Title of Invention: PARTICLE BEAM IRRADIATION APPARATUS AND PARTICLE BEAM THERAPY SYSTEM Abstract: The objective is to eliminate the effect of the hysteresis of a scanning electromagnet so that, in the raster scanning or the hybrid scanning, there is obtained a particle beam irradiation apparatus that realizes high-accuracy beam irradiation. There are provided a scanning power source that outputs the excitation current for a scanning electromagnet and an irradiation control apparatus that controls the scanning power source; the irradiation control apparatus is provided with a scanning electromagnet command value learning generator that evaluates the result of a run-through, which is a series of irradiation operations through a command value for the excitation current outputted from the scanning power source, that updates the command value for the excitation current, when the result of the evaluation does not satisfy a predetermined condition, so as to perform the run-through, and that outputs to the scanning power source the command value for the excitation current such that its evaluation result has satisfied the predetermined condition. Detailed Description: TECHNICAL FIELD The present invention relates to a particle beam therapy system utilized in the medical field and R&Ds, and particularly to a particle beam irradiation apparatus and a particle beam therapy system of a scanning type such as a raster-scanning type. BACKGROUND ART In general, a particle beam therapy system is provided with a beam generation apparatus that generates a charged particle beam; an accelerator that is connected with the beam generation apparatus and accelerates a generated charged particle beam; a beam transport system that transports a charged particle beam that is accelerated by the accelerator so as to gain predetermined energy and then emitted; and a particle beam irradiation apparatus, disposed at the downstream side of the beam transport system, for irradiating a charged particle beam onto an irradiation subject. Particle beam irradiation apparatuses are roughly divided into apparatuses utilizing a broad irradiation method in which a charged particle beam is enlarged in a dispersion manner by a scatterer, and the shape of the enlarged charged particle beam is made to coincide with the shape of an irradiation subject in order to form an irradiation field; and apparatuses utilizing a scanning irradiation method (the spot-scanning method, the raster-scanning method, and the like) in which an irradiation field is formed by performing scanning with a thin, pencil-like beam in such a way that the scanning area coincides with the shape of an irradiation subject. The spot-scanning method is, briefly speaking, a method of forming an irradiation field by irradiating a particle beam in a small spot shape as in pointillism. In other words, the cycle consisting of supply of a beam (dotting), stoppage of a beam, and movement is repeated. The spot-scanning method is a high-flexibility irradiation method in which an irradiation dose can be changed in accordance with a spot position, and it has been attracting a large attention in recent years. The raster-scanning method is, briefly speaking, a method of forming an irradiation field by keeping a particle beam irradiated as in single-stroke painting. That is to say, it is a method of continuously irradiating a beam and making the beam move at a constant speed within a region where the target dose is constant. It has an advantage in that, because it is not required to repeat the cycle consisting of supply of a beam and stoppage of a beam, the therapy takes only a short time. There has been proposed an irradiation method that is intermediate between the spot-scanning method and the raster-scanning method. As in the raster-scanning method, a beam is kept irradiated, and as in the spot-scanning method, the beam spot position moves among the spot positions one after another. The intermediate irradiation method intends to acquire the advantages of both the spot-scanning method and the raster-scanning method. In this description, the foregoing intermediate irradiation method will be referred to as a hybrid scanning method. In the broad irradiation method, an irradiation field that coincides with the shape of a diseased site is formed by use of a collimator or a bolus. The broad irradiation method is a most universally utilized and superior irradiation method where an irradiation field that coincides with the shape of a diseased site is formed so as to prevent unnecessary irradiation onto a normal tissue. However, it is required to create a bolus for each patient or to change the shape of a collimator in accordance with a diseased site. In contrast, the scanning irradiation method is a high-flexibility irradiation method where, for example, neither collimator nor bolus is required. However, because these components for preventing irradiation onto not a diseased site but a normal tissue are not utilized, there is required a positional accuracy of beam irradiation that is the same as or higher than that of the broad irradiation method. With regard to a particle beam therapy system, there have been implemented various inventions that raise the accuracies of an irradiation position and an irradiation dose. Patent Document 1 discloses an invention, stated below, that has an objective of providing a particle beam therapy system capable of accurately irradiating a diseased site. In the invention disclosed in Patent Document 1, there are stored, in a memory device, the amount of charged particle beams scanned by a scanning apparatus and the position of a charged particle beam detected by a beam position detector while the charged particle beam is emitted; then, by utilizing the stored scanning amount and the beam position, the scanning amount of the beam scanning apparatus is set by a control apparatus, in accordance with the beam position based on information about a treatment plan. The relationship between the scanning amount and the beam position, which is obtained by actually performing irradiation, is stored in the memory device; therefore, accurate irradiation onto a diseased site can be expected. Patent Document 2 discloses an invention, stated below, that has an objective of providing a particle beam therapy system capable of ensuring high safety and emitting a charged particle beam in a highly accurate manner. In the invention disclosed in Patent Document 2, a charged particle beam emitted