WO2017080118A1 - Dispositif d'irradiation de particules et système de thérapie par particules comprenant le dispositif - Google Patents

Dispositif d'irradiation de particules et système de thérapie par particules comprenant le dispositif Download PDF

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Publication number
WO2017080118A1
WO2017080118A1 PCT/CN2016/072760 CN2016072760W WO2017080118A1 WO 2017080118 A1 WO2017080118 A1 WO 2017080118A1 CN 2016072760 W CN2016072760 W CN 2016072760W WO 2017080118 A1 WO2017080118 A1 WO 2017080118A1
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Prior art keywords
particle
particle beam
therapy system
central axis
shutter
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Ceased
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PCT/CN2016/072760
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English (en)
Chinese (zh)
Inventor
蒲越虎
马晓颖
贾亚军
张潇
吴超
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Shanghai Apactron Particle Equipment Co Ltd
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Shanghai Apactron Particle Equipment Co Ltd
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Publication of WO2017080118A1 publication Critical patent/WO2017080118A1/fr
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy

Definitions

  • the present invention relates to a device and system for treating cancer using radiation, and more particularly to a particle irradiation device and a particle therapy system including the same.
  • Particle radiotherapy is one of the most advanced cancer treatments in the world.
  • a particle When a particle is irradiated into a patient, it will form a maximum dose peak at the particle range end, ie, a so-called Bragg Peak, as compared to conventional photon radiation therapy (X-ray radiotherapy). Therefore, by precisely controlling the particle beam energy and the particle beam irradiation position, high-dose particles can be concentratedly irradiated into the target tumor target region, and the adverse irradiation dose to the normal tissue and the normal organ around the target tumor can be minimized, thereby achieving More conformable dose distribution than X-ray radiotherapy, improve the therapeutic effect of tumors and reduce side effects.
  • a particle therapy system using a two-dimensional illumination method includes a particle accelerator 1, a particle transport device 2, a particle irradiation device 3, an illumination control device 4, and a patient positioning device, as shown in FIG. 1, in which particles generated by the particle accelerator 1
  • the beam current usually has a beam spot size of 10 mm or less, so when it is necessary to uniformly irradiate the particle beam to, for example, a tumor target region 5 having a diameter of 10 cm, the particle irradiation device 3 is required to have a beam spot diameter of less than 1 cm.
  • the particle beam is expanded to a range of 10 cm.
  • the starting particle beam 11 from the particle accelerator 1 is transported into the particle irradiation device 3 by the particle transport device 2, and the rocking magnet 31 causes the starting particle beam 11 to be scanned in a planned trajectory to form a fixed trajectory (such as a circle).
  • a first particle beam 32 of a shape or a ZigZag shape the first particle beam 32 is scattered by the scatterer 33 to form a second particle beam 34, which has a larger divergence than the first particle beam 32.
  • the second particle beam 34 removes unnecessary particles through the collimator 35, and finally illuminates the tumor target region 5.
  • the rocking magnet 31 is mainly used to scan the starting particle beam 11 on a planned trajectory, so that the particles finally reaching the tumor target region 5 are evenly distributed on the plane.
  • the rocking magnet 31 and the corresponding driving power source the structure of the existing particle therapy system tends to be complicated and costly.
  • the present invention aims to provide a particle irradiation apparatus and a particle treatment system including the same.
  • the present invention provides a particle irradiation apparatus comprising: a beam of particles transmitted along a central axis, comprising a second particle beam and a third particle beam; a collimator mounted on a transmission path of the third particle beam, the first The three-particle beam forms a two-dimensional distribution in which the shape of the field corresponding to the tumor target region is completely uniform through the collimator; a planarization device mounted on the transmission path of the second particle beam, the planarization device including the rotation about the central axis a shielding member; the second particle beam passes through the planarizing device to form a third particle beam.
  • the third particle beam has a more uniform particle density distribution than the second particle beam in a plane perpendicular to the central axis.
  • the arc angle acr-angle(r) of the shutter is a product of 360 degrees and the attenuation ratio (r), wherein the attenuation ratio (r) is The ratio of the number of particles blocked by the occlusion member to the number of particles distributed over the entire circumference.
  • a flattening range is formed in the radial range of the radius r, and the arc angle acr-angle(r) of the shutter gradually decreases in the flattening range along the direction away from the central axis.
  • the flattening device further includes a rotating member and a fixing member, wherein the rotating member is a circular ring member rotatably supported on the fixing member about a central axis, and an end of the shielding member away from the central axis is fixedly connected to the annular member On the circle.
