JP2014176709A - Method and apparatus for evaluating patient's respiration - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a method and apparatus for evaluating a patient's respiration for detecting an unforeseen situation such as aggravation of a patient.SOLUTION: The patient respiration evaluation method is provided for evaluating a deviation of an actual respiration signal R(t) representing actual respiration of a patient from a reference respiration signal R(t) representing target respiration of the patient. The patient respiration evaluation method includes the steps of: calculating a first gain and a first phase in a description function equivalent to a primary term when expanding the reference respiration signal R(t) into Fourier series: calculating a second gain and a second phase in the description function equivalent to the primary term when expanding the actual respiration signal R(t) into Fourier series; and performing any one of a gain comparison of comparing the first gain with the second gain and a phase comparison of comparing the first phase to the second phase.

Description

  The present invention relates to a particle beam therapy apparatus used for medical use or research, and more particularly to a scanning particle beam therapy apparatus such as spot scanning or raster scanning.

  In general, a particle beam therapy system is connected to a beam generator for generating a charged particle beam, an accelerator for accelerating the generated charged particle beam, and a charge emitted after being accelerated to energy set by the accelerator. A beam transport system that transports a particle beam, and a particle beam irradiation device that is installed downstream of the beam transport system and that irradiates an irradiation target such as an affected part of a patient. The particle beam irradiation device is large, so that the charged particle beam is scattered and expanded by a scatterer, and the expanded charged particle beam is matched to the shape of the irradiation target to form an irradiation field, and to match the shape of the irradiation target There are scanning irradiation methods (spot scanning, raster scanning, etc.) in which an irradiation field is formed by scanning a thin pencil beam.

  In the broad irradiation method, an irradiation field that matches the shape of the affected area is formed using a collimator or a bolus. An irradiation field that matches the shape of the affected area is formed to prevent unnecessary irradiation of normal tissue. This is the most widely used irradiation method. However, it is necessary to manufacture a bolus for each patient or to deform the collimator according to the affected area.

  On the other hand, the scanning irradiation method is a highly flexible irradiation method in which a collimator and a bolus are unnecessary. However, since these components that prevent irradiation of normal tissues other than the affected part are not used, higher beam irradiation position accuracy than that of the broad irradiation method is required.

  Patent Document 1 discloses the following invention for the purpose of reducing the influence of hysteresis of a scanning electromagnet that scans a charged particle beam and realizing highly accurate beam irradiation. The invention of Patent Document 1 includes an irradiation management device that controls a scanning electromagnet based on a target irradiation position coordinate of a charged particle beam, and a position monitor that measures a measurement position coordinate of the charged particle beam. To the scanning electromagnet based on the correction data generated based on the measurement position coordinates and the target irradiation position coordinates measured by the position monitor and the target irradiation position coordinates in the pre-irradiation in which the excitation pattern of the electromagnet is the same as the main irradiation plan. A command value generator for outputting the control input.

  As a result, the invention of Patent Document 1 corrects the control input to the scanning electromagnet in advance based on the result obtained by the pre-irradiation by making the excitation pattern of the scanning electromagnet the same in the pre-irradiation and the main irradiation plans. Thus, the influence of the hysteresis of the scanning electromagnet was eliminated, and high-precision beam irradiation could be realized.

Japanese Patent No. 4532606 (FIGS. 1 and 2)

  The invention of Patent Document 1 corrects in advance based on the pre-irradiation in which the excitation pattern of the scanning electromagnet is the same as the main irradiation plan, and thus has a special effect of realizing high-accuracy beam irradiation in the main irradiation. It is something that demonstrates. Certainly, if the treatment is normally performed, the invention of Patent Document 1 does not cause any problem. However, at the treatment site, irradiation must be interrupted due to unforeseen circumstances such as the size of the charged particle beam exceeding the allowable range or the condition of the patient becoming worse, that is, the emergency of the particle beam therapy system. There may be situations where stop processing must be performed.

  In this case, emergency stop processing is executed, and irradiation of the charged particle beam is once stopped. Since irradiation has been performed partway through the affected area, it is necessary to resume irradiation from the irradiation position where the charged particle beam was interrupted so that the entire affected area has a dose planned in the treatment plan. At this time, if the irradiation is simply resumed from the interrupted irradiation position, the excitation pattern of the scanning electromagnet is performed halfway. As a result, since the scanning electromagnet is affected by hysteresis, the state of the scanning electromagnet is different between when the irradiation is interrupted and when it is not interrupted. There was a remaining problem that the beam was irradiated at a different position and the beam could not be irradiated with high accuracy.

  The present invention has been made to solve the above-described problems, and it is intended to obtain a patient respiratory evaluation method and a patient respiratory evaluation apparatus for detecting an unexpected situation such as a patient condition becoming worse. Objective.

  A patient respiration evaluation method for evaluating a deviation from a reference respiration signal representing a patient's target respiration in an actual respiration signal representing a patient's actual respiration, and a description corresponding to a primary term when the reference respiration signal is expanded in a Fourier series Obtaining a first gain and a first phase in a function; obtaining a second gain and a second phase in a description function corresponding to a first-order term when an actual respiratory signal is expanded in Fourier series; Performing at least one of gain comparison for comparing the first gain and the second gain and phase comparison for comparing the first phase and the second phase.

  The patient respiration evaluation method according to the present invention compares the first gain or first phase in the description function of the reference respiration signal with the second gain or second phase in the description function of the actual respiration signal. Deviation from the reference respiration signal representing the target respiration can be evaluated, and unforeseen circumstances such as the patient becoming unwell can be detected.

It is a block diagram which shows the particle beam therapy apparatus by Embodiment 1 of this invention. It is a schematic block diagram of the accelerator of FIG. It is a schematic block diagram of the particle beam irradiation apparatus of FIG. It is a control block diagram of the particle beam therapy system according to the first embodiment of the present invention. It is a figure explaining the correction method of command current. It is a flowchart which shows the beam stop and restart procedure in the particle beam therapy system by Embodiment 1 of this invention. It is a figure which shows a reference | standard respiration signal and an actual respiration signal. It is the schematic diagram which showed that a beam is scanned to an affected part along the beam path in the particle beam therapy system by Embodiment 2 of this invention. It is the figure which showed the hysteresis characteristic of the scanning electromagnet of the particle beam therapy apparatus by Embodiment 2 of this invention. It is a flowchart which shows the beam stop and restart procedure in the particle beam therapy system by Embodiment 2 of this invention. It is a flowchart which shows the other beam stop and restart procedure in the particle beam therapy system by Embodiment 2 of this invention.

Embodiment 1 FIG.
Hereinafter, the configuration of the particle beam therapy system according to the first embodiment of the present invention will be described. FIG. 1 is a block diagram showing a particle beam therapy system according to Embodiment 1 of the present invention. FIG. 2 is a schematic configuration diagram of the accelerator, and FIG. 3 is a schematic configuration diagram of the particle beam irradiation apparatus. FIG. 4 is a control block diagram of the particle beam therapy system according to Embodiment 1 of the present invention.