from a charged particle beam generation apparatus is supplied to a scanning electromagnet that performs irradiation on an irradiation plane perpendicular to the traveling direction of the beam; then, the amount of charged particle beams emitted from the charged particle beam generation apparatus is controlled based on the position and the dose, on the irradiation plane, of the charged particle beam that passes through the scanning electromagnet. Specifically, the supply of a charged particle beam to the region, among a plurality of regions formed by dividing the irradiation plane, where a target dose has been achieved is stopped, and charge particle beams are supplied to the other regions where the target dose has not been achieved. As described above, the irradiation dose in each of the regions is compared with the target dose, and the emission amount of a charged particle beam is on/off-controlled (supplied/not supplied), so that high safety is expected. With regard to a problem that hysteresis characteristics existing in the relationship between the current and the magnetic field of a scanning electromagnet deteriorates the accuracy of a beam irradiation position, Patent Document 3 discloses an invention stated below. The invention disclosed in Patent Document 3 has a first calculation means that calculates, without taking the effect of the hysteresis into account, the current value of a scanning electromagnet in accordance with the beam irradiation position based on an irradiation plan; and a second calculation means that performs, taking the effect of the hysteresis into account, a correction calculation of the current value of the scanning electromagnet calculated by the first calculation means. An irradiation control apparatus controls the current of the scanning electromagnet, based on the result of the calculation by the second calculation means. As described above, a correction calculation is performed by the second calculation means so as to eliminate the effect of the hysteresis, i.e., the second calculation means has a mathematical model where the hysteresis characteristics are represented, so that the improvement of the accuracy of a beam irradiation position is expected through the calculation. PRIOR ART REFERENCE Patent Document [Patent Document 1] Japanese Patent Application Laid-Open No. 2005-296162 [Patent Document 2] Japanese Patent Application Laid-Open No. 2008-272139 [Patent Document 3] Japanese Patent Application Laid-Open No. 2007-132902 DISCLOSURE OF THE INVENTION Problem(s) to be Solved by the Invention In the invention disclosed in Patent Document 1, a transformation table is created based on actual data on the scanning amount and the position, of a charged particle beam, which are obtained through actual irradiation, and by utilizing this transformation table, the setting current value of scanning electromagnet is calculated. However, in fact, as disclosed in Patent Document 3, because there exist hysteresis characteristics between the current and the magnetic field of the scanning electromagnet, the magnetic field at a time when the current value increases differs from the magnetic field at a time when the current decreases. That is to say, even though the current value of the scanning electromagnet at an instant is obtained, the accurate value of the magnetic field cannot be determined only through the information. Accordingly, in the invention disclosed in Patent Document 1, there has been a problem that, due to the effect of the hysteresis of the electromagnet, accurate irradiation of a diseased site cannot be performed. In the invention disclosed in Patent Document 2, the emission amount of a charged particle beam is on/off controlled (supplied/not supplied) in such a way that the irradiation dose at each of defined regions becomes a target dose. However, the plurality of regions, formed on an irradiation plane through division, which are described in the invention disclosed in Patent Document 2 are regions (excitation regions) in the excitation current space defined by the range of the excitation current of the corresponding scanning electromagnet; thus, the excitation region does not coincide with the region (irradiation region) in the actual irradiation space. That is because the excitation region and the irradiation region do not correspond to each other on a one-to-one basis unless the hysteresis of the scanning electromagnet is considered. Accordingly, even in an apparatus or a method where the irradiation dose for each excitation region is administered so as to raise the safety, there is not demonstrated the effect of administrating the dose in a small region, unless the effect of the hysteresis of the scanning electromagnet is eliminated. That is to say, there has been a problem that the hysteresis of the scanning electromagnet deteriorates the accuracy of the beam irradiation position. In the invention disclosed in Patent Document 3, a mathematical hysteresis model is made in the inside of a calculation means, and through calculation, the current value of a scanning electromagnet is corrected. However, even though the hysteresis is considered, a number of problems still exist in the invention disclosed in Patent Document 3. The first problem is that it is practically rather difficult to accurately correct the hysteresis characteristic by use of a calculation method. For example, the mode of the curve representing the hysteresis characteristic between the current and the magnetic field varies depending on not only the amplitude of the input (current) but also the speed of changing the input (current) or the changing pattern. In order to express the complicated hysteresis phenomenon by a calculation method, i.e., a mathematical model, studies and contrivances have been made for a long time in many fields; however, it is practically difficult to achieve it. The second problem is found in the method of detecting a beam irradiation position. As the invention disclosed in Patent Document 3, most of conventional methods try to detect a beam irradiation position by only a single beam position monitor or a plurality of beam position monitors. A beam position monitor does not learn a beam irradiation position by the time a charged particle beam is emitted. Accordingly, when a beam is way off the target and is irradiated onto a normal tissue or the like, all can be done is to stop the beam; thus, there has been a problem that the beam irradiation position cannot