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    • 专利摘要:
    Compact gantry for particle therapy. The present invention relates to a particle therapy apparatus for use in radiation therapies. More specifically, this invention relates to an isocentric compact gantry for emitting particle beams perpendicular to a gantry rotation axis. The gantry comprises three bipolar magnets. the angle of the last bipolar magnet is less than 90 °, and one of the preferred angles of inclination for the latter bipolar magnet is 60 °.
    公开号:BR112012006799B1
    申请号:R112012006799-0
    申请日:2010-09-24
    公开日:2018-01-16
    发明作者:Jongen Yves
    申请人:Ion Beam Applications；
    IPC主号:
    专利说明:

    (54) Title: COMPACT GANTRY FOR PARTICULATE THERAPY (51) lnt.CI .: A61N 5/10; G21K 1/093; G21K 5/04 (30) Unionist Priority: 28/09/2009 EP 09171550.8 (73) Holder (s): ΙΟΝ BEAM APPLICATIONS (72) Inventor (s): YVES JONGEN / 20
    COMPACT GANTRY FOR PARTICULATE THERAPY
    FIELD OF THE INVENTION [0001] The present invention relates to an apparatus for therapy with charged particles, used for radiation therapies. More specifically, this invention relates to a compact gantry for the emission of particle beams.
    BACKGROUND OF THE INVENTION [0002] Radiotherapy with the use of charged particles (such as protons, carbon ions, etc.) has been shown to be a precise and conformational technique of radiotherapy, capable of enabling the emission of a high dose for a target volume, as well as minimizing the dose emitted to healthy tissues that surround it. An apparatus for particle therapy comprising an accelerator that produces charged energetic particles, as well as a beam transport system to guide the particle beam towards one or more treatment rooms, and, for each treatment room, a system particle beam emission. It is possible to distinguish two types of beam emission systems, namely: fixed beam emission systems, which emit the beam to the target from a fixed irradiation direction, and rotary beam emission systems, which are capable of beam the beam to the target from multiple directions of radiation. Such a rotating beam emission system is also called gantry. The target is usually located in a fixed position, defined by the cross between the axis of rotation of the gantry and the central axis of the beam. The crossing point is designated as an isocenter, and the aforementioned type of gantry, capable of emitting beams from different directions to the isocenter, is called an isocentric gantry.
    [0003] The gantry beam emission system comprises devices designed to shape the beam, so that it fits the target. The two main techniques used in particle beam therapy to shape the beam are as follows: the most common passive dispersion techniques and the most advanced dynamic radiation techniques. An example of the dynamic radiation technique is the so-called “pen beam” (PBS) scanning technique. In the technique of
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    PBS, a narrow pen-shaped beam is scanned magnetically over an orthogonal plane, towards the central beam. Lateral compliance in the target volume is achieved through an adequate control of the scanning magnets. By varying the energy of the particle beam, it is then possible to irradiate different layers in the target volume, which are characterized by the fixed energy of their particles. In this way, the radiation dose of the particles can be emitted to the entire target volume in 3D.
    [0004] The energy levels that have to be presented by the particle bundle in order for them to reach a sufficiently deep penetration in the patient depend on the type of particles used. For example, for proton therapies, the beam energy usually varies between 70 MeV and 250 MeV. The depositor built proton gantries, to be used with proton beam energy levels up to 235 MeV. Such a gantry, whose model is shown in Fig. 1, had its configuration described by JB Flanz in “Large Medical Gantries”, in the procedures brought up during the 1995 Conference on Particle Accelerators, Volume 3, pages 2007-2008. In this gantry, the beam is first focused by a series of quadrupoles, before being deflected by means of a 45 ° bipolar magnet 12, and then it is focused by 5 quadrupole magnets 19, before being tilted by by means of a 135 ° bipolar magnet 15, and directed towards the isocenter (perpendicular to the axis of rotation). This gantry also comprises two scanning magnets 18 intended to scan the beam in two orthogonal directions, for use in scanning the pen beams. Thanks to the long distance of 3 meters between the last tilt magnet of 135 ° and the isocenter, these scanning magnets 18 are mounted in a downward direction, starting from the last tilt magnet. Between the last tilt magnet 15 and the scanning magnets 18, two other quadrupole magnets 19 are installed. The disadvantage of this gantry consists of its large dimensions: an approximate diameter of 10m, and a length of more than 10m. This gantry also implies a high manufacturing cost.
    [0005] A more recent overview of gantries for proton therapies and
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    3/20 carbon is supplied by U. Weinrich, in “Gantry design for proton and carbon hadrontherapy facilities”, EPAC 2006 Procedures (European Conference on Particle Accelerators), in Edinburgh, Scotland. As shown, all proton isocentric gantries have longitudinal dimensions from 9 to 12m, as well as a maximum radial displacement of the beam from the axis of rotation of the gantry that varies between 3.2m and 5m.
