a proton beam in a proton therapy system. In this example, assembly 75 includes a superconducting magnet 77 . The superconducting magnet includes superconducting coils 78 and 79 . A superconducting coil is formed from a plurality of integrated conductors, each of which includes a superconducting strand, such as four strands or six strands, wound around a central strand It can itself be superconducting or non-superconducting. Each of the superconducting coils 78, 79 is used to conduct an electric current that generates a magnetic field (B). Magnetic yokes 80, 81 or smaller pole pieces are used in a cavity where particles are accelerated 84 to shape the magnetic field. In one example, a cryostat (not shown) uses liquid helium (He) to conductively cool each coil to superconducting temperatures, for example, about 4 Kelvin (K).

在某些實施方案中，粒子加速器包含一粒子源85，諸如一潘甯離子計(PIG)源，以將一離子化電漿柱提供給腔84。氫氣或者氫氣與一稀有氣體之一組合經離子化以產生電漿柱。一電壓源將一變化之射頻(RF)電壓提供給腔84，以使腔內來自電漿柱之粒子加速。如所提及，在一實例中，粒子加速器係一同步迴旋加速器。因此，當在加速腔內加速粒子時，RF電壓跨越一頻率範圍進行掃掠以計及粒子上之相對論效應，諸如增加粒子質量。RF電壓驅動含納於腔內之一D形極板，且具有在加速週期期間向下掃掠之一頻率，以計及質子之相對論質量增加及磁場減小。一虛設D形極板充當D形極板之一接地參考。藉由使電流運行通過超導線圈所產生之磁場與掃掠RF電壓一起致使來自電漿柱之粒子在腔內沿軌道加速，並隨著匝之一數目之增加而增加能量。 In certain embodiments, the particle accelerator includes a particle source 85, such as a Penning Ion Gauge (PIG) source, to provide a column of ionizing plasma to the chamber 84. Hydrogen or a combination of hydrogen and a noble gas is ionized to create a plasma column. A voltage source provides a varying radio frequency (RF) voltage to the cavity 84 to accelerate particles from the plasma column within the cavity. As mentioned, in one example, the particle accelerator is a synchrocyclotron. Therefore, when a particle is accelerated within an accelerating cavity, the RF voltage is swept across a range of frequencies to account for relativistic effects on the particle, such as increasing particle mass. The RF voltage drives a D-shaped plate contained within the cavity and has a frequency that sweeps downward during the acceleration cycle to account for the increase in the relativistic mass of the proton and the decrease in the magnetic field. A dummy D-shaped plate serves as the ground reference for one of the D-shaped plates. The magnetic field generated by running an electric current through the superconducting coil, together with the swept RF voltage, causes particles from the plasma column to accelerate along orbits within the cavity, increasing energy as the number of turns increases.

腔中之磁場經塑形以致使粒子在腔內沿軌道移動。實例性同步迴旋加速器採用旋轉角度均勻且強度隨半徑增加而下降之一磁場。在某些實施方案中，由超導(主)線圈產生之最大磁場在腔之一中心處可在3特士拉(T)至20T之範圍中，該磁場隨半徑增加而下降。舉例而言，超導線圈可用於產生處於或超過以下量值中之一或多者下之磁場：3.0T、3.1T、3.2T、3.3T、3.4T、3.5T、3.6T、3.7T、3.8T、3.9T、4.0T、4.1T、4.2T、4.3T、4.4T、4.5T、4.6T、4.7T、4.8T、4.9T、5.0T、5.1T、5.2T、5.3T、5.4T、5.5T、5.6T、5.7T、5.8T、5.9T、6.0T、6.1T、6.2T、6.3T、6.4T、6.5T、6.6T、6.7T、6.8T、6.9T、7.0T、7.1T、7.2T、7.3T、7.4T、7.5T、7.6T、7.7T、7.8T、 7.9T、8.0T、8.1T、8.2T、8.3T、8.4T、8.5T、8.6T、8.7T、8.8T、8.9T、9.0T、9.1T、9.2T、9.3T、9.4T、9.5T、9.6T、9.7T、9.8T、9.9T、10.0T、10.1T、10.2T、10.3T、10.4T、10.5T、10.6T、10.7T、10.8T、10.9T、11.0T、11.1T、11.2T、11.3T、11.4T、11.5T、11.6T、11.7T、11.8T、11.9T、12.0T、12.1T、12.2T、12.3T、12.4T、12.5T、12.6T、12.7T、12.8T、12.9T、13.0T、13.1T、13.2T、13.3T、13.4T、13.5T、13.6T、13.7T、13.8T、13.9T、14.0T、14.1T、14.2T、14.3T、14.4T、14.5T、14.6T、14.7T、14.8T、14.9T、15.0T、15.1T、15.2T、15.3T、15.4T、15.5T、15.6T、15.7T、15.8T、15.9T、16.0T、16.1T、16.2T、16.3T、16.4T、16.5T、16.6T、16.7T、16.8T、16.9T、17.0T、17.1T、17.2T、17.3T、17.4T、17.5T、17.6T、17.7T、17.8T、17.9T、18.0T、18.1T、18.2T、18.3T、18.4T、18.5T、18.6T、18.7T、18.8T、18.9T、19.0T、19.1T、19.2T、19.3T、19.4T、19.5T、19.6T、19.7T、19.8T、19.9T、20.0T、20.1T、20.2T、20.3T、20.4T、20.5T、20.6T、20.7T、20.8T、20.9T或更大。此外，超導線圈可用於產生在3T至20T之範圍之外或者在3T至20T範圍內但本文中未具體列出之磁場。 The magnetic field in the cavity is shaped so that the particles move along orbits within the cavity. An example synchrocyclotron uses a magnetic field whose rotation angle is uniform and whose intensity decreases with increasing radius. In certain embodiments, the maximum magnetic field generated by the superconducting (main) coil may be in the range of 3 Tesla (T) to 20 T at the center of one of the cavities, with the magnetic field decreasing as the radius increases. For example, superconducting coils can be used to generate magnetic fields at or above one or more of the following magnitudes: 3.0T, 3.1T, 3.2T, 3.3T, 3.4T, 3.5T, 3.6T, 3.7T, 3.8T, 3.9T, 4.0T, 4.1T, 4.2T, 4.3T, 4.4T, 4.5T, 4.6T, 4.7T, 4.8T, 4.9T, 5.0T, 5.1T, 5.2T, 5.3T, 5.4T , 5.5T, 5.6T, 5.7T, 5.8T, 5.9T, 6.0T, 6.1T, 6.2T, 6.3T, 6.4T, 6.5T, 6.6T, 6.7T, 6.8T, 6.9T, 7.0T, 7.1 T, 7.2T, 7.3T, 7.4T, 7.5T, 7.6T, 7.7T, 7.8T, 7.9T, 8.0T, 8.1T, 8.2T, 8.3T, 8.4T, 8.5T, 8.6T, 8.7T, 8.8T, 8.9T, 9.0T, 9.1T, 9.2T, 9.3T, 9.4T, 9.5T , 9.6T, 9.7T, 9.8T, 9.9T, 10.0T, 10.1T, 10.2T, 10.3T, 10.4T, 10.5T, 10.6T, 10.7T, 10.8T, 10.9T, 11.0T, 11.1T, 11.2 T, 11.3T, 11.4T, 11.5T, 11.6T, 11.7T, 11.8T, 11.9T, 12.0T, 12.1T, 12.2T, 12.3T, 12.4T, 12.5T, 12.6T, 12.7T, 12.8T, 12.9T, 13.0T, 13.1T, 13.2T, 13.3T, 13.4T, 13.5T, 13.6T, 13.7T, 13.8T, 13.9T, 14.0T, 14.1T, 14.2T, 14.3T, 14.4T, 14.5T , 14.6T, 14.7T, 14.8T, 14.9T, 15.0T, 15.1T, 15.2T, 15.3T, 15.4T, 15.5T, 15.6T, 15.7T, 15.8T, 15.9T, 16.0T, 16.1T, 16.2 T, 16.3T, 16.4T, 16.5T, 16.6T, 16.7T, 16.8T, 16.9T, 17.0T, 17.1T, 17.2T, 17.3T, 17.4T, 17.5T, 17.6T, 17.7T, 17.8T, 17.9T, 18.0T, 18.1T, 18.2T, 18.3T, 18.4T, 18.5T, 18.6T, 18.7T, 18.8T, 18.9T, 19.0T, 19.1T, 19.2T, 19.3T, 19.4T, 19.5T , 19.6T, 19.7T, 19.8T, 19.9T, 20.0T, 20.1T, 20.2T, 20.3T, 20.4T, 20.5T, 20.6T, 20.7T, 20.8T, 20.9T or larger. Additionally, superconducting coils may be used to generate magnetic fields outside the range of 3T to 20T or within the range of 3T to 20T but not specifically listed herein.

