JP6063983B2 - Particle beam therapy system - Google Patents

Description

  The present invention relates to a treatment planning apparatus, and more particularly, to a treatment planning apparatus used for a particle beam extraction apparatus that irradiates an affected area with a charged particle beam such as protons and carbon ions.

  In the particle beam therapy, treatment is performed by irradiating a target tumor cell with a particle beam. Although X-rays are the most widely used treatment using radiation, there is a demand for treatments using proton beams and particle beams (charged particle beams) typified by carbon rays that have high dose concentration to the target. It is growing.

  Excessive irradiation or insufficient dose leads to side effects on normal tissues other than tumors and tumor recurrence. Therefore, it is required to irradiate the designated dose so as to concentrate on the tumor area as accurately as possible. In particle beam therapy, the use of scanning irradiation as a method for concentrating dose is spreading. The scanning irradiation method is a method of giving a high dose only to a tumor region by irradiating a thin charged particle beam so as to fill the inside of the tumor. In the case of the scanning irradiation method, a patient-specific instrument such as a collimator for shaping the dose distribution of the charged particle beam into a tumor shape is basically unnecessary, and various distributions can be formed.

  In order to irradiate an arbitrary position inside the tumor, the scanning method requires control of the depth (range) of the charged particle beam and irradiation position control in the plane (lateral direction) perpendicular to the beam traveling direction. It becomes. The range is controlled by changing energy with an accelerator or a range modulator. The lateral control is performed by deflecting the beam traveling direction by two sets of scanning electromagnets and guiding it to an arbitrary position in the plane.

  In the scanning irradiation method, the entire tumor is not irradiated simultaneously with the expanded beam as in the case of irradiation with X-rays, but irradiation is performed in order for each divided region. For this reason, when a target moving with respiration or heartbeat is irradiated, the relative distance of each irradiation position changes from the time of planning, and there is a possibility that the dose distribution as planned cannot be obtained. In order to avoid this, for example, there is a method of irradiating a charged particle beam only when the target is at a specific position while observing the movement of the target to be irradiated.

  In addition to this, a method of reducing the difference from the planned dose distribution by controlling the number of times of irradiation and the scanning path has been proposed. For example, in Patent Document 1, by dividing and irradiating the same position a plurality of times, an error due to target movement is averaged to approximate the planned dose distribution. Further, Non-Patent Document 1 shows that a dose distribution closer to the target is obtained by matching the main scanning direction of the charged particle beam with the moving direction of the target.

Japanese Patent No. 4273502 JP 2009-66106 A

S Water, R Kreuger, S Zenklusen, E Hug and A J Lomax, “Tumour tracking with scanned proton beams assessing the accuracy and practicalities”, Phys. Med. Biol. 54 (2009) 6549-6563.

  On the other hand, in the conventional treatment planning apparatus, it is difficult to arbitrarily set the scanning direction of the charged particle beam. In the conventional treatment planning apparatus, the scanning direction is determined as follows regardless of the moving direction of the target. The lateral irradiation position is controlled by two sets of scanning magnets as described above, and these scan the charged particle beam in directions perpendicular to each other. The scanning speed is not the same for the two electromagnets, and generally the electromagnet on the upstream side with respect to the beam traveling direction can scan at a higher speed. For this reason, the scanning path moves in the direction capable of high-speed scanning, and when it reaches the end of the target, it moves a little in the direction of another scanning electromagnet and then moves again in the high-speed scanning direction. It is common to take a zigzag path. For example, in Patent Document 2, such a route is used.

  In order to scan the charged particle beam in the same direction as the target movement direction, it is necessary for the treatment planning apparatus to determine which scanning direction corresponds to the target movement after grasping the movement of the target. . This is because the irradiation device can irradiate the patient with a charged particle beam from any direction, so the scanning direction must be determined in consideration of the irradiation direction even with the same target movement, and the operator can easily determine it. That was difficult.

  As described above, the conventional treatment planning apparatus has no means that allows the operator to easily specify the scanning direction from the three-dimensional movement of the actual target and the designated irradiation direction.

Above-mentioned problems, an accelerator that generates a load charged particles beam, a scanning magnet for scanning the charged particle beam irradiated to the target, e Bei and a control device for controlling the amount of current of the scanning electromagnet, the control device moves the target It has a reading unit to read the first scan path for a direction to the scanning direction and resolve more particle beam therapy system, characterized by controlling the amount of current of said scanning electromagnet based on the first scan path be able to.