    [0006] A particle rotation gantry has a beam rotation line that generally comprises a vacuum tube for transporting the particle beam in a vacuum, as well as several quadrupole magnets to focus and defocus the particle beam, various magnets to tilt the beam of particles and monitors to monitor the beams. The category of rotary gantries covered in this application falls under that of the so-called rotary gantries in a single plane, which comprise bipolar magnets configured so that the inclination in each bipolar magnet of the gantry beam line is carried out in the same plane. This category of gantries in a single plane is distinguished from another category, that of the so-called “stopper-screw” gantries, which have two orthogonal planes of inclination. In the category of gantries in a single plane, there are currently two main configurations, whose schematic representation, shown in Fig. 1B, illustrates the central paths followed by the beams in these gantries. The beam enters the gantry substantially parallel to the axis of rotation, at the coupling point or at the entry point 11, and initiates a first section of straight line of beams, before introducing into a first bipolar magnet 12 , 13. This coupling or entry point is defined as the transition between the fixed part of a beam line and the beam line of the rotating gantry. The difference between the two main configurations of the gantries in a single plane concerns the number of bipolar magnets installed in the gantry. The inclination plane of the gantry dipole in a single plane is also referred to as the “horizontal” plane, while the non-inclined plane is called the “vertical” plane or Y plane.
    [0007] The first major configuration in the category of gantries in a single plane is the so-called conical gantry. An example of this is the proton gantry
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    4/20 built by the depositor, and shown in Fig. 1 A. The central beam path followed by a proton beam in said gantry is shown in Fig. 1B, in the form of a dotted line. A first 45 ° bipolar magnet 12 tilts the beam out of the axis of rotation of the gantry, and then the beam follows a second straight line section of beams, before entering the second 135 ° bipolar magnet 15, which it will be tilting and directing the beam substantially perpendicular to the axis of rotation. The intersection between the beam and the axis of rotation of the gantry is called the treatment center 17. The target to be irradiated is positioned in the treatment center. In the conical gantry configuration constructed by the depositor (Fig. 1 A), the beam section in a straight line between the coupling point and the first 45 ° bipolar magnet 12 comprises four quadrupole magnets, and the second section in a straight line between the the first bipolar magnet 12 and the second bipolar magnet 15 comprise five quadrupole magnets (Fig. 1B does not show any quadrupole magnet). The conical gantry configuration constructed by the depositor is also discussed by Pavlovic, in “Beam-optics study of the gantry beam delivery system for light-ion cancer therapy, Nucl. Instr. Meth. In Phys. Res. A 399 (1997), on page 440.
    [0008] The second most relevant configuration in the category of gantries in a single plane is the so-called cylindrical gantry, also known as barrel-shaped gantry. The main path of the bundles in a cylindrical gantry is also illustrated in Fig. 1B, where the bundle, represented by a solid line, enters the gantry at the coupling point 11, and travels through a first section in a straight line of bundles, before introducing on the first bipolar magnet 13, such as, for example, a first 60 ° magnet, which is tilting the beam out of the rotation axis, followed by a second straight section of beams, before entering the second magnet bipolar 14, endowed with the same angle of inclination, but placed in an opposite direction, which leads to the propagation of a beam in a third section in a straight line of bundles, parallel to the axis of rotation of the gantry. Then, a third 90 ° bipolar magnet is also used to tilt the beam in a direction perpendicular to the axis of rotation. The three straight sections of beams comprise two, two and three quadrupole magnets respectively
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    5/20 (not shown in Fig. 1B). This cylindrical gantry configuration illustrated in Fig. 1B corresponds to the proposed geometry for the proton Gantry 2 PSI, discussed by Weinrich (page 966-967 and Figure 8 on page 966). Among all the configurations of isocentric gantries discussed by Weinrich, the gantry that has the smallest maximum radial displacement of beams from its axis of rotation (which will also be referred to as the radius of the gantry) is obtained from the design proposed for Gantry 2 Proton PSI, as mentioned above. From this geometry, a gantry radius of 3.2m is obtained (last column of Table 2 on page 967). [0009] A variant of cylindrical gantry consists of the so-called oblique gantry, presented by M. Pavlovic in “Oblique gantry- an alternative solution forabeam delivery system for heavy-ion cancer therapy, Nucl. Instr. Meth. in Phys. Res. A 434 (1999), on pages 454-466. As with standard cylindrical gantry, the oblique gantry also comprises three bipolar magnets, where the first two have the same inclination angles, although they are in opposite directions, which leads to the beam spreading in a direction between the second and third bipolar magnets that is parallel to the axis of rotation of the gantry (see Pavlovic et al, Fig. 3 on page 460). The third bipolar magnet has an angle less than 90 ° (for example, 60 °) and, as a result, the final beam is not emitted perpendicular to the axis of rotation of the gantry, as occurs in the case of the standard cylindrical gantry discussed above . On the contrary, the final beam is emitted to the isocenter, forming an angle other than 90 ° with the gantry axis. For example, the beam is emitted at an angle of 60 °, if this is the angle of inclination of the third bipolar magnet. The disadvantage of such an oblique gantry is that it is impossible to cover all treatment angles without the need to move the patient. For example, in the case of a 60 ° oblique gantry, the treatment angle is restricted to the sector ranging from -60 ° to + 60 ° (see page 463, section 4, first sentence).