be controlled to fall on a right irradiation position onto which the beam should be emitted. The present invention has been implemented in order to solve the foregoing problems; the objective thereof is to eliminate the effect of the hysteresis of a scanning electromagnet so that, in the raster scanning or the hybrid scanning, there is obtained a particle beam irradiation apparatus that realizes high-accuracy beam irradiation. Means for Solving the Problems There are provided a scanning power source that outputs an excitation current for a scanning electromagnet and an irradiation control apparatus that controls the scanning power source. The irradiation control apparatus has a scanning electromagnet command value learning generator that evaluates the result of a run-through, which is a series of irradiation operations through a command value for the excitation current outputted from the scanning power source, that updates the command value for the excitation current, when the result of the evaluation does not satisfy a predetermined condition, so as to perform the run-through, and that outputs to the scanning power source the command value for the excitation current such that its evaluation result has satisfied the predetermined condition. Advantage of the Invention In the particle beam irradiation apparatus according to the present invention, based on the result of the run-through, the scanning electromagnet command value learning generator can suitably learn the excitation-current command value outputted to the scanning power source; thus, the effect of the hysteresis of the scanning electromagnet is eliminated, so that high-accuracy beam irradiation can be realized in the raster-scanning and the hybrid scanning. BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 is a schematic block diagram illustrating a particle beam therapy system according to Embodiment 1 of the present invention; FIG. 2 is a block diagram of an irradiation control apparatus in FIG. 1; FIG. 3 is a block diagram of another irradiation control apparatus in FIG. 1; FIG. 4 is a table representing a plurality of regions defined in a magnetic-field space; FIG. 5 represents an example of score table at a time when learning irradiation is performed; FIG. 6 is a block diagram of an irradiation control apparatus according to Embodiment 2 of the present invention; FIG. 7 is a block diagram of another irradiation control apparatus according to Embodiment 2 of the present invention; FIG. 8 is an example of mathematical model for generating a command current in Embodiment 3 of the present invention; and FIG. 9 is a block diagram of an irradiation control apparatus according to Embodiment 3 of the present invention. BEST MODE FOR CARRYING OUT THE INVENTION Embodiment 1 FIG. 1 is a schematic block diagram illustrating a particle beam therapy system according to Embodiment 1 of the present invention. The particle beam therapy system includes a beam generation apparatus 51, an accelerator 52, a beam transport apparatus 53, a particle beam irradiation apparatus 54, a treatment plan apparatus 55, and a data server 56. The treatment planning apparatus 55 can also be provided as not a component of the particle beam therapy system but an independent apparatus. The beam generation apparatus 51 generates a charged particle beam by accelerating charged particles generated in an ion source. The accelerator 52 is connected with the beam generation apparatus 51 and accelerates a generated charged particle beam. The beam transport apparatus 53 transports a charged particle beam that is accelerated by the accelerator 52 so as to gain predetermined energy and then emitted. The particle beam irradiation apparatus 54 is disposed at the downstream side of the beam transport system 53 and irradiates a charged particle beam onto an irradiation subject 15. Based on the 3-dimensional data on the diseased site 15, which is an irradiation subject, the treatment planning apparatus 55 can make plans for several therapies such as irradiation conditions so as to simulate the particle beam therapy. In the treatment planning apparatus 55, the treatment plan that has been finally selected by a doctor who carries out the particle beam therapy is converted into codes for driving the particle beam therapy system. For example, in the case of the spot-scanning method, the code for driving the particle beam therapy system means the coordinates Xj, Yj (the subscript “j” signifies a spot number) of a spot for each irradiation layer Zi (the subscript “I” signifies a layer number) and a target dose Dj to be irradiated onto the spot; in the case of the raster-scanning method, the code means time-series data and the like obtained by representing an irradiation orbit for each irradiation layer Zi by an irradiation position Xk, Yk (the subscript “k” signifies a sequence number) for each sampling period. Here, the reason why the wording “a target dose Dj to be irradiated onto the spot” has been utilized is that, due to the characteristics of the Bragg peak, the irradiation onto a lower layer affects the upper layer; the foregoing target dose does not signify the target dose to be required at the spot. The data server 56 stores treatment plan data that is created by the treatment plan apparatus 55 for each patient and codes for driving the driving the particle beam therapy system. The particle beam irradiation apparatus 54 is provided with a beam transport duct 2 for transporting an incident charged particle beam 1a injected by the beam transport apparatus 53; scanning electromagnets 3a and 3b that scan the incident charged particle beam 1a in the X direction and the Y direction, respectively, which are directions perpendicular to the incident charged particle beam 1a; magnetic-field sensors 20a and 20b that detect magnetic fields generated by the scanning electromagnets 3a and 3b; a magnetic-field data converter 21; a beam position monitor 7; a position data converter 8; a dose monitor 11; a dose data converter 12; an irradiation control apparatus 5; and a scanning power source 4. The magnetic-field sensors 20a and 20b are, for example, magnetic-field sensors having a pickup coil. As illustrated in FIG. 1, the traveling direction of the incident charged particle beam 1a is the Z direction. The scanning electromagnet 3a is an X direction scanning electromagnet that performs X-direction scanning with the incident charged particle beam 1a; the scanning electromagnet 3b is a Y direction