  The direction designated as the target moving direction is calculated from the tomographic image obtained by imaging a plurality of states including the target region, the position of the specific region is extracted, the moving direction of the region position is extracted, and the moving direction is set as the particle beam scanning plane It can be calculated by the arithmetic unit by using the direction projected onto the.

  According to the present invention, it is possible to create treatment plan data that improves the uniformity of dose distribution.

It is a figure which shows the flow until a treatment plan is drawn up by suitable one Embodiment of this invention. It is a flowchart figure which shows the flow of planning of the treatment plan by the treatment plan apparatus of suitable Embodiment 1 of this invention. It is explanatory drawing which shows the structure of the whole particle beam therapy system. It is explanatory drawing which shows the structure of an irradiation field formation apparatus. It is explanatory drawing which shows the structure of the control apparatus containing the treatment planning apparatus of Embodiment 1. FIG. It is explanatory drawing which shows the structure of the treatment plan apparatus of Embodiment 1. FIG. It is a figure explaining the input of the target area | region within the slice of CT data. It is a conceptual diagram which shows the mode of the beam irradiation by a scanning method. It is explanatory drawing which shows the procedure of the method of calculating the target moving direction in Embodiment 1. It is explanatory drawing which shows the procedure of the method of calculating the target moving direction in Embodiment 1. It is a figure showing the screen which designates a target moving direction with the method of Embodiment 1. FIG. It is explanatory drawing which shows the procedure of the method of calculating a spot position. 6 is an explanatory diagram illustrating a scanning direction calculated by the procedure of Embodiment 1. FIG. 10 is an explanatory diagram showing a coordinate system in Embodiment 2. FIG. It is a flowchart figure showing the flow of the planning of the treatment plan by the treatment plan apparatus of Embodiment 3. FIG. FIG. 10 is a conceptual diagram illustrating changing a scanning path by the method described in the third embodiment.

  Hereinafter, embodiments of the present invention will be described with reference to the drawings.

  A treatment planning apparatus according to a preferred embodiment of the present invention will be described with reference to the drawings. First, before describing the treatment planning apparatus of the present embodiment, a particle beam treatment system targeted by the treatment planning apparatus will be described with reference to FIGS.

  The configuration of the entire particle beam therapy system will be described with reference to FIG. The charged particle beam generator 301 includes an ion source 302, a pre-accelerator 303, and a particle beam accelerator 304. In this embodiment, a synchrotron type particle beam accelerator is assumed, but the function of this embodiment can be applied to any other particle beam accelerator such as a cyclotron. As shown in FIG. 3, the synchrotron type particle beam acceleration device 304 includes a deflection electromagnet 305, an acceleration device 306, an extraction high frequency application device 307, an extraction deflector 308, and a quadrupole electromagnet (see FIG. 3). Not shown).

  A process until a charged particle beam is emitted toward a patient in the particle beam generation apparatus 301 using the synchrotron type particle beam acceleration apparatus 304 will be described with reference to FIG. Particles (such as protons and heavy particles) supplied from the ion source 302 are accelerated by the pre-stage accelerator 303 and sent to the synchrotron 304 which is a beam accelerator. The synchrotron 304 is provided with an acceleration device 306, and a high-frequency acceleration cavity (not shown) provided in the acceleration device 306 in synchronization with a cycle in which a charged particle beam circulating in the synchrotron 304 passes through the acceleration device 306. )) To accelerate the charged particle beam. In this way, the charged particle beam is accelerated until it reaches a predetermined energy.

  After the charged particle beam is accelerated to a predetermined energy (for example, 70 to 250 MeV), when an emission start signal is output from the central controller 312 via the irradiation control system 314, the high-frequency power from the high-frequency power source 309 is A high frequency application electrode installed in the high frequency application device 307 is applied to the charged particle beam circulating in the synchrotron 304, and the charged particle beam is emitted from the synchrotron 304.

  The high energy beam transport system 310 connects the synchrotron 304 and the irradiation field forming device 400. The charged particle beam extracted from the synchrotron 304 is guided to the irradiation field forming device 400 installed in the rotary irradiation device 311 via the high energy beam transport system 310. The rotary irradiation apparatus 311 irradiates a charged particle beam from an arbitrary direction of the patient 406, and can rotate in any direction around the bed 407 where the patient 406 is installed by rotating the entire apparatus. .