    [0010] In patent application EP1041579A1, other examples of cylindrical gantry configurations are shown. In Fig. 1B of this patent application, a cylindrical gantry is shown according to the specifications in Table 2: the first and second bipolar magnets have a tilt angle of 42 °,
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    6/20 while the third has a 90 ° tilt angle. As mentioned in the summary of this patent application, other configurations are designed in advance, namely, a first bipolar magnet with an angle of inclination in the range between 40 ° and 45 °, and a second bipolar magnet with an angle of inclination identical to the first, to tilt the beam parallel to the axis of rotation of the gantry. The third tilt magnet has a tilt angle in the range between 45 ° and 90 °, in order to tilt the beam forward and promote the intersection of the beam with the axis of rotation of the gantry. As discussed above, if the last tilt magnet has a tilt angle of less than 90 ° (ie the so-called oblique gantry), the beam will not be emitted perpendicular to the axis of rotation of the gantry. Again, the disadvantage of such an oblique gantry configuration is that it is impossible to cover all treatment angles.
    [0011] Both the tapered gantry developed by the depositor and shown in Fig. 1A and the cylindrical configuration of gantry 2 PSI (see Weinrich, Fig. 8, pg. 966) were designed to be used with a pen beam scanning system . In the conical gantry configuration between 45 ° and 135 °, the scanning magnets for scanning the beam in the horizontal (also called X direction) and vertical (also called Y direction) planes are installed downwards, starting from the bipolar magnet of 135 °. A disadvantage of such a gantry configuration is the need for a wide spacing between the outlet of the last tilt magnet (in this example, the 135 ° magnet) and the gantry isocenter, which leads to the formation of a wide gantry radius R The scanning magnets must be installed at a certain distance from the isocenter (for example, at least 2m), in order to reach a sufficient distance SAD (distance from the source to the axis). The higher the SAD, the lower the dosage on the skin. As shown in Fig. 1B, in cases involving this type of conical gantry, the radius of the gantry, defined as the maximum beam distance to the axis of rotation of the gantry, corresponds to the approximate value of 4.5m.
    [0012] In the cylindrical configuration of the gantry 2 PSI, the scanning magnets 18 are installed between the second 60 ° bipolar magnet 14 and the
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    7/20 last bipolar magnet 16 of 90 °. One of the main disadvantages of this gantry configuration is the fact that the last 90 ° tilt magnet requires a wide (vertical) slot and a thick (horizontal) pole, in order to be able to scan the beam over a large target area in the isocenter (for example, 25cm x 20cm, or 40cm x 30cm). As a result, such a 90 ° bipolar magnet becomes long and heavy, and energy consumption is high. Such a 90 ° magnet can weigh up to 20 tons. A second disadvantage lies in the relatively long length of the parallel section of straight lines between the second 60 ° bipolar magnet and the last 90 ° inclination magnet, which implies long axial dimensions of the gantry. This 2 PSI gantry has an axial length, thus defined as the axial distance between the coupling point 11 and the isocenter, of 11.6m, as described by Weinrich (Table 2, page 966). Such a cylindrical gantry configuration, equipped with a last 90 ° tilt magnet, is also discussed in US patent no. US7348579. [0013] The present invention is intended to provide a device that circumvents the problems presented by the prior art. One of the objectives of this invention is to design a gantry that can be built at a reduced cost, when compared to the gantries provided for in the prior art, and where the energy consumption of the last bipolar magnet is reduced. Another objective is still to reduce the total size of the gantry, so that the volume of the treatment room and, therefore, also the costs with its construction can be reduced.
    SUMMARY OF THE INVENTION [0014] The present invention is described and characterized by the appended claims.
    [0015] According to a first aspect of the invention, there is an isocentric gantry, designed to rotate around an axis of rotation and to emit a beam of particles to be used in particle therapies. This isocentric gantry comprises:
    • a line of gantry beams, with an entry point in the gantry to allow the entry of said particle bundle into the gantry, in a
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    8/20 direction substantially parallel to the axis of rotation;
    • a first, a second, and a third bipolar magnet arranged in sequence, to tilt the particle beam successively in a single plane, and to emit said particle beam to an isocenter, in a direction substantially perpendicular to the axis of rotation ;
    • quadrupole magnets to focus and blur said beam of particles;
    said isocentric gantry further characterized by comprising said third bipolar magnet having an inclination angle of less than 90 °, preferably less than 80 °, and even more preferably less than 70 °. [0016] More preferably, the third bipolar magnet has an inclination angle of 60 °.
    [0017] More preferably, a section of beam lines between the mentioned entry point of the gantry and an entrance of the first bipolar magnet consists of a section of short pulses, which means that between the entry point and the entrance of the first bipolar magnet, there is no quadrupole magnet installed.
    [0018] Even more preferably, the section of beam lines between the first and the second second bipolar magnets comprises five quadrupole magnets, while the section of the beam lines between said second and said third bipolar magnets does not comprise any magnet. quadrupole.
    [0019] Even more preferably, the isocentric gantry comprises means for rotating the gantry over a range of angles of at least 180 °.
    [0020] The gantry according to the invention can also comprise means for scanning particle bundles, which are installed between said second bipolar magnet and said third bipolar magnet and configured to scan said particle bundle over an area target in the isocenter, or even means for the dispersion of particle beams, adapted to emit a very broad beam in the isocenter.