  • the end of the shutter adjacent the central axis is formed as a free end.
  • the flattening device further includes a driving member and a transmission member, and the driving member and the rotating member are connected by the transmission member.
  • the rotating member is engaged with the transmission member.
  • the transmission member is a belt.
  • the particle beam stream further includes a first particle beam, the particle irradiation device further comprising a scatterer mounted on a transmission path of the first particle beam, the first particle beam being scattered by the scatterer to form a second particle beam, the second particle The beam has a larger divergence angle than the first particle beam.
  • the particle irradiation apparatus further includes a monitor mounted on a transmission path of the first particle beam or the second particle beam.
  • the present invention also provides a particle therapy system comprising the particle irradiation device described above.
  • the particle therapy system also includes a particle accelerator and a particle transport device that provides a starting particle beam that is transported into the particle irradiation device by the particle transport device.
  • the particle therapy system further includes a ridge filter mounted on the transport path of the third particle beam for adjusting the dose distribution of the particle beam in the depth direction of the tumor.
  • the particle therapy system further includes a range compensator mounted on the transmission path of the third particle beam for stopping the particle beam at the deepest portion of the tumor target region at the corresponding illumination location.
  • the invention realizes the uniform distribution of the dose by the flattening device, omits the use of the rocking magnet and the driving power source thereof, and only needs a simple shielding member to obtain a desired particle irradiation device and a particle treatment system including the device, thereby improving the irradiation. Reliability of the device and treatment system while reducing costs.
  • Figure 1 is a schematic illustration of a particle therapy system in accordance with the prior art
  • Figure 2 is a schematic illustration of a particle therapy system in accordance with a first embodiment of the present invention
  • Figure 3 is a perspective view of the rotating member and the shutter of the particle therapy system of Figure 2;
  • Figure 4 is a schematic illustration of the shutter of Figure 3 in a beam of particles
  • Figure 5 is a schematic view showing the occlusion principle of the occluding member in the particle beam flow of Figure 3;
  • Figure 6 is a schematic diagram of a particle beam flow upstream of the shield
  • Figure 7 is a schematic diagram of a particle beam flow downstream of the shield
  • Figure 8 is a schematic diagram of a particle beam flow downstream of the collimator
  • Figure 9 is a perspective view of a rotary member and a shutter of a particle therapy system in accordance with a second embodiment of the present invention.
  • Figure 10 is a perspective view of a planarization device of a particle therapy system in accordance with a third embodiment of the present invention.
  • Zone 50 is positioned on the patient positioning device.
  • the particle accelerator 10, the particle transport device 20, and the particle irradiation device 30 are each in communication with the illumination control device 40 to control the particle beam flow.
  • the center of the particle irradiation device 30 is at the center of the tumor target region 50
  • the central axis 110a of the beam current is on.
  • the particle beam flow can be artificially distinguished into a starting particle beam 110, a first particle beam 320, a second particle beam 340, and a third particle beam 370.
  • the starting particle beam 110 is derived from the particle accelerator 10, which is transported into the particle irradiation device 30 by the particle transport device 20 to form a first particle beam 320; the first particle beam 320 is scattered by the scatterer 330 to form a second particle.
  • the second particle beam 340 has a larger divergence angle than the first particle beam 320; the second particle beam 340 passes through the planarization device 360 to form a third particle beam 370, the third particle beam 370 is second
  • the particle beam 340 has a more uniform particle density distributed across the plane; the third particle beam 370 removes unnecessary particles through the collimator 350, ultimately illuminating the tumor target zone 50.
  • the flattening device 360 is mounted on the transport path of the second particle beam 340 along the irradiation direction of the particle beam (hereinafter simply referred to as the axial direction).
  • the planarizing device 360 is disposed downstream of the scatterer 330 and disposed upstream of the collimator 350.
  • the present invention causes the second particle beam 340 to have a uniform dose distribution in a plane region perpendicular to the axial direction corresponding to the tumor target region 50 (hereinafter simply referred to as a lateral direction) by the planarizing device 360, thereby omitting the rocking magnet of the prior art. 31, the structure is simply achieved homogenization, greatly reducing the cost of the particle treatment system.
  • the planarizing device 360 includes a driving member 361, a transmission member 362, a rotating member 363, a fixing member 364, and a shielding member 365.
  • the rotating member 363 is an annular member rotatable around the central axis 110a, that is, the central axis 110a is formed as the center of rotation of the rotating member 363.
