WO2004039133A1 - 電子加速器及びそれを用いた放射線治療装置 - Google Patents
電子加速器及びそれを用いた放射線治療装置 Download PDFInfo
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- WO2004039133A1 WO2004039133A1 PCT/JP2003/013656 JP0313656W WO2004039133A1 WO 2004039133 A1 WO2004039133 A1 WO 2004039133A1 JP 0313656 W JP0313656 W JP 0313656W WO 2004039133 A1 WO2004039133 A1 WO 2004039133A1
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- electromagnet
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- H—ELECTRICITY
- H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
- H05H—PLASMA TECHNIQUE; PRODUCTION OF ACCELERATED ELECTRICALLY-CHARGED PARTICLES OR OF NEUTRONS; PRODUCTION OR ACCELERATION OF NEUTRAL MOLECULAR OR ATOMIC BEAMS
- H05H13/00—Magnetic resonance accelerators; Cyclotrons
- H05H13/08—Alternating-gradient magnetic resonance accelerators
-
- 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
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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
- A61N2005/1085—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy characterised by the type of particles applied to the patient
- A61N2005/1089—Electrons
Definitions
- the present invention relates to an electron accelerator that generates an electron beam having an energy of several MeV to 10 several MeV and uses a fixed magnetic field type strong convergence, and a radiation therapy apparatus using the electron accelerator.
- a linear accelerator As a linear accelerator, a microtron electron accelerator is known (for example, see Patent Document 2 below).
- FIG. 20 is a diagram illustrating an example of a configuration of a medical linear accelerator of Conventional Example 1.
- the medical linear accelerator 100 includes an electron gun 101, an accelerator device 102, and a magnetic bending device 103 provided outside the accelerator device 102.
- the electrons incident on the accelerator device 102 by the electron gun 101 are accelerated along the beam axis of the accelerator device 102.
- the accelerator device 102 is composed of a microwave accelerating cavity, and the microwave oscillator 104 and its control circuit 105 are connected.
- the microwave oscillator 104 generates an electromagnetic field in the accelerating cavity of the accelerator device 102.
- the electron beam 106 accelerated in this way is emitted from the exit window 107, becomes an output electron beam 108, and is used for radiotherapy.
- the orbit of the output electron beam 108 is changed by the magnetic bending device 103 to irradiate a target 109, such as gold or tungsten, which generates X-rays.
- a line beam 110 can be generated.
- This X-ray —110 is also used for radiation therapy.
- the size of the accelerator device 102 requires a length of about 2 m in order to accelerate the electron beam to 1 OMeV (for example, see Patent Document 3 below).
- the heavy particle beam accelerator has high energy, enables irradiation limited to cancerous tissue, and reduces damage to normal tissue compared to the linear accelerator of Conventional Example 1 using electron beams and X-rays.
- advantages for example, see Patent Document 4 below).
- FF GA accelerator Fixed Field A 1 ternative Grad i ent accelerator
- Taiga of Japan in 1953 See Patent Document 1 The FFGA accelerator uses a so-called strongly converging magnetic stone that has zero chromatic aberration in the convergence of particles such as electron beams, and does not need to change the magnetic field with acceleration as in the conventional synchrotron accelerator. There is a feature. Therefore, the particles can be accelerated quickly.
- Patent Document 5 discloses a noise reduction technique in an FFAG electron accelerator using a betatron accelerator. This noise reduction technology is to generate a sound that cancels out the noise generated by the FFAG electron accelerator from the speaker, and does not eliminate the noise from the FFAG electron accelerator itself.
- Patent Document 1 JP-A-10-64700 (page 4, FIG. 1)
- Patent Document 2 Japanese Patent Application Laid-Open No. 07-169600 (Pages 2 to 3, FIGS. 1 and 2)
- Patent Document 3 Japanese Patent Application Laid-Open No. 2001-219699 (Page 2)
- Patent Document 4 Japanese Patent Application Laid-Open No. 2002-110400 (pages 1-2)
- Patent Document 5 JP-A-2003-159342 (pages 1 and 2)
- Non-Patent Document 1 Chihiro Okawa, Annual Report of the Physical Society of Japan, 1953
- Non-patent Document 2 Y. Mori et al., 14, "FFAG (Fixed-field Aernating Gradi ent) Proton Syncrotron ", 1999, The 12th Syposium on Accelerator Science and Technology, pp. 81-83
- Non Patent Literature 3 Nakano Yasuhiro KEK FFAG Group, “150 MeV Fixed Field Alternative Gradient (FFAG) Accelerator”, September 2002, Nuclear Research Vol. 47, No. 4, pp. 91-101
- the beam intensity of the linac of Conventional Example 1 is as small as several hundred degrees A, it takes a long time to perform radiation treatment for cancer, etc., burdening the patient, causing a deviation in the irradiation field due to respiratory movement, and causing cancer.
- There are problems such as difficulty in irradiating the diseased parts such as tissues. For this reason, in electron beam and X-ray treatment, irradiation limited to cancerous tissue is more difficult than conventional cancer treatment equipment using heavy ion beams, and damage to normal tissue is large. .
- the radiation therapy system for cancer and the like using the heavy ion beam of Conventional Example 2 has an accelerator length of 1 Om to several 1 Om compared to 2 to several m of the electron beam accelerator, and the weight is also large. Over 100 tons. In addition, the cost is 100 times that of an electron beam accelerator, and it cannot be easily installed in general hospitals. '
- the FFAG accelerator of Conventional Example 3 has a larger beam current than the accelerators of Conventional Examples 1 and I, and is capable of rapid repetition. It has an accelerating voltage of about V and can be easily installed in general hospitals. There are problems such as the fact that an accelerator that can be used has not been realized yet, and audible frequency noise is generated from the accelerator used for the accelerator. Disclosure of the invention
- the present invention provides an electron accelerator using a small and light fixed magnetic field strong convergence with a strong electron beam intensity, and a fixed magnetic field strong convergence electron capable of irradiating cancer tissue with an electron beam in a short time. It aims to provide a radiation therapy device using an accelerator.
- an electron accelerator comprises a vacuum vessel, an electromagnet disposed inside or outside the vacuum vessel, and an electron beam incident section for projecting an electron beam into the vacuum vessel.