  First, a rough configuration of the particle beam therapy system will be described with reference to FIG. The particle beam therapy system 51 includes a beam generation device 52, a beam transport system 59, and particle beam irradiation devices 58a and 58b. The beam generator 52 includes an ion source (not shown), a pre-accelerator 53, and a circular accelerator (hereinafter simply referred to as an accelerator) 54 that is a synchrotron. The particle beam irradiation device 58b is installed in a rotating gantry (not shown). The particle beam irradiation device 58a is installed in a treatment room having no rotating gantry. The role of the beam transport system 59 is in communication between the accelerator 54 and the particle beam irradiation devices 58a and 58b. A part of the beam transport system 59 is installed in a rotating gantry (not shown), and the part has a plurality of deflection electromagnets 55a, 55b, and 55c. The beam generator 52, the beam transport system 59, and the particle beam irradiation devices 58a and 58b are controlled in cooperation by a control system.

  A charged particle beam 1 that is a particle beam such as a proton beam or a carbon beam (heavy particle beam) generated by an ion source is accelerated by a pre-accelerator 53 and is incident on an accelerator 54. The charged particle beam 1 is accelerated to a predetermined energy. The accelerator 54 is accelerated to about 70 to 80% of the speed of light while being accelerated by a high frequency electric field and bent by a magnet. The charged particle beam 1 emitted from the accelerator 54 is transported to the particle beam irradiation devices 58a and 58b through the beam transport system 59. In the beam transport system 59, the charged particle beam 1 to which sufficient energy is applied, the path formed by the vacuum duct, the trajectory is changed by an electromagnet as necessary, and the particle beam irradiation device 58a in the designated treatment room is provided. To 58b. The particle beam irradiation devices 58a and 58b shape the irradiation field according to the size and depth of the affected part of the patient 24, which is the irradiation target 15, and irradiate the irradiation target 15 (see FIG. 3) with the charged particle beam 1.

  Although described as “designated treatment rooms”, the particle beam treatment apparatus generally includes a plurality of treatment rooms from the viewpoint of treatment efficiency. That is, it is necessary to provide as many particle beam irradiation apparatuses 58 as the number of treatment rooms. In general, a large and complex system including a plurality of subsystems generally includes a sub controller that exclusively controls each subsystem and a main controller that directs and controls the entire subsystem. The particle beam therapy system 51 shown in the first embodiment of the present invention will also be described in the case where the configuration of the main controller and the sub controller is employed. For simplicity, all of the subsystems having the beam generator 52 and the beam transport system 59 are referred to herein as the accelerator system 60. The particle beam irradiation device 58 and the rotating gantry are referred to as “irradiation system”. FIG. 1 shows the case where there are two treatment rooms, a horizontal irradiation room and a gantry irradiation room. The controller for controlling the accelerator system and the irradiation system in cooperation is a control system for the particle beam therapy system.

<Accelerator>
The accelerator 54 will be described with reference to FIG. The accelerator 54 includes a vacuum duct 61 serving as an orbital path around which the charged particle beam 1 circulates, an incident device 62 for making the charged particle beam 1 supplied from the previous stage accelerator 53 enter the vacuum duct 61, and the charged particle beam 1 being a vacuum duct. The deflecting electromagnets 63a, 63b, 63c, and 63d for deflecting the trajectory so as to form the charged particle beam 1 that circulates along the circular trajectory in 61, and the charged particle beam 1 formed on the circular trajectory do not diverge. The converging electromagnets 64a, 64b, 64c, 64d for converging to the high frequency acceleration cavity 65 that accelerates by applying a high frequency voltage synchronized with the circulating charged particles, and the charged particle beam 1 accelerated in the accelerator 54 are taken out from the accelerator 54. An exit device 66 for exiting to the beam transport system 59, and charged particles for exiting the charged particle beam 1 from the exit device 66. And a sextupole electromagnet 67 to excite the resonance orbit of the beam 1.

  The deflection electromagnets 63 a, 63 b, 63 c, 63 d have a high frequency voltage applied to the high frequency acceleration cavity 65, and the high frequency acceleration cavity 65 has a deflection electromagnet controller that controls the excitation current of the deflection electromagnets 63 a, 63 b, 63 c, 63 d. A device (not shown) for controlling each part, such as a high-frequency source for supply and a high-frequency control device for controlling the high-frequency source, is provided, and includes a deflection electromagnet control device, a high-frequency control device, a converging electromagnet 64a, The control system includes an accelerator control device that controls other components such as 64b, 64c, and 64d to control the entire accelerator. However, in the technical idea of the present invention, the control of the accelerator itself is not limited. Therefore, the present invention is not limited to the above configuration, and various types can be used as long as the charged particle beam 1 can be stably emitted to the beam transport system 59. It goes without saying that the deformation of is allowed.

<Beam transport system>
The charged particle beam 1 accelerated by the accelerator 54 is emitted to a beam transport system 59 called a HEBT (High Energy Beam Transport) system. The beam transport system 59 includes a vacuum duct serving as a transport path of the charged particle beam 1, a switching electromagnet 68 that is a switching device that switches the beam trajectory of the charged particle beam 1, and a deflection electromagnet that deflects the beam to a predetermined angle. Yes. The charged particle beam 1 which is sufficiently energized by the accelerator 54 and travels in the transport path created by the vacuum duct is changed by the switching electromagnet 68 as necessary, and the irradiation provided in the designated treatment room. Lead to equipment.

<Irradiation system>
The irradiation system includes a particle beam irradiation apparatus 58 that shapes the charged particle beam 1 supplied from the beam transport system 59 into an irradiation field corresponding to the size and depth of the affected area of the patient who is the irradiation target 15 and irradiates the affected area. It is a thing. In general, a scatterer method, a wobbler method, and a scanning method have been proposed as irradiation field forming methods in the particle beam therapy system 51. The configuration of the irradiation system (particle beam irradiation apparatus) differs depending on each irradiation method. The present invention is directed to a particle beam therapy system (also referred to as a “scanning particle beam therapy system”) that employs a scanning method typified by spot scanning or raster scanning. In the case of a scanning particle beam therapy system, the particle beam irradiation device 58 measures a set of scanning electromagnets 3 for scanning the pencil-shaped charged particle beam 1 in accordance with the shape of the irradiation object 15 and the irradiation position. Position monitor 7 and the like. The detailed configuration of the particle beam irradiation device 58 will be described later.

<Control system>
The control system will be described with reference to FIG. 4 showing functional blocks. By the way, a workstation or a computer is generally used as the controller in the particle beam therapy system 51. Therefore, the controller is often called “computer”. For example, the main controller 70 in FIG. 4 is a function on a computer that is often referred to as an irradiation system common computer, but is treated as a controller having a certain function here. The sub-controllers 71a and 71b are functions on a computer that are often called device control computers, but are treated as controllers having a certain function here. The sub-controllers 71a and 71b use a part of the treatment room as one subsystem, such as a treatment table for mounting the patient 24 and an X-ray imaging device for photographing the position of the affected part (irradiation target 15). The subsystem is controlled.

  The irradiation system 80 includes a main controller 70, devices disposed in the irradiation operation room 81, devices disposed in the treatment room 82a, and devices disposed in the treatment room 82b. In the treatment room 82a, the irradiation device unit 31a of the particle beam irradiation apparatus 58a is arranged. In the treatment room 82b, the irradiation device unit 31b of the particle beam irradiation apparatus 58b is arranged.

