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WO2023217320A1 - Dispositif de détermination d'énergie et de détermination d'une distribution de dose de profondeur de rayonnement de particules - Google Patents

Dispositif de détermination d'énergie et de détermination d'une distribution de dose de profondeur de rayonnement de particules Download PDF

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Publication number
WO2023217320A1
WO2023217320A1 PCT/DE2023/100332 DE2023100332W WO2023217320A1 WO 2023217320 A1 WO2023217320 A1 WO 2023217320A1 DE 2023100332 W DE2023100332 W DE 2023100332W WO 2023217320 A1 WO2023217320 A1 WO 2023217320A1
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WO
WIPO (PCT)
Prior art keywords
phantom
radiation
energy
determination
interaction layer
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Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
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PCT/DE2023/100332
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German (de)
English (en)
Inventor
Alina Hanna DITTWALD
Timo Fanselow
Jürgen BUNDESMANN
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Helmholtz Zentrum Berlin fuer Materialien und Energie GmbH
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Helmholtz Zentrum Berlin fuer Materialien und Energie GmbH
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Application filed by Helmholtz Zentrum Berlin fuer Materialien und Energie GmbH filed Critical Helmholtz Zentrum Berlin fuer Materialien und Energie GmbH
Priority to EP23729935.9A priority Critical patent/EP4523014A1/fr
Publication of WO2023217320A1 publication Critical patent/WO2023217320A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/169—Exploration, location of contaminated surface areas