- a fixed magnetic field type strongly focused electron accelerator comprising: an accelerator for accelerating an electron beam; and an electron beam transport unit for transporting an electron beam accelerated from a vacuum vessel, wherein the electromagnet is a strongly focused electromagnet;
- This strong focusing electromagnet is composed of a focusing electromagnetic stone and a diverging electromagnet provided on both sides of the focusing electromagnet, or is composed of a diverging section provided on both sides of the focusing electromagnetic stone and the focusing electromagnet,
- An internal target that generates X-rays is placed in the vacuum vessel just before, and accelerated electron beams and X-rays can be extracted selectively.
- the electron beam incident unit preferably includes an electron gun and an electromagnet that changes the trajectory of the electron beam generated from the electron gun and causes the electron beam to enter the vacuum vessel.
- the electron beam transport unit preferably includes an electromagnetic stone or a converging lens that changes the trajectory of the electron beam out of the vacuum vessel, and the electron beam or the X-ray passing through the electron beam transport unit is scanned.
- the acceleration device is a high-frequency acceleration system or an induction acceleration system, and is provided with at least a continuous output or pulse oscillator.
- the electron beam is efficiently accelerated by the strong focusing electromagnet and the accelerator using high frequency, etc., so that the electron beam is about 10 times or more as compared with the electron accelerator such as the conventional linac.
- a fixed magnetic field type strong focusing electron accelerator which selectively generates an electron beam and X-rays generated by the electron beam.
- a high-frequency oscillator having a low output with a continuous output or a pulse output can be used as an accelerator, it can be manufactured with a small size, light weight and low cost.
- the electron accelerator of the present invention comprises: a vacuum vessel; an electromagnet disposed inside or outside the vacuum vessel; an electron beam incident unit for projecting an electron beam into the vacuum vessel; and an accelerator for accelerating the electron beam.
- a fixed-field strong focusing electron accelerator comprising: an electromagnet for extracting an accelerated electron beam in a vacuum vessel; and an electron beam transport unit for transporting the accelerated electron beam from the vacuum vessel.
- a strongly converging electromagnet which consists of a focusing electromagnet and a dispersing magnet provided on both sides of the focusing electromagnet, or a focusing electromagnet and a diverging portion provided on both sides of the focusing electromagnet. And the electron beam emitted from the electron beam transport unit is scanned.
- an internal target for generating X-rays is provided in a vacuum vessel immediately before the accelerated electron beam transport unit, and the accelerated electron beam and X-rays can be selectively extracted.
- the electron beam or X-ray is scanned by a scanning unit including at least a pinhole slit.
- an electron beam approximately 10 times or more and X-rays generated by this electron beam can be obtained compared to a conventional linac or other electron accelerator, and a fixed magnetic field that can be scanned by the electron beam or X-rays
- a strongly focused electron accelerator is provided. Also
- a high-frequency oscillator of low power with continuous output or pulse output can be used as an accelerator, it can be manufactured with a / J, type, light weight and low cost.
- the electron beam transport unit includes a septum electromagnet or a converging lens that changes the trajectory of the electron beam to the outside of the vacuum container, and the first electron beam is provided near the electron beam emission unit of the strong focusing electromagnet in the vacuum container.
- An electromagnet for beam trajectory correction is provided.
- the first electron beam trajectory correcting electromagnet is disposed at a position delayed by 7 C / 2 radians in the electron beam phase space with respect to the septum electromagnet or the convergent lens. According to the above configuration, a stronger electron beam can be obtained by including the first electron beam trajectory correcting electromagnet.
- a second electron beam trajectory correction electromagnet is disposed near the electron beam incident portion of the strong convergence electromagnet, and the first electron beam trajectory correction electromagnet is used for the first electron beam trajectory correction. Adjust the trajectory of the electron beam together with the electromagnet.
- the first and second electron beam trajectory correcting electromagnets are preferably ⁇ ⁇ radians (where ⁇ is an integer) in the topological space. According to this configuration, a stronger electron beam can be obtained by further providing the second electron beam trajectory correcting electromagnet.
- the winding portion of the electromagnet constituting the strong convergence electromagnet has a split winding structure, and the drive of each current of the split winding portion is controlled so as to have a predetermined magnetic field distribution.
- the magnetic field distribution can be adjusted by driving and controlling the current in each winding portion, using the strong focusing electromagnet as an electromagnet having a split winding structure, and a continuous electron beam with higher intensity can be obtained.
- the electron accelerator of the present invention includes a vacuum vessel, an electromagnet disposed inside or outside the vacuum vessel, an electron beam incident section for projecting an electron beam into the vacuum vessel, and an accelerator for accelerating the electron beam.
- a fixed magnetic field type strong focusing electron accelerator comprising: an electromagnet for extracting an accelerated electron beam in a vacuum vessel; and an electron beam transport unit for transporting the accelerated electron beam from the vacuum vessel.
- a strongly converging electromagnet which is a focusing electromagnet and a diverging electromagnet provided on both sides of the focusing electromagnet, or a focusing electromagnet and a diverging portion provided on both sides of the focusing electromagnet.
- the winding of the electromagnet constituting the strong convergence electromagnet has a split winding structure, and the current of each of the split windings is driven and controlled to have a predetermined magnetic field distribution. And it features.
- the current of each section of the split winding section is controlled by a resistor connected in parallel to each winding section or by a current source connected to each winding section.
- the strong focusing electromagnet since the strong focusing electromagnet has a split winding structure, the current in each winding portion can be set to an optimum magnetic field distribution, and an electron beam with higher intensity can be obtained. Since the electromagnet is driven by direct current and the accelerator can use a high-frequency oscillator higher than the audio frequency, no noise is generated from the electron accelerator.
- a radiotherapy apparatus using the electron accelerator of the present invention includes: an electron accelerator that selectively generates an electron beam or an X-ray; an irradiation head; a support unit; a treatment table on which a patient is placed; Wherein the electron accelerator is a fixed magnetic field type strong focusing electron accelerator. According to this configuration, a fixed magnetic field type strongly focused electron accelerator is used. Since the electron beam intensity is about 10 times stronger and scanning can be easily performed, the time for irradiating a tissue such as cancer can be reduced to one tenth or less. In addition, since it is small and lightweight, it does not generate noise and is low cost, it can be installed in general hospitals. BRIEF DESCRIPTION OF THE FIGURES
- FIG. 1 is an external view showing a configuration of an embodiment of a radiotherapy apparatus used for treatment of cancer or the like using a fixed magnetic field type strong focusing electron accelerator according to the present invention.