  The consoles 72a, 72b, 73a, 73b, 74a, 74b connected to the sub-controllers 71a, 71b are terminals such as so-called keyboards, displays, or controller boxes, and are man-machine interface units. The operation consoles 72a and 72b are installed in the irradiation operation room 81, the operation consoles 73a and 74a are installed in the treatment room A (82a), and the operation consoles 73b and 74b are installed in the treatment room B (82b). Control boards 75a and 75b are connected to the lower parts of the sub-controllers 71a and 71b. Specifically, the control boards 75a and 75b are drivers, amplifiers, sequencers, and the like of various devices 76a, 76b, 77a, and 77b that are controlled objects. Further, the control panels 75a and 75b pass signals between the main controller 70, the interlock information input devices 84a and 84b, and the irradiation device units 31a and 31b. The devices 76a, 76b, 77a, 77b, the interlock information input devices 84a, 84b, and the irradiation device units 31a, 31b are connected to the lower part via the control panels 75a, 75b. The devices 76a, 76b, 77a, 77b are specifically a motor for moving each axis of the treatment table, a motor for driving the X-ray imaging apparatus in the irradiation apparatus, and the like. Excitation currents to the scanning electromagnets 3 a and 3 b provided in the irradiation device sections 31 a and 31 b are supplied from the scanning electromagnet power supply 4 via the switching circuit 79.

  Now, the motor for the treatment table and the motor for the X-ray imaging apparatus do not move during the beam irradiation. That is, it is not necessary to control in synchronization with an electromagnet such as an accelerator controlled by the accelerator system 60. The exchange between the main controller 70 and the sub-controllers 71a and 71b is a ready signal indicating which treatment room irradiation device units 31a and 31b may be irradiated after completion of positioning, and which treatment room irradiation device unit. This is for the purpose of informing each other such as a signal for irradiating a beam to 31a and 31b and informing the end of the irradiation. Simply put, it is an image of a sequential event.

  Here, the roles of the irradiation system common computer (main controller 70) and the device control computers (sub-controllers 71a and 71b) will be described. As described above, the treatment rooms 82a and 82b are provided with the irradiation device sections 31a and 31b of the particle beam irradiation apparatuses 58a and 58b, respectively. As described above, in the case of a scanning particle beam therapy system, the irradiation device units 31a and 31b are provided with a set of scanning electromagnets 3 and a position monitor 7 for measuring the irradiation position. However, as shown in FIG. 4, the control of the scanning electromagnet 3 and the signal processing from the position monitor 7 are not performed by the equipment control computer, but are performed by an irradiation system common computer (an irradiation management device described later).

  This is due to two reasons. The first reason is the necessity of synchronous control with the accelerator system, and the second reason is instantaneousness (necessity to eliminate dead time as much as possible). In order to realize irradiation according to the treatment plan, it is necessary to control the accelerator system 60 and the irradiation system 80 in synchronization. It is true that the sub-controllers 71a and 71b and the main controller 70 can perform processing simultaneously and in parallel using a synchronization signal or the like. However, the more devices that are routed, the more time is wasted and the control performance is degraded. Therefore, in the particle beam therapy system 51 according to the present invention, what is required to be controlled in real time during beam irradiation, such as the accelerator system 60 and the scanning electromagnet 3, is performed by the irradiation system common computer (irradiation management apparatus) which is the main controller 70. On the other hand, devices that do not need to be driven during irradiation, such as a treatment table and an X-ray imaging apparatus, are performed by the device control computer that is the sub-controllers 71a and 71b.

  This is because centralized management by one main controller 70 can eliminate dead time as much as possible and realize high-precision beam irradiation without deteriorating control performance. For the same reason of instantaneousness, the signal processing of the interlock information input devices 84a and 84b functioning as an interlock (emergency stop processing) is also performed by the irradiation system common computer (irradiation management device) as the main controller 70. Is good. The irradiation system common computer also has a so-called “accelerator interaction” function for managing which treatment room occupies the charged particle beam 1.

  Next, the particle beam irradiation apparatus 58 will be described with reference to FIG. The particle beam irradiation device 58 includes an irradiation device unit 31, a scanning electromagnet power source 4, an interlock information input device 84, an irradiation management device that controls the irradiation device unit 31 and the interlock information input device 84, collects data, and the like. 32. The interlock information input device 84 includes a patient sensor 78 described later. The irradiation equipment unit 31 scans the charged particle beam 1 in the X direction and the Y direction that are perpendicular to the charged particle beam 1 and the beam transport duct 2 that transports the charged particle beam 1 incident from the beam transport system 59. Scanning electromagnets 3x and 3y, a position monitor 7, a preamplifier 9 for amplifying the signal of the position monitor 7, a position monitor unit 8, a dose monitor 11, a preamplifier 13 for amplifying the signal of the dose monitor 11, and a dose monitor unit 12, a beam expansion device 16, a beam expansion control device 17, a bellows 18, a vacuum duct 19, a ripple filter 20, a range shifter 21, and a range shifter unit 23. As shown in FIG. 3, the direction in which the charged particle beam 1 is incident is the Z direction.

  The scanning electromagnet 3x is an X-direction scanning electromagnet that scans the charged particle beam 1 in the X direction, and the scanning electromagnet 3y is a Y-direction scanning electromagnet that scans the charged particle beam 1 in the Y direction. The position monitor 7 detects a passing position (center of gravity position) and a beam size through which the charged particle beam 1 deflected by the scanning electromagnets 3x and 3y passes. The preamplifier 9 amplifies the passage position and beam size analog data detected by the position monitor 7. Here, the beam size is an area passing through the XY plane perpendicular to the Z direction of the charged particle beam 1. The position monitor unit 8 receives the passing position and beam size detected by the position monitor 7 via the preamplifier 9, converts the passing position and beam size into digital data, and generates the measurement position coordinates Ps and the measurement beam size Ss. .

  The dose monitor 11 detects the dose of the charged particle beam 1. The preamplifier 13 amplifies the analog data of the dose detected by the dose monitor 11. The dose monitor unit 12 receives the dose detected by the dose monitor 11 via the preamplifier 13, converts the dose into digital data, and generates a measured dose Ds.

  The beam expanding device 16 expands the beam size of the charged particle beam 1 as necessary. The vacuum duct 19 ensures a vacuum region through which the charged particle beam 1 passes. The bellows 18 connects the beam transport duct 2 and the vacuum duct 19 so as to extend and contract, and extends the vacuum region to the irradiation target 15. The ripple filter 20 is also called a ridge filter, and has a convex shape. The ripple filter 20 causes an energy loss to the charged particle beam 1 which is a monochromatic beam having almost a single energy transmitted from the accelerator 54, and gives a wide range of energy.

  Control of position coordinates in the depth direction (Z direction) in the irradiation target 15 is performed by changing the acceleration energy of the accelerator 54 to change the energy of the charged particle beam 1 and changing the energy of the charged particle beam 1 by the range shifter 21. By doing. The range shifter 21 adjusts the range of the charged particle beam 1 in small increments. A significant range change of the charged particle beam 1 is performed by changing the acceleration energy of the accelerator 54, and a range change of the small charged particle beam 1 is performed by changing the setting of the range shifter 21.