    [0021] In accordance with a second aspect of the invention, a
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    9/20 apparatus for particle therapies, comprising a particle accelerator, as well as means for promoting the variation of energy of the particles, a beam transport system and an isocentric gantry according to the first aspect of the invention.
    Brief Description of the Drawings [0022] Fig. 1A illustrates a representation of a gantry configuration according to the prior art.
    [0023] Fig. 1B shows a schematic representation of the paths followed by a particle beam, in two gantry configurations according to the prior state of the technique.
    [0024] Fig. 2 shows a schematic representation of the layout of an example of gantry according to the invention.
    [0025] Fig. 3 presents the results of a beam optics calculation for the gantry of Fig. 2.
    [0026] Fig. 4 shows the results of a beam optics calculation when scanning the beam in the gantry of Fig. 2.
    [0027] Fig. 5 presents a conceptual view of an example of the mechanical structure of a gantry according to the invention.
    [0028] Fig. 6 presents a layout of a treatment room that used the gantry provided in the previous state of the art, as well as the layout of a treatment room equipped for the use of a gantry according to the invention.
    [0029] Fig. 7 shows the central beam path, followed by a proton beam for various gantry configurations according to the invention.
    DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS OF THE PRESENT INVENTION [0030] Below, the present invention will be described in detail with respect to the attached drawings. However, anyone skilled in the art will obviously be able to design equivalent embodiments or, further, other means of carrying out the present invention.
    [0031] Firstly, an example of gantry in a single plane is presented, which includes a pen beam scanning system and which
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    10/20 is also compact, has a low weight, and implies a lower production cost and reduced energy consumption. Fig. 2 presents a preferred layout of such a gantry, which is represented at a 90 ° angle (that is, when looking in a direction parallel to the axis of the gantry, starting from the isocenter 27 towards the first bipolar magnet 20, the gantry is is at the three o'clock position). The gantry has three bipolar magnets 20, 21, 22, being provided with means 23 for scanning the X and Y beam, which are installed between the second bipolar magnet 21 and the third bipolar magnet 23. Between the first bipolar magnet 20 and the second bipolar magnet 21, quadrupole magnets 24 are installed. The section of beam lines between the entry point of gantry 25 and the entrance of the first bipolar magnet 20 preferably consists of a section of short pulses, which does not comprise any quadrupole magnet. As illustrated in the dotted lines of Fig. 2, the general appearance of this gantry, when rotating, can be compared to that of a double cone, where the first cone presents its apex at the level of the coupling point 25, being provided with a base perpendicular to the axis of rotation of the gantry, and crossing the second bipolar magnet 21 in a position where the beam has formed a first angular rotation corresponding to the angle of the first bipolar magnet. The second cone consists of a truncated cone, whose base coincides with that of the first cone, and whose apex is limited by a plane parallel to the plane of the base, as shown in Fig. 2.
    [0032] In a preferred embodiment of the invention, the third bipolar magnet 22 has a tilt angle of 60 °, while the first bipolar magnet 20 has a tilt angle of 36 °. Therefore, the inclination angle of the second magnet is calculated to correspond to 36 ° + 90 ° - 60 ° = 66 °. Between the second 21 and the third 22 bipolar magnets, means can be offered for scanning the X and Y particle beam. As the case may be, a combined XY scanning magnet can be used preferably for this purpose, as it takes less space that two isolated scanning magnets for the X and Y directions. The length of the first straight section of beams between the entry point of the gantry (25) and the first bipolar magnet (20) corresponds to the approximate value of 0.4 m , this being a
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    11/20 pulse only section (ie, there is no quadrupole magnet installed in this section). In a preferred embodiment of the invention, five quadrupole magnets are installed between the first 36 ° bipolar magnet 20 and the second 66 ° bipolar magnet 21. The space available for installing these quadrupole magnets, that is, the length of the section of straight lines between the first and the second bipolar magnets corresponds to the approximate value of 3.5m. The length of the section of straight beam lines between the second 66 ° bipolar magnet and the third 60 ° bipolar magnet corresponds to the approximate value of 0.8m. The distance between the outlet of the last 60 ° tilt magnet 22 and the isocenter 27 corresponds to an approximate value of 1m, which allows enough space to be installed to install not only the patient, but also some devices, such as monitors. detection between the output of the 60 ° bipolar tilt magnet 22 and the patient (such as, for example, monitors for dose detection and / or beam positioning). Table 1 summarizes the main characteristics of a magnet designed to be used as the last bipolar magnet 22 of the gantry according to the preferred embodiment of the invention. The example provided is for a design for particle beams with a magnetic stiffness of 2.3 Tm (such as 235 MeV protons). To restrict energy consumption, this magnet uses a wide cross-section, as well as saddle-shaped coils (also called head coils). As shown in Table 1, the weight of the magnet corresponds to the approximate value of 9.17 tons (including 2.05 tons from the coils), and the total energy of the magnet in a beam energized at 235 MeV is 226 kW. This 60 ° bipolar magnet has faces at the poles, which are rotated by 17 °, in order to offer yet another vertical focus, as will be discussed below.