Definitions

  • the invention relates to a device for determining the energy and determining a depth dose distribution of particle radiation, such as is used, for example, in the proton therapy of tumors.
  • PRIOR ART Devices for determining energy and determining a depth dose distribution of particle radiation are known from the prior art.
  • the depth dose distribution of particle radiation describes the absorbed radiation energy of a particle beam depending on the so-called travel distance, ie the distance traveled by the particles in the particle beam in the irradiated material.
  • the depth dose distribution is usually measured in a so-called water phantom.
  • Phantoms are objects that have physical properties, such as: B. the absorption behavior of a biological tissue.
  • the behavior of particle beams in soft tissue is very similar to that in water, so that the knowledge gained in the water phantom about the nature of the particle beam can be transferred to soft tissue.
  • a plastic or similar materials that have a permeability to ionizing radiation from a source used that is comparable to that of living tissue can also be used.
  • What is also crucial here is the water equivalence, which is equivalent to that of a water phantom.
  • Common water-equivalent plastics and other water-equivalent materials are those that have a density close to 1 g/cm 3 and are predominantly composed of the light elements hydrogen, oxygen and carbon, such as those from the incomplete group polymethyl methacrylate (PMMA, also known as “Plexiglas®”), polyethylene, polystyrene, epoxy resins, urethane and petroleum jelly.
  • PMMA polymethyl methacrylate
  • the energy determination of a particle beam, especially a predominantly monoenergetic beam, can be determined via the penetration depth in a material and thus also in a phantom. For this purpose, the devices are usually calibrated accordingly.
  • the depth dose distribution of a particle beam and also the energy determination in materials whose absorption coefficient is not adapted to the soft tissue must be determined if the corresponding conversion factors are known through calibration.
  • the term phantom therefore also includes one that is made of a material that has a different absorption coefficient than that of soft tissue.
  • the absorbed dose is the energy transferred to the matter in a volume element by particle radiation, ie the energy absorbed by the matter per mass of the volume element.
  • the unit is Gray (sign: Gy, unit: J/kg).
  • the absorbed dose rate is the quotient of the absorbed absorbed dose within a certain time (Gy/h).
  • particle beams are all those that consist of charged particles and in particular positively charged particles such as protons and carbon ions or other cations.
  • Predominantly monoenergetic proton or cation beams ie those with predominantly uniform energy show a so-called Bragg curve in the depth dose distribution with a steep increase in the absorbed dose, ie the absorption, in the form of a peak (also referred to as a Bragg peak) at the end of the running distance.
  • a peak also referred to as a Bragg peak
  • the number and layer thickness of the plates used can be used to simulate the absorption behavior of particle radiation in a certain section of water.
  • the manufacturing costs for an MLFC are high.
  • the energy of the particle radiation to be determined is also limited to the thickness of the pre-absorber, which brings the Bragg peak into the measuring range of the MLFC.
  • the resolution of a measurement is 0.1 mm and the measurement duration is in the range of 10 s - 20 s.
  • only the Bragg peak is recorded, which means a limitation of the information.
  • Torino Srl offers a medical device (“QEye”) for energy determination and depth dose distribution of particle radiation, in particular proton beams, based on MFC technology with 512 channels. The resolution is 0.12 mm.
  • Ionization chambers in conjunction with different phantoms are also used in a variety of ways to detect particle beams, such as in Article 2 by J. Medin et al. (Ionization chamber dosimetry of proton beams using cylindrical and plane parallel chambers. Nw versus NK ion chamber calibrations, Physics in Medicine & Biology, Vol. 40, 1995, pp. 1161 - 1176). Measurements of this type are disadvantageously associated with long measurement times.
  • ionization chambers instead of ionization chambers, other detection systems, such as diodes or camera systems, such as so-called CCD (Charge Coupled Device) cameras, can also be used, as for example in article 3 by S. Beddar et al. (Exploration of the potential of liquid scintillators for real-time 3D dosimetry of intensity modulated proton beams, Medical Physics, Vol.36, No.5, 2009, pp.1737 -1743) in combination with a scintillator. Such measurements also have the disadvantage of long measurement times. In paper 4 by Y. Fukushima et al.
  • the object of the present invention is to provide a device for energy determination and determination of a depth dose distribution of particle radiation, which provides results for the energy and depth dose distribution of particle radiation in an energy range that is expanded compared to the prior art, for a shorter period of time compared to the prior art delivers and can also be produced at low cost.
  • the task is solved by claim 1.
  • Advantageous refinements are the subject of the dependent claims.
  • the device according to the invention for determining energy and determining a depth dose distribution of particle radiation comprises at least the components listed below.
  • the device initially has a phantom, which in particular, as also corresponds to an embodiment, is formed from a water-equivalent material and which has at least a first and a second surface which are arranged at a 90 ° angle to one another and has the shape of a wedge .
  • the first and second surfaces are advantageously designed to be square.
  • the first surface is intended for the vertical incidence of a particle beam and the second surface is intended to be arranged parallel to a flat, spatially resolving radiation detector.
  • the wedge further comprises a third surface, which is arranged opposite the 90 ° angle between the first and second surfaces and, together with the first and second surfaces, completes an irregular triangular prism, which in the case of the wedge is also formed by two lateral surfaces (base surfaces of the prism ) is completed.