  The irradiation management device 32 reads the treatment plan data F0 created by the treatment planning device, and generates setting data Fi rearranged in the irradiation order of irradiation spots that are divided irradiation units in order to control the irradiation dose. That is, the setting data Fi is sequenced treatment plan data (sequential data described later). The irradiation management device 32 outputs setting data Fo that is a command to each device based on the setting data Fi.

  The elements of the setting data Fi are the target irradiation position coordinates Pi, the target dose Di, the target beam size Si, the target accelerator setting Bi, and the range shifter insertion amount Ri, and each element of the setting data Fi is a target that is an element of the treatment plan data F0. This is data in which irradiation position coordinates Pi0, target dose Di0, target beam size Si0, target accelerator setting Bi0, and range shifter insertion amount Ri0 are sequenced. The setting data Fo includes an accelerator setting command Bo, a range shifter command Ro, a command current Io (command current not corrected), a command current Ir (command current corrected with the command current Io), a beam size command So, and a target dose Do. is there.

  The irradiation management device 32 receives irradiation records such as the measurement position coordinates Ps, the measurement dose Ds, and the measurement beam size Ss in the pre-irradiation performed without the patient 24, and evaluates the irradiation records. The irradiation management device 32 generates a command current Ir obtained by correcting the command current Io based on the measurement position coordinates Ps, and transmits the command current Io or the command current Ir to the scanning electromagnet power source 4. The irradiation management device 32 receives irradiation records such as measurement position coordinates Ps, measurement dose Ds, and measurement beam size Ss in the main irradiation actually irradiated on the patient 24, and stores the irradiation records in the main irradiation in the patient file server. To do.

  The irradiation management device 32 outputs a trigger signal, a count start signal, a beam supply command, and a beam stop command to each device, and controls the irradiation spot and irradiation dose in the irradiation target 15. The irradiation spot is a layer divided in the Z direction, and is divided into a slice corresponding to the kinetic energy of the charged particle beam 1 and the XY direction in each slice. Here, a description will be given of an irradiation method in which the charged particle beam 1 is stopped when the slice is changed, and the charged particle beam 1 is continuously irradiated when the same slice is irradiated. The irradiation management device 32 scans the charged particle beam 1 for each slice that is a layer corresponding to the kinetic energy of the irradiation target 15. The irradiation management device 32 changes the setting of each device for each irradiation spot by the trigger signal, starts measuring the irradiation dose of the irradiation spot by the count start signal, and when the measured dose Ds reaches the target dose Do, the next irradiation spot When the irradiation with respect to each of the irradiation sections (slices) into which the irradiation object 15 is divided is completed, a beam stop command is output to the accelerator system 60 and the charged particle beam 1 is stopped. Next, the irradiation management device 32 outputs a trigger signal, sequentially changes the corrected command current Ir, beam size command So, accelerator setting command Bo, and range shifter command Ro, and irradiation is completed for all slices of the irradiation target 15. Irradiation of the charged particle beam 1 is performed until

  The scanning electromagnet power source 4 changes the set currents of the scanning electromagnets 3x and 3y based on a command current Io (Ir) that is a control input to the scanning electromagnet 3 output from the irradiation management device 32. The beam expansion control device 17 outputs a beam size command So for setting the beam size in the position monitor 7 to the beam expansion device 16. The range shifter unit 23 outputs a range shifter command Ro for changing the energy of the charged particle beam 1 to the range shifter 21.

  The patient sensor 78 detects the movement of the patient 24 and outputs a patient signal reflecting the movement of the patient 24. The patient sensor 78 is for stopping the irradiation when the movement of the patient exceeds a predetermined range, that is, for performing an emergency stop process of the particle beam therapy system. The following can be considered for the patient sensor 78. Specifically, it detects the flow of exhalation by a flow sensor, measures the temperature change in the vicinity of the nasal cavity due to inspiration using image processing with a thermistor or infrared camera, and a laser attached to the abdomen of the patient's abdomen A method is conceivable in which the light source is detected by a position sensitive detector (position sensor), or the movement of the abdomen of the patient is signaled by a laser displacement meter. The patient sensor 78 may also serve as a respiration sensor used for the respiration synchronization irradiation of the particle beam therapy system 51. This is because both are used for the purpose of detecting the movement of the patient 24.

  Next, the technique described in Patent Document 1 serving as the basis of the present invention will be briefly described. The invention described in Patent Document 1 is made with respect to a particle beam therapy system 51 that irradiates an irradiation target 15 with a charged particle beam 1 that is accelerated by an accelerator 54 and scanned by a scanning electromagnet 3, and has the following characteristics. Have. (A) An irradiation management device 32 that controls the scanning electromagnet 3 based on the target irradiation position coordinates Pi of the charged particle beam 1 is provided. (B) A position monitor 7 for measuring the measurement position coordinates Ps of the charged particle beam 1 is provided. (C) The irradiation management device 32 is generated based on the measurement position coordinates Ps and the target irradiation position coordinates Pi measured by the position monitor 7 in the pre-irradiation in which the excitation pattern of the scanning electromagnet 3 is the same as the main irradiation plan. A command value generator is provided that outputs a control input Io (Ir) to the scanning electromagnet 3 based on the correction data Ia and the target irradiation position coordinate Pi.

  A method for generating the current correction data Ia will be described. FIG. 5 is a diagram for explaining a method of correcting the command current. The BL product for the current I output to the scanning electromagnet 3 is measured by the command current Io to the scanning electromagnet power source 4. The BL product is a product of the magnetic field strength B and the effective length L of the magnetic pole of the scanning electromagnet 3. The maximum hysteresis curve α passing through the saturation magnetic flux density is drawn. The average of the current increasing direction and the current decreasing direction of the maximum hysteresis curve α is taken to determine the center line β of the hysteresis loop.

  The current value I (id) set by the command current Io is the target irradiation position coordinate Pi, which is the irradiation planned position, the hysteresis loop center line β, the energy of the charged particle beam 1, and the installation position of the scanning electromagnet 3 to the irradiation position. It is obtained from the distance. In consideration of the Lorentz force acting on the charged particle beam 1, the BL product value can be obtained from the position coordinates of the charged particle beam 1. The command current Io corresponds to a current I (id) at an intersection P ′ (not shown) between the ideal BL product value BL (id) calculated from the target irradiation position coordinate Pi and the center line β of the hysteresis loop. It is a command value. This BL (id) is the expected value BL (ex) of the BL product value to be measured.

  A BL product value BL (me) is calculated from the measured measurement position coordinates Ps. The point P in FIG. 5 is an actual measurement value. Consider a case where the measured BL product value BL (me) is shifted from the expected value BL (ex) by ΔBL. The current is corrected by shifting by ΔBL using a straight line having a tangential slope K at the intersection P ′ where the command current Io is obtained. The correction may be performed by obtaining a current value I1 at which the BL product becomes BL (ex). If the current value I1 is obtained, the command current Ir to be set to the current value I1 that becomes BL (id) can be generated. By such a method, the positional deviation of the charged particle beam 1 due to the influence of the hysteresis of the scanning electromagnet 3 can be within an allowable range.