  The irradiation field forming device 400 is a device that shapes the shape of the charged particle beam that is finally irradiated to the patient 406, and its structure differs depending on the irradiation method. As typical irradiation methods, there are a scatterer method and a scanning method, but this embodiment is directed to the scanning method. In the scanning method, a thin charged particle beam transported from the high-energy beam transport system 310 is directly irradiated onto the target, and this is scanned three-dimensionally to finally form a high-dose region only on the target. Can do.

  FIG. 4 shows the configuration of an irradiation field forming apparatus 400 corresponding to the scanning method. Each role and function will be briefly described with reference to the figure. The irradiation field forming apparatus 400 includes two scanning electromagnets 401 and 402, a dose monitor 403, and a beam position monitor 404 from the upstream side. The dose monitor measures the amount of charged particle beam that has passed through the monitor. On the other hand, the beam position monitor can measure the position through which the charged particle beam has passed. The information from these monitors enables the irradiation control system 314 to manage that the planned amount of the charged particle beam is irradiated at the planned position.

  The thin charged particle beam transported from the charged particle beam generator 301 through the high energy beam transport system 310 is deflected in the traveling direction by the scanning electromagnets 401 and 402. These scanning electromagnets are provided so that magnetic lines of force are generated in a direction perpendicular to the beam traveling direction. For example, in FIG. 4, the scanning electromagnet 401 deflects the beam in the scanning direction 405, and the scanning electromagnet 402 Deflection in the vertical direction. By using these two scanning electromagnets, the charged particle beam can be moved to an arbitrary position in a plane perpendicular to the beam traveling direction, and the target 406a can be irradiated with the beam.

  The irradiation control system 314 controls the amount of current that flows through the scanning electromagnets 401 and 402 via the scanning electromagnet magnetic field strength controller 411. The scanning electromagnets 401 and 402 are supplied with current from the scanning electromagnet power supply 410, and a magnetic field corresponding to the amount of current is excited to freely set the deflection amount of the charged particle beam. The relationship among the charged particle beam, the deflection amount, and the current amount is held in advance in the memory 313 in the central control device 312 as a table, and is referred to.

  There are two scanning methods of the charged particle beam in the scanning method. One is a discrete method that repeats the movement and stop of the irradiation position, and the other is a method that continuously changes the irradiation position. To move discretely, a prescribed amount of charged particle beam is irradiated while the irradiation position is kept at a certain point. This point is called a spot. Subsequently, after the supply of the charged particle beam is temporarily stopped, the amount of current of the scanning electromagnet is changed so that the next position can be irradiated. After moving to the next irradiation position, the charged particle beam is irradiated again. At this time, if high-speed scanning is possible, it is possible not to stop the charged particle beam even during movement.

  In the method of moving continuously, the irradiation position is changed while the charged particle beam is irradiated. That is, while continuously changing the excitation amount of the scanning electromagnet, it is moved while irradiating the charged particle beam so as to pass through the entire irradiation field. In this method, the change in the irradiation amount for each irradiation position is realized by modulating the scanning speed by the scanning magnet and / or the current amount of the charged particle beam.

  Subsequently, a treatment planning apparatus according to a preferred embodiment of the present invention will be described with reference to FIG. First, the treatment planning device 501 is connected to the data server 502 and the central control device 312 via a network. As illustrated in FIG. 6, the treatment planning apparatus 501 includes an input device 602, a display device 603, a memory 604, an arithmetic processing device 605, and a communication device 606. An arithmetic processing device 605 is connected to the input device 602, the display device 603, the memory (storage device) 604, and the communication device 606.

  Prior to treatment, an image for treatment planning is taken. CT data is most commonly used as an image for treatment planning. CT data is data obtained by reconstructing three-dimensional data from fluoroscopic images acquired from a plurality of directions of a patient. Along with the recent increase in imaging time, multiple CT data for each phase can be obtained by capturing multiple images in different states (referred to as phases) due to respiratory movement even at sites with periodic movements associated with respiration, for example. Some CTs can be set. This is called 4DCT. In the 4DCT image, it is possible to confirm the movement of the target due to respiration and the like by comparing the CT data at different phases. At this time, in order to grasp the movement more clearly, a method of grasping the position of the target by embedding a marker such as a metal ball and following the movement may be used.

  CT data imaged by a CT apparatus (not shown) is stored in the data server 502. The treatment planning apparatus 501 uses this CT data. The flow of treatment planning is shown in FIG. First, when planning of a treatment plan is started (step 101), the treatment planning device 501 receives target CT data from the data server 502 in accordance with an instruction from an engineer (or doctor) who is an operator of the treatment planning device 501. Is read. That is, the treatment planning apparatus 501 copies (stores) CT data from the data server 502 onto the memory 604 through a network connected to the communication apparatus 606.