- FIG. 2 is a diagram showing a schematic configuration of a fixed magnetic field type strong focusing electron accelerator of the present invention.
- FIG. 3 is a schematic diagram illustrating a configuration of an electron beam incident unit.
- FIG. 4 is a perspective view showing a configuration example of the electromagnet.
- FIG. 5 is a perspective view of a modification of FIG. 4 showing a configuration example of an electromagnet.
- FIG. 6 is a plan view showing the configuration of the electron beam transport unit.
- FIG. 7 is a diagram schematically showing the trajectory of an electron beam generated from the fixed magnetic field type strong convergence electron accelerator of the present invention.
- FIG. 8 is a diagram showing a beam trajectory calculation for accelerating electrons to 10 MeV in the fixed magnetic field strong convergence electron accelerator of the present invention.
- FIG. 9 is a schematic side view showing the configuration of the fixed-field-type strong convergence electron accelerator according to the first embodiment of the present invention.
- FIG. 10 is a diagram schematically showing correction of the electron beam trajectory by the first electron beam trajectory correction electromagnet.
- FIG. 11 is a diagram schematically showing correction of the electron beam trajectory by the first and second electron beam trajectory correction electromagnets.
- FIG. 12 shows the simulation of the electron beam orbit in the phase space in Fig. 11.
- FIG. 13 is a perspective view schematically showing spot scanning which is a configuration of the beam scanning unit in FIG.
- FIG. 14 is a perspective view schematically showing an electron beam which is another configuration of the beam scanning unit in FIG.
- FIG. 15 is a schematic side view showing the configuration of a fixed-field-type strong convergence electron accelerator according to the third embodiment of the present invention.
- FIGS. 16A and 16B show a configuration of an electromagnet used in the third embodiment.
- FIG. 16A is a plan view showing a plane of the electromagnet
- FIG. 16B is a cross-sectional view showing a configuration of a winding portion of the electromagnet.
- FIG. 17 is a diagram showing a method of exciting the electromagnet shown in FIG.
- FIG. 18 is a diagram showing another excitation method of the electromagnet shown in FIG.
- FIG. 19 is a diagram schematically showing the magnetic flux density distribution of the electromagnet shown in FIG.
- FIG. 20 is a diagram showing an example of the configuration of a conventional medical linear accelerator. BEST MODE FOR CARRYING OUT THE INVENTION
- FIGS. 1 and 1 are an external view showing the configuration of an embodiment of a radiotherapy apparatus used for treatment of cancer or the like using the fixed magnetic field type strongly focused electron accelerator according to the present invention, and the configuration of the fixed magnetic field type strongly focused electron accelerator. It is the schematic diagram seen from the side surface shown.
- a radiotherapy device 1 using a fixed magnetic field type strongly focused electron accelerator has a fixed magnetic field type strongly focused electron accelerator 2 for accelerating electrons, and a support unit 3 for supporting a fixed magnetic field type strongly focused electron accelerator 2. And a treatment table 4 on which the subject is placed.
- the fixed magnetic field type strong convergence electron accelerator2, the portion 2a on the treatment table 4 side is an electron beam transport portion in which an electron beam transport portion 26 described later is housed, and the electron beam transport portion 2
- the tip of 6 is an irradiation head 2b for irradiating the patient with an electron beam or X-rays generated using the electron beam.
- the fixed magnetic field type strongly focused electron accelerator 2 is rotatably supported by a support unit 3 so that the patient can be irradiated at an arbitrary angle (see the arrow in FIG. 1).
- the fixed magnetic field type strongly focused electron accelerator 2 is composed of a vacuum vessel 10, an electron beam incident part 11, an electromagnet 20 (20a to 20f), an accelerator 13, and an electron It consists of a beam transport section 26 and.
- the vacuum container 10 is a ring-shaped hollow container to be evacuated.
- the electron beam incident section 11 is composed of an electron gun and the like.
- the electromagnet 20 is an electromagnet that generates a fixed magnetic field that is arranged so as to go around the vacuum vessel 10.
- Each electromagnet 20 includes a diverging electromagnet 22 on both sides of the focusing electromagnet 21. .
- an electromagnet of the same structure is arranged on the upper side so as to face the same.
- the electromagnet 20 can be provided in a vacuum vessel.
- the vacuum vessel is made of a non-magnetic material
- the electromagnet 20 may be provided outside the vacuum vessel to form a magnetic field distribution inside the vacuum vessel.
- A1 (aluminum) or the like can be used as the non-magnetic material.
- the approximate width of the vacuum vessel 10 is indicated by, where L for obtaining an acceleration voltage of 10 MeV is about 1 m.
- FIG. 3 is a schematic diagram showing the configuration of the electron beam incident section 11.
- the electron beam incident portion 11 includes an electron gun 14 and a kicker magnet 15. The trajectory of the electrons generated from the electron gun 14 is bent into the vacuum vessel 10 by the kicker magnet 15, and becomes an incident electron beam 16.
- FIG. 4 is a perspective view showing a configuration example of the electromagnet.
- the electromagnet 0 includes a strongly converging electromagnet having a diverging electromagnet 22 on both sides of a focusing electromagnet 21.
- the upper part is the outer peripheral side of the vacuum vessel 10 of the electromagnet 20
- the lower part is the inner peripheral side of the vacuum vessel 10 of the electromagnet 20.
- a coil 23a and a coil 23b are wound around the focusing electromagnet 21 and the diverging electromagnetic stone 2, respectively.
- a voltage and a current are applied to the coils 23a and 23b of the focusing electromagnet 21 and the diverging electromagnet 22 so as to generate a constant magnetic field, that is, a fixed magnetic field, and the directions of the magnetic fields are mutually opposite. It is in the opposite direction.
- Arrows 2 la and 22 a in the figure indicate the directions of the magnetic field of the focusing electromagnet 21 and the diverging electromagnet 22, respectively.