ここでΔＢＬはＢＬ（ｍｅ）−ＢＬ（ｅｘ）である。電流補正データＩａにより設定される補正電流値ΔＩはΔＢＬ／Ｋである。 A dashed line γ is a straight line having the same slope K as the tangent to the center line β in the current value I (id). The slope K can be expressed as in equation (1), and the corrected current value I1 can be expressed as in equation (2).

Here, ΔBL is BL (me) −BL (ex). The correction current value ΔI set by the current correction data Ia is ΔBL / K.

Next, consider a case where an emergency stop process of the particle beam therapy system 51 is performed. As described above, the emergency stop process is a process of interrupting irradiation due to an unexpected situation. The situation where the emergency stop process has to be performed is, for example, when the measurement position coordinate Ps or the measurement beam size Ss of the charged particle beam 1 detected by the position monitor 7 exceeds an allowable value, or the condition of the patient 24 becomes worse. This is a situation where an unexpected situation has occurred. In FIG. 3, the particle beam irradiation apparatus 58 according to the first embodiment is provided with the patient sensor 78 that detects the movement of the patient. However, the patient call button (FIG. And an irradiation stop button (not shown) for enabling a doctor / engineer to stop the irradiation by an operation in an emergency. The patient sensor 78, the patient call button, the irradiation stop button, and the position monitor 7 stop the beam irradiation in the event of an unexpected situation, and generate an interlock signal that activates an interlock function for ensuring safety. It becomes the information input device 84. The interlock information input unit 84 includes a patient sensor 78, a patient call button, an irradiation stop button, and a signal generator that generates an interlock signal from the signal output from the position monitor 7.

  Since the interlock process (emergency stop process) requires instantaneousness as described above, this signal process is preferably performed by the irradiation system common computer (irradiation management device 32) as the main controller 70. The irradiation management device 32 as the main controller 70 according to the first embodiment of the present invention has the following features.

  From the signal (patient signal) detected by the patient sensor 78, it is determined that the irradiation is stopped when the movement of the patient 24 exceeds a predetermined range. Irradiation when the measurement position coordinates Ps and measurement beam size Ss of the charged particle beam 1 detected by the position monitor 7 exceed a predetermined range (allowable value) (corresponding to the case where the quality of the charged particle beam 1 is deteriorated). Is determined to stop. If the patient 24 expresses the will of failure by operating the patient call button in an emergency, or if a doctor / engineer expresses the intention to stop the irradiation by operating the irradiation stop button in an emergency, the irradiation is similarly stopped. Judge that. Since the irradiation management device 32 as the main controller 70 also controls the accelerator system 60 (accelerator 54, beam transport system 59), when it is determined that the irradiation is stopped, the accelerator system 60 is controlled and the charged particle beam is controlled. 1 beam irradiation can be stopped. The predetermined range in the movement of the patient 24 detected by the patient sensor 78 is obtained by adding a margin to the detection value corresponding to the movement range when the patient 24 is performing normal breathing. A method for detecting the movement of the patient 24 and determining whether or not the predetermined range has been exceeded will be described later.

  The irradiation management device 32 according to the first embodiment further includes the following features. As described above, the irradiation management device 32 includes a command value generator that outputs the correction data Ia generated based on the preliminary irradiation and the control input to the scanning electromagnet 3. That is, the irradiation management device 32 has the control input corrected in advance by the command value generator as sequential data. Sequential data refers to data in a format that is executed for each step (individual processing executed at a predetermined time). Since the target irradiation position coordinates Pi are given as sequential data, control input to the scanning electromagnet 3 corresponding to the target irradiation position coordinates Pi is also required as sequential data. The irradiation management device 32 determines the irradiation stop based on the interlock signal generated by the interlock information input device. When the irradiation stop is performed, the irradiation management device 32 sets the target irradiation position coordinate Pi (that is, the stop position coordinate) at this time. The corresponding step (stop step) is stored in the built-in stop step storage memory. For example, the step number n output as the control input corresponding to the target irradiation position coordinate Pi in a certain slice is stored (stop step storage procedure). The stop step storage memory is not limited to being inside the irradiation management device 32 but may be outside.

  The irradiation management device 32 according to the first embodiment further includes the following features. The treatment time for one particle beam treatment is about 30 minutes, and the irradiation time is about several minutes. During such a time, it cannot be said that there is no unexpected situation such as the patient 24 feeling sick, coughing, or the quality of the charged particle beam 1 being deteriorated. If the measurement position coordinates Ps and the measurement beam size Ss of the charged particle beam 1 detected by the position monitor 7 exceed a predetermined range (allowable value), this corresponds to a case where the quality of the charged particle beam 1 is deteriorated. In this case, irradiation is stopped by sensing with a sensor or an operation of a button or the like, and the treatment is interrupted. When the unexpected situation is resolved and irradiation is resumed, the irradiation management device 32 controls the scanning electromagnet 3 from the first step in the slice, for example, in a state where the beam is not irradiated (empty operation procedure). Controlling the scanning electromagnet 3 without irradiating this beam will be referred to as “operating idling” here. Further, the step for starting the idling operation is called a start step.

  This is because if the irradiation is simply resumed from the interrupted irradiation position, the excitation pattern of the scanning electromagnet 3 is performed halfway. However, if the scanning electromagnet 3 is controlled from the first step in the slice, the pre-irradiation is performed. This is because the control is performed with the same excitation pattern as the time. Of course, if it irradiates with a beam here, since it will become redundant irradiation, it is meaningful to run idle. As a result, correction based on pre-irradiation becomes effective, and high-precision beam irradiation can be realized at the same level as when there was no interruption.

  The idling is preferably performed from the first step in the slice from the viewpoint of reproducibility. However, it is empirically found that a suitable effect can be obtained even if it is performed before a predetermined step (a predetermined number of spots). ing. Therefore, in the first embodiment, the start step is selected before a predetermined step set in advance than the first step in the slice or the step corresponding to the stop position. That is, it is possible to select an operator such as a doctor or an engineer to perform an idling operation from the first step in the slice, or to perform an idling operation before a predetermined step set in advance from the step corresponding to the stop position.

  Here, how to determine a predetermined step is described. The number of effective idling steps largely depends on the scale and performance of the scanning electromagnet 3. Therefore, it is better to actually reproduce the interruption situation intentionally and confirm and determine the effect with different number of steps by experiment. In some cases, the idling may be performed from the middle of the previous slice. In this way, it may be a case where the idling operation is performed from the previous step beyond the first step in the slice.

  Finally, the irradiation management device 32 must control the particle beam irradiation device 58 so as to irradiate the portion that has not been irradiated due to the interruption. Therefore, the irradiation management device 32 executes the accelerator system 60 (accelerator 54, beam transport system 59) so that the beam irradiation is started from the restart step next to the stop step after the idle operation is executed up to the step corresponding to the stop position. Is controlled so that the remaining steps can be executed (irradiation start procedure). In the case of an irradiation method in which the charged particle beam 1 is stopped when changing a slice and the charged particle beam 1 is continuously irradiated when irradiating the same slice, the irradiation position and the irradiation dose at the irradiation position are also sequential times. Can be reproduced by management (step management). That is, even if the irradiation dose of the irradiation spot at the interrupted stop position has not reached the target dose Do, the next irradiation spot is resumed after the irradiation dose of the irradiation spot reaches the target dose Do. Can move on.