    Generic characteristics Value unity Deflection angle 60 O Poles face rotation 17 O Slope radius 120 cm Slit (vertical) 20.00 cm Pole thickness (horizontal) 22.00 cm
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    12/20
    Generic characteristics Value unity Radial coil thickness 25.00 cm Flow return thickness 24 cm Middle field 1.92 T Total coil height 35.00 cm Poles thickness 7.50 cm Total magnet height 83.00 cm Steel weight 6866.97 kg Coil weight 1024.4 kg Total weight 9.17 Tons Total energy consumption 225.3 kW
    Table 1 [0033] Then, a preferential calculation is discussed for the beam optics in the gantry shown in Fig. 2. The entrance of the gantry, at the level of the coupling point 25, is defined as being the point located at 0.4m below the entrance of the first bipolar magnet 20. At the entrance of the gantry, the beam must present the same level of emissions verified in X and Y, in order to reach a solution for the beam optics that does not depend on the angle of gantry rotation. X and Y are now defined as the crossing of a plane perpendicular to the axis of the central beam's trajectory with the horizontal and vertical plan respectively. In addition to the same level of emissions in X and Y, a belt of identical size in X and Y is specified at entry point 25. From these initial conditions for that beam at the entrance to the gantry, it becomes necessary to meet a set of complementary prerequisites, namely:
    1. At isocenter 27, the bundle must have a small waist, identical in size to X and Y.
    2. The optical beam system of the gantry must be achromatic double, that is, the image properties of the beam must be independent of the impulse (without dispersion) and position.
    3. The maximum beam size (one sigma) inside the quadrupoles must not exceed 2 cm, in order to maintain a reasonable efficiency in the transmission inside the gantry.
    [0034] To meet these varied optical conditions, the field must be defined
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    13/20 magnetic in the five quadrupole magnets installed between the first and the second bipolar magnets. Other parameters that can be used to achieve an optimal optical solution are the angles of the pole faces of the bipolar magnets. A beam optics is calculated using a 170 MeV proton beam. The tilt radii for the first and second bipolar magnets are set at 1.5m. At the entry point of the gantry, it starts with a circular beam equipped with a double waist of 12.5mm in size, and a divergence of 0.6 mrad. This size and divergence correspond to an emission of 7.5 Pi mm mrad, which is a typical beam emission value, according to the current proton therapy systems developed by the depositor. For the first 36 ° bipolar magnet, a rectangular pole (with 18 ° rotating faces) was adopted, while for the second 66 ° bipolar magnet, a rotation of the pole face is used for entry and exit. output at 15 ° and 21 ° respectively. The resulting X and Y trajectory, and calculated according to the TRANSPORT code for beam optics, is shown in Fig. 3. More information on the TRANSPORT code can be found in DC Carey, KL Brown and F. Rothacker, “ Third-Order TRANSPORT -A Computer Program for Designing Charged Particle Beam Transport Systems, ”SLAC-R-95-462 (1995). The relative positions of the beams during the trajectory of the central beam are plotted in the X and Y directions, in the lower and upper panels of Fig. 3 respectively. The positions along the beam path of the quadrupole magnets 24 and bipolar magnets 20, 21, 22 are indicated. In Fig. 3, the position of the scanning magnets 23 is shown for information purposes only; in this calculation, scanning magnets are not taken into account (the effects of scanning magnets will be discussed below). In the isocenter 27, a circular beam spot is obtained, where the X and Y waist has an approximate size of 3.5 mm and an approximate divergence of 2.2 mrad, which constitute the appropriate beam measurements for beam scanning. in pen. This optical beam solution also meets the requirements of a double achromatic system.
    [0035] In addition to the need to obtain a beam spot size
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    14/20 in the isocenter that is suitable for use in pen beam scanning, it is also necessary to be sure about the possibility of obtaining a wide scanning area in the isocenter from the proposed geometry for the beam lines. The adaptation of the specifications to the field sizes results from the fact that a field of 25cm (X) x 20cm (Y) has to be covered by the isocentric plane, preferably requiring a SAD of sufficient size (namely, larger or equal to 2m). The geometry shown in Fig. 2 for the beam line, as well as the optical beam solution presented in Fig. 3, fulfill these requirements regarding the field size and the SAD. This statement is shown in Fig. 4, where the trajectory of a 170 MeV proton beam is calculated between the scanning magnets and the isocenter, while the beam is scanned at maximum amplitude, both in X and Y. In this calculation , the scanning magnets are deflecting the beam at 66 mrad in X, and at 50 mrad in Y, which are considered moderate inclination angles, which can be easily obtained from the technology already known in the area of scanning magnets. In Fig. 