  • the volume of the phantom is designed so that it can accommodate a particle beam over the entire path of the volume to be irradiated by the particle beam, ie the entire beam from the first surface to complete absorption or, in the case of electrons, at least one sufficient Absorption includes.
  • the volume must therefore be adapted to the energy and diameter of the particle beam if necessary.
  • the material is in particular, as also corresponds to one embodiment, a plastic or similar material which has a permeability for ionizing radiation from a source used that is comparable to that of living tissue.
  • a phantom In radiation medicine, such a phantom is also referred to as a water phantom if it is predominantly made of water.
  • Common water-equivalent plastics include those from the incomplete group polymethyl methacrylate (PMMA, also known as “Plexiglas®”), polyethylene, polystyrene, epoxy resins, urethane and petroleum jelly.
  • PMMA polymethyl methacrylate
  • the material of the phantom is advantageous Radiation-hard, ie durable against particle radiation but also against electromagnetic radiation.
  • An interaction layer which comprises at least one phosphor is applied to the third surface of the wedge.
  • a phosphor in the sense of the invention is a material that, when charged particles pass through, is converted into an excited state through interaction with the particles in the form of collision processes, which spontaneously relaxes with the emission of electromagnetic radiation, usually in the spectrum of visible light (Fluorescence).
  • the interaction layer can be in the form of a film which is arranged on the third surface of the wedge.
  • the interaction layer can also be deposited on the third surface of the wedge.
  • the material of the interaction layer is advantageously radiation-hard, ie durable against particle radiation but also against electromagnetic radiation.
  • Materials that are suitable for a phosphor are in particular those that emit spontaneously, such as those of the unfinished group consisting of: cesium iodide doped with thallium (Th:CsI), cesium iodide (CsI), gadolinium oxysulfide doped with terbium (Tb:Gd2O2S) , bismuth germanium oxide (Bi 4 Ge 3 O 12 ), barium fluoride (BaF), yttrium aluminum garnet (Y 3 Al 5 O 12 ), calcium tungstate (CaWO 4 ), calcium fluoride doped with europium (Eu:CaF 2 ) .
  • the phosphor can also be produced from an organic scintillator in conjunction with another fluorescent material.
  • a correction of the signals obtained regarding undesired effects, in particular the so-called “quenching”, may have to be carried out, as described, for example, in article 5 by L. Kelleter and S. Jolly (A mathematical expression for depth-light curves of therapeutic proton beams in a quenching scintillator, Medical Physics, Vol. 47 (5), 2020, pp. 2300 - 2308) and is otherwise known to the person skilled in the art.
  • the interaction layer is always arranged on the third surface of the wedge in such a way that it extends to the common edge of the third and first surfaces of the wedge.
  • the interaction layer advantageously covers the entire third surface of the wedge. Calculations for dimensioning the wedge and the interaction layer so that a particle beam lies in the volume of the phantom over its entire path and can be detected by the interaction layer do not have to be carried out separately between the interaction layer and the wedge.
  • the material of the phantom must be largely transparent (> 95%) to the electromagnetic radiation (usually in the visible light spectrum) emitted by the interaction layer during irradiation.
  • a radiation detector for the spatially resolved detection of photons such as, for example, through a so-called CCD camera or, advantageously, through an active pixel detector in CMOS (complementary metal-oxide-semiconductor ) technology is given.
  • CCD camera compact metal-oxide-semiconductor
  • Other detector systems such as so-called imaging plates, X-ray films or similar are possible, but may require adjustment in the evaluation.
  • the detector must be sensitive to at least an expected intensity range and energy range of an incident electromagnetic radiation (photons, mostly in the spectrum of visible light) emitted by the interaction layer.
  • the spatially resolved detection must also be designed in such a way that a depth dose distribution that occurs depending on the particle radiation to be characterized, for example in the form of a Bragg curve, of a particle beam can be represented with sufficient resolution, usually in a range of 0.01 mm 2 /pixel - 1 mm 2 /pixel.
  • the surface of the spatially resolving radiation detector is arranged parallel to the second surface of the phantom.
  • the size of the area of the spatially resolving radiation detector is to be adapted to the penetration depth (travel distance) of a particle beam in the phantom and its diameter perpendicular to it, taking into account an objective possibly arranged between the phantom and the detector, as corresponds to one embodiment (see below). These sizes are usually in the range of a few centimeters.
  • the particle beam to be characterized is a homogeneous beam. Beam width and travel distance must also correlate with the dimensions of the phantom and the interaction layer. If necessary, the diameter of the particle beam must be adjusted to the phantom size, for example by trimming it with an aperture.
  • a lens must also advantageously be arranged between the phantom and the spatially resolved radiation detector, which concentrates the electromagnetic radiation from the interaction layer and images it onto the radiation detector, so that a favorable ratio of image and image on the radiation detector is achieved, as is also the case in one embodiment corresponds.
  • the distance between the lens and the phantom and/or the radiation detector must therefore also be adapted to the travel distance of the particle beam in the phantom.
  • the sizes of the first and second surfaces of the phantom and the size of the interaction layer as well as their angles formed with the surface normals of the first and second surfaces correspond to a diameter and a penetration depth in the phantom of a particle beam to be characterized with the device with regard to a depth dose distribution to adapt.