- the magnetic fluxes generated by the focusing electromagnet 21 and the diverging electromagnet 22 return directly to the diverging electromagnet 22 and the focusing electromagnet 21, respectively, to form a so-called closed and positive magnetic circuit with a reverse magnetic field.
- the electromagnet 20 has a magnetic flux density of about 0.5 T (tesla) as an example of the magnetic field strength. Further, a superconducting magnet may be used as the electromagnet 20. Further, the electromagnet 20 may be a strongly converging electromagnet by including diverging ends provided on both sides of the focusing electromagnet 21.
- FIG. 5 is a perspective view showing another configuration example of the electromagnet. As shown in the figure, the electromagnet 20 is provided with a short circuit 24 which forms a magnetic circuit in addition to the electromagnet 20 of FIG. The other configuration is the same as that of FIG.
- the above-described electromagnet is merely an example of a configuration example, and another configuration may be used.
- the shunt yoke 24 may be any one of the upper and lower parts according to the divergent magnetic field strength.
- the coil 23b of the diverging electromagnet 22 may be omitted, and a magnetic field induced by the magnetic field from the focusing electromagnet 21 or a diverging magnetic field induced by the end shape may be used.
- FIG. 2 shows an example in which six electromagnets 20 (20a to 20f) are arranged in the vacuum vessel 10, but the electron beam is fixed by the electromagnets 20 as described later. It is sequentially passed through the magnetic field distribution and orbits inside the vacuum vessel 10. As a result, the fixed magnetic field distribution formed by the electromagnets 20 allows the electron beam to converge within the vacuum vessel 10 with good convergence. You can orbit. This action is called fixed magnetic field type strong convergence.
- An accelerator 13 for accelerating the electron beam is provided between the electromagnet 20b and the electromagnet 20c in FIG.
- the acceleration device 13 is composed of a high-frequency oscillator and its control device.
- the accelerating device 13 need only include an energy supply means such as an antenna or a coil for applying high-frequency energy for accelerating the electron beam in the vacuum vessel.
- Other high-frequency oscillators and their control devices or power supplies are required. May be installed outside the vacuum vessel. At this time, the electron beam is accelerated by an accelerator 13 using a high-frequency acceleration method or an induction acceleration method.
- the caro-speed device 13 using a high-frequency oscillator when the frequency is 5 MHz to several 100 MHz and the power is 500 kW, an acceleration voltage of several 10 kV can be obtained.
- a continuous operation or pulse operation oscillator can be used as the high frequency oscillator.
- the frequency of the accelerator 13 is set to be equal to or higher than the audible frequency, noise can be prevented from being generated.
- FIG. 6 is a plan view showing the configuration of the electron beam transport unit 26.
- the electron beam 27 accelerated to 10 MeV to 15 MeV is incident on the electron beam transport unit 26.
- Extraction of the electron beam 27 to the outside of the accelerator is performed using any one of a septum electrode, a septum magnet, and a kicker magnet 28, and a four-lens bundle lens 29.
- FIG. 7 is a diagram schematically showing the trajectory of an electron beam generated from the fixed magnetic field type strong convergence electron accelerator of the present invention.
- an incident electron beam 16 from the electron beam incident section 11 enters the vacuum vessel 10.
- the incident electron beam 16 circulates until reaching a predetermined acceleration voltage while being accelerated by the electromagnet 20 in the vacuum vessel 10 by the accelerator 13.
- the dashed line in the figure indicates a schematic trajectory of the electron beam 16.
- the incident electron beam 16 makes one round of the vacuum vessel 10 to form a second round of the electron beam 17.
- the trajectories of the electron beams 16 and 17 are almost concentric, and the diameter gradually increases as the electron beam energy increases, and is accelerated to a predetermined accelerating voltage.
- the electron beam 18 is an electron beam having a predetermined acceleration voltage. Therefore, since the trajectory of the accelerated electron beam and the trajectory of the electron beam at the highest energy are spatially separated, an internal target 25 used for generating X-rays 31 must be installed in the vacuum vessel 10. Becomes easier.
- the internal target 25 is moved to a position not irradiated by the electron beam 27, and What is necessary is just to make 27 into the electron beam transport section 26.
- the internal target 15 is moved within the vacuum vessel 10 only when X-rays are generated, and the electron beam 27 is irradiated to the internal target 25. X-rays may be generated.
- the electron beam 27 accelerated to 10 MeV to 15 MeV can be used by being extracted from the vacuum container 10 and used by the internal target 25 to generate X-rays 31. It is possible to use both of them after converting to.
- FIG. 8 is a diagram showing a beam trajectory calculation for accelerating electrons to 10 MeV in the fixed magnetic field strong convergence electron accelerator of the present invention.
- the horizontal and vertical beta-tunnels in the figure are the frequencies when the electron beam makes one round around the closed orbit when the electron beam repeatedly converges and diverges in the vacuum vessel 10 and makes an oscillating motion. This frequency is the frequency of the electron beam in the horizontal and vertical directions when the electron beam makes one round of the vacuum vessel 10.
- the electron beam is well converged by the beam entrance and the accelerated beam exit, and the tron tune in both the horizontal and vertical directions does not change significantly with the acceleration energy.
- the fixed magnetic field distribution by the electromagnet 20 has a so-called zero chromatic aberration shape in which the convergence of the electron beam does not change much with the acceleration energy even when the electron beam is accelerated.
- beam acceleration is possible if the beam acceleration speed is extremely high.
- the fixed magnetic field type strong convergence electron accelerator 2 of the present invention since a fixed magnetic field which does not change over time is used, extremely high repetition acceleration is possible as compared with a normal accelerator whose magnetic field intensity changes over time. is there.
- the operation of the fixed magnetic field type strong convergence electron accelerator of the present invention will be described.
- the electron beam 16 generated by the electron gun 14 is injected into the vacuum vessel 10 by the electron beam incidence unit 11.
- the incident electron beam 16 is prevented from diverging due to the strong convergence effect of the fixed magnetic field distribution of the electromagnet 20, and furthermore, the accelerating device 13 placed on the orbit of the electron beam in the vacuum vessel 10 Accelerates the electron beam.