scanning electromagnet that performs Y-direction scanning with the incident charged particle beam 1a. The magnetic-field sensor 20a is an X direction magnetic-field sensor that detects an X direction magnetic field; the magnetic-field sensor 20b is a Y direction magnetic-field sensor that detects a Y direction magnetic field. The magnetic-field data converter 21 converts an electric signal of a sensor, which indicates a magnetic field detected by the magnetic-field sensors 20a and 20b, into a digital-data measured magnetic field Bs. The beam position monitor 7 detects the passing position of an outgoing charged particle beam 1b that has been deflected by the scanning electromagnets 3a and 3b. The position data converter 8 calculates the irradiation position on an irradiation layer based on an electric signal of a sensor, which indicates the passing position detected by the beam position monitor 7, and generates digital-data measured irradiation position coordinates Ps. The dose monitor 11 detects the dose of the outgoing charged particle beam 1b. The dose data converter 12 converts an electric signal of a sensor, which indicates a dose detected by the dose monitor 11, into digital-data measured dose Ds. The irradiation control apparatus 5 outputs excitation-current command currents Ixk, Iyk, which are excitation-current command values for the scanning power source 4, so as to control the irradiation position on each irradiation layer Zi. The scanning power source 4 outputs an excitation current for actually driving the scanning electromagnets 3a and 3b, based on the command currents Ixk and Iyk outputted from the irradiation control apparatus 5. FIG. 2 is a block diagram of the irradiation control apparatus 5. The irradiation control apparatus 5 is provided with an inverse map generator 30, an inverse map calculator 22, a command value outputting device 25, a command evaluator 33, a command updater 34, a scanning electromagnet command value series generator 35, and a beam supply command outputting device 26. The scanning electromagnet command value series generator 35 has a command value storage apparatus 36. The command value outputting device 25, the command evaluator 33, the command updater 34, the scanning electromagnet command value series generator 35 configure a scanning electromagnet command value learning generator 37. The scanning electromagnet command value learning generator 37 evaluates the result of a run-through, which is a series of irradiation operations through a command current Ik (Ixk, Iyk) outputted from the scanning power source 4; when the result of the evaluation does not satisfy a predetermined condition, the command current Ik (Ixk, Iyk) is updated and the run-through is implemented; then, the command current Ik (Ixk, Iyk) such that its evaluation result has satisfied the predetermined condition is outputted to the scanning power source 4. The operation of the irradiation control apparatus 5 will be explained. Irradiations by a particle beam therapy system are roughly divided into trial irradiation for calibration and actual irradiation for treatment. In general, because being irradiation for correction, trial irradiation for calibration is performed only when no patient exists and correction is required. Each time trial irradiation is performed while varying a control input (current Ix) to the X direction scanning electromagnet 3a and a control input (current Iy) to the Y direction scanning electromagnet 3b, the irradiation position is measured. In Embodiment 1, trial irradiation for calibration is performed in the same manner as in a conventional irradiation control apparatus; however, supply and stoppage of a charged particle beam is performed in a spot-scanning manner, and when the trial irradiation is performed, not only the measured irradiation position coordinates Ps (xs, ys) of a beam are measured, but also the measured magnetic field Bs (Bxs, Bys) is measured by use of the magnetic-field sensors 20a and 20b. By performing the trial irradiation in a spot-scanning manner, the measured irradiation position coordinates Ps (xs, ys) of a beam can accurately be measured. In this situation, the relationship between the measured magnetic field Bs (Bxs, Bys) of the scanning electromagnet 3 and the measured irradiation position coordinates Ps (xs, ys) of a beam is realized as a mathematical expression model, of the inverse map calculator 22, which is generated by the inverse map generator 30. A command current Il (Ixl, Iyl) (the subscript “l” signifies a spot number in the trial irradiation) is preliminarily prepared for a trial irradiation (the step S001). The command current Il (Ixl, Iyl) for trial irradiation is prepared in such a way that a spot is irradiated within the assumed irradiation coverage of the particle beam irradiation apparatus 54. The command value outputting device 25 outputs the command current Il (Ixl, Iyl) to the scanning power source 4 (the step S002). The scanning power source 4 controls the scanning electromagnet 3 in accordance with the command current Il (Ixl, Iyl) (the step S003). In synchronization with the command value outputting device 25, the beam supply command outputting device 26 waits for a sufficient stabilization time in which the magnetic fields of the scanning electromagnets 3a and 3b stabilize and then outputs a beam supply command Sstart for instructing the beam generation apparatus 51 to generate a beam. The beam generation apparatus 51 starts irradiation of a charged particle beam. After an irradiation time Ton required for trial irradiation elapses, the beam supply command outputting device 26 outputs a beam stop command Sstop for instructing the beam generation apparatus 51 to stop a beam, and then the beam generation apparatus 51 stops irradiation of a charged particle beam. The magnetic-field sensors 20a and 20b measure the magnetic fields, of the scanning electromagnets 3a and 3b, that are controlled through the command current Il (Ixl, Iyl). A measured magnetic field Bl (Bxl, Byl) measured for each spot in trial irradiation is inputted to the inverse map generator 30 by way of the magnetic-field data converter 21. The beam position monitor 7 calculates the irradiation position coordinates Pl (Xl, Yl) of an outgoing charged particle beam 1b with which scanning has been performed by the scanning electromagnet 3 for each spot. The irradiation position coordinates Pl (Xl, Yl) is inputted to the inverse map generator 30 by way