  When the reading of the CT data is completed, the operator should designate the CT data as a target for each slice of the CT data using a device such as a mouse corresponding to the input device 602 while checking the CT data displayed on the display device 603. Enter the area. When there are a plurality of data sets obtained by imaging the same part as in 4DCT, a single composite image is generated from a plurality of images, and the above-described target selection operation is performed on this image. For example, a set of synthesized images can be obtained by comparing the CT values of points representing the same position from the respective images and selecting numerical values with the highest luminance at all points.

  When the input is completed in each slice, the operator registers the input area in the apparatus (step 102). By registering, the area input by the operator is stored in the memory 604 as three-dimensional position information. If there are other areas that need to be evaluated and controlled, such as when an important organ whose radiation dose should be suppressed as much as possible exists in the vicinity of the target area, the operator registers the positions of these important organs in the same way. FIG. 7 shows an example in which the operator inputs a target area 702 on a slice 701 having CT data on the display device 603.

  Next, the operator designates the irradiation direction, that is, the angle between the rotary irradiation device 311 and the bed 407. When performing irradiation from a plurality of directions, a plurality of angles are selected. Other parameters for irradiation to be determined by the operator include a dose value (prescription dose) to be irradiated to the region registered in step 102 and an interval between adjacent spots. The prescription dose includes the dose that should be delivered to the target and the maximum dose that important organs should avoid. The initial value of the spot interval is automatically determined so as to be approximately the same as the beam size of the charged particle beam, but can be changed by the operator. The operator sets these necessary irradiation parameters (step 103).

  In addition to these irradiation parameters, the target moving direction, which is a feature of the treatment planning apparatus of this embodiment, is designated. The designation method will be described with reference to FIGS. As shown in FIG. 8, it is assumed that the center of gravity of the target area 702 is positioned so as to coincide with the isocenter (rotation center position of the rotary irradiation device 311) 801 at the time of irradiation. The spot position is defined by coordinates on a plane (isocenter plane) 804 that includes the isocenter 801 and is perpendicular to a straight line (beam center axis) 803 that connects the scan center point (line source) 802 and the isocenter 801. In the following, the surface 804 is called an isocenter surface, and the straight line 803 is called a beam center axis. For example, when there is a spot at a position 805 on the isocenter surface 804, the currents of the scanning electromagnets 401 and 402 are adjusted so that the charged particle beam passes a point 805 on the isocenter surface 804, and the locus of the charged particle beam is a straight line. It becomes like 806. Where this charged particle beam stops depends on the beam energy.

  Below, it demonstrates based on the example which imaged 4DCT in the state which embedded the marker. Even when there is no marker, the same effect can be obtained when the operator designates an arbitrary feature point in the image. The treatment planning device 501 searches all slice images of CT data for the CT data of each phase of 4DCT read on the memory 604, and specifies the marker position. When automatic search is difficult, the operator may specify directly. As a result, the marker position in the CT data corresponding to each phase is determined. FIG. 9 shows this state. Points 902 and 903 are marker positions in a certain phase. If the marker positions in all phases are connected by straight lines, a three-dimensional locus 904 of the marker can be obtained. The marker position is determined so that this movement represents the movement of the target.

  Next, the marker position at each phase including the point 902 and the point 903 is projected onto the isocenter surface 804. In FIG. 9, the point 902 is a point 905 projected onto the isocenter plane 804. In this way, by projecting all the points onto the isocenter surface 804, the locus 906 of the marker projected onto the isocenter surface 804 is obtained.

  The projection result is displayed on the display device 603 of the treatment planning device 501. This is shown in FIG. Points 1001, 1002, 1003, 1004, 1005, and 1006 shown in FIG. 10 represent positions obtained by projecting the marker positions for each phase onto the isocenter plane 804. From this displayed image, the arithmetic processing device 605 of the treatment planning device 501 automatically calculates the target moving direction. For example, the arithmetic processing unit 605 calculates the distance between the points 1001 to 1006 and searches for the point and the point that are the longest combination. In FIG. 10, the direction along the straight line 1007 connecting the resulting points 1001 and 1004 is defined as the moving direction. When the beam is irradiated only when the marker is within a specific range, the same calculation can be performed after extracting only the point corresponding to the phase where the marker is within the range.