  • the interaction layer is therefore arranged at an angle to the first surface, which allows the irradiated volume formed in the phantom to be completely traversed by a particle beam incident perpendicularly onto the first surface up to its maximum or at least achievable (in the case of electrons) penetration depth Direction of the particle beam is guaranteed.
  • the device must therefore be adapted to an energy range that determines the penetration depth in the phantom and the diameter of the particle beam to be characterized by the device.
  • the magnitudes and ranges of these parameters of a particle beam are known to the person skilled in the art through other determinations, at least to a sufficient approximation, or can be determined separately experimentally.
  • the irradiated volume that can be generated by a particle beam of given energy and diameter in a material from which the phantom is formed should advantageously be completely encompassed by the phantom of the device.
  • the interaction layer is arranged between two identical wedges.
  • the first surface of the phantom of the device is to be aligned perpendicularly to an incident particle beam provided and in such a way that the particle beam detects the interaction layer and the edge of the first and third surfaces of the wedge is always included, so that the zero point of the path of the particle beam in the phantom is always captured by the interaction layer.
  • the diameter of the particle beam is smaller than the dimensions of the first surface and can be detected entirely by the interaction layer. The dimensioning of the particle beam can be influenced and adjusted using apertures.
  • the particle steel then forms in the wedge of the phantom a volume irradiated by it, which is limited along the entire running distance by the interaction layer, depending on the running distance already covered.
  • the particle beam causes the emission of electromagnetic radiation in the interaction layer (usually in the spectrum of visible light) and this in accordance with the depth dose distribution, i.e. the absorbed radiation energy at the respective location on the path of penetration of the beam up to its maximum penetration depth.
  • the device according to the invention is housed in a housing for shielding the influence of electromagnetic radiation (light), which has an opening as a beam inlet opposite the first surface of the phantoms. All components of the device are arranged within the shield.
  • the spatially resolving radiation detector is usually provided with readout electronics and is connected to a data processing and graphical display device for data processing.
  • the advantage of the device according to the invention lies in particular in the measurement time of ⁇ 1 second caused by the choice of the phantom with an interaction layer, the type of interaction layer and the spatially resolving radiation detector.
  • the device is inexpensive and simple to construct and easy to adapt to given conditions. Exemplary embodiment The invention will be explained in more detail in an exemplary embodiment and with reference to two figures.
  • the figures show: Fig.1: Schematic representation of a cross section through the device according to the invention with a) a higher energy incident particle beam and b) a particle beam with lower energy than in a).
  • Fig.2 Depth dose distribution of a particle beam (count rate vs. extent along the travel route); Evaluation from a measurement with the device according to the invention a) according to Fig.1a) and b) according to Fig.1b).
  • the phantom 1 is made of polymethyl methacrylate and has the dimensions of width (b) 5 cm, height (h) 3 cm and depth (perpendicular to the leaf plane) 3 cm and is formed from two wedges.
  • the interaction layer 2 is provided by a film that uses terbium as a phosphor doped gadolinium oxysulfide includes (Tb:Gd2O2S).
  • the interaction layer 2 is arranged at an angle ⁇ of 15° to the second surface 2F of the phantom 1 on the third surface 3F and extends from one edge to the diagonally opposite edge (figure not to scale).
  • the wedge which is formed from the first surface 1F, the second surface 2F and the third surface 3F, can be seen.
  • a second wedge is arranged so that the interaction layer 2 lies between the wedges.
  • the spatially resolving radiation detector 3 is provided by a commercially available digital camera based on CMOS technology with an integrated lens, which has 1.3 MP with a resolution of 1280x1024 and an image frequency of 85 fps, with a minimum illumination duration of 11 ⁇ s.
  • the device is arranged within a shield 4 made of metal, which has an opening 5 for the inlet of a particle beam and otherwise completely surrounds the device and protects it from light.
  • the opening 5 is arranged opposite the first surface 1F of the phantom 1, so that a particle beam can be irradiated perpendicularly onto the first surface 1F of the phantom 1.
  • Incident particle beams solid lines are also shown in Fig. 1 for illustration purposes.
  • a particle beam which in the exemplary embodiment is a proton beam, is shown with an energy of 68 MeV, which is sufficient for the beam's travel distance to end after 3.5 cm.
  • the diameter of the beam is 10 mm (illustration is not to scale).
  • the proton beam has a lower energy of 50 MeV, with the same diameter. The running distance ends here after 2.1 cm. This means that only part of the beam is evaluated.
  • FIG. 2 shows the evaluation of the depth dose profile of the particle beams, which in the exemplary embodiment are proton beams for a) Fig.1a) and b) Fig.1b).
  • the Plot corresponds to count rate ([au]) over the distance in the image of the detector in mm.
  • the depth dose profile (---) is shown along the running route and, on the other hand, the cross section ( ⁇ ⁇ ⁇ ) of the image of the particle beam on the detector 3.
  • the extent of the depth dose profile begins after the first peak, which results from a reflection within the Wedge results and ends at the top of Bragg Peak.
  • the cross section is obtained from a cut across the path of the particle beam and the depth dose profile is obtained from the summation over the cross section in the image in the detector.
  • the underlying recordings with the radiation detector for the evaluation were each taken in a time of 1 second.
  • the invention advantageously combines a cost-effective, simple and time-saving detection of an energy and a depth dose profile of a particle beam.