4, the positions of the scanning magnet 23 in X and Y are shown, as well as the last bipolar magnet 22 of 60 ° and the isocenter 27. The specifications of the 60 ° bipolar magnet referring to the edges of the poles, the radius of inclination, and the thickness of the slot and pole are given in Table 1. The distance between the center of the scanning magnet and the inlet of the 60 ° bipolar magnet corresponds to the approximate value of 0.4m, while the beam path center on the 60 ° bipolar magnet is approximately 1.25 m, taking a distance of 1.0 m between the exit of the 60 ° bipolar magnet and the isocenter. The calculations show that, in the isocentric plane perpendicular to the central beam, the beam size corresponds to 25cm in X and 22cm in Y, while the beam size at the exit of the 60 ° bipolar magnet is 17.2cm in X and 15.2 cm in Y. You can then calculate the virtual SAD, that is, the SAD obtained as if the beam had originated from a source point, without the presence of any magnetic element between it and the isocentre. This geometry now proposed leads to a virtual SAD that, in both X and Y, is greater than 3m. [0036] An example of mechanical design is now being debated for a
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    15/20 gantry, which corroborates the double cone gantry shown by the invention, and whose schematic representation is shown in Fig. 5. A plane structure made, for example, of metal beams 51, can be used to house all the magnets of the gantry , together with a counterweight 52. As a means of promoting rotation, two self-aligning spherical roller bearings and commercial pattern 53 are used. For the second roller bearing, located on the patient side, a fixed structure in the form of a swing 54 is used to support the main roller bearing, also allowing the gantry structure to be positioned under the bearing, in order to reach extreme angles of the gantry, up to 180 ° (upwards and vertically to the beam). At the level of the first bipolar magnet, a drum structure 55 is installed to support the cable spool. In addition, in a configuration not shown in Fig. 5, the gantry is equipped with a drive system and brakes for gantries, which consists of an assembly of a single motor-gearbox structure, connected to the gantry by a transmission chain. An advantage of the gantry configuration according to the invention is that the center of gravity of the last bipolar magnet is closer to the axis of rotation (compared to the example of gantry configuration based on the last 90 ° bipolar magnet, see Fig. 8 in Weinrich's publication), which leads to the reduction of obstacles related to the mechanical structure (for example, the counterweight can be placed closer to the axis of rotation, thus reducing the size of the gantry). The gantry can be rotated preferably by 190 °, that is, depending on the layout of the building, whether it is a configuration that rotates clockwise from 180 ° to 10 °, or a configuration that rotates, clockwise, 350 ° to 180 ° (angles are defined according to IEC International Standard 61217 for radiotherapy equipment - coordinates, movements and scales, 1996).
    [0037] This mechanical concept is intended to reduce costs with the mechanical structure of the gantry, while also allowing good accessibility to the patient. One of the main current components of costs with gantries structures (as, for example, for the 45 ° -135 ° conical configuration) is the need to rotate the gantry in large and very precise rings, which have to be built under
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    16/20 measure, and endowed with high solidity, made with steel resistant to use, and that are supported by complex tricks. Other cost components consist of the drive and brake mechanisms, developed through the cylinders of the gantrie bogies and where the torque is strictly restricted to the sliding of the cylinders; another cost element, finally, lies in the three-dimensional structure of the gantry.
    [0038] An apparatus for particle therapies comprises an accelerator that produces charged energetic particles, as well as means to promote the variation of the particle energy, a beam transport system to guide the beam to one or more treatment rooms and, for each treatment room, a particle beam emission system. The particle beam emission system can consist of either a gantry or a so-called fixed beam emission system. In general, treatment rooms containing gantries have required a large coverage area, and a significant volume of building. With the gantry design according to the invention, a smaller room for gantries can be used, compared to, for example, a configuration for 45 ° - 135 ° tapered gantries. This statement is illustrated in Figure 6 where, on the same scale, a coverage area 61 of a treatment room covering a conical gantry is shown, as well as a coverage area 62 of a treatment room covering an example of compact gantry in the form of a double cone, in line with the invention. With the gantry according to the invention, the gantry treatment room, with a coverage area of 10.5m by 6.4m, can be used as shown in Figure 6, while the current gantry treatment rooms , which use a conical configuration of 45 ° - 135 °, as presented by the depositor, require a coverage area of 13.7m by 10.7m.