- the electron beam accelerated by the accelerator 13 is further accelerated by the fixed magnetic field of the electromagnet 20 to orbit around the vacuum vessel 100 in a substantially ring shape while rotating about 100 to 100 times. Accelerated by 13
- the acceleration voltage of the incident electron beam 16 is gradually increased until reaching the desired acceleration voltage.
- the trajectory of the electron beam 27 accelerated to a predetermined acceleration voltage is bent outward in the electron beam transport unit 26. As a result, the electron beam 30 can be taken out.
- the orbital position of the electron beam becomes slightly larger on the outer peripheral side of the vacuum vessel 10 with the increase of the electron beam energy. Orbit and the electron beam orbit 18 at the highest energy are spatially separated. This facilitates both taking out the electron beam out of the vacuum vessel 10 and placing an internal target 25 used for generating X-rays 31 in the vacuum vessel 10. . That is, the electron beam 27 can be used both when it is taken out of the vacuum vessel 10 and used, and when it is converted into X-rays 31 by the internal target 25 and used.
- the electromagnet 20 used in the fixed magnetic field type strong convergence electron accelerator is a fixed magnetic field type and can perform high-repetition acceleration. Therefore, it does not require an extremely high accelerating electric field unlike the conventional linear accelerator.
- the electron beam acceleration efficiency (duty factor) of the fixed magnetic field type strong focusing electron accelerator of the present invention can be as high as several 10% or more.
- the electron beam intensity is low, an efficiency of typically a few 0/0.
- an electron beam intensity of 1 mA to 1 O mA which is more than 10 times that of the conventional electron accelerator, and X-rays by this electron beam can be obtained.
- the fixed-field-type strong convergence electron accelerator 2 of the present invention does not use an oscillator that uses a very high frequency of several GHz, which is a frequency in the microphone mouthband, which is used in a conventional accelerator. No need and costly high frequency cavities are required.
- the accelerating device 13 used in the fixed magnetic field type strong convergence electron accelerator 2 of the present invention accelerates the electron beam while converging the electron beam many times while converging by the electromagnet 20, so that even if the accelerating voltage per operation is reduced, It can accelerate to a predetermined acceleration voltage.
- low-cost high-frequency oscillators with continuous operation at very low frequencies (several kHz to several tens of MHz) can be used, resulting in low cost. Therefore, although the electron beam intensity is lmA to lOmA, which is 10 times or more, the size of the device is almost the same as the conventional one, so that it can be manufactured at the same cost as the conventional electron beam accelerator.
- FIG. 9 is a schematic side view showing the configuration of a fixed-field-type strongly focused electron accelerator according to the second embodiment of the present invention.
- the fixed magnetic field type strong convergence electron accelerator 40 according to the first embodiment includes a first electron beam orbit correction electromagnet 41, a second electron beam orbit correction electromagnet 4, and a beam scanning unit 43. , And is configured to drive the electromagnets 20a to 0e with direct current, which is different from the fixed magnetic field type strongly focused electron accelerator 2 shown in FIG. 17 shows the electron beam accelerated to the maximum energy of 1 O MeV to 15 MeV.
- the other configuration is the same as that of FIG.
- the first electron beam orbit correction electromagnet 41 is inserted into a region between the internal target 25 and the electromagnet 20 e in the vacuum vessel 10 to correct the electron beam orbits 16, 17, 18. Used.
- the second electron beam trajectory correcting electromagnet 42 is provided in the vacuum vessel 10 and is provided at a position facing the electron beam incident portion 11.
- windowless electromagnets can be used as the first and second electron beam trajectory correction electromagnets 41 and 42.
- the electron beam orbit correction electromagnet 41 alone can be The electron beam can be emitted after correcting the orbit of the electron beam.
- FIG. 10 is a diagram schematically showing the correction of the electron beam trajectory by the first electron beam trajectory correction electromagnet 41.
- the first electron beam orbit correction electromagnet 41 is located at a position delayed by ⁇ / 2 radians in the electron beam phase space with respect to the septum electrode or the septum electromagnet 28 provided in the electron beam transport section 26. It is arranged.
- the lines in the figure indicate the electron beam 18 at a predetermined acceleration voltage and the nearest electron beam 17 at a predetermined acceleration voltage.
- the dotted line 18, 18 of the electron beam 18 indicates the trajectory of the electron beam without the septum electrode or the electromagnet 28.
- the septum electrode or the electromagnet 28 is located at a position where ⁇ / 2 radians advances in the electron beam phase space with respect to the first electron beam orbit correction electromagnet 41, so that The electron beam 18 at the accelerating voltage is incident on the septum electrode or the electromagnet 28 and the orbit is corrected most efficiently to become the electron beam 46, which is emitted to the beam scanning section 43.
- the first electron beam trajectory correcting electromagnet 41 By providing the first electron beam trajectory correcting electromagnet 41, the electron beam trajectory correction and beam emission can be performed efficiently.
- FIG. 11 is a diagram schematically showing the correction of the electron beam trajectory by the first and second first electron beam trajectory correction electromagnets 41 and 42.
- the first and second electron beam orbit correction electromagnets 41 and 42 are arranged so as to be an integral multiple of 180 degrees ( ⁇ radians, where ⁇ is an integer) in the electron beam phase space. ing.
- the first and second electron beam trajectory correcting electromagnets 41 and 42 with respect to the septum electrode or the septum electromagnet 28 become integral multiples of 180 degrees in the electron beam phase space.
- the electron beam 18 having a predetermined accelerating voltage is incident on the septum electrode or the septum electromagnet 28 and the orbit is corrected most efficiently to become the electron beam 47. It is emitted to 3.
- FIG. 12 is a diagram showing an electron beam orbit simulation in the phase space in FIG.
- the horizontal axis indicates the radial distance R (mm)
- the vertical axis indicates the phase angle (mrad).
- R 100 O mm. That is, when it becomes larger than lm, the phase angle rapidly increases, and the electron beam is extracted. You can see that By providing the first electron beam trajectory correction electromagnet 41 or the first and second electron beam trajectory correction electromagnets 41 and 42, the electron beam trajectory correction and beam emission can be performed with high accuracy. You can see what happens.
- the beam scanning unit 43 is a region in which the electron beam or the X-ray 27 moves in an arbitrary direction on a vertical plane (referred to as an XY plane) in the straight traveling direction of the beam 27 ′, that is, a region where the beam 27 ′ runs.