在某些實施方案(諸如圖11中所展示之實施方案)中，相對大之鐵磁磁軛80、81充當由超導線圈產生之雜散磁場之磁返回。在某些系統中，一磁屏蔽件(未展示)環繞軛。返回軛與屏蔽件一起用於減少雜散磁場，藉此減少雜散磁場對粒子加速器之操作產生不利影響之可能性。 In some embodiments, such as the one shown in FIG. 11 , relatively large ferromagnetic yokes 80, 81 act as magnetic returns for stray magnetic fields generated by the superconducting coils. In some systems, a magnetic shield (not shown) surrounds the yokes. The return yokes and shields are used together to reduce stray magnetic fields, thereby reducing the likelihood that stray magnetic fields will adversely affect the operation of the particle accelerator.

在某些實施方案中，返回軛及屏蔽件可被一主動返回系統 替換或遞增。一實例性主動返回系統包含在與通過主超導線圈之電流相反之一方向上傳導電流的一或多個主動返回線圈。在某些實例性實施方案中，對於每一超導主線圈，存在一主動返回線圈，例如，兩個主動返回線圈，每一主超導線圈一個。每一主動返回線圈亦可係同心地環繞一對應主超導線圈外部之一超導線圈。藉由使用一主動返回系統，相對大之鐵磁磁軛80、81可用更小且更輕之磁極片替換。因此，可在不犧牲效能的情況下進一步減小同步迴旋加速器之大小及重量。可使用之一主動返回系統之一實例闡述於標題為「Active Return System」之美國專利第8,791,656(Zwart)號中。美國專利第8,791,656號之內容(尤其與返回線圈組態相關之內容(例如，美國專利第8,791,656號之圖2、圖4及圖5以及隨附闡述))以引用方式併入本文中。 In some embodiments, the return yoke and shield may be replaced or augmented by an active return system. An exemplary active return system includes one or more active return coils that conduct current in a direction opposite to the current through the main superconducting coils. In some exemplary embodiments, there is an active return coil for each superconducting main coil, for example, two active return coils, one for each main superconducting coil. Each active return coil may also be a superconducting coil that concentrically surrounds the outside of a corresponding main superconducting coil. By using an active return system, the relatively large ferromagnetic yokes 80, 81 may be replaced with smaller and lighter pole pieces. Thus, the size and weight of the synchrocyclotron may be further reduced without sacrificing performance. An example of an active return system that may be used is described in U.S. Patent No. 8,791,656 (Zwart), entitled "Active Return System." The contents of U.S. Patent No. 8,791,656, particularly those relating to the return coil configuration (e.g., FIGS. 2, 4, and 5 of U.S. Patent No. 8,791,656 and the accompanying description), are incorporated herein by reference.

可用於本文中之粒子治療系統之一粒子加速器之另一實例闡述於標題為「Ultra-Light Magnetically Shielded High-Current,Compact Cyclotron」之美國專利第8,975,836(Bromberg)號中。美國專利第8,975,836號之內容(尤其與美國專利第8,975,836號之圖4、圖17及18中之「迴旋加速器11」或「無鐵迴旋加速器11」相關之內容以及隨附闡述)以引用方式併入本文中。 Another example of a particle accelerator that can be used in the particle therapy system described herein is described in U.S. Patent No. 8,975,836 (Bromberg), entitled "Ultra-Light Magnetically Shielded High-Current, Compact Cyclotron". The contents of U.S. Patent No. 8,975,836 (particularly the contents related to "cyclotron 11" or "iron-free cyclotron 11" in Figures 4, 17 and 18 of U.S. Patent No. 8,975,836 and the accompanying description) are incorporated herein by reference.

在某些實施方案中，本文中所闡述之質子治療系統中所使用之同步迴旋加速器可係一可變能量同步迴旋加速器。在某些實施方案中，一可變能量同步迴旋加速器經組態以藉由使粒子束在其中被加速之磁場變化來使輸出粒子束之能量變化。舉例而言，可將電流設定為多個值中之任一者來產生一對應磁場。舉例而言，可將電流設定為兩個值中之一者來產生先前所闡述之雙能量粒子加速器。在一實例性實施方案中，一組或 多組超導線圈接收可變電流，以在腔中產生一可變磁場。在某些實例中，一組線圈接收一固定電流，而一組或多組其他線圈接收一可變電流，使得線圈組所接收之總電流變化。在某些實施方案中，所有組線圈皆係超導的。在某些實施方案中，某些組線圈(諸如用於固定電流之一組線圈)係超導的，而其他組線圈(諸如用於可變電流之一組或多組線圈)係非超導(例如，銅)線圈。 In certain embodiments, the synchrocyclotron used in the proton therapy systems described herein may be a variable energy synchrocyclotron. In certain embodiments, a variable energy synchrocyclotron is configured to vary the energy of an output particle beam by varying the magnetic field in which the particle beam is accelerated. For example, the current can be set to any of a plurality of values to generate a corresponding magnetic field. For example, the current can be set to one of two values to create the dual energy particle accelerator described previously. In an exemplary embodiment, a group or Multiple sets of superconducting coils receive variable current to generate a variable magnetic field in the cavity. In some examples, one set of coils receives a fixed current and one or more other sets of coils receives a variable current, such that the total current received by the set of coils varies. In certain embodiments, all sets of coils are superconducting. In certain embodiments, certain sets of coils, such as one for a fixed current, are superconducting, while other sets of coils, such as one or more sets of coils for a variable current, are non-superconducting. (e.g. copper) coil.