of the position data converter 8. The inverse map generator 30 stores in a memory the measured magnetic field Bl (Bxl, Byl) and the irradiation position coordinates Pl (Xl, Yl) of each spot, which is an incorporated storage device (the step S004). The inverse map generator 30 creates a mathematical expression model, based on the stored measured magnetic field Bl (Bxl, Byl) and the stored measured irradiation position coordinates Pl (Xl, Yl), and stores the created mathematical expression model in the inverse map calculator 22 (the step S005). The mathematical expression model for the inverse map calculator 22 is realized, as a preferred example, by use of a polynomial expression. There will be explained the reason why the inverse map calculator 22 is adopted instead of a conventional transformation table. Under the assumption that the specification of the scanning electromagnet 3, the specification of the scanning power source 4, and the specification of an irradiation beam (the irradiation energy, the incident beam position, and the like) are constant, if the magnetic field B (Bx, By) of the scanning electromagnet 3 is determined, the beam irradiation position coordinates P (x, y) is uniquely determined; thus, the physical phenomenon related to the relationship between the magnetic field B and the beam irradiation position coordinates P can be regarded as a positive map of two inputs and two outputs. However, in the case of actual irradiation for treatment, the target irradiation position coordinates Pobj (Pxobj, Pyobj) of a beam is preliminarily given, and it is required to control the magnetic field B (Bx, By) of the scanning electromagnet 3 so as to realize the target irradiation position coordinates Pobj (Pxobj, Pyobj) of the beam. In other words, in the case of actual irradiation for treatment, it is required to calculate the estimated value Best (▴Bx▾, ▴By▾) of the magnetic field B (Bx, By) of the scanning electromagnet 3, based on the target irradiation position coordinates Pobj (Pxobj, Pyobj) of a beam, so as to realize the target irradiation position coordinates Pobj (Pxobj, Pyobj) of the beam (with regard to the explanations for ▴Bx▾ and ▴By▾, refer to the mathematical expression (1) and the mathematical expression (2)). As described above, attention should be paid to the fact that, in actual irradiation, there is required an inverse map having a direction from the position to the magnetic field. Accordingly, in order to obtain the estimated value Best of the magnetic field B (Bx, By), the inverse map calculator 22 is required. There will be explained the outline of the method of realizing the mathematical expression model for the inverse map calculator 22 by use of a polynomial expression. Here the polynomial expression signifies a polynomial commonly defined in mathematics; it is defined, for example, as “an expression consists only of constants, and the sums and the multiplication products of indeterminate elements”. Specifically, it is exemplified by the following expression. Bx=m00+m01Pxobj+m02Pxobj2+m10Pyobj+m11PxobjPyobj+m20Pyobj2 (1) By=n00+n01Pxobj+n02Pxobj2+n10Pyobj+n11PxobjPyobj+n20Pyobj2 (2) where m00, m01, m02, m10, m11, m20, n00, n01, n02, n10, n11, n20 are unknown parameter constants; and Pxobj, Pyobj correspond to indeterminate elements in a polynomial expression. The left-hand side (Bx with a small “∩” on “B”; this is expressed by ▴Bx▾) of the equation (1) signifies an estimated value of Bx; the left-hand side (By with a small “∩” on “B”; this is expressed by ▴By▾) of the equation (2) signifies an estimated value of By. The estimated value Best of the magnetic field B (Bx, By) is expressed as (▴Bx▾, ▴By▾). The indeterminate parameter constants in a polynomial expression are obtained through the least square method or the like, based on the measured magnetic field Bl (Bxl, Byl) and the irradiation position coordinates Pl (Xl, Yl) for trial irradiation. The estimated value Best of the magnetic field B (Bx, By) for realizing the target irradiation position coordinates Pobj (Pxobj, Pyobj) is obtained from the equations (1) and (2) for which, the obtained indeterminate parameter constants are substituted. A conventional technology utilizes a method in which there is created, as a transformation table, the relationship between the control input (the command current Il (Ixl, Iyl)) to the scanning electromagnet 3 under calibration and the beam irradiation position coordinates Pl (Xl, Yl), and the transformation table is stored in the scanning electromagnet command value generator 6. The control input (the command current Ixl) to the X direction scanning electromagnet 3a and the control input (the command current Iyl) to the Y direction scanning electromagnet 3b are independently obtained from the x coordinate value (Pxobj) of the beam target irradiation position coordinates Pobj and from the y coordinate value (Pyobj) of the beam target irradiation position coordinates Pobj, respectively. However, in practice, the control input (the command current Ixl) to the X direction scanning electromagnet 3a affects both the x coordinate value and the y coordinate value of the beam target irradiation position coordinates P, and the control input (the command current Iyl) to the Y direction scanning electromagnet 3b also affects both the x coordinate value and the y coordinate value of the beam target irradiation position coordinates P, i.e., there exists an interference term; therefore, the method utilizing a transformation table, which is independently obtained, deteriorates the accuracy of an irradiation position. In the particle beam irradiation apparatus 54 according to Embodiment 1, in order to obtain the estimated value Best of the magnetic field B (Bx, By) for realizing the target irradiation position coordinates Pobj (Pxobj, Pyobj) there is realized, in the inverse map calculator 22, a mathematical expression model where the interference terms are considered; therefore, unlike the conventional technology, the accuracy of the irradiation position of the outgoing charged particle beam 1b can be raised. Next, there will be explained actual treatment irradiation in a particle beam therapy system according to Embodiment 1. Actual irradiation is divided into learning irradiation for optimizing the control of a beam irradiation position and a dose and therapy irradiation for irradiating a beam onto the irradiation subject 15 of a patient. The learning irradiation is performed in accordance