- FIG. 13 is a perspective view schematically showing spot scanning which is a configuration of the beam scanning unit in FIG. As shown in the figure, the electron beam or X-ray 27 ′ is scanned by the lens 50, 51 whose beam diameter is enlarged and the pinhole slit 52 is scanned in the X, Y directions shown in the figure. The resulting electron beam or X-ray 44 is obtained.
- FIG. 14 is a perspective view schematically showing electronic scanning which is another configuration of the beam scanning unit in FIG.
- the electron beam 27 ′ is transmitted by the driving circuit (not shown) of the lenses 53, 54 composed of an electrostatic lens or an electromagnetic lens or a combination thereof in the X and Y directions shown in FIG. Is scanned.
- the driving circuit not shown
- the electron beam or the X-ray 27 ′ can be scanned by spot scanning, and the electron beam alone can be quickly and efficiently scanned by electronic scanning. can do.
- the trajectory of the electron beam can be corrected, and the extraction of the electron beam or X-ray can be performed continuously and efficiently.
- the electron beam or X-ray is scanned by the beam scanning unit.
- FIG. 15 is a schematic side view showing a configuration of a fixed-field strong focusing electron accelerator according to a third embodiment of the present invention.
- the fixed magnetic field type strongly converging electron accelerator 60 shown in FIG. 9 differs from the fixed magnetic field type strongly converging electron accelerator 40 shown in FIG.
- the other configuration is the same as that of FIG. 9 and the description is omitted.
- the six electromagnets 62 (62 a to 62 f) are arranged in the vacuum vessel 10.
- FIG. 16 shows the configuration of an electromagnet 60 used in the third embodiment.
- FIG. 3B is a plan view of the stone
- FIG. 4B is a cross-sectional view illustrating a configuration of a winding part of the electromagnet.
- the electromagnet 62a is a strongly converging electromagnet having a diverging electromagnet 64 on both sides of the converging electromagnet 63, like the electromagnet 20a.
- the converging electromagnet 63 and the diverging electromagnet 64 have a structure in which the winding part is divided into a plurality of blocks.
- the converging electromagnet 63 and the diverging electromagnet 64 are both shown as having five divisions.However, the number of divisions of the winding part is not limited to five and depends on the shape of the target magnetic field distribution. What is necessary is just to set suitably.
- FIG. 17 is a diagram showing a method of exciting the electromagnet shown in FIG.
- shunt resistors 66 a to 66 e for current adjustment are connected in parallel to the winding portions 64 a to 64 e of the divergent electromagnet coil divided into five.
- the value of the shunt resistor is increased in parallel so that two resistors with the shunt resistor 66a of r0 and the shunt resistor 661) of 0 are connected in parallel.
- Both ends 6 4 g and 6 4 h of the winding are driven by the current source 68 at a constant current.
- the focusing electromagnet 63 has the same configuration.
- the magnetic flux density distribution of the diverging electromagnet 64 can be controlled.
- the converging electromagnet 63 it is possible to control the magnetic flux density distribution of the electromagnet 62 a composed of the diverging electromagnet and the converging electromagnet to be optimal.
- FIG. 18 is a diagram showing another method of exciting the electromagnet shown in FIG.
- the winding portions 64a to 64e of the divergent electromagnet coil divided into five are independently driven by a constant current from current sources 70 to 74, respectively.
- a current of I, to 15 can be passed through each of the coil winding portions 64a to 64e. Therefore, the magnetic flux density generated from each winding portion changes, and the magnetic flux density distribution of the divergent electromagnet 64 can be controlled.
- the converging electromagnet 63 similarly, it is possible to control the magnetic flux density distribution of the electromagnetic stone 62 a composed of the diverging electromagnet and the converging electromagnet so as to be optimal.
- FIG. 19 is a diagram schematically showing the magnetic flux density distribution of the electromagnet shown in FIG.
- the horizontal axis represents the radial distance of the vacuum vessel 10 in the horizontal plane
- the vertical axis represents the magnetic flux density.
- B Is the magnetic field strength on the incident orbit
- r. Is the orbital radius of the orbit (see Fig. 15)
- k is the field index (fieldindex).
- the magnetic field coefficient k can be arbitrarily changed by adjusting the winding portions 64 a to 64 e of the 62 a coil of the electromagnet. Therefore, by setting the radial magnetic field distribution to optimize the orbital convergence of the electron orbit, the zero-chromatic aberration shape of the electron beam can be easily realized, and the electron beam intensity can be increased. In addition, it is possible to easily change the energy of the electron beam.
- the convergence state of the electron beam can be optimized, so that the electron beam intensity can be increased. Further, the electron beam energy can be easily changed.
- an acceleration voltage of 10 MeV to 15 MeV and a current of 1 mA to 10 mA are obtained. Since it is 0 times or more, the irradiation time is extremely reduced.
- the radiation therapy apparatus 1 using the fixed magnetic field type strong focusing electron accelerator of the present invention has a light weight of about 1 ton, the fixed magnetic field type strong focusing electron accelerator 2, 40, 60 is rotated.
- the fixed magnetic field type strong focusing electron accelerator 2, 40, 60 is rotated.
- irradiation from multiple directions to the subject can be performed in a short time. Therefore, radiation damage to normal tissues can be reduced.
- the fixed magnetic field type strongly focused electron accelerator 2, 40, 60 used in the radiotherapy apparatus 1 of the fixed magnetic field type strongly focused electron accelerator of the present invention is based on an extremely stable beam focusing and acceleration method in principle in beam acceleration. Because of this, it is easy to operate, does not require any special adjustment work, and can be used by non-specialists.
- the electron beam trajectory of the fixed-field-type strongly focused electron accelerators 2, 40, and 60 is largely covered with electromagnets 20, which is effective as a radiation shield. Thereby, in the radiotherapy apparatus 1 using the fixed magnetic field type strong focusing electron accelerator of the present invention, the cost required for radiation protection at the installation location can be reduced.