一般而言，在一可變能量同步迴旋加速器中，磁場之量值可隨電流之量值而按比例縮放。在一預定範圍中調整線圈之總電流可產生在一對應預定範圍中變化之一磁場。在某些實例中，電流之一連續調整可導致磁場之一連續變化以及輸出束能量之一連續變化。另一選擇係，當以一不連續逐步方式調整施加至線圈之電流時，磁場及輸出束能量亦相應地以一不連續(逐步)方式變化。逐步調整可產生先前所闡述之雙能量。在某些實施方案中，每一步長係在10MeV與80MeV之間。磁場對電流之縮放可允許相對精確地實行束能量之變化，因此減少對能量降級器之需要。可用於本文中所闡述之粒子治療系統之一可變能量同步迴旋加速器之一實例闡述於標題為「Particle Accelerator That Produces Charged Particles Having Variable Energies」之美國專利第9,730,308號中。美國專利第9,730,308號之內容(尤其使得一同步迴旋加速器能夠在可變能量下操作之內容(包含美國專利第9,730,308號之第5欄至第7欄中及圖13所闡述之內容以及其隨附闡述))以引用方式併入本文中。 Generally speaking, in a variable energy synchrocyclotron, the magnitude of the magnetic field can be scaled proportionally with the magnitude of the current. Adjusting the total current of the coil within a predetermined range can produce a magnetic field that varies within a corresponding predetermined range. In some examples, a continuous adjustment of the current can result in a continuous change in the magnetic field and a continuous change in the output beam energy. Another option is that when the current applied to the coil is adjusted in a discontinuous step-by-step manner, the magnetic field and the output beam energy also change accordingly in a discontinuous (step-by-step) manner. The step-by-step adjustment can produce the dual energy previously described. In some embodiments, each step size is between 10MeV and 80MeV. Scaling of the magnetic field to the current allows relatively precise implementation of changes in beam energy, thereby reducing the need for energy degraders. An example of a variable energy synchrocyclotron that can be used in the particle therapy system described herein is described in U.S. Patent No. 9,730,308 entitled "Particle Accelerator That Produces Charged Particles Having Variable Energies". The contents of U.S. Patent No. 9,730,308 (particularly the contents that enable a synchrocyclotron to operate at variable energy (including the contents described in columns 5 to 7 of U.S. Patent No. 9,730,308 and Figure 13 and the accompanying descriptions)) are incorporated herein by reference.

在使用一可變能量同步迴旋加速器之粒子治療系統之實施方案中，藉由改變由同步迴旋加速器輸出之粒子束之能量，可根據醫療計劃來執行控制粒子束之能量來醫療輻照標靶之一部分。在此類實施方案 中，可使用或可不使用一範圍移位器。舉例而言，控制粒子束之能量可包含將同步迴旋加速器主線圈中之電流設定為多個值中之一者，每一值對應於粒子束自同步迴旋加速器輸出之一不同能量。一範圍移位器可連同一可變能量同步迴旋加速器一起使用，以例如在由同步迴旋加速器提供之離散能階之間提供額外能量改變。 In an embodiment of a particle therapy system using a variable energy synchrocyclotron, by changing the energy of the particle beam output by the synchrocyclotron, the energy of the particle beam can be controlled according to the medical plan to treat the irradiation target. part. In such implementations , a range shifter may or may not be used. For example, controlling the energy of the particle beam may include setting the current in the main coil of the synchrocyclotron to one of a plurality of values, each value corresponding to a different energy of the particle beam output from the synchrocyclotron. A range shifter may be used in conjunction with a variable energy synchrocyclotron to provide additional energy changes, for example, between discrete energy levels provided by the synchrocyclotron.

本文中所闡述之系統及其變體可用於將超高劑量率之輻射(所謂「FLASH」劑量率之輻射)施加至一患者體內之一輻照標靶。就此而言，輻射治療之實驗結果已展示，當在超高(FLASH)劑量率下遞送醫療劑量時，經受輻射之健康組織之狀況得到改良。在一實例中，當以小於500毫秒(ms)之脈衝遞送在10戈至20戈(Gy)之輻射劑量達到20戈每秒(Gy/S)至100戈每秒(Gy/S)之有效劑量率時，健康組織比在一更長時間尺度上用相同劑量輻照時經受更少損傷，而腫瘤以類似有效性得到醫療。一種可解釋此「FLASH效應」之理論係基於以下事實，即組織之輻射損傷與組織中之氧供應成比例。在健康組織中，超高劑量率僅使氧自由基化一次，此與在一更長時間尺度內多次使氧自由基化之劑量應用相反。此可使用超高劑量率來導致健康組織之損傷更小。 The systems and variations thereof described herein can be used to apply ultra-high dose rates of radiation (so-called "FLASH" dose rates of radiation) to an irradiation target within a patient. In this regard, experimental results of radiation therapy have shown that when a therapeutic dose is delivered at ultra-high (FLASH) dose rates, the condition of healthy tissue subjected to the radiation is improved. In one example, when radiation doses between 10 and 20 Gy are delivered in pulses of less than 500 milliseconds (ms) to achieve effective dose rates of 20 Gy/S to 100 Gy/S, healthy tissues sustain less damage than when irradiated with the same dose over a longer time scale, while tumors are treated with similar effectiveness. One theory that may explain this "FLASH effect" is based on the fact that radiation damage to tissue is proportional to the oxygen supply in the tissue. In healthy tissue, ultra-high dose rates radicalize oxygen only once, as opposed to dose application over a longer time scale that radicalizes oxygen multiple times. This allows for ultra-high dosing rates resulting in less damage to healthy tissue.