with the following procedure. For a certain irradiation subject 15, the treatment plan, among the treatment plans created by the treatment planning apparatus 55, which is finally selected by the doctor is converted into codes for driving the particle beam therapy system and transmitted to the irradiation control apparatus 5 (the step S101). In this description, it is assumed that the raster-scanning method is utilized in the learning irradiation and the therapy irradiation; the explanation will be made under the assumption that the codes for driving the particle beam therapy system is time-series data in which the irradiation orbit in each irradiation layer Zi (the subscript “i” signifies the layer number) is expressed by the irradiation position Pk (Xk, Yk) (the subscript “k” signifies the sequence number) in each sampling period. A command current Ik (Ixk, Iyk) (the subscript “k” signifies a sequence number) for learning irradiation is created through a method described later (the step S102). In the learning irradiation, a run-through is performed in accordance with the command current Ik (Ixk, Iyk) for learning irradiation, under the condition that there exists no patient. In an extreme case, anything may be utilized as the candidate of the command current Ik (Ixk, Iyk) for learning irradiation or as the initial value for learning. In the present embodiment, what is obtained through the method according to a prior art is utilized as the initial value. The command current for learning irradiation is expressed as aIk (aIxk, aIyk) (in this regard, “a” signifies the number of learning instances; in the case of the initial value, a=0); it is clearly described that the command current is updated each time learning is implemented. The scanning electromagnet command value series generator makes the command value storage apparatus 36 store the command current aIk (aIxk, aIyk). The command current aIk (aIxk, aIyk) is a control input in each sampling period; the subscript “k” signifies a sequence number. A run-through is performed in accordance with the initial-value command current 0Ik (0Ixk, 0Iyk) under the condition that there exists no patient (the step S103). In response to a leaning irradiation start instruction by the operator of the particle beam therapy system, a actual irradiation start signal St, created by a signal generator 29, is transmitted to the beam supply command outputting device 26 and the scanning electromagnet command value series generator 35. The scanning electromagnet command value series generator 35 outputs the 0th-learning command current 0Ik (0Ixk, 0Iyk) in each sampling period, in accordance with the sequence number. In response to the actual irradiation start signal St, the beam supply command outputting device 26 outputs to the beam generation apparatus 51 a beam supply command Sstart for generating a beam. The beam generation apparatus 51 starts irradiation of a charged particle beam. The beam position monitor 7 detects the passing position of the outgoing charged particle beam 1b; aPk, which is the measured irradiation position coordinates Ps calculated by the position data converter 8, is inputted to the command evaluator 33. The command evaluator 33 compares the irradiation position Pk (Xk, Yk), which is the target irradiation position, with aPk (aXk, aYk), which is the measured irradiation position coordinates Ps; then, the run-through with the initial-value command current 0Ik (0Ixk, 0Iyk) is scored (the step S104). The run-through scoring method will be described later. The signal generator 29 transmits a actual irradiation end signal Se when actual irradiation is ended. The time when actual irradiation is ended means a time instant when a time corresponding to “sampling period×k (total sequence number)” has elapsed after actual irradiation is started. In response to the actual irradiation end signal Se, the beam supply command outputting device 26 outputs to the beam generation apparatus 51 the beam stop command Sstop for stopping a beam. In response to the beam stop command Sstop, the beam generation apparatus 51 stops the charged particle beam 1a (the step S105). Based on the result of scoring, which is the result of evaluation outputted from the command evaluator 33, the command updater 34 selects part of the sequence of 0th-learning command current aIk (aIxk, aIyk), as the subject of alteration, and alters the sequence (the step S106). For example, the third sequence 0I3 (0Ix3, 0Iy3) of the 0th-learning command current 0Ik (0Ixk, 0Iyk) is altered from 0Ix3 to (0Ix3+ΔI). Next, under the condition that there exists no patient, the run-through is implemented again by use of the command current, the sequence of which has partially been altered (the step S107). That is to say, the steps S103 through S105 are implemented as the second run-through. It is assumed that partial alteration of the sequence has caused the result of scoring to change from J points to (J+ΔJ) points. Then, it can be understood that the third sequence 0Ix3 of the command current may be updated by use of the information on ΔJ/ΔI. As is the case with a general learning function, in the case where, when ΔI is positive, the result of scoring is poor, there may be performed an update in which, for example, ΔI is changed to negative. This work may be implemented for every sequence that provides an effect on the result of scoring. This update causes the number of learning instances to be incremented by one (“a” is incremented to (a+1)). The command updater 34 creates the updated 1st-learning command current aIk (aIxk, aIyk) (the step S108). It is confirmed that the second run-through is superior to the first run-through in terms of the result of scoring; then, the learning is continued. The learning is repeated until a preliminarily set condition (such as a passing score) is satisfied. The command current aIk (aIxk, aIyk) at a time when the learning has finally been completed is stored in the command value storage apparatus 36. In the case where, due to the learning, the result of scoring is deteriorated compared with the last run-through, the speed of update (the amount to be updated at one time) is lowered, or the command current is updated, as explained above. The therapy irradiation is performed in accordance with the following procedure. In response to a therapy irradiation start instruction by the operator of the particle beam therapy system, the actual irradiation start signal St is transmitted