- the radiotherapy apparatus using the fixed magnetic field type strong convergence electron accelerator of the present invention As described above, if the treatment of cancer or the like is performed by the radiotherapy apparatus using the fixed magnetic field type strong convergence electron accelerator of the present invention, the irradiation time to the affected part of the patient can be significantly reduced, and the patient can be breathed. Displacement of the irradiation field using stop irradiation can be prevented, and the irradiation area can be limited by multi-directional irradiation and radiation damage to normal tissues can be reduced. Further, the radiotherapy apparatus using the fixed magnetic field type strong convergence electron accelerator of the present invention is small and lightweight, does not generate noise, and can be manufactured at low cost, so that it can be easily installed in general hospitals.
- the present invention is not limited to the above embodiments, and various modifications are possible within the scope of the invention described in the claims, and it goes without saying that they are also included in the scope of the present invention.
- the configuration and number of the electron beam incident portion, the electron beam transport portion, and the electromagnet can be appropriately changed according to the acceleration voltage and the electron beam current.
- the intensity is 1 to 1 O mA, which is 10 times or more higher than that of the conventional electron beam accelerator.
- X-rays can be selectively generated by this electron beam.
- the device is small and lightweight, and can be manufactured at low cost.
- the radiation therapy system using the fixed-field-type strong convergence electron accelerator of the present invention can obtain a high-intensity electron beam current more than 10 times that of the conventional electron beam accelerator, greatly reducing the treatment time for cancer and the like. And the like can be performed, and the burden on the patient can be reduced.
- the fixed magnetic field type strong convergence electron accelerator of the present invention can be made compact with a diameter of about 1 m and can be manufactured at a cost of about 1/100 of a cancer treatment apparatus using heavy ion beams. This has the advantageous effect that it can be easily installed in hospitals.
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- Engineering & Computer Science (AREA)
- Physics & Mathematics (AREA)
- Plasma & Fusion (AREA)
- Spectroscopy & Molecular Physics (AREA)
- Health & Medical Sciences (AREA)
- Biomedical Technology (AREA)
- Radiology & Medical Imaging (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Pathology (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
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- Radiation-Therapy Devices (AREA)
- Particle Accelerators (AREA)
Abstract
Description
Claims
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/532,735 US7190764B2 (en) | 2002-10-25 | 2003-10-24 | Electron accelerator and radiotherapy apparatus using same |
CA002503160A CA2503160A1 (en) | 2002-10-25 | 2003-10-24 | Electron accelerator and radiotherapy apparatus using same |
EP03758894A EP1560475A4 (en) | 2002-10-25 | 2003-10-24 | ELECTRONIC ACCELERATOR AND RADIOTHERAPY DEVICE WITH IT |
JP2004546477A JP4356019B2 (ja) | 2002-10-25 | 2003-10-24 | 電子加速器及びそれを用いた放射線治療装置 |
Applications Claiming Priority (2)
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JP2002-310412 | 2002-10-25 | ||
JP2002310412 | 2002-10-25 |
Publications (1)
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WO2004039133A1 true WO2004039133A1 (ja) | 2004-05-06 |
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PCT/JP2003/013656 WO2004039133A1 (ja) | 2002-10-25 | 2003-10-24 | 電子加速器及びそれを用いた放射線治療装置 |
Country Status (7)
Country | Link |
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US (1) | US7190764B2 (ja) |
EP (1) | EP1560475A4 (ja) |
JP (1) | JP4356019B2 (ja) |
KR (1) | KR20050083810A (ja) |
CN (1) | CN1943284A (ja) |
CA (1) | CA2503160A1 (ja) |
WO (1) | WO2004039133A1 (ja) |
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JP2015014465A (ja) * | 2013-07-03 | 2015-01-22 | 有限会社マイテック | 芯出し装置および芯出し方法 |
JP2019133745A (ja) * | 2018-01-29 | 2019-08-08 | 株式会社日立製作所 | 円形加速器、円形加速器を備えた粒子線治療システム、及び円形加速器の運転方法 |
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Citations (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPH0298952U (ja) * | 1989-01-23 | 1990-08-07 | ||
JPH02201898A (ja) * | 1989-01-31 | 1990-08-10 | Mitsubishi Electric Corp | 荷電粒子装置用偏向電磁石 |
JPH0654917A (ja) * | 1992-08-10 | 1994-03-01 | Nec Corp | 荷電粒子加速器 |
US5471516A (en) * | 1994-10-06 | 1995-11-28 | Varian Associates, Inc. | Radiotherapy apparatus equipped with low dose localizing and portal imaging X-ray source |
JPH07320680A (ja) * | 1994-05-25 | 1995-12-08 | Nissin High Voltage Co Ltd | 電子線照射装置 |
JPH08148327A (ja) * | 1994-11-18 | 1996-06-07 | Hitachi Ltd | 超電導磁石及び当該超電導磁石を備えた粒子加速器 |
JP2000082599A (ja) * | 1998-09-02 | 2000-03-21 | Mitsubishi Electric Corp | 円形加速器用電磁石 |