  • the shutter 365 is fixedly coupled to the inner ring of the rotating member 363 such that the shutter 365 follows the rotating member 363 to rotate about the central axis 110a.
  • a bearing 366 is disposed on the outer ring of the rotating member 363 such that the rotating member 363 is supported by the fixing member 364 through the bearing 366.
  • the driving member 361 is a motor that is coupled to the rotating member 363 through the transmission member 362 to drive the rotating member 363 to rotate by the motor.
  • FIG 3 is a perspective view of the rotating member 363 and the shutter 365 of the planarizing device 360 of the present embodiment, wherein one end of the blocking member 365 away from the central axis 110a is formed as a connecting end 365a, and the other end is formed as a free end 365b.
  • the shutter 365 is welded to the inner ring of the rotary member 363 through the connection end 365a. It should be understood that the connecting end 365a can also be coupled to the inner ring of the rotating member 363, for example, by adhesive bonding.
  • the shutter 365 does not have other support structures, so that the particle beam flow is not blocked by other support structures, that is, the overall contour of the shutter 365 is configured to be the only pair of particle beams (ie, the second particle beam).
  • the components that are occluded are shown in Figure 4.
  • the shutter 365 may be a polymer material such as polymethyl methacrylate (PMMA) forming an organic glass, or may be a material such as aluminum or aluminum alloy.
  • PMMA polymethyl methacrylate
  • the shutter 365 has a thickness d in the axial direction, as long as it can The transmission of the particle beam is effectively blocked, and the specific value of the thickness depends on the range of the particle beam within the shutter 365.
  • the thickness d when the proton beam energy for cancer treatment is 230 MeV, and the shutter 365 is plexiglass, the thickness d is more than about 33 cm; when the proton beam energy for cancer treatment is 70 MeV, and the shutter 365 is plexiglass In time, the thickness d may exceed about 4 cm; when the proton beam energy for cancer treatment is 230 MeV, and the shutter 365 is aluminum, the thickness d may exceed 16 cm.
  • the shutter 365 is in the second particle beam 340 of the near Gaussian distribution F1(r), that is, the particle density in the central region is large, and the density of the surrounding region is small.
  • 5 is a schematic diagram of the shielding principle of the shielding member.
  • the central axis 110 On a plane perpendicular to the central axis 110a, the central axis 110 is centered, r is a circle, and a corresponding arc formed on the shielding member 365 is called a shielding member 365 ( r), for the occlusion member 365(r) at a certain radius r, the ratio of the number of particles that are blocked and the number of particles distributed over the entire circumference is called the deviation ratio attenuation (r), which is equal to The ratio of the arc angle arc-angle(r) of the shutter 365(r) to 360 degrees.
  • Figures 6-7 The process of homogenization is shown in Figures 6-7, wherein Figure 6 is a graphical representation of the particle beam upstream of the shield (i.e., the second particle beam 340), and Figure 7 is the particle beam downstream of the shield ( That is, a schematic diagram of the curve of the third particle beam 370).
  • the Gaussian distribution F1(r) is artificially divided into the central region Q1 and the surrounding region Q2 surrounding the central region. It should be understood that the boundary between the central region Q1 and the surrounding region Q2 is not determined as long as the final arrival is ensured. All particle beams of the tumor target region 50 are from the central region Q1.
  • the purpose of the shielding member 365 is to weaken the particle density of the central region Q1 (the region of the shielding member 365 in the central region Q1 is the flattening range) so as to be close to the particle density of the surrounding region Q2, thereby achieving flatness of F1(r).
  • the F2(r) shown in Fig. 7 is obtained. It should be understood that the outer edge of the shutter 365 that is furthest from the central axis 110a can be defined by the boundary between the central region Q1 and the surrounding region Q2.
  • the shutter 365 only weakens the particle density of the central region Q1, along the distance In the direction of the central axis 110a, the arc angle acr-angle(r) of the shutter 365 is gradually reduced; however, the outer edge of the shutter 365 farthest from the central axis 110a may also extend beyond the central region Q1 and the surrounding region Q2. Boundary, at this time, the shutter 365 not only weakens the particle density of the central region Q1, but also weakens the particle density of a portion of the surrounding region Q2. Along the direction away from the central axis 110a, the arc angle acr-angle(r) of the shutter 365 gradually decreases in the flattening range.
  • the total time for illuminating the tumor target region 50 is T0, and the requirement for planarization is realized within this T0 time. Due to the occlusion of the occlusion member 365, some particles in the particle beam are blocked by the occlusion member 365 after the irradiation time T0.
  • the total number of revolutions N of the shutter 365 in the time T0 is selected to be sufficiently large, and the speed of the specific rotation depends on the distribution error.
  • the total number of revolutions N needs to be at least much larger than 100.
  • the error due to the shutters 365 at different positions is about 1%.