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  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Molecular Biology (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Radiation-Therapy Devices (AREA)
  • Measurement Of Radiation (AREA)

Abstract

L'invention concerne un dispositif de détermination d'énergie et de détermination d'une distribution de dose de profondeur de rayonnement de particules, comprenant au moins un détecteur de rayonnement (3) ayant une lentille d'objectif pour la détection à résolution spatiale de photons et un fantôme (1) qui est sous la forme d'un coin et présente une première et une deuxième face (1F, 2F) agencées à un angle de 90° l'une par rapport à l'autre, une troisième face 3F opposée à l'angle formé par les première et deuxième faces (1F, 2F), ainsi qu'une couche d'interaction (2) au moins constituée d'un matériau luminescent. Selon l'invention, la couche d'interaction (2) est agencée sur le fantôme (1) sur la troisième face (3F) et la deuxième face (2F) est parallèle à un plan du détecteur de rayonnement (3).
PCT/DE2023/100332 2022-05-10 2023-05-09 Dispositif de détermination d'énergie et de détermination d'une distribution de dose de profondeur de rayonnement de particules Ceased WO2023217320A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
EP23729935.9A EP4523014A1 (fr) 2022-05-10 2023-05-09 Dispositif de détermination d'énergie et de détermination d'une distribution de dose de profondeur de rayonnement de particules

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DEDE102022111674.3 2022-05-10
DE102022111674.3A DE102022111674A1 (de) 2022-05-10 2022-05-10 Vorrichtung zur Energiebestimmung und Bestimmung einer Tiefendosisverteilung von Teilchenstrahlung

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Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2005119295A1 (fr) * 2004-06-04 2005-12-15 Bc Cancer Agency Procede et appareil permettant de verifier des distributions de doses de rayonnement
WO2014189260A1 (fr) * 2013-05-23 2014-11-27 국립암센터 Dispositif de mesure de dose de rayonnement apte à un fonctionnement horizontal et rotationnel et dispositif de détection de rayonnement associé
CN110988957A (zh) * 2019-12-24 2020-04-10 深圳大学 一种基于质子辐照源的深度剂量分布的测量装置及方法

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2005119295A1 (fr) * 2004-06-04 2005-12-15 Bc Cancer Agency Procede et appareil permettant de verifier des distributions de doses de rayonnement
WO2014189260A1 (fr) * 2013-05-23 2014-11-27 국립암센터 Dispositif de mesure de dose de rayonnement apte à un fonctionnement horizontal et rotationnel et dispositif de détection de rayonnement associé
CN110988957A (zh) * 2019-12-24 2020-04-10 深圳大学 一种基于质子辐照源的深度剂量分布的测量装置及方法

Non-Patent Citations (5)

* Cited by examiner, † Cited by third party
Title
VON C. KUNERT ET AL.: "A Multi-leaf Farraday Cup Especially for the Therapy of Ocular Tumors with Protons", 5TH PROCEEDINGS OF THE INTERNATIONAL PARTICLE ACCELERATOR CONFERENC 2014 (IPAC'14, June 2014 (2014-06-01), pages 2149 - 2152
VON J. MEDIN ET AL.: "lonization chamber dosimetry of proton beams using cylindrical and plane parallel chambers. Nw versus NK ion chamber calibrations", PHYSICS IN MEDICINE & BIOLOGY, vol. 40, 1995, pages 1161 - 1176
VON L. KELLETERS. JOLLY: "A mathematical expression for depth-light curves of therapeutic proton beams in a quenching scintillator", MEDICAL PHYSICS, vol. 47, no. 5, 2020, pages 2300 - 2308
VON S. BEDDAR ET AL.: "Exploration of the potential of liquid scintillators for real-time 3D dosimetry of intensity modulated proton beams", MEDICAL PHYSICS, vol. 36, no. 5, 2009, pages 1737 - 1743, XP012130007, DOI: 10.1118/1.3117583
Y. FUKUSHIMA ET AL.: "Development of an easy-to-handle range measurement tool using a plastic scintillator for proton beam therapy", PHYSICS IN MEDICINE AND BIOLOGY, vol. 51, 2006, pages 5927 - 5936, XP020096044, DOI: 10.1088/0031-9155/51/22/014

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DE102022111674A1 (de) 2023-11-16
EP4523014A1 (fr) 2025-03-19

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