在某些實例中，如上文所提及，超高劑量率之輻射可包含在小於500ms之一持續時間內超過1戈每秒之輻射劑量。在某些實例中，超高劑量率之輻射可包含在10ms與5s之間的一持續時間內超過1戈每秒之輻射劑量。在某些實例中，超高劑量率之輻射可包含在小於5s之一持續時間內超過1戈每秒之輻射劑量。 In some examples, as mentioned above, ultra-high dose rate radiation may include a radiation dose in excess of 1 Gy per second for a duration of less than 500 ms. In some examples, ultra-high dose rate radiation may include radiation doses in excess of 1 Gy per second for a duration between 10 ms and 5 s. In some examples, ultra-high dose rate radiation may include a radiation dose in excess of 1 Gy per second for a duration of less than 5 s.

在某些實例中，超高劑量率之輻射包含在小於500ms之一持續時間內超過以下劑量中之一者之輻射劑量：2戈每秒、3戈每秒、4戈 每秒、5戈每秒、6戈每秒、7戈每秒、8戈每秒、9戈每秒、10戈每秒、11戈每秒、12戈每秒、13戈每秒、14戈每秒、15戈每秒、16戈每秒、17戈每秒、18戈每秒、19戈每秒、20戈每秒、30戈每秒、40戈每秒、50戈每秒、60戈每秒、70戈每秒、80戈每秒、90戈每秒或100戈每秒。在某些實例中，超高劑量率之輻射包含在10ms與5s之間的一持續時間內超過以下劑量中之一者之輻射劑量：2戈每秒、3戈每秒、4戈每秒、5戈每秒、6戈每秒、7戈每秒、8戈每秒、9戈每秒、10戈每秒、11戈每秒、12戈每秒、13戈每秒、14戈每秒、15戈每秒、16戈每秒、17戈每秒、18戈每秒、19戈每秒、20戈每秒、30戈每秒、40戈每秒、50戈每秒、60戈每秒、70戈每秒、80戈每秒、90戈每秒或100戈每秒。在某些實例中，超高劑量率之輻射包含在小於5s之一持續時間內超過以下劑量中之一者之輻射劑量：2戈每秒、3戈每秒、4戈每秒、5戈每秒、6戈每秒、7戈每秒、8戈每秒、9戈每秒、10戈每秒、11戈每秒、12戈每秒、13戈每秒、14戈每秒、15戈每秒、16戈每秒、17戈每秒、18戈每秒、19戈每秒、20戈每秒、30戈每秒、40戈每秒、50戈每秒、60戈每秒、70戈每秒、80戈每秒、90戈每秒或100戈每秒。 In some instances, ultra-high dose rate radiation includes a radiation dose that exceeds one of the following doses for a duration of less than 500 ms: 2 Gy per second, 3 Gy per second, or 4 Gy. per second, 5 Ge per second, 6 Ge per second, 7 Ge per second, 8 Ge per second, 9 Ge per second, 10 Ge per second, 11 Ge per second, 12 Ge per second, 13 Ge per second, 14 Ge per second per second, 15 Ge per second, 16 Ge per second, 17 Ge per second, 18 Ge per second, 19 Ge per second, 20 Ge per second, 30 Ge per second, 40 Ge per second, 50 Ge per second, 60 Ge per second per second, 70 Ge per second, 80 Ge per second, 90 Ge per second or 100 Ge per second. In some instances, ultra-high dose rate radiation includes a radiation dose that exceeds one of the following doses for a duration between 10 ms and 5 s: 2 Gy per second, 3 Gy per second, 4 Gy per second, 5 Ge per second, 6 Ge per second, 7 Ge per second, 8 Ge per second, 9 Ge per second, 10 Ge per second, 11 Ge per second, 12 Ge per second, 13 Ge per second, 14 Ge per second, 15 Ge per second, 16 Ge per second, 17 Ge per second, 18 Ge per second, 19 Ge per second, 20 Ge per second, 30 Ge per second, 40 Ge per second, 50 Ge per second, 60 Ge per second, 70 Geps, 80 Geps, 90 Geps or 100 Geps. In some instances, ultra-high dose rate radiation includes radiation doses exceeding one of the following for a duration of less than 5 s: 2 Gy per second, 3 Gy per second, 4 Gy per second, 5 Gy per second second, 6 Ge per second, 7 Ge per second, 8 Ge per second, 9 Ge per second, 10 Ge per second, 11 Ge per second, 12 Ge per second, 13 Ge per second, 14 Ge per second, 15 Ge per second second, 16 Ge per second, 17 Ge per second, 18 Ge per second, 19 Ge per second, 20 Ge per second, 30 Ge per second, 40 Ge per second, 50 Ge per second, 60 Ge per second, 70 Ge per second seconds, 80 Geps, 90 Geps or 100 Geps.

在某些實例中，超高劑量率之輻射包含在小於500ms之一持續時間內、在10ms與5s之間的一持續時間內或者在小於5s之一持續時間內超過以下劑量中之一或多者之輻射劑量：100戈每秒、200戈每秒、300戈每秒、400戈每秒或500戈每秒。 In some embodiments, ultra-high dose rate radiation includes radiation doses exceeding one or more of the following doses within a duration of less than 500 ms, within a duration between 10 ms and 5 s, or within a duration of less than 5 s: 100 Ge per second, 200 Ge per second, 300 Ge per second, 400 Ge per second, or 500 Ge per second.

在某些實例中，超高劑量率之輻射包含在小於500ms之一持續時間內介於20戈每秒與100戈每秒之間的輻射劑量。在某些實例中，超高劑量率之輻射包含在10ms與5s之間的一持續時間內介於20戈每秒與 100戈每秒之間的輻射劑量。在某些實例中，超高劑量率之輻射包含在小於5s之一持續時間內介於20戈每秒與100戈每秒之間的輻射劑量。在某些實例中，超高劑量率之輻射包含在諸如小於5s之一時間週期內介於40戈每秒與120戈每秒之間的輻射劑量。時間週期之其他實例係上文所提供之彼等實例。 In some embodiments, the ultra-high dose rate radiation comprises a radiation dose of between 20 and 100 Ge per second over a duration of less than 500 ms. In some embodiments, the ultra-high dose rate radiation comprises a radiation dose of between 20 and 100 Ge per second over a duration of between 10 ms and 5 s. In some embodiments, the ultra-high dose rate radiation comprises a radiation dose of between 20 and 100 Ge per second over a duration of less than 5 s. In some embodiments, the ultra-high dose rate radiation comprises a radiation dose of between 40 and 120 Ge per second over a time period of, for example, less than 5 s. Other examples of time periods are those provided above.