  The calculated direction is also displayed on the display device 603 of the treatment planning device 501. An example of the displayed screen is shown in FIG. The calculated direction 1101 is displayed with an arrow. This screen is displayed simultaneously with FIG. 10 showing the isocenter plane 804. Alternatively, the arrow 1101 may be displayed on the screen of FIG. The coordinate system for defining the direction is common to the coordinate system 1008 in FIG. 10 and the coordinate system 1102 in FIG. The operator can confirm this and manually correct the direction if necessary. What is necessary is just to input the component of the x direction of the arrow 1101, and the y direction to the input screen 1103 of FIG. Alternatively, the direction can be directly designated on the screen using an input device such as a mouse (step 104).

  As described above, the movement direction may be determined after projecting the marker position onto the plane, but the movement direction may be determined without projection. That is, at each point including the point 902 and the point 903 in FIG. 9, a set of two points having the longest distance is searched, and the direction connecting them is set as the target movement direction. In the case of FIG. 9, the direction along the straight line connecting the points 902 and 903 is the moving direction. Subsequently, the direction of movement on the isocenter surface is determined by projecting the direction onto the isocenter surface 804.

  The advantage of this method is that the moving component in the direction perpendicular to the isocenter plane 804 can also be calculated. The dose distribution by the charged particle beam is almost Gaussian in the direction perpendicular to the traveling direction, but has a sharp peak just before stopping in the traveling direction. Therefore, the movement of the target in the beam traveling direction, that is, the direction perpendicular to the isocenter plane 804 generally has a larger influence on the dose distribution than the movement in the lateral direction. By simultaneously displaying the moving component perpendicular to the target isocenter surface 804 on the screen of FIG. 11, the operator can adjust the beam irradiation direction, that is, the rotary irradiation device 311 or the bed 407 so that the value becomes smaller than a desired value. It becomes possible to correct the angle.

  After the above parameters are determined, the treatment planning device 501 automatically calculates (step 105). Hereinafter, the details of the calculation contents performed by the treatment planning apparatus 501 will be described with reference to FIG.

  First, the treatment planning apparatus 501 determines a beam irradiation position. In the case of a discrete scanning method, a discrete spot position is calculated, and in the case of continuous irradiation, a scanning path is calculated. In this embodiment, the description is based on a discrete scanning method, but a continuous scanning method may be used. If the continuous scanning method is considered that fine and discrete passing positions are prepared on the scanning path, the same effect as in this embodiment can be obtained. When a plurality of directions are designated as the irradiation direction (the angle between the rotary irradiation device 311 and the bed 407), the same operation is performed for each direction.

  The treatment planning apparatus 501 starts the spot position selection from the CT data read into the memory 604 and the region information input by the operator (step 201). As described above, the irradiation position is determined by the coordinates on the isocenter plane 804. As an example, assume that a position on the isocenter plane 804 and a point 805 are selected as irradiation positions in FIG. The treatment planning device 501 searches for the energy where the beam stop position is substantially within the target when the beam is irradiated along the line 806 connecting the source 802 and the point 805, and the energy (one type is (Not limited) is selected as the energy applied to the position of the point 805. By performing this for all irradiation positions set on the isocenter surface, a set of irradiation positions and energy on the isocenter surface necessary for irradiating the target can be obtained. This is the spot that is actually irradiated.

  The irradiation positions on the isocenter surface 804 are selected so that the interval between adjacent irradiation positions is equal to or less than the value specified in step 103. The simplest method is to arrange one side on a square lattice with a specified interval. The treatment planning apparatus 501 of the present embodiment can select the direction determined in step 104 as the lattice axis at this time, that is, the direction in which the irradiation positions are aligned on a straight line. FIG. 12 shows a conceptual diagram until a spot is selected. In FIG. 12, the direction 1101 determined in step 104 is also written.

  First, the treatment planning device 501 sets a plurality of straight lines parallel to the direction 1101 (step 202). One of them is a straight line 1201. The interval between the straight lines is the interval selected in step 103. Next, an irradiation position is set on the set straight line (step 203). The interval between adjacent irradiation positions on the same straight line is also equal to the interval between the straight lines. The set irradiation positions are represented by circles such as 1202 and 1203 in FIG. 12, but it can be seen that they are arranged on a square lattice with the direction 1101 as an axis. Finally, when these positions are irradiated with a charged particle beam, the beam energy at which the beam stop position falls within the target is selected (step 204). The irradiation position outside the target is not irradiated with the charged particle beam. In FIG. 12, the charged particle beam is not irradiated to the irradiation position indicated by the white circle mark such as 1202, and the charged particle beam is irradiated only to the irradiation position of the black circle indicated by 1203. A dotted line 1204 represents a contour line of the target shape at a depth corresponding to the stop position of the charged particle beam having a certain energy.