  Although the feature of the irradiation management device 32 has been described, the flow of the emergency stop process of the particle beam therapy device 51 will be summarized with reference to FIG. FIG. 6 is a flowchart showing a beam stop and restart procedure in the particle beam therapy system according to the first embodiment. During the treatment, if an unexpected situation occurs, such as the patient 24 feeling sick, coughing, or the quality of the charged particle beam 1 is deteriorated, the irradiation management device 32 is generated by the interlock information input device. Based on the interlock signal, the irradiation stop is determined and the irradiation is stopped. When the irradiation management device 32 stops the irradiation, the irradiation management device 32 stores a step corresponding to the target irradiation position coordinate Pi (that is, the stop position coordinate) at this time. For example, the step number n output from the control input corresponding to the target irradiation position coordinate Pi in a certain slice is stored (step S1, stop step storage procedure). When the unexpected situation is resolved and irradiation is resumed, the irradiation management device 32 operates the scanning electromagnet power source 4 without performing beam irradiation from a predetermined start step to a stop step, and performs only magnetic field excitation of the scanning electromagnet 3. Perform (step S2, idle operation procedure). After the idling operation is executed up to the step corresponding to the stop position, the irradiation management device 32 controls the accelerator system 60 (accelerator 54, beam transport system 59) from the restart step next to the stop step to perform beam irradiation. Restart (step S3, irradiation start procedure).

  As described above, in the particle beam therapy system 51 according to the first embodiment, irradiation can be interrupted by operating a sensor or a button or the like even when an unexpected situation such as deterioration of the patient's condition occurs. In order to control the scanning electromagnet 3 from the first step in the slice or before a predetermined step (starting step) in a state where the scanning is not performed, the excitation pattern of the scanning electromagnet 3 can be made the same as the pre-irradiation, and correction based on the pre-irradiation (ie, pre-irradiation The information obtained in (1) can be made effective, and thus high-precision beam irradiation can be realized. Therefore, even when an emergency stop process is performed during treatment, the influence of the hysteresis of the scanning electromagnet 3 can be eliminated, and high-precision beam irradiation can be restarted from the interrupted irradiation position.

  A method of detecting the movement of the patient 24 and determining whether or not the predetermined range has been exceeded will be described. The patient sensor 78 described above measures a change caused by normal breathing as a respiratory signal, and a reference patient state waveform that is a time-varying waveform of a reference respiratory signal (reference respiratory signal) is acquired in advance. The actual patient state waveform generated from the respiration signal (actual respiration signal) measured by the patient sensor 78 during the main irradiation is compared with the reference patient state waveform, and a difference between the actual patient state waveform and the reference patient state waveform is predetermined. It is determined whether or not the range is exceeded. The patient sensor 78 for measuring the reference respiratory signal is of the same type (same measurement principle) as the patient sensor 78 for measuring the respiratory signal at the time of treatment.

The reference respiratory signal is not a clean trigonometric function, but is a signal with a substantially constant period, and therefore, it is considered that the gain (the amplitude of the trigonometric function) and the phase are calculated by converting to the nearest trigonometric function. Corresponding to the primary term as shown in equation (4) among the zero-order term to the n-th term developed when the reference respiratory signal R _tj (t) is expanded, for example, as shown in equation (3). The coefficients a ₁ and b ₁ of the trigonometric functions forming a pair are calculated, and the calculated coefficients a ₁ and b ₁ are defined as a description function indicating the state of the respiratory signal. That is, the coefficients a ₁ and b ₁ of the cosine function and sine function constituting the basic waveform component excluding the constant term and the high frequency component of the reference respiratory signal are calculated. In FIG. 7 (a), the reference respiratory signal R _tj (t) and the description function consisting of a ₁ and b ₁ obtained by the equation (2) are displayed in waveform.

From a ₁ and b ₁ constituting the description function extracted as described above, the gain G _res can be obtained as shown in Expression (5), and the phase φ _res can be obtained as shown in Expression (6).

FIG. 7 is a diagram showing a reference respiratory signal and an actual respiratory signal. Fig.7 (a) is a figure which shows a reference | standard respiration signal, FIG.7 (b) is a figure which shows a real respiration signal. The horizontal axis is time, and the vertical axis is the signal value of the respiratory signal R (t). The period of the reference respiration signal R _tj (t) is T _res and the period of the actual respiration signal R _rl (t) is T _res 1. BL is a baseline of the reference respiratory signal R _tj (t) and the actual respiratory signal R _rl (t). The actual respiration signal R _rl (t) is an irregular signal. However, for example, a sinusoidal signal based on the period _{T res} reference respiration signal _R tj (t), when performing the breathing guidance based on the reference respiration signal _R tj (t), the real respiration signal _R rl (t) is also It becomes a periodic function having the same period as the reference respiration signal R _tj (t). By utilizing the respiration characteristics, the real respiration signal R _rl (t) is also converted into a first order term when Fourier series expansion is performed as shown in the equation (4), similarly to the reference respiration signal R _tj (t). It is possible to calculate a description function composed of the coefficients a ₁ and b _{1 of the} trigonometric functions forming a corresponding pair.

Detecting a movement of the patient 24, when determining whether exceeds a predetermined range, the period _{T res} 1 of the real respiration signal _R rl (t) is the reference respiration signal _R period _{T res} of tj (t) As long as it almost matches. It provided a predetermined range in the gain _{G res} and phase phi _res, can be a range of the gain _{G res} and phase phi _res a predetermined range. For example, when the patient coughs, the gain and phase of the actual breathing signal fluctuate rapidly, so that the gain G _res and the phase φ _res exceed a predetermined range, and the movement of the patient coughing can be detected. Further, when the patient falls into a sleep state, the gain of the actual respiratory signal is gradually reduced, and the phase of the actual respiratory signal is no longer correlated with the phase of the reference respiratory signal. Also in this case, by providing appropriate ranges for the gain G _res and the phase φ _res , it is possible to detect that the patient has fallen into sleep or signs that the patient is about to go to sleep.

As described above, according to the particle beam therapy system of the first embodiment, the irradiation management device 32 that controls the scanning electromagnet 3 based on the target irradiation position coordinates Pi of the charged particle beam 1 and the measurement position coordinates of the charged particle beam 1. The irradiation management device 32 includes a position monitor 7 that measures Ps and an interlock information input device 84 that generates an interlock signal that stops irradiation of the charged particle beam 1 when an unexpected situation occurs. Correction data Ia and target irradiation position coordinates Pi generated based on the measurement position coordinates Ps and target irradiation position coordinates Pi measured by the position monitor 7 in the pre-irradiation in which the excitation pattern of the electromagnet 3 is the same as the main irradiation plan. A command value generator for outputting the control input Io (Ir) to the scanning electromagnet 3 based on the control signal and an interlock information input device 84 to generate an interlock signal. A stop step storage memory for storing a stop step corresponding to the target irradiation position coordinate Pi where irradiation of the charged particle beam 1 is stopped, and the irradiation management device 32 resumes irradiation of the charged particle beam 1 In this case, scanning from the start step before the stop step, which is different from the start step corresponding to the initial target irradiation position coordinates of the main irradiation, to the stop step without irradiation with the charged particle beam 1 Since the idling operation for controlling the electromagnet 3 is executed and the charged particle beam 1 is irradiated from the target irradiation position coordinate Pi corresponding to the stop step, the step before the stop step is performed when the emergency stop process is performed during the treatment. Then, from the start step different from the starting point step, the idle operation was performed based on the irradiation command data including the control input to the scanning electromagnet 3, and the operation was interrupted. Since starting the beam irradiated from the elevation position, to eliminate the influence of the hysteresis of the scanning electromagnet 3 can resume accurate beam irradiation from the interrupted irradiation position.