在某些實施方案中，粒子治療系統可使用超高劑量率輻射(FLASH輻射劑量)來醫療標靶之三維柱。此等系統使用鉛筆形束掃描來縮放遞送給標靶之超高劑量率。在某些實例中，鉛筆形束掃描包含遞送一系列粒子輻射之小束，每一小束可具有一唯一方向、能量及電荷。藉由組合來自此等個別束之劑量，可利用輻射來醫療一個三維標靶醫療體積。此外，系統不是以恆定能量將醫療組織成層，而是將醫療組織成由一靜止束之方向界定之柱。束之方向可朝向標靶之表面。 In some embodiments, particle therapy systems can use ultra-high dose rate radiation (FLASH radiation dose) to treat a three-dimensional column of a target. These systems use pencil beam scanning to scale the ultra-high dose rate delivered to the target. In some instances, pencil beam scanning involves delivering a series of small beams of particle radiation, each of which can have a unique direction, energy, and charge. By combining the doses from these individual beams, a three-dimensional targeted treatment volume can be treated with radiation. In addition, rather than organizing treatment into layers at a constant energy, the system organizes treatment into columns defined by the direction of a static beam. The direction of the beam can be toward the surface of the target.

在某些實施方案中，在粒子束沿著另一路徑被引導穿過輻照標靶之前，對一柱之全部或部分進行醫療。在某些實施方案中，穿過標靶之一路徑係穿過標靶之全部或部分通路。在一實例中，粒子束可沿著穿過標靶之一路徑引導，且不偏離彼路徑。當沿著彼路徑被引導時，粒子束之能量發生改變。粒子束不會隨著其能量之改變而移動，因此，粒子束醫療沿著粒子束之一長度並沿著束斑之一寬度延伸的標靶之一內部部分之全部或一部分。因此，醫療係沿著束之一縱向方向在深度方向上進行的。舉例而言，所醫療之標靶之一部分可自標靶之表面處束之一斑向下延伸穿過標靶之一內部之全部或一部分。結果係粒子束使用超高劑量率之輻射來醫療標靶之一個三維柱狀部分。在某些實例中，粒子束可能不再沿著同一三維柱狀部分被引導一次以上。 In some embodiments, all or part of a column is treated before the particle beam is directed along another path through the irradiation target. In some embodiments, a path through the target is a passage through all or part of the target. In one example, the particle beam can be directed along a path through the target without deviating from the path. The energy of the particle beam changes while being directed along the path. The particle beam does not move as its energy changes, and therefore, the particle beam treats all or part of an interior portion of the target extending along a length of the particle beam and along a width of the beam spot. Therefore, treatment is performed in a depth direction along a longitudinal direction of the beam. For example, a portion of the target being treated can extend from a spot of the beam at the surface of the target downward through all or part of an interior of the target. The result is a particle beam that treats a three-dimensional cylindrical portion of the target using an extremely high dose rate of radiation. In some instances, the particle beam may not be directed more than once along the same three-dimensional cylindrical portion.

在某些實施方案中，一輻照標靶可被***成微體積。儘管可使用立方體微體積，但微體積可具有任何適當形狀，諸如三維棱正交的多胞形、規則彎曲之形狀或者無定形形狀。在此實例中，藉由以本文中所闡述之方式由柱遞送FLASH輻射來醫療每一微體積。舉例而言，可藉由使用能量降級板來改變束能量或者藉由控制一可變能量同步迴旋加速器來改變束能量，利用輻射來醫療一微體積之柱深度。在一個別微體積得到醫療之後，下一微體積得到醫療，等等，直至整個輻照標靶得到醫療為止。可以任何適當次序或序列進行對微體積之醫療。 In certain embodiments, an irradiated target can be broken into microvolumes. Although cubic microvolumes may be used, the microvolumes may have any suitable shape, such as a three-dimensional orthogonal polytope, a regularly curved shape, or an amorphous shape. In this example, each microvolume is treated by delivering FLASH radiation from the column in the manner described herein. For example, radiation can be used to treat a microvolume column depth by using energy degradation plates to vary the beam energy or by controlling a variable energy synchrocyclotron to vary the beam energy. After an individual microvolume is treated, the next microvolume is treated, and so on, until the entire irradiated target is treated. Treatment of microvolumes may be performed in any suitable order or sequence.

本文中所闡述之粒子治療系統可以標題為「Delivery Of Radiation By Column And Generating A Treatment Plan Therefor」之美國專利公開案第2020/0298025號中所闡述之方式藉由柱來遞送FLASH輻射，該美國公開案之內容(尤其與圖2、圖11、圖12至圖19、圖33至圖43B及其隨附闡述相關之內容)以引用方式併入本文中。 The particle therapy system described herein can deliver FLASH radiation through columns in the manner described in U.S. Patent Publication No. 2020/0298025 entitled "Delivery Of Radiation By Column And Generating A Treatment Plan Therefor" The contents of this document (especially those related to Figures 2, 11, 12 to 19, 33 to 43B and their accompanying explanations) are incorporated herein by reference.

在某些實施方案中，除了一同步迴旋加速器之外的一粒子加速器可用於本文中所闡述之粒子治療系統中。舉例而言，一迴旋加速器、一同步加速器、一線性加速器或諸如此類可替代本文中所闡述之粒子治療系統中之同步迴旋加速器。 In certain embodiments, a particle accelerator other than a synchrocyclotron may be used in the particle therapy systems described herein. For example, a cyclotron, a synchrotron, a linear accelerator, or the like may be substituted for the synchrocyclotron in the particle therapy systems described herein.

在某些實施方案中，可在單位數或雙位數毫秒內執行使用彎曲磁體自束角度至束角度之切換。因此，可減少輻射遞送時間。在某些實例中，藉由為一個角度遞送束之一部分(一隔層或一個層之一部分)，範圍移位器及準直器可重新定位，藉此減少層切換延遲、準直器定位延遲及醫療角度切換延遲。 In certain embodiments, switching from beam angle to beam angle using curved magnets can be performed in single or double digit milliseconds. Therefore, radiation delivery time can be reduced. In some examples, the range shifter and collimator can be repositioned by delivering part of the beam at an angle (a partition or part of a layer), thereby reducing layer switching delay, collimator positioning delay and delays in switching medical perspectives.

使用一或多個電腦程式產品(例如有形地體現在一或多個非 暫時性機器可讀媒體中之一或多個電腦程式)可至少部分地控制本文中所闡述之實例性質子治療系統之操作及其所有或某些部件之操作，用於由一或多個資料處理裝備執行或控制其操作，該資料處理裝備例如係一可程式化處理器、一電腦、多個電腦及/或可程式化邏輯組件。 The operation of the example proton therapy system described herein and the operation of all or some of its components may be at least partially controlled using one or more computer program products (e.g., one or more computer programs tangibly embodied in one or more non-transitory machine-readable media) for execution or control by one or more data processing devices, such as a programmable processor, a computer, multiple computers, and/or a programmable logic unit.