  • the shutter 365 rotates a total of 500 revolutions, then the error of one revolution represents only 1/500 of the total dose, and at the moment of the irradiation time T0 at the last revolution, the shutter 365 is stopped.
  • the distribution error caused by the angle can be ignored. At this time, the distribution error is below 2%, which satisfies the clinical needs.
  • the gradient of the radius r of the shutter 365 depends on the distribution accuracy. For example, it can be selected to be 0.1 mm, 1 mm or 2 mm as required. Preferably, the gradient of the radius r of the shutter 365 does not exceed 1/10 of the radius r of the central region Q1.
  • the collimator 350 can be a multi-leaf collimator (MLC) for limiting the planarized third particle beam 370 to the tumor target area. 50.
  • MLC multi-leaf collimator
  • the collimator may also be a Patient Collimator that is machined according to the shape of the field given by the metal block or the like according to the treatment plan. Specifically, the collimator is prepared according to the treatment plan to calculate the two-dimensional shape to remove unwanted laterally distributed particles, leaving only the particles required to illuminate the tumor target region 50 to form an illumination determined by the shape of the collimator.
  • the wild shape that is, the two-dimensional lateral distribution F3(r) which finally forms the same shape as the field corresponding to the tumor target region 50, is as shown in FIG.
  • the particle irradiation apparatus 30 of the present invention further includes a monitor 380 as shown in FIG.
  • the monitor 380 is mounted on the transmission path of the second particle beam 340, that is, disposed downstream of the scatterer 330.
  • the monitor 380 can also be mounted on the transmission path of the first particle beam 320, that is, upstream of the scatterer 330.
  • the monitor 380 is used to monitor the physical quantity of the particle beam associated with the particle beam, such as the dose of the particle beam as commonly referred to.
  • the monitor 380 is also used to monitor the position of the particle beam to ensure that the central axis 110a of the particle beam flow is substantially the center of rotation of the shutter 365 without substantial deviation therebetween.
  • the particle irradiation device 30 of the present invention further includes Ridge filter.
  • the ridge filter is mounted on the transport path of the third particle beam 370 for adjusting the dose distribution of the particle beam in the depth direction of the tumor to form a uniform three-dimensional conformal dose distribution in the three-dimensional tumor target region 50,
  • the particle irradiation device 30 of the present invention further includes a range compensator.
  • the range compensator is mounted on the transmission path of the third particle beam 370 so that the particle beam can be stopped at the deepest portion of the tumor target region 50 corresponding to the irradiation position, thereby achieving the conformation of the tumor bottom.
  • the particles are protons. It should be understood that the invention is not limited to the use of proton beams. Since the proton beam is the most widely used particle in the particle radiotherapy field, the proton beam is here only by way of example and not limitation, and other particle beams, even photons, are equally suitable for use in the present invention, such as a carbon ion beam.
  • the particle therapy system includes a particle accelerator, a particle transport device, a particle irradiation device, an illumination control device, and a patient positioning device, and the tumor target region is positioned on the patient positioning device.
  • the particle irradiation device includes a flattening device 360' including a rotating member 363' and a shutter 365'.
  • the outer ring of the rotary member 363' is a gear structure for meshing transmission with the transmission member gear.
  • the shape of the shutter 365' is slightly different from that of the first embodiment in accordance with the requirements of the flattening.
  • the particle therapy system includes a particle accelerator, a particle transport device, a particle irradiation device, an illumination control device, and a patient positioning device, and the tumor target region is positioned on the patient positioning device.
  • the particle irradiation apparatus includes a flattening device 360" including a driving member 361", a transmission member 362", a rotating member 363", and a shutter 365".
  • the transmission member 362" is a belt, so that the driving member 361” drives the rotation of the rotary member 363" by the belt.
  • the shape of the shutter 365" is slightly different from that of the first embodiment, but is the same as that of the second embodiment.
  • the above embodiments include a scatterer for expanding the particle beam spot to a few centimeters in diameter, the scatterer can be omitted because it comes from the particle accelerator.
  • the starting particle beam itself has a certain divergence angle, and as long as the distance is sufficient, the flattening requirement can also be achieved by means of the spirit of the invention.
  • the lateral distribution of the second particle beam 340 in the above embodiment is shown as a Gaussian distribution F1(r), the Gaussian distribution is used only as an example and not a limitation, and in the case of a non-Gaussian distribution, the second particle beam The lateral distribution of 340 cannot be obtained directly through the curve, which can be achieved by measurement, and finally achieve the requirement of flattening.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Pathology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Radiation-Therapy Devices (AREA)