  If it is a discrete scan and the charged particle beam is stopped during movement between spots, the final dose distribution will not be on the scan path. In this case, the scanning path may be determined after the irradiation dose for each spot is determined. However, in other irradiation methods, it is necessary to calculate the dose distribution after taking the scanning path into consideration, so the scanning path is determined at this stage. To do. In this embodiment, it is assumed that the scanning path is determined here regardless of the scanning method (step 205).

  The scanning path is determined along the straight line set in step 202. In FIG. 13, the spot position of a beam with a certain energy is represented by a black circle mark such as a point 1203. Of the straight lines parallel to the direction determined by the operator, the scanning path starts from a straight line 1301 which is the uppermost straight line in the figure. The scanning path moves between the spots on the straight line along the straight line 1301 and moves to the next straight line when reaching the end. The scanning direction on the next straight line is reversed. The process ends when all spots on the straight line 1302 are finally passed while repeating this movement. As a result, a zigzag path as indicated by an arrow 1303 is obtained.

  The operation of determining the scanning path is performed on spots corresponding to all selected beam energies. When all the energies are completed, the path is determined for all spots necessary for irradiation (step 206). If there are a plurality of irradiation directions, the same operation is performed for all directions (step 207).

  When all the spot positions and their routes are determined, the treatment planning apparatus 501 starts the optimization calculation of the irradiation amount as it is (step 208). The dose to each spot is determined so as to approach the target dose distribution set in step 103. In this calculation, a method using an objective function in which a deviation from a target dose with the irradiation dose for each spot as a parameter is quantified is widely adopted. The objective function is defined so that the dose distribution becomes small enough to meet the target dose, and the optimum dose is calculated by searching the dose that minimizes the dose by iterative calculation. To do.

  When the dose is determined by iterative calculation, the treatment planning apparatus 501 calculates a dose distribution using the spot position and the spot dose finally obtained (step 209). The calculated result is displayed on the display device 603 (step 210). The operator examines this result and determines whether or not the dose distribution satisfies the target condition. Not only the dose distribution but also the spot position and scanning path calculated by the treatment planning device 501 can be confirmed on the display device 603 (step 106). If the distribution or scanning path is not desirable, the process returns to step 103 to reset the irradiation parameters. Parameters to be changed include irradiation direction, prescription dose, and spot interval.

  Even when the process returns to step 103 and the conditions are changed, the target moving direction determined in step 104 is stored. Under the new conditions specified by the operator, the scanning path and the dose distribution are updated according to the method from step 201 to step 209, and the new result is displayed on the display device 603. When a desired result is obtained, the treatment planning is completed (step 107). The obtained irradiation conditions are stored in the data server 502 through the network (steps 108 and 109).

  When irradiating a charged particle beam, the central controller 312 reads the corresponding treatment plan data stored in the data server 502. If necessary, the data is converted into a format that can be read by the central controller 312. In the irradiation control system 314, the energy, scanning position, and irradiation amount of the charged particle beam to be irradiated are designated by the central controller 312. In accordance with this instruction, the irradiation control system 314 emits a charged particle beam.

  According to the present embodiment, it is possible to input the movement of the affected area of the patient and create treatment plan data that mainly scans the charged particle beam in the direction matching the direction, so that the uniformity of the dose distribution is improved. Treatment plan data can be provided.

  In the first embodiment, the method of extracting the moving direction of the target using the 4DCT image has been described. Even when normal CT data is used instead of the 4DCT, the same operation can be performed by directly specifying the moving direction by the operator. The effect of can be obtained. Example 2 describes this method.

  The operation method in this embodiment is the same as that in the first embodiment up to step 103 in FIG. Hereinafter, a method different from the first embodiment will be described. In this embodiment, the operator determines the target moving direction in step 104 without using the result of 4DCT. Even if the target position is not confirmed directly with a marker, etc., if the movement direction due to respiration or heartbeat of a specific organ is not expected to change significantly, the operator moves directly without the need to extract the target movement direction. It is possible to specify the direction.