to the beam supply command outputting device 26 and the scanning electromagnet command value series generator 35. The scanning electromagnet command value series generator 35 outputs the after-learning command current aIk (aIxk, aIyk) in each sampling period, in accordance with the sequence number. In response to the actual irradiation start signal St, the beam supply command outputting device 26 outputs to the beam generation apparatus 51 the beam supply command Sstart for generating a beam. The beam generation apparatus 51 starts irradiation of a charged particle beam (the step S109). The signal generator 29 transmits the actual irradiation end signal Se when the actual irradiation is to be ended. The time when actual irradiation is ended means a time instant when a time corresponding to “sampling period×k (total sequence number)” has elapsed after actual irradiation is started. In response to the actual irradiation end signal Se, the beam supply command outputting device 26 outputs to the beam generation apparatus 51 the beam stop command Sstop for stopping a beam. In response to the beam stop command Sstop, the beam generation apparatus 51 stops the charged particle beam 1a (the step S110). Next, a run-through scoring method will be explained. In the most direct scoring method (a first scoring method), there is compared the time-series data in which the code for performing raster-scanning driving, i.e., the irradiation orbit for each irradiation layer Zi is expressed by the irradiation position Pk (Xk, Yk) (the subscript “k” signifies a sequence number) in each sampling period with the irradiation position aPk (aXk, aYk) (“a” signifies the number of learning instances) in each sampling period at a time when a run-through has actually been performed, and then the following evaluation function is examined. When the value of the evaluation function becomes a predetermined value (when a predetermined condition is satisfied), the learning is ended. J = ∑ k  ( ( a  X k - X k ) 2 + ( a  Y k - Y k ) 2 ) ( 3 ) The run-through scoring can also be performed through the following method (a second scoring method) while paying attention to an irradiation dose. In the run-through scoring, the target dose Di and the measured dose Ds are compared with each other in each of small regions defined, as represented in FIG. 4, in the magnetic field space, and the scoring is implemented in accordance with the score table T in FIG. 5. As far as the run-through evaluation is concerned, for example, the evaluation function is defined as the sum of the respective scores in the small regions defined in the magnetic field space, and based on the score of the evaluation function, the evaluation is implemented. It is determined that the run-through with a higher score of the evaluation function is superior to the run-through with a lower score. FIG. 4 is a table representing a magnetic-field small region Si, j defined by the magnetic-field space (Bx, By); FIG. 5 represents an example of score table T at a time when learning irradiation is performed. In addition, the target dose Di for a small region is calculated by the treatment planning apparatus. The measured dose Ds is obtained from the result of measurement by the beam position monitor 7, the time instant when the charged particle beam 1b passes through the small region, and the like. In the second run-through scoring method, as illustrated in FIG. 3, the signal inputted to the command evaluator 33 is different. Because of this, the step S104 is different. FIG. 3 is a block diagram of an irradiation control apparatus in which the second run-through scoring method is adopted. The target dose Di and the measured dose Ds (aDk) are inputted to a command evaluator 33b of a scanning electromagnet command value learning generator 37b in an irradiation control apparatus 5b. In the step S104, the dose monitor 11 detects the dose, and the measured dose Ds obtained through conversion by the dose data converter 12 is inputted to the command evaluator 33b. The command evaluator 33b compares the target dose Di with the measured dose Ds, and then scores the run-through with the initial-value command current 0Ik (0Ixk, 0Iyk). In FIG. 4, (B0, B1) in the left column of the table briefly represents that the X component Bx of the magnetic field B satisfies the relationship B0 Bx<B1; similarly, (Bm-1, Bm) briefly represents that Bx satisfies the relationship Bm-1≦Bx<Bm. (B0, B1) in the top row of the table briefly represents that the Y component By of the magnetic field B satisfies the relationship B0≦By <B1; similarly, (Bm-1, Bm) briefly represents that By satisfies the relationship Bm-1≦By<Bm. The region S0, 0 is a region in which the relationships B0≦Bx<B1 and B0≦By<B1 are satisfied; the region Sm-1, m-1 is a region in which the relationships Bm-1≦Bx<Bm and Bm-1<By <Bm are satisfied. The scoring of the run-through is performed in the whole region of the magnetic-field space corresponding to the irradiation coverage of the particle beam irradiation apparatus 54. Accordingly, the irradiation subject 15 of a patient is administered through the target dose Di, and the site, other than the irradiation subject 15, corresponding to a normal tissue is administered in such a way that the dose therefor is “zero”; therefore, the dose of a charged particle beam in the irradiation subject 15 and non-irradiation subject can accurately be administered. Once the magnetic field of the scanning electromagnet 3 is determined, the irradiation position of a charged particle beam is uniquely determined. In other words, the magnetic field of the scanning electromagnet 3 is in a one-to-one relationship with the irradiation position of a charged particle beam. Therefore, unlike the region defined in the command current space in a prior art, the hysteresis of the scanning electromagnet does not provide any effect on the irradiation of a charged particle beam. In addition, the relationship, between the magnetic field detected by the magnetic-field sensor 20 and the beam position detected by the beam position monitor 7, which is obtained by performing calibration irradiation of a charged particle beam coincides very well with the relationship between the magnetic field and the beam position in the case of actual irradiation where irradiation of a charged particle beam is performed in the same manner as the calibration irradiation. An actual irradiation space can be obtained through the outgoing position of a charged