本說明書中所闡述之系統之全部或部分及其各種修改可至少部分地由一或多個電腦(諸如控制系統34)使用有形地體現在一或多個資訊載體(諸如一或多個非暫時性機器可讀儲存媒體)中之一或多個電腦程式來組態或控制。可以任何形式之程式設計語言(包含編譯語言或解譯語言)寫入一電腦程式，且可以任何形式部署該電腦程式，包含部署為一獨立式程式或部署為一模組、部分、子常式或適合在一運算環境中使用之其他單元。一電腦程式可經部署以在一個電腦上或在位於一個位點處或跨越多個位點分佈且由一網路互連之多個電腦執行。 All or part of the system described in this specification, and various modifications thereof, may be tangibly embodied, at least in part, by one or more computers (such as control system 34) on one or more information carriers (such as one or more non-transitory one or more computer programs in a machine-readable storage medium) to configure or control. A computer program can be written in any form of programming language (including compiled language or interpreted language), and the computer program can be deployed in any form, including deployment as a stand-alone program or deployment as a module, part, or subroutine or other units suitable for use in a computing environment. A computer program may be deployed to execute on one computer or on multiple computers located at one site or distributed across multiple sites and interconnected by a network.

與組態或控制本文中所闡述之系統相關聯之動作可由執行一或多個電腦程式之一或多個可程式化處理器執行，以控制或執行本文中所闡述之所有或某些操作。本文中所闡述之系統及程序之全部或部分可由諸如一FPGA(場可程式化閘陣列)及/或ASIC(特殊應用積體電路)或者局域化至儀器硬體之嵌入式微處理器等專用邏輯電路系統組態或控制。 Actions associated with configuring or controlling the systems described herein may be performed by one or more programmable processors executing one or more computer programs to control or perform all or some of the operations described herein. All or part of the systems and procedures described herein may be implemented by a dedicated processor such as an FPGA (Field Programmable Gate Array) and/or an ASIC (Application Specific Integrated Circuit) or an embedded microprocessor localized to the instrument hardware. Logic circuit system configuration or control.

藉由實例方式，適合於執行一電腦程式之處理器包含通用微處理器及專用微處理器二者，以及任一種類之數位電腦之任何一或多個處理器。一般而言，一處理器將自一唯讀儲存區域或一隨機存取儲存區域或兩者接收指令及資料。一電腦之元件包含用於執行指令之一或多個處理器以及用於儲存指令及資料之一或多個儲存區域裝置。一般而言，一電腦亦將包含一或多個機器可讀儲存媒體，或者可操作地耦合至一或多個機器 可讀儲存媒體，以自一或多個機器可讀儲存媒體接收資料，或者將資料傳送給一或多個機器可讀儲存媒體，或者兩者，該機器可讀儲存媒體諸如係用於儲存資料之大容量儲存裝置，諸如磁碟、磁光碟或光碟。適合於體現電腦程式指令及資料之非暫時性機器可讀儲存媒體包含所有形式之非揮發性儲存區域，藉由實例方式包含半導體儲存區域裝置，諸如EPROM(可抹除可程式化唯讀記憶體)、EEPROM(電可抹除可程式化唯讀記憶體)及快閃儲存區域裝置；磁碟，諸如內部硬碟或可抽換磁碟；磁光碟；以及CD-ROM(壓縮碟片唯讀記憶體)及DVD-ROM(數位通用碟片唯讀記憶體)。 By way of example, processors suitable for executing a computer program include both general purpose microprocessors and special purpose microprocessors, and any one or more processors of any kind of digital computer. Generally speaking, a processor will receive instructions and data from a read-only storage area or a random access storage area, or both. The components of a computer include one or more processors for executing instructions and one or more storage area devices for storing instructions and data. Generally, a computer will also include, or be operatively coupled to, one or more machine-readable storage media to receive data from or transfer data to, or both, one or more machine-readable storage media, such as mass storage devices for storing data, such as magnetic disks, magneto-optical disks, or optical disks. Non-transitory machine-readable storage media suitable for embodying computer program instructions and data include all forms of non-volatile storage areas, including by way of example semiconductor storage area devices such as EPROM (erasable programmable read-only memory), EEPROM (electrically erasable programmable read-only memory) and flash storage area devices; magnetic disks, such as internal hard disks or removable disks; magneto-optical disks; and CD-ROMs (compressed disc read-only memory) and DVD-ROMs (digital versatile disc read-only memory).

所闡述之不同實施方案之元件可經組合以形成先前未具體闡述之其他實施方案。元件可自先前所闡述之系統省去，而不會對其操作或系統之總體操作產生不利影響。此外，各種單獨元件可組合成一或多個個別元件，以執行本說明書中所闡述之功能。 Elements of the different embodiments described may be combined to form other embodiments not previously described in detail. Elements may be omitted from a previously described system without adversely affecting its operation or the overall operation of the system. In addition, various individual elements may be combined into one or more individual elements to perform the functions described in this specification.

本說明書中未具體闡述之其他實施方案亦在以下申請專利範圍之範疇內。 Other implementation schemes not specifically described in this specification are also within the scope of the following patent application.

10:粒子治療系統 10:Particle therapy system

12:加速器/粒子加速器 12:Accelerator/particle accelerator

14:檯座/環形檯座 14: Table/Ring Table

17:醫療床 17:Medical bed

18:外殼 18: Shell

20:向量磁體 20: Vector magnet

22:磁體/彎曲磁體/不同形狀之彎曲磁體 22: Magnet/Bent Magnet/Bent Magnet of Different Shapes

34:控制系統 34:Control system

Claims (43)