JP2002141198A (ja) * | 2000-11-01 | 2002-05-17 | Sumitomo Heavy Ind Ltd | 電子ビームの軌道補正装置及び軌道補正方法 |
JP2002184600A (ja) * | 2000-12-12 | 2002-06-28 | Sumitomo Heavy Ind Ltd | マイクロトロンの電子ビーム軌道調整装置及び電子ビーム軌道調整方法 |
JP2002217000A (ja) * | 2001-01-19 | 2002-08-02 | Hitachi Ltd | ビーム位置モニタおよびこれを用いたシンクロトロン |
Family Cites Families (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPH0298952A (ja) | 1988-10-05 | 1990-04-11 | Nec Yamagata Ltd | 半導体用プロービング装置 |
JP3096547B2 (ja) | 1993-12-15 | 2000-10-10 | 株式会社日立メディコ | 治療用マイクロトロン装置 |
US5734168A (en) | 1996-06-20 | 1998-03-31 | Siemens Medical Systems, Inc. | Monolithic structure with internal cooling for medical linac |
JP2001021699A (ja) | 1999-07-05 | 2001-01-26 | Toshiba Corp | 高周波電子加速器および電子線照射装置 |
JP2001110709A (ja) * | 1999-10-08 | 2001-04-20 | Nikon Corp | 多層膜反射鏡及び露光装置ならびに集積回路の製造方法。 |
JP3839652B2 (ja) | 2000-09-29 | 2006-11-01 | 独立行政法人科学技術振興機構 | 永久磁石を用いた荷電粒子加速用磁石と高磁場円形荷電粒子加速器 |
US6487274B2 (en) * | 2001-01-29 | 2002-11-26 | Siemens Medical Solutions Usa, Inc. | X-ray target assembly and radiation therapy systems and methods |
JP3527950B2 (ja) * | 2001-10-31 | 2004-05-17 | 高エネルギー加速器研究機構長 | Ffag加速器用電磁石 |
US6888919B2 (en) * | 2001-11-02 | 2005-05-03 | Varian Medical Systems, Inc. | Radiotherapy apparatus equipped with an articulable gantry for positioning an imaging unit |
JP2003159342A (ja) | 2001-11-27 | 2003-06-03 | Mitsubishi Electric Corp | 医療用加速器及び医療用加速器の騒音低減方法 |
US6993112B2 (en) * | 2002-03-12 | 2006-01-31 | Deutsches Krebsforschungszentrum Stiftung Des Oeffentlichen Rechts | Device for performing and verifying a therapeutic treatment and corresponding computer program and control method |
-
2003
- 2003-10-24 WO PCT/JP2003/013656 patent/WO2004039133A1/ja active Application Filing
- 2003-10-24 CA CA002503160A patent/CA2503160A1/en not_active Abandoned
- 2003-10-24 KR KR1020057007050A patent/KR20050083810A/ko not_active Application Discontinuation
- 2003-10-24 JP JP2004546477A patent/JP4356019B2/ja not_active Expired - Fee Related
- 2003-10-24 US US10/532,735 patent/US7190764B2/en not_active Expired - Fee Related
- 2003-10-24 EP EP03758894A patent/EP1560475A4/en not_active Withdrawn
- 2003-10-24 CN CNA2003801020892A patent/CN1943284A/zh active Pending
Patent Citations (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPH0298952U (ja) * | 1989-01-23 | 1990-08-07 | ||
JPH02201898A (ja) * | 1989-01-31 | 1990-08-10 | Mitsubishi Electric Corp | 荷電粒子装置用偏向電磁石 |
JPH0654917A (ja) * | 1992-08-10 | 1994-03-01 | Nec Corp | 荷電粒子加速器 |
JPH07320680A (ja) * | 1994-05-25 | 1995-12-08 | Nissin High Voltage Co Ltd | 電子線照射装置 |
US5471516A (en) * | 1994-10-06 | 1995-11-28 | Varian Associates, Inc. | Radiotherapy apparatus equipped with low dose localizing and portal imaging X-ray source |
JPH08148327A (ja) * | 1994-11-18 | 1996-06-07 | Hitachi Ltd | 超電導磁石及び当該超電導磁石を備えた粒子加速器 |
JP2000082599A (ja) * | 1998-09-02 | 2000-03-21 | Mitsubishi Electric Corp | 円形加速器用電磁石 |
JP2002141198A (ja) * | 2000-11-01 | 2002-05-17 | Sumitomo Heavy Ind Ltd | 電子ビームの軌道補正装置及び軌道補正方法 |
JP2002184600A (ja) * | 2000-12-12 | 2002-06-28 | Sumitomo Heavy Ind Ltd | マイクロトロンの電子ビーム軌道調整装置及び電子ビーム軌道調整方法 |
JP2002217000A (ja) * | 2001-01-19 | 2002-08-02 | Hitachi Ltd | ビーム位置モニタおよびこれを用いたシンクロトロン |
Non-Patent Citations (4)
Title |
---|
F. T. COLE: "Electron Model Fixed Field Alternating Gradient Accelerator", THE REVIEW OF SCIENTIFIC INSTRUMENTS, vol. 28, no. 6, June 1957 (1957-06-01), XP002986742 * |
See also references of EP1560475A4 * |
Y. MORI: "FFAG(Fixed-field Alternating Gradient)Proton Synchrotron", THE 12TH SYMPOSIUM ON ACCELERATOR SCIENCE AND TECHNOLOGY, WAKO., 1999, JAPAN, pages 81 - 83, XP002986740 * |
YUZURU NAKANO, KEN FFAG GROUP KEK: "150MeV Fixed Field Alternating Gradients (FFAG) Accelerator.", GENSHIKAKU KENKYU, vol. 47, no. 4, September 2002 (2002-09-01), pages 91 - 101, XP002986741 * |
Cited By (8)
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JP2007018770A (ja) * | 2005-07-05 | 2007-01-25 | Mitsubishi Electric Corp | 電磁石装置 |
JP4509880B2 (ja) * | 2005-07-05 | 2010-07-21 | 三菱電機株式会社 | 電磁石装置 |
JP2007026818A (ja) * | 2005-07-14 | 2007-02-01 | Nhv Corporation | 磁場勾配を形成する電磁石 |
JP2015014465A (ja) * | 2013-07-03 | 2015-01-22 | 有限会社マイテック | 芯出し装置および芯出し方法 |
JP2019133745A (ja) * | 2018-01-29 | 2019-08-08 | 株式会社日立製作所 | 円形加速器、円形加速器を備えた粒子線治療システム、及び円形加速器の運転方法 |
JP7002952B2 (ja) | 2018-01-29 | 2022-01-20 | 株式会社日立製作所 | 円形加速器、円形加速器を備えた粒子線治療システム、及び円形加速器の運転方法 |
CN113692101A (zh) * | 2020-05-19 | 2021-11-23 | 四川智研科技有限公司 | 一种紧凑型电子加速器 |
CN113692101B (zh) * | 2020-05-19 | 2023-06-16 | 四川智研科技有限公司 | 一种紧凑型电子加速器 |
Also Published As
Publication number | Publication date |
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CN1943284A (zh) | 2007-04-04 |
US7190764B2 (en) | 2007-03-13 |
EP1560475A4 (en) | 2008-07-09 |
CA2503160A1 (en) | 2004-05-06 |
JPWO2004039133A1 (ja) | 2006-02-23 |
US20060056596A1 (en) | 2006-03-16 |
KR20050083810A (ko) | 2005-08-26 |
JP4356019B2 (ja) | 2009-11-04 |
EP1560475A1 (en) | 2005-08-03 |
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