particle beam, the passing position in the beam position monitor 7, and the positional relationship between the particle beam irradiation apparatus 54 and the irradiation subject 15; thus, a region in the actual irradiation space has a mapping relationship with a region defined in the magnetic-field space, and this mapping relationship hardly changes even in the case of actual irradiation. Accordingly, because the scoring of the run-through is performed for each of small magnetic field regions Si, j defined in the magnetic-field space, and charged particle beam dose administration is performed for each of the small magnetic field regions Si, j, the dose administration for the irradiation subject 15 in the actual irradiation space can accurately be performed. The score table T, represented in FIG. 5, at a time when learning irradiation is performed is an example of scoring by deducting points. A dose error de is a difference obtained by subtracting the target dose Di from a measured regional dose Dss. The measured regional dose Dss is an actual irradiation amount in the small magnetic field region Si, j defined in the magnetic-field space (Bx, By) and is created from the measured magnetic field Bs measured by the magnetic-field sensor 20 and the measured dose Ds measured by the dose monitor 11. Δd is the range of the dose error and is set to a predetermined value, which is within a tolerance range. The absolute value of the score changing rate in the case where the measured dose Ds exceeds the target dose Di is set to be larger than the absolute value of the score changing rate in the case where the measured dose Ds is smaller than the target dose Di. As a result, in the case where the measured dose Ds exceeds the target dose Di, correction can rapidly and accurately be implemented. In the particle beam irradiation apparatus 54, utilizing the first scoring method, according to Embodiment 1, an actual irradiation position is utilized as the evaluation function; thus, the command current aIk (aIxk, aIyk) to the scanning electromagnet 3 can suitably be learned. In the particle beam irradiation apparatus 54, utilizing the second scoring method, according to Embodiment 1, scoring is performed based on the target dose Di and the measured regional dose Dss, for each of the magnetic field small regions Si, j defined in the magnetic-field space (Bx, By), and based on the scores, the evaluation function is defined; therefore, the command current aIk (aIxk, aIyk) to the scanning electromagnet 3 can suitably be learned. Accordingly, a high-accuracy high-safety particle beam irradiation apparatus can be provided. In the particle beam irradiation apparatus 54, in the first scoring method, there is utilized, as the evaluation function, the actual irradiation position in which the effect of the hysteresis produced between the current and the magnetic field of the scanning electromagnet 3 is reflected, so the command current aIk (aIxk, aIyk) to the scanning electromagnet 3 is suitably be learned; thus, the hysteresis produced between the current and the magnetic field of the scanning electromagnet 3 can be eliminated. Through the second scoring method, the particle beam irradiation apparatus 54 performs dose administration for a charged particle beam for each of magnetic-field small regions Si, j defined in the magnetic-field space (Bx, By); thus, the hysteresis produced between the current and the magnetic field of the scanning electromagnet 3 can be eliminated. As a result, the effect of the hysteresis of the scanning electromagnet is eliminated, so that high-accuracy beam irradiation can be realized. The magnetic-field sensor 20 may be a magnetic-field sensor having a hall device. Because utilizing a hall device makes it possible to measure the absolute value of the magnetic field generated by the scanning electromagnet 3, it is not required to perform calculation, such as integration, of a voltage measured by a pickup coil. As a result, the magnetic-field data converter 21 can be simplified and downsized. A magnetic-field sensor having both a pickup coil and a hall device is most desirable, as the magnetic-field sensor 20. That is because there can be obtained both the hall device's advantage in which the absolute value of the magnetic field can be measured and the pickup coil's advantage in which the variation of the magnetic field can be measured without any effect of the hysteresis. In a conventional particle beam irradiation apparatus, a beam irradiation position has been detected only with a single beam position monitor or a plurality of beam position monitors, and a charged particle beam has been feedback-controlled based on measured irradiation position coordinates. Arranging a great number of devices, such as a position monitor and the like, that cut off a charged particle beam leads to the enlargement of beam dispersion; thus, there has been a problem that a desired beam spot diameter cannot be obtained. In the particle beam irradiation apparatus 54 according to Embodiment 1, while therapy irradiation is performed, the scanning electromagnet command value series generator 35 outputs, in each sampling period, the after-learning command current aIk (aIxk, aIyk) in accordance with the sequence number so as to perform control of the irradiation position of a charged particle beam and the irradiation dose; therefore, the particle beam irradiation system 54 may be configured in such a way that in the case of actual irradiation, the beam position monitor 7 is moved by an unillustrated moving apparatus so that the outgoing charged particle beam 1b does not pass through the beam position monitor 7. The foregoing method can prevent the outgoing charged particle beam 1b from being dispersed and enlarged by the beam position monitor 7. Accordingly, the beam spot diameter can be reduced. As a result, in the case where it is better to perform irradiation with a beam having a small diameter, treatment can be carried out with
{'application_number': '<application-reference appl-type="utility">\n<document-id>\n<country>US</country>\n<doc-number>13055479</doc-number>\n<date>20100331</date>\n</document-id>\n</application-reference>', 'publication_number': '<publication-reference>\n<document-id>\n<country>US</country>\n<doc-number>20110240875</doc-number>\n<kind>A1</kind>\n<date>20111006</date>\n</document-id>\n</publication-reference>', 'source_file': './application/2011/ipa111006.xml', 'source_data': 'USPTO-Application'}