    [0039] We now discuss how certain geometric dimensions, such as the radius and length of a gantry, are influenced by certain variable parameters of the preferred configuration of the gantry. According to the preferred configuration of the gantry according to the invention, which comprises three dipoles of 36 ° (= B1), 66 ° (= B2) and 60 ° (= B3) respectively, the length
    Petition 870170058759, of 08/14/2017, p. 27/42
    17/20 of the gantry, defined as the axial distance between the coupling point 25 and the isocenter 27, corresponds to the approximate value of 7.05m, and the radius of the gantry, defined as the maximum distance from the path of the central beam to the axis of rotation of the gantry, corresponds to the approximate value of 2.64m. In fact, such a radius is defined, on the one hand, by selecting the angle of inclination of the last bipolar magnet 22 and, on the other, by the spacing between the outlet of the last bipolar magnet 22 and the isocenter (the clearance of the isocenter) and the spacing between the second bipolar magnet 21 and the third and last bipolar magnet 22 (spacing B2-B3). According to the preferred geometry, these spacing corresponds to approximately 1m (clearance from the isocenter) and to approximately 0.8m (B2-B3 spacing). When the radius of the gantry is defined in this way, the only parameter that will still be able to influence the length of the gantry is the choice of the angle of inclination of the first bipolar magnet. As soon as the angle of inclination of the first bipolar magnet and the radius of the gantry are specified, the distance L1 between the first bipolar magnet 20 and the second bipolar magnet 21 will also be determined. In the preferred geometry, this distance corresponds to the approximate value of 3, 5 m. Obviously, other embodiments of the invention can be devised by adjusting these parameters that define the geometry of the gantry. For example, the top panel of Fig. 7 shows the geometry of the preferred configuration 36 ° - 66 ° - 60 °. For example, it is possible to slightly increase or decrease the angle of the first bipolar magnet 20, thus causing a decrease or an increase in the length of the gantry, as shown in the figure. The respective changes in the distance L1 are mentioned in figure 7. In the panel located in the central part of Fig. 7, the angle of the last tilt magnet was fixed at 45 °, maintaining the same clearance from the isocenter and the same distance B2-B3 that shown in configuration B3 = 60 °. Due to the reduction in the angle of inclination of the last bipolar magnet 22, the radius of the gantry is increased by approximately 0.2m. With a gantry configuration of 38 ° (B1) - 83 ° (B2) - 45 ° (B3), the length of the gantry is maintained at approximately 7m. In the third panel of Fig. 7, the angle of the last bipolar magnet is fixed at 70 °. With the maintenance of the isocenter clearance and the B2-B3 spacing in the values
    Petition 870170058759, of 08/14/2017, p. 28/42
    18/20 pointed out in the previous cases, the radius of the gantry, due to an increase in the angle of inclination of B3, suffers an approximate reduction of 0.15, when compared to the preferred solution. In a configuration of 34 ° (B1) - 54 ° (B2) - 70 ° (B3), the length of the gantry corresponds to the approximate value of 7m.
    [0040] The optimal configuration of the double cone shaped gantry reconciles, on the one hand, the technical feasibility and costs of the last bipolar magnet 22, and, on the other hand, the reach of the maximum acceptable dimensions (radius of the gantry, length of the gantry). A good conciliatory solution consists, for example, in choosing a last bipolar magnet 22 with the specifications provided in Table 1, which can be constructed at a reasonable cost and presents a significant reduction in size and weight, when compared, for example, to a last 90 ° bipolar magnet, as used in the prior art. As discussed above, this preferred solution is suitable for a treatment room with a range of 6.4 m by 10.5 m, as shown in Fig. 6. However, anyone skilled in the field will recognize that the advantages of the invention can be gained as soon as the last bipolar magnet 22 has an inclination angle of less than 90 °. Preferably, the last bipolar magnet 22 should have an inclination angle of less than 80 °. More preferably, the last bipolar magnet 22 should have an inclination angle of less than 70 °.
    [0041] The above description concerns a gantry comprising means for scanning particle bundles 23. Alternatively, the gantry according to the invention must also comprise means for dispersing bundles of particles which are adapted to emit a wide beam in the isocenter 27. By "wide beam", we mean a beam with dimensions that, in the XY plane, correspond substantially to the size of the target in the XY plane. The dispersion means for the emission of such broad beams have been described by Chu et al. in “Instrumentation for treatment of cancer using proton and light-ion beams”, Rev. Sei. Instrum. 64 (8), August 1993, pages 2074 to 2084. A broad beam can, for example, be obtained by means of the so-called double dispersion beam emission system and generally comprises the following components: a first disperser ( for example, a set of films), a second disperser
    Petition 870170058759, of 08/14/2017, p. 29/42
    19/20 (for example, a track modulator wheel or a recessed filter), and a gap and track compensator. In a classic configuration of broad beam emitting gantry, the various components of the dispersion particle emission system are installed downstream of the last bipolar magnet 22. However, to integrate a dispersion beam emission system into a compact gantry in accordance with with the invention, some components of the dispersion means are preferably installed upstream of the last bipolar magnet 22. For example, when adopting a double dispersion system, the first disperser is preferably installed between the second bipolar magnet 21 and the third (last) bipolar magnet 22. Other components, such as, for example, a recess filter, are preferably installed after the third bipolar magnet. [0042] Although the embodiments revolve around proton gantries, the invention is not restricted to these. Anyone skilled in the field will be able to easily apply the geometry described in the invention to gantries intended for use with any type of charged particles, such as carbon ion gantries or other light ions. The same optical beam configuration is applied, regardless of the beam's magnetic stiffness, requiring only to scale the magnetic fields in the various magnets in the beam line.
    [0043] Although gantries for particle therapies have been designed for many years, until now no solution has been proposed to overcome the problems raised by the prior art gantry designs. According to the present invention, a new gantry design is introduced, which implies the provision of remarkable solutions to solve the problems generated by the prior state of the art. The new gantry design proposed by the invention has significant advantages over current designs for gantries (such as conical gantries, cylindrical gantries, etc.).
    In comparison with the conical gantries, the following significant advantages obtained from the use of the gantry according to the invention can be highlighted:
    • marked reduction in the diameter and length of the gantry;
    • the positioning of the heavy elements of the gantry, closer
    Petition 870170058759, of 08/14/2017, p. 30/42
    20/20 to the axis of rotation;
    • the reduction in costs related to the mechanical configuration of the gantry.