  The operator designates the target moving direction in the three-dimensional coordinate system in the CT data. For example, the coordinate system is as shown in FIG. In FIG. 14, the direction from the foot to the head is defined as the z-axis, and the x-axis and the y-axis are set in a direction orthogonal to the z-axis. When it is determined that the target is moving from the foot to the head, the operator designates a three-dimensional direction in this coordinate system. That is, a value of (x, y, z) = (0, 0, 1) is input using an input screen similar to FIG.

  When the direction is determined, the treatment planning apparatus projects the direction specified in the coordinate system of FIG. 14 onto the isocenter surface 804, and calculates the direction on the isocenter surface 804. When the direction is determined, step 105 and subsequent steps can be performed in the same manner as in the first embodiment. According to the present embodiment, since it is not necessary to confirm the position of the marker for each phase by 4DCT, the labor of the operator can be reduced.

  According to the present embodiment, it is possible to input the movement of the affected area of the patient and create treatment plan data that mainly scans the charged particle beam in the direction matching the direction, so that the uniformity of the dose distribution is improved. Treatment plan data can be provided.

  In the methods of the first embodiment and the second embodiment, spots are arranged on a straight line parallel to a designated direction. In this method, when the designated direction is changed, the spot position is also changed. In FIG. 2, all calculations after step 203 need to be performed again.

  On the other hand, if the charged particle beam is stopped during scanning, the dose distribution does not depend on the scanning path as long as the spot position is the same. In that case, it is possible to change only the scanning path along an arbitrary direction from a predetermined spot position separately from the methods of the first and second embodiments. This method will be described below as Example 3.

  FIG. 15 shows a flow of the part corresponding to the automatic calculation of the treatment planning apparatus 501 (step 105 in FIG. 1) in this embodiment. After the start of automatic calculation (step 1501), the spot position is selected (step 1502), the dose is optimized for each spot (step 1503), and the dose distribution without considering the scanning direction, as in the conventional treatment planning apparatus. Calculation (step 1504) is performed.

  In the method of this embodiment, the scanning path is changed after the dose distribution calculation in step 1504. First, the moving direction of the target previously designated at step 104 in FIG. 1 is read (step 1505). Thereafter, for the spots irradiated from the same energy and the same direction, the scanning path is set as follows (step 1506). The arithmetic processing unit 605 of the treatment planning apparatus 501 prepares a function for converting the path into an appropriate value when the scanning path is given. For example, the total scanning distance of the scanning path may be defined as a basic value, and the value may be defined so that the value becomes smaller when the scanning direction is close to the direction specified in step 104. By using a technique such as an annealing method, an optimum scanning path having the smallest function value defined in various scanning paths is searched.

  An example is shown in FIG. Reference numeral 1601 denotes a state before changing the scanning path for a certain energy spot. A black circle represents a spot position, and an arrow 1602 is a scanning path in the initial state. In the path 1602, the moving direction of the target is not considered. Subsequently, 1603 is a result of changing the scanning path based on the designated direction. The spot position is the same as in the state 1601 before changing the scanning path, but the target moving direction 1604 is specified, and it can be seen that the scanning path 1605 is set so as to mainly scan in this direction.

  This is performed for beams of all energy to be irradiated and all irradiation directions (angles of the rotary irradiation device 311 and the bed 407) (steps 1507 and 1508). Finally, the irradiation parameters including the scanning path information are output as a result, and the process ends (steps 1509 and 1510).

  In the method of this embodiment, the scanning path can be changed after the spot position and the irradiation amount for each spot are determined. Therefore, this operation can also be performed by a device other than the treatment planning device. For example, it is conceivable to change the scanning path using the central controller 312 immediately before irradiation. The treatment plan data created by the treatment planning device 501 is stored in the data server 502. This data is read by the central controller 312 when actual irradiation is performed. At this time, the central controller displays the scanning path on the display device 315 and provides an interface for changing the scanning path, so that the operator can use the input device (not shown) of the central controller to scan the path. Can be corrected. When the operator indicates a direction for changing the scanning path on the screen similar to FIG. 11 or the coordinate system shown in FIG. 14, the scanning path is changed in the same manner as in step 1506.

  According to the present embodiment, immediately before irradiation, the state of the target at that time can be observed to change the scanning path of the charged particle beam, so that the movement of the target at the time of irradiation can be well reflected. Although it is possible to change the scanning path immediately before the irradiation in the methods of the first and second embodiments, the dose distribution is not changed only by changing the scanning path in the method of the present embodiment as compared with those methods. In addition, the calculation time is short, and there is an advantage that the reconfirmation of the validity of the plan (step 107) required when the dose distribution is changed can be easily performed.