一種粒子治療系統，其包括：一粒子加速器，其經組態以在一預定義最大能量下輸出一粒子束；一環形檯座，其在其一內部中包括磁體，該等磁體包括接近於該粒子加速器之一輸出之一第一磁體以及接近於一醫療位置之第二磁體，該第一磁體經組態以將該粒子束引導至一第二磁體，該第二磁體經組態以將處於該預定義最大能量之粒子束朝向該醫療位置彎曲；及一能量降級器，其可在該等第二磁體中之每一者與該醫療位置之間移動，該能量降級器用以在該粒子束到達該醫療位置之前改變該粒子束之一能量。 A particle therapy system includes: a particle accelerator configured to output a particle beam at a predetermined maximum energy; a toroidal pedestal including magnets in an interior thereof, the magnets including a first magnet near an output of the particle accelerator and a second magnet near a treatment location, the first magnet configured to direct the particle beam to a second magnet, the second magnet configured to bend the particle beam at the predetermined maximum energy toward the treatment location; and an energy degrader movable between each of the second magnets and the treatment location, the energy degrader used to change an energy of the particle beam before the particle beam reaches the treatment location. 如請求項1之粒子治療系統，其中該粒子加速器與該環形檯座係在同一醫療空間內。 A particle therapy system as claimed in claim 1, wherein the particle accelerator and the annular table are in the same medical space. 如請求項1之粒子治療系統，其中該粒子加速器係一固定能量粒子加速器。 The particle therapy system of claim 1, wherein the particle accelerator is a fixed energy particle accelerator. 如請求項1之粒子治療系統，其中該等第二磁體係間隔開的且各自位於該環形檯座之一不同圓周扇區中。 The particle therapy system of claim 1, wherein the second magnetic systems are spaced apart and each are located in a different circumferential sector of the annular base. 如請求項4之粒子治療系統，其中該環形檯座包括六個與二十個之間的第二磁體。 A particle therapy system as claimed in claim 4, wherein the annular table includes between six and twenty second magnets. 如請求項1之粒子治療系統，其中該等第二磁體在該環形檯座上係靜止的。 The particle therapy system of claim 1, wherein the second magnets are stationary on the annular base. 如請求項1之粒子治療系統，其中該等第二磁體經組態以將該粒子束彎曲至少90°。 The particle therapy system of claim 1, wherein the second magnets are configured to bend the particle beam by at least 90°. 如請求項1之粒子治療系統，其進一步包括：一醫療床，其可在該環形檯座之一孔內移動，該醫療床用於將一患者固持在該醫療位置處。 The particle therapy system of claim 1 further comprises: a medical bed that can move in a hole of the annular table, and the medical bed is used to hold a patient at the medical position. 如請求項1之粒子治療系統，其中該第二磁體與該醫療位置之間的一距離係兩米(2m)或更小。 A particle therapy system as claimed in claim 1, wherein a distance between the second magnet and the treatment location is two meters (2m) or less. 如請求項1之粒子治療系統，其中該第二磁體與該醫療位置之間的一距離係一米(1m)或更小。 The particle therapy system of claim 1, wherein a distance between the second magnet and the medical location is one meter (1m) or less. 如請求項1之粒子治療系統，其中該粒子加速器包括一同步迴旋加速器。 A particle therapy system as claimed in claim 1, wherein the particle accelerator comprises a synchrocyclotron. 如請求項1之粒子治療系統，其中該粒子加速器包括經組態以在兩種能量下操作之一同步迴旋加速器，該兩種能量中之一者大於該兩種能量中之另一者。 The particle therapy system of claim 1, wherein the particle accelerator includes a synchrocyclotron configured to operate at two energies, one of the two energies being greater than the other of the two energies. 如請求項1之粒子治療系統，其中該粒子加速器包括一同步加速器。 The particle therapy system of claim 1, wherein the particle accelerator includes a synchrotron. 如請求項1之粒子治療系統，其進一步包括：一或多個成像裝置，其被安裝至該環形檯座，該一或多個成像裝置經組態用於圍繞該環形檯座移動。 The particle therapy system of claim 1 further comprises: one or more imaging devices mounted to the annular table, the one or more imaging devices being configured to move around the annular table. 如請求項14之粒子治療系統，其進一步包括：一噴嘴，其經組態用於圍繞該環形檯座移動，該噴嘴用於將該粒子束輸出至該醫療位置。 The particle therapy system of claim 14, further comprising: a nozzle configured to move around the annular pedestal, the nozzle being used to output the particle beam to the medical location. 如請求項15之粒子治療系統，其進一步包括：一控制系統，其經程式化以控制該一或多個成像裝置之移動並控制該噴嘴之移動，該控制系統經程式化以防止該噴嘴與該一或多個成像裝置之間發生碰撞。 The particle therapy system of claim 15 further comprises: a control system programmed to control the movement of the one or more imaging devices and the movement of the nozzle, the control system being programmed to prevent collision between the nozzle and the one or more imaging devices. 如請求項15之粒子治療系統，其中該噴嘴經組態以圍繞該環形檯座中之一第一內部軌道旋轉，並且該一或多個成像裝置經組態以圍繞該環形檯座中之一第二內部軌道旋轉，該第一內部軌道與該第二內部軌道位於該環形檯座之不同位置處。 A particle therapy system as claimed in claim 15, wherein the nozzle is configured to rotate around a first inner track in the annular table, and the one or more imaging devices are configured to rotate around a second inner track in the annular table, and the first inner track and the second inner track are located at different positions of the annular table. 如請求項1之粒子治療系統，其中該等第二磁體係間隔開的且各自位於該環形檯座之一不同圓周扇區中，該等扇區中之每一者包括用於將該粒 子束輸出至該醫療位置之一噴嘴。 The particle therapy system of claim 1, wherein the second magnetic systems are spaced apart and each located in a different circumferential sector of the annular base, and each of the sectors includes a device for placing the particle. The beamlets are output to one of the nozzles at the medical location. 如請求項1之粒子治療系統，其中該粒子加速器包括用以產生用於加速粒子來產生該粒子束之一磁場的主超導線圈；且其中該粒子加速器包括用以在與該等主超導線圈相反之一方向上傳導電流之主動返回線圈。 The particle therapy system of claim 1, wherein the particle accelerator includes a main superconducting coil used to generate a magnetic field for accelerating particles to generate the particle beam; and wherein the particle accelerator includes a main superconducting coil used to interact with the main superconducting coil. An active return coil that conducts current in the opposite direction of the coil. 如請求項1之粒子治療系統，其中在FLASH劑量下將該粒子束遞送給一患者。 A particle therapy system as claimed in claim 1, wherein the particle beam is delivered to a patient at a FLASH dose. 如請求項20之粒子治療系統，其中在少於五(5)秒之一持續時間內在超過二十(20)戈每秒之一劑量下將該粒子束遞送給該患者。 A particle therapy system as claimed in claim 20, wherein the particle beam is delivered to the patient at a dose of more than twenty (20) Ge per second for a duration of less than five (5) seconds. 一種粒子治療系統，其包括：一多扇區檯座，每一扇區經組態以將包括一粒子束之輻射自該多扇區檯座上之一不同位置遞送給位於一醫療位置之一患者；一粒子加速器，其連接至該多扇區檯座以將該輻射朝向該多扇區檯座輸出；及一能量降級器，其可在該多扇區檯座之不同扇區之間移動，該能量降級器用以在該粒子束到達該醫療位置之前改變該粒子束之一能量；其中該多扇區檯座與該粒子加速器係在同一醫療室中且未被該多扇區檯座或該粒子加速器外部之屏蔽件分隔。 