    In comparison to cylindrical gantries (such as the PSI 2 gantry or Heidelberg carbon gantry, as discussed by Weinrich on pages 966 (Fig. 8) and pages 967 and 968 respectively), the following significant advantages can be noted obtained from the use of gantry according to the invention:
    • the last tilt magnet, with a slit and large surfaces at the poles, is less heavy, and consumes less energy;
    • the center of gravity of the last tilt magnet is closer to the axis of rotation, which leads to a reduction in the mechanical disorders linked to the mechanical structure of the gantry;
    • in the case of the scanning configuration, a smaller amount of energy can be used to feed the magnets needed to cover the same scanning area in the isocenter.
    Petition 870170058759, of 08/14/2017, p. 31/42 / 2
    权利要求:
    Claims (10)
    [1]
    1. An ISOCENTRIC GANTRY designed to perform a rotation around an axis of rotation and to emit a beam of particles to be used in particle therapy, comprising:
    - a line of bundles in the gantry, provided with an entry point in the gantry (25) for the entry of said particle bundle inside the gantry, in a direction parallel to that of the axis of rotation;
    - a first (20), a second (21) and a third (22) bipolar magnets, arranged in sequence to successively tilt the beam of particles in a single plane, and to emit the aforementioned beam of particles to an isocenter (27) , in a direction perpendicular to the axis of rotation; and
    - quadrupole magnets (24) to focus and blur the beam of particles;
    characterized in that the third bipolar magnet (22) has an inclination angle of less than 80 °.
    [2]
    2. ISOCENTRIC GANTRY, according to claim 1, characterized in that the said third magnet (22) has an inclination angle of 60 °.
    [3]
    3. ISOCENTRIC GANTRY, according to claim 1 or 2, characterized by a section of beam lines between said entry point of the gantry (25) and an entry of the first bipolar magnet (20) corresponding to a section of short pulses .
    [4]
    4. ISOCENTRIC GANTRY, according to any of the preceding claims, characterized by a section of beam lines between said first (20) and said second (21) bipolar magnet comprising five quadrupole magnets (24), and where a section of beam lines between said second (21) and said third (22) bipolar magnets do not comprise any quadrupole magnet (24).
    [5]
    5. ISOCENTRIC GANTRY, according to any of the preceding claims, characterized by still comprising means to promote the rotation of the mentioned gantry over an angular range of at least 180 °.
    Petition 870170058759, of 08/14/2017, p. 32/42
    2/2
    [6]
    6. ISOCENTRIC GANTRY, according to any of the preceding claims, characterized in that it further comprises means for scanning particle bundles (23) installed between the said second bipolar magnet (21) and the said third bipolar magnet (22), and configured to scan the beam of particles over a target area of the isocenter (27).
    [7]
    ISOCENTRIC GANTRY according to claim 6, characterized in that said means for scanning beams (23) comprise a combined magnet X-Y for scanning.
    [8]
    8. ISOCENTRIC GANTRY according to any of claims 1 to 5, characterized in that it further comprises means for dispersing particle bundles which are adapted to send a wide bundle to the isocenter (27).
    [9]
    ISOCENTRIC GANTRY, according to claim 8, characterized in that the means of dispersion of particle bundles comprise a first dispersion means, installed between said second bipolar magnet (21) and said third bipolar magnet (22), and a second dispersion means, installed after said third bipolar magnet (22).
    [10]
    A PARTICLE THERAPY APPARATUS, according to any one of claims 1 to 9, characterized in that it comprises a particle accelerator, means for promoting variation in particle energy, a beam transport system, and an isocentric gantry.
    Petition 870170058759, of 08/14/2017, p. 33/42
    1/8 c
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    同族专利:
    公开号 | 公开日
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    法律状态:
    2017-03-21| B65X| Notification of requirement for priority examination of patent application|
    2017-04-11| B65Y| Grant of priority examination of the patent application (request complies with dec. 132/06 of 20061117)|
    2017-05-16| B07A| Technical examination (opinion): publication of technical examination (opinion)|
    2017-09-26| B09A| Decision: intention to grant|
    2018-01-16| B16A| Patent or certificate of addition of invention granted|
    2019-07-23| B21F| Lapse acc. art. 78, item iv - on non-payment of the annual fees in time|Free format text: REFERENTE A 9A ANUIDADE. |
    2019-11-12| B24J| Lapse because of non-payment of annual fees (definitively: art 78 iv lpi, resolution 113/2013 art. 12)|Free format text: EM VIRTUDE DA EXTINCAO PUBLICADA NA RPI 2533 DE 23-07-2019 E CONSIDERANDO AUSENCIA DE MANIFESTACAO DENTRO DOS PRAZOS LEGAIS, INFORMO QUE CABE SER MANTIDA A EXTINCAO DA PATENTE E SEUS CERTIFICADOS, CONFORME O DISPOSTO NO ARTIGO 12, DA RESOLUCAO 113/2013. |
    优先权:
    申请号 | 申请日 | 专利标题
    EP09171550.8|2009-09-28|
    EP09171550A|EP2308561B1|2009-09-28|2009-09-28|Compact gantry for particle therapy|
    PCT/EP2010/064155|WO2011036254A1|2009-09-28|2010-09-24|Compact gantry for particle therapy|
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