Abstract

La présente invention concerne un dispositif d'irradiation de particules (30) qui comprend : des faisceaux de particules, transmis le long d'un axe central (110a) et comprenant un deuxième faisceau de particules (340) et un troisième faisceau de particules (370); un collimateur (350), monté sur un trajet de transmission du troisième faisceau de particules (370), le troisième faisceau de particules (370) traversant le collimateur (350) et formant une distribution bidimensionnelle qui est totalement cohérente avec la forme d'un champ correspondant à un volume de tumeur (50); et une unité de planarisation (360), disposée sur un trajet de transmission du deuxième faisceau de particules (340) et pourvue d'un élément de blindage rotatif (365) qui peut tourner autour de l'axe central (110a), l'élément de blindage (365) aplanissant le deuxième faisceau de particules (340) de manière à former le troisième faisceau de particules (370). L'invention concerne un système de thérapie par particules comprenant le dispositif d'irradiation de particules (30). Au moyen de l'unité de planarisation (360), la distribution uniforme d'un dosage est mis en œuvre, et le dispositif d'irradiation de particules souhaité (30) et le système de thérapie par particules comportant le dispositif d'irradiation de particules (30) peut être obtenu uniquement au moyen de l'élément de blindage simple (365) et, en conséquence, la fiabilité du dispositif d'irradiation de particules (30) et le système de thérapie par particules est amélioré et, par ailleurs, les coûts sont réduits.
PCT/CN2016/072760 2015-11-13 2016-01-29 Dispositif d'irradiation de particules et système de thérapie par particules comprenant le dispositif Ceased WO2017080118A1 (fr)

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CN201510778390.X 2015-11-13
CN201510778390.XA CN105251138B (zh) 2015-11-13 2015-11-13 一种粒子照射装置以及包括该装置的粒子治疗系统

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CN109011213A (zh) * 2018-08-17 2018-12-18 江苏莱福医疗器械科技有限公司 一种放射性粒子自动排序装置

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CN105797282B (zh) * 2016-03-07 2018-09-04 上海艾普强粒子设备有限公司 一种粒子照射装置以及包括该装置的粒子治疗系统
CN106110523B (zh) * 2016-08-18 2019-04-26 上海艾普强粒子设备有限公司 一种粒子照射装置以及包括该装置的粒子治疗系统
CN109260606A (zh) * 2017-07-17 2019-01-25 住友重机械工业株式会社 带电粒子束治疗系统
CN108671417A (zh) * 2018-03-27 2018-10-19 中科超精（安徽）科技有限公司 基于自洽性的笔形束剂量算法
JP2021159110A (ja) * 2020-03-30 2021-10-11 住友重機械工業株式会社 荷電粒子線照射装置
CN112083467B (zh) * 2020-09-28 2022-05-31 中国科学院近代物理研究所 一种粒子治疗装置的三维剂量测量探测系统
CN116095938A (zh) * 2022-12-22 2023-05-09 同方威视技术股份有限公司 阻挡器旋转切换装置及其控制方法以及加速器

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