  According to the present embodiment, it is possible to input the movement of the affected area of the patient and create treatment plan data that mainly scans the charged particle beam in the direction matching the direction, so that the uniformity of the dose distribution is improved. Treatment plan data can be provided.

DESCRIPTION OF SYMBOLS 301 Charged particle beam generator 302 Ion source 303 Pre-stage accelerator 304 Particle beam accelerator 305 Deflection magnet 306 Accelerator 307 High frequency application device 308 Deflector for extraction 309 High frequency supply device 310 High energy beam transport system 311 Rotating irradiation device 312 Central controller 313 , 604 Memory 315, 603 Display device 400 Irradiation field forming device 401, 402 Scanning magnet 403 Dose monitor 404 Beam position monitor 405 Scanning direction 406 Patient 406a Target 410 Scanning magnet power supply 411 Scanning magnet magnetic field strength control device 501 Treatment planning device 502 Data Server 602 Input device 605 Processing unit 606 Communication device 701 CT data slice 702 Target region 801 Isocenter 802 Radiation source 803 Beam center axis 804 Isocenter plane 8 06 Lines 902 and 903 connecting point 805 and radiation source 802 Marker position 904 Marker locus 905 Point 902 is projected onto isocenter plane 804 Point 906 Marker locus 904 is projected onto plane 804 Trajectories 1001, 1002, 1003, 1004 1005, 1006 Point 1007 projected from the surface 804 1007 A straight line connecting the point 1001 and the point 1004 1008 The coordinate system 1101 in FIG. 10 The specified direction 1102 The coordinate system in FIG. 11 (common with 1008)
1103 Input screen 1201 for specifying the direction 1101 by a numerical value 1201 A straight line 1202 parallel to the direction 1101 Irradiation position 1203 A beam irradiation position 1204 Target contour 1301 A straight line 1302 at the endmost end Straight line 1303 Scan path 1601 State before scan path change 1602 Scan path before change 1603 State after scan path change 1604 Specified scan direction 1605 Scan path after change by the method in the third embodiment

Claims (11)

An accelerator that generates a charged particle beam;
A scanning electromagnet that scans the charged particle beam that irradiates the target;
A particle beam therapy system comprising a control device for controlling a current amount of the scanning electromagnet,
The control device includes a reading unit that reads a first scanning path in which a moving direction of the target is a scanning direction of the charged particle beam,
A particle beam therapy system that controls the amount of current of the scanning electromagnet based on the first scanning path. The particle beam therapy system according to claim 1,
A particle beam therapy system comprising input means for receiving an input related to the moving direction. The particle beam therapy system according to claim 1 or 2,
A particle beam therapy system, wherein a second scanning path created in advance is changed to the first scanning path having the moving direction as the scanning direction. The particle beam therapy system according to claim 3,
A treatment planning device for creating treatment plan data for performing particle beam therapy;
The treatment planning apparatus changes the second scanning path to the first scanning path with the moving direction as the scanning direction. The particle beam therapy system according to claim 3,
The control apparatus changes the second scanning path to the first scanning path having the moving direction as the scanning direction, and the particle beam therapy system. The particle beam therapy system according to claim 1 or 2,
A treatment planning device for creating treatment plan data for performing particle beam therapy;
The particle beam therapy system, wherein the therapy planning device calculates the first scanning path. The particle beam therapy system according to any one of claims 1 to 6,
A particle beam therapy system that determines a scanning direction of the charged particle beam on the isocenter surface based on the moving direction, and scans the charged particle beam in the scanning direction on the isocenter surface. The particle beam therapy system according to any one of claims 1 to 7,
A particle beam therapy system that scans the charged particle beam in a direction that matches the moving direction of the organ due to respiration or heartbeat. The particle beam therapy system according to any one of claims 1 to 8,
A display device for displaying a dose distribution when the charged particle beam is irradiated;
The said display apparatus is a particle beam therapy system which displays the instruction | indication part which instruct | indicates the change of the said scanning direction. The particle beam therapy system according to any one of claims 1 to 9,
Based on the moving direction, determine a component perpendicular to the isocenter plane,
A particle beam therapy system comprising means for correcting an irradiation direction of a charged particle beam so that the vertical component becomes small. A particle beam therapy system according to claim 4 , comprising:
The particle beam therapy system, wherein the therapy planning device calculates the second scanning path.

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