Embodiment 2. FIG.
In the first embodiment, the idle operation of the scanning electromagnet 3 at the time of restart after the treatment interruption is described. In the second embodiment, an initialization method of the electromagnet before the idle operation of the scanning electromagnet 3 is described.

  FIG. 8 is a schematic diagram showing that the affected part is scanned along the beam path in the particle beam therapy system according to Embodiment 2 of the present invention. The charged particle beam 1 scanned by the scanning electromagnet 3 is irradiated along each irradiation path 14 (also referred to as a beam path) to each layer (slice) of an affected area such as cancer that is the irradiation target 15. In the scanning particle beam therapy system 51, the beam path 14 for each layer is created using a therapy planning apparatus. In the treatment planning apparatus, an optimum treatment plan is made so that the cancerous part is as short as possible and there is no unnecessary irradiation to normal tissues. The treatment planning apparatus incorporates a computer that performs optimization, and the optimal route is obtained by the computer. The doctor who is the subject of treatment (responsible person) ultimately determines whether or not the route is appropriate. The X-direction scanning electromagnet 3x and the Y-direction scanning electromagnet 3y are controlled by the irradiation management device 32 so that the charged particle beam 1 is scanned along the created beam path 14, and from the scanning electromagnet power source 4 (also referred to as a pattern power source). A drive current (command current) is supplied.

  FIG. 9 is a diagram showing hysteresis characteristics of the scanning electromagnet of the particle beam therapy system according to the second embodiment. FIG. 9A shows the hysteresis characteristics of the X-direction scanning electromagnet 3x, and FIG. 9B shows the hysteresis characteristics of the Y-direction scanning electromagnet 3y. As shown in FIG. 9, the magnetic material that is the material of the scanning electromagnet has hysteresis characteristics. In FIG. 9, the horizontal axis represents the magnetic field strength H generated by the input command current, and the vertical axis represents the magnetic flux density B. αx is a maximum hysteresis curve of the X-direction scanning electromagnet 3x, and αy is a maximum hysteresis curve of the Y-direction scanning electromagnet 3y. As shown in FIG. 9, the hysteresis characteristic means a relationship in which the magnetic flux density B is not uniquely determined only by the magnetic field intensity H. The scanning electromagnet 3 is excited in a different pattern for each affected part in order to realize the beam path 14 optimized for each affected part. Therefore, the BH history curve on the BH plane that the scanning electromagnet 3 follows is different for each beam path.

  For example, when excited in a certain pattern, the scanning electromagnet 3 follows a BH history curve such as the thin solid lines 26a and 27a in FIG. Since the particle beam therapy apparatus 51 is a therapy apparatus for the human body, irradiation stops when an unexpected situation occurs. The points on the hysteresis curve at the stop position (stop spot) where the irradiation is stopped are P1x and P1y. Then, after confirming safety, irradiation is resumed. When restarting, it is necessary to restart after reproducing the state of the scanning electromagnet 3 before stopping. In order to reproduce the state of the scanning electromagnet 3, it is necessary to make the magnetic flux density B, the magnetic field strength H, and the magnetic field time gradient dH / dt the same at that time. Therefore, before starting the irradiation of the charged particle beam 1, the scanning electromagnet 3 always starts irradiation from the same state, for example, B = 0, H = 0, dH / dt = 0, that is, the scanning electromagnet 3 It is effective to initialize the scanning electromagnet 3 so that the BH history curve is always started from the same points P1x and P1y when the state is represented by the BH plane. Broken lines 26b and 27b are BH history curves when the scanning electromagnet 3 is controlled without stopping irradiation. By initializing the scanning electromagnet 3 and the idling described in the first embodiment, the BH history curve can always be started from the same points P1x and P1y when expressed on the BH plane.

  Initialization of the scanning electromagnet 3 gives a predetermined excitation pattern to the scanning electromagnet 3, for example, by exciting the scanning electromagnet 3 to the maximum value in the + H direction that is within the specification range and then exciting it to the maximum value in the −H direction. Thus, by exciting at the maximum value, it can be expected that the residual magnetic field in the magnetic material which is the material of the scanning electromagnet 3 is eliminated. Note that the initialization of the scanning electromagnet 3 is not limited to B = 0, H = 0, dH / dt = 0, and may be offset as long as reproducibility is ensured.

  In the first embodiment, the example in which the scanning electromagnet 3 is not initialized before the idling operation has been described. In the first embodiment, although rare, there may be a case where it is not sufficient to eliminate the influence of the hysteresis of the scanning electromagnet 3 even in idling. When the influence of the hysteresis of the scanning electromagnet 3 is not sufficiently eliminated, the position accuracy of the beam irradiation may be somewhat lowered. However, in the second embodiment, since the scanning electromagnet 3 is initialized before the idling operation, the influence of the hysteresis of the scanning electromagnet 3 can be sufficiently eliminated.

  Note that an auxiliary coil may be used as a method of adjusting the state of the scanning electromagnet 3. When the command value to the scanning electromagnet 3 is 0, that is, when there is no drive current from the scanning electromagnet power supply 4 and the scanning electromagnet 3 is not excited, the magnetic flux density B must be zero. However, as shown in FIG. 9, the magnetic flux density B may not become zero due to hysteresis characteristics. At this time, the magnetic flux density B can be made zero so as to cancel the residual magnetic field by controlling the current to be sent to the auxiliary coil provided in the scanning electromagnet 3. Also by such a method, the beam irradiation can be started with the scanning electromagnet 3 always in the same state (for example, the origin in the BH plane or the stop positions P1x and P1y in FIG. 9). The initialization of the scanning electromagnet 3 before the idling operation is not limited to setting the magnetic flux density B to 0 as described above, and it is sufficient if reproducibility can be ensured.

  The beam stop and restart procedure will be described with reference to FIG. FIG. 10 is a flowchart showing a beam stop and restart procedure in the particle beam therapy system according to the second embodiment. The beam stop and restart procedure of the second embodiment is different from the beam stop and restart procedure of the first embodiment in that a procedure for initializing the scanning electromagnet 3 (step S10) is added, and the starting point of the idling operation is the main irradiation. The scanning electromagnet 3 is controlled from the first step, that is, the first step in the first slice (step S11, idling procedure).

  If an unexpected situation occurs during the treatment, the irradiation management device 32 determines the irradiation stop based on the interlock signal generated by the interlock information input device, and stops the irradiation. The irradiation management device 32 stores the interruption step (step S1, stop step storage procedure). The irradiation management device 32 initializes the scanning electromagnet 3 (step S10, magnetic field initialization procedure). The method described above can be used for initialization of the scanning electromagnet 3. After the initialization of the magnetic field, the irradiation management device 32 operates the scanning electromagnet power source 4 without performing beam irradiation from the first step to the stop step in the main irradiation, and performs only the magnetic field excitation of the scanning electromagnet 3 (step S11, Empty driving procedure). As in the first embodiment, beam irradiation is resumed (step S3, irradiation start procedure).