A particle therapy system comprising: a multi-sector table, each sector being configured to deliver radiation including a particle beam from a different location on the multi-sector table to a patient at a medical location; a particle accelerator connected to the multi-sector table to output the radiation toward the multi-sector table; and an energy degrader movable between different sectors of the multi-sector table, the energy degrader being used to change an energy of the particle beam before the particle beam reaches the medical location; wherein the multi-sector table and the particle accelerator are in the same medical room and are not separated by shielding external to the multi-sector table or the particle accelerator. 如請求項22之粒子治療系統，其中該多扇區檯座與該粒子加速器係在同一醫療空間中。 A particle therapy system as claimed in claim 22, wherein the multi-sector pedestal and the particle accelerator are in the same medical space. 如請求項22之粒子治療系統，其中該多扇區檯座之每一扇區包括經組態以將該輻射朝向該患者引導之一磁體。 A particle therapy system as claimed in claim 22, wherein each sector of the multi-sector pedestal includes a magnet configured to direct the radiation toward the patient. 如請求項24之粒子治療系統，其中每一磁體係實質上D形的。 A particle therapy system as claimed in claim 24, wherein each magnet is substantially D-shaped. 如請求項24之粒子治療系統，其中每一磁體經組態以將該輻射之該粒子束彎曲至少90°。 A particle therapy system as claimed in claim 24, wherein each magnet is configured to bend the particle beam of the radiation by at least 90°. 如請求項24之粒子治療系統，其中該多扇區檯座在形狀上係環形的；且其中該多扇區檯座包括在該多扇區檯座之每一扇區中之一第二磁體以及介於該第二磁體與該粒子加速器之間的一第一磁體，該第一磁體用於將該粒子束引導至一標靶扇區中之一第二磁體。 The particle therapy system of claim 24, wherein the multi-sector pedestal is annular in shape; and wherein the multi-sector pedestal includes a second magnet in each sector of the multi-sector pedestal. and a first magnet between the second magnet and the particle accelerator for directing the particle beam to a second magnet in a target sector. 如請求項27之粒子治療系統，其中該第一磁體經組態以將該粒子束引導至不同扇區。 A particle therapy system as claimed in claim 27, wherein the first magnet is configured to direct the particle beam to different sectors. 如請求項22之粒子治療系統，其中該粒子加速器包括一同步迴旋加速器。 The particle therapy system of claim 22, wherein the particle accelerator includes a synchrocyclotron. 如請求項29之粒子治療系統，其中該同步迴旋加速器經組態以在兩種不同能量中之一者下輸出該粒子束。 A particle therapy system as claimed in claim 29, wherein the synchrocyclotron is configured to output the particle beam at one of two different energies. 如請求項22之粒子治療系統，其中該粒子加速器包括一同步加速器。 A particle therapy system as claimed in claim 22, wherein the particle accelerator comprises a synchrotron. 一種供在一粒子治療系統中使用之檯座，該檯座包括：一環形結構，其可連接至一粒子加速器，該環形結構包括圍繞該環形結構之一圓周配置在扇區中之第一磁體，該等第一磁體用於將源於該粒子加速器處之一粒子束朝向一醫療位置彎曲至少90°；一外殼，其將該環形結構連接至該粒子加速器，該外殼包括第二磁體，該等第二磁體用於接收該粒子束並將該粒子束朝向該等第一磁體引導；該外殼內之一可旋轉結構，該可旋轉結構經組態用於安裝輻射遞送組件或成像組件中之至少一者；及一能量降級器，其可在該等第一磁體中之每一者與該醫療位置之間移動，該能量降級器用以在該粒子束到達該醫療位置之前改變該粒子束之一能量，該能量降級器被安裝至該可旋轉結構。 A table for use in a particle therapy system, the table comprising: an annular structure connectable to a particle accelerator, the annular structure comprising first magnets arranged in sectors around a circumference of the annular structure, the first magnets being used to bend a particle beam originating from the particle accelerator by at least 90° toward a treatment location; a housing connecting the annular structure to the particle accelerator, the housing comprising second magnets, the second magnets being used to Receive the particle beam and direct the particle beam toward the first magnets; a rotatable structure within the housing, the rotatable structure configured to mount at least one of a radiation delivery assembly or an imaging assembly; and an energy degrader movable between each of the first magnets and the treatment location, the energy degrader being used to change an energy of the particle beam before the particle beam reaches the treatment location, the energy degrader being mounted to the rotatable structure. 如請求項32之檯座，該檯座與該粒子加速器係在同一醫療空間內。 For example, the table in claim 32, the table and the particle accelerator are in the same medical space. 如請求項32之檯座，其中該等第一磁體係間隔開的且各自位於該環形結構之一不同圓周扇區中。 A table as claimed in claim 32, wherein the first magnets are spaced apart and each is located in a different circumferential sector of the annular structure. 如請求項32之檯座，其中該環形結構包括六個與二十個之間的第一磁體。 A table as claimed in claim 32, wherein the annular structure includes between six and twenty first magnets. 如請求項32之檯座，其中該等第一磁體在該環形結構上係靜止的。 A table as claimed in claim 32, wherein the first magnets are stationary on the annular structure. 如請求項32之檯座，其中該等第二磁體經組態以將該粒子束彎曲至少90°。 A table as claimed in claim 32, wherein the second magnets are configured to bend the particle beam by at least 90°. 如請求項32之檯座，其中該等第一磁體中之每一者與該醫療位置之間的一距離係兩米(2m)或更小。 A table as claimed in claim 32, wherein a distance between each of the first magnets and the medical location is two meters (2m) or less. 如請求項32之檯座，其中該第二磁體與該醫療位置之間的一距離係一米(1m)或更小。 The pedestal of claim 32, wherein a distance between the second magnet and the medical location is one meter (1m) or less. 如請求項32之檯座，其進一步包括：一或多個成像裝置，其被安裝至該可旋轉結構，該一或多個成像裝置經組態用於圍繞該環形結構移動。 The table of claim 32 further comprises: one or more imaging devices mounted to the rotatable structure, the one or more imaging devices being configured to move around the annular structure. 如請求項32之檯座，其進一步包括：一噴嘴，其經組態用於圍繞該環形結構移動，該噴嘴用於將該粒子束輸出至該醫療位置，該噴嘴被安裝至該可旋轉結構。 The table of claim 32 further comprises: a nozzle configured to move around the annular structure, the nozzle being used to output the particle beam to the treatment location, the nozzle being mounted to the rotatable structure. 如請求項32之檯座，其進一步包括：一個或多個成像裝置，其經組態用於圍繞該環形結構移動；及一噴嘴，其經組態用於圍繞該環形結構移動，該噴嘴用於將該粒子束輸出至該醫療位置；其中該噴嘴及該一或多個成像裝置被安裝至該可旋轉結構。 The pedestal of claim 32, further comprising: one or more imaging devices configured to move around the annular structure; and a nozzle configured to move around the annular structure, the nozzle using In outputting the particle beam to the medical location; wherein the nozzle and the one or more imaging devices are mounted to the rotatable structure. 如請求項32之檯座，其中該等第一磁體係間隔開的且各自位於該環形結構之一不同圓周扇區中，該等扇區中之每一者包括用於將該粒子束輸出至該醫療位置之一噴嘴。 The pedestal of claim 32, wherein the first magnetic systems are spaced apart and each located in a different circumferential sector of the annular structure, each of the sectors including a pedestal for outputting the particle beam to The medical position is one of the nozzles.
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