By performing idling after the magnetic field initialization, it is possible to reproduce the irradiation resumption state (that is, the BH history curve in the BH plane), B = B ₀ , H = H ₀ , and dH / dt = H ′ ₀ . However, B ₀ is the magnetic flux density before the irradiation interruption, H ₀ is the magnetic field strength before the irradiation interruption, and H ′ ₀ is the magnetic field time gradient before the irradiation interruption.

The effect of adopting this sequence is that irradiation can be resumed in the state of the same scanning electromagnet 3 following the same BH history curve even if interruption is performed in the middle of irradiation, and the positional deviation of the irradiation spot is minimized. It is possible to suppress it. Here, as an example for reproducing the states B = B ₀ , H = H ₀ , dH / dt = H ′ ₀ before the interruption of irradiation, a method of performing the minimum excitation after the maximum excitation or an example using an auxiliary coil Although shown, the initialization method of the scanning electromagnet 3 capable of reproducing B = B ₀ , H = H ₀ , dH / dt = H ′ ₀ at the time of resuming treatment has the same effect and is intended to limit the present invention. It was n’t.

  As described above, since the particle beam therapy system 51 according to the second embodiment performs magnetic field initialization before the idling operation, the influence of the hysteresis of the scanning electromagnet 3 can be sufficiently eliminated as compared with the first embodiment. .

  In the case of an irradiation method in which the charged particle beam 1 is stopped when changing the slice and the charged particle beam 1 is continuously irradiated when irradiating the same slice, a magnetic field sensor is provided in the scanning electromagnet 3 and each slice is provided. It is also possible to measure the residual magnetic field with a magnetic field sensor before beam irradiation at. If the residual magnetic field is measured, the scanning electromagnet 3 can be initialized based on the measurement value of the residual magnetic field when returning to the first step in the slice before performing the idling operation. Further, before performing the idle operation, the scanning electromagnet 3 can be initialized based on the measurement value of the residual magnetic field in the first step in the slice where the idle operation is started. Further, since the scanning electromagnet 3 can be initialized before the idling operation is performed, the operation can be performed from the first step or before a predetermined step in the slice where the beam irradiation is interrupted. FIG. 11 shows a beam stop and restart procedure in this case.

  FIG. 11 is a flowchart showing another beam stop and restart procedure in the particle beam therapy system according to the second embodiment. FIG. 11 differs from FIG. 10 in that step S11 is changed to step S2 described in the first embodiment. In each of the scanning electromagnets 3, the magnetic field at the initial target irradiation position coordinate Pi is measured by the magnetic field sensor in each slice. The irradiation management device 32 performs initialization processing of the scanning electromagnet 3 based on the measured value of the magnetic field at the first target irradiation position coordinate Pi in the slice where the idling operation is started. According to this method, when the irradiation object 15 is large and the number of irradiation steps is large, even if the irradiation is interrupted at the last slice, the interrupted slice is not performed without starting the idling from the first step of the main irradiation. Since the idling operation is performed from the first step, the idling time can be shortened.

  In the first embodiment, it is desirable to start from the first step in the slice from the viewpoint of reproducibility as the starting step of the idling operation, but even when it is performed from a predetermined step (before a predetermined number of spots) confirmed experimentally. , Explained that the corresponding effect can be obtained. When this method is applied, not only when the initialization process of the scanning electromagnet 3 is performed based on the measured value of the magnetic field at the first target irradiation position coordinate Pi in the slice, for example, B = 0, H = 0, dH / dt Even when the scanning electromagnet 3 is initialized under a predetermined initialization condition such as = 0, the influence of the hysteresis of the scanning electromagnet 3 can be sufficiently eliminated, and the irradiation accuracy can be within the range.

  In the first and second embodiments, the charged particle beam 1 is stopped when the slice is changed, and the irradiation method in which the charged particle beam 1 is continuously irradiated when irradiating the same slice is described. Without being limited, the present invention can also be applied to other irradiation methods such as spot scanning in which the charged particle beam 1 stops for each irradiation spot and raster scanning.

DESCRIPTION OF SYMBOLS 1 ... Charged particle beam 3, 3a, 3b, 3x, 3y ... Scanning magnet, 7 ... Position monitor, 15 ... Irradiation object, 24 ... Patient, 32 ... Irradiation management apparatus, 51 ... Particle beam therapy apparatus, 54 ... Accelerator, 78 ... Patient sensor, 84, 84a, 84b ... Interlock information input device, Ia ... Current correction data, Io, Ir ... Command current, Pi ... Target irradiation position coordinate, Ps ... Measurement position coordinate.

Claims (6)

A patient respiration evaluation method for evaluating a deviation from a reference respiration signal representing a target respiration of a patient in an actual respiration signal representing an actual respiration of the patient,
Obtaining a first gain and a first phase in a description function corresponding to a first-order term when the reference respiratory signal is expanded in a Fourier series;
Obtaining a second gain and a second phase in a description function corresponding to a primary term when the real respiratory signal is expanded in a Fourier series;
Performing at least one of gain comparison for comparing the first gain and the second gain, and phase comparison for comparing the first phase and the second phase;
A method for evaluating patient breathing, comprising: It is a patient respiration evaluation method of Claim 1, Comprising:
When the second gain suddenly deviates from a preset gain threshold range from the first gain, and the second phase suddenly deviates from a preset phase threshold range from the first phase. A method for evaluating patient respiration, further comprising the step of determining that the patient has coughed in at least one of the cases of separation. The patient respiratory evaluation method according to claim 1,
When the second gain is gradually reduced within a preset gain threshold range from the first gain, or the correlation between the second phase and the first phase is a preset correlation A method for evaluating patient respiration, further comprising a step of determining that the patient has fallen into a sleep state or a sign of going into a sleep state when there is no correlation beyond the determination range. A patient respiration evaluation apparatus for evaluating a deviation from a reference respiration signal representing a target respiration of a patient in an actual respiration signal representing an actual respiration of the patient,
A gain calculation unit for obtaining a first gain and a first phase in a description function corresponding to a first-order term when the reference respiratory signal is expanded in a Fourier series;
A phase calculation unit for obtaining a second gain and a second phase in a description function corresponding to a first-order term when the real respiratory signal is expanded in a Fourier series;
A comparison unit that performs at least one of gain comparison that compares the first gain and the second gain, and phase comparison that compares the first phase and the second phase;
A patient respiratory evaluation apparatus comprising: The patient respiration evaluation apparatus according to claim 4,
When the second gain suddenly deviates from a preset gain threshold range from the first gain, and the second phase suddenly deviates from a preset phase threshold range from the first phase. A patient respiration evaluation apparatus, comprising: a determination unit that determines that the patient coughed in at least one of the cases of separation. The patient respiration evaluation apparatus according to claim 4,
When the second gain is gradually reduced within a preset gain threshold range from the first gain, or the correlation between the second phase and the first phase is a preset correlation A patient respiration evaluation apparatus, comprising: a determination unit that determines that the patient has fallen into a sleep state or is a sign of going into a sleep state when the correlation is lost beyond a determination range.

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