Patent Number: 
Section: description

This application is a continuation-in-part of U.S. patent application Ser. No. 15/892,240 filed Feb. 8, 2018, which is: a continuation-in-part of U.S. patent application Ser. No. 15/838,072 filed Dec. 11, 2017, which is a continuation-in-part of U.S. patent application Ser. No. 15/823,148 filed Nov. 27, 2017, which is a continuation-in-part of U.S. patent application Ser. No. 15/467,840 filed Mar. 23, 2017, which is a continuation-in-part of U.S. patent application Ser. No. 15/402,739 filed Jan. 10, 2017, which is a continuation-in-part of U.S. patent application Ser. No. 15/348,625 filed Nov. 10, 2016, which is a continuation-in-part of U.S. patent application Ser. No. 15/167,617 filed May 27, 2016; and a continuation-in-part of U.S. patent application Ser. No. 15/868,897 filed Jan. 11, 2018, which is a continuation of U.S. patent application Ser. No. 15/152,479 filed May 11, 2016, which is a continuation-in-part of U.S. patent application Ser. No. 14/216,788 filed Mar. 17, 2014, which is a continuation-in-part of U.S. patent application Ser. No. 13/087,096 filed Apr. 14, 2011, which claims benefit of U.S. provisional patent application No. 61/324,776 filed Apr. 16, 2010, all of which are incorporated herein in their entirety by this reference thereto.  The invention relates generally to a cancer therapy scanning and/or treatment apparatus and method of use thereof. Cancer Treatment Proton therapy works by aiming energetic ionizing particles, such as protons accelerated with a particle accelerator, onto a target tumor. These particles damage the DNA of cells, ultimately causing their death. Cancerous cells, because of their high rate of division and their reduced ability to repair damaged DNA, are particularly vulnerable to attack on their DNA. Patents related to the current invention are summarized here. Proton Beam Therapy System F. Cole, et. al. of Loma Linda University Medical Center “Multi-Station Proton Beam Therapy System”, U.S. Pat. No. 4,870,287 (Sep. 26, 1989) describe a proton beam therapy system for selectively generating and transporting proton beams from a single proton source and accelerator to a selected treatment room of a plurality of patient treatment rooms. Problem There exists in the art of charged particle cancer therapy a need for safe, accurate, precise, and rapid imaging of a patient and/or treatment of a tumor using charged particles. The invention relates generally to a multi-use magnet in a charged particle cancer therapy system. Elements and steps in the figures are illustrated for simplicity and clarity and have not necessarily been rendered according to any particular sequence. For example, steps that are performed concurrently or in different order are illustrated in the figures to help improve understanding of embodiments of the present invention. The invention comprises a method and apparatus for using a turning magnet of an accelerator of a cancer therapy system, the accelerator comprising first magnet coils and second correction coils wound about a magnet core where: (1) at a first time, the second correction coils are used to correct a magnetic field, resultant from the first magnet coils, used to turn cations and (2) at a second time, after reversing polarity of the correction coils, the correction coils are used to turn anions and/or electrons, the cations and electrons used to treat a tumor of a patient positioned in a treatment position relative to a treatment beam from the accelerator during the first and second time periods. The above described embodiment is optionally used in combination with a proton therapy cancer treatment system and/or a proton tomography imaging system. The above described embodiment is optionally used in combination with a set of fiducial marker detectors configured to detect photons emitted from and/or reflected off of a set of fiducial markers positioned on one or more objects in a treatment room and resultant determined distances and/or calculated angles are used to determine relative positions of multiple objects or elements in the treatment room. Generally, in an iterative process, at a first time objects, such as a treatment beamline output nozzle, a specific portion of a patient relative to a tumor, a scintillation detection material, an X-ray system element, and/or a detection element, are mapped and relative positions and/or angles therebetween are determined. At a second time, the position of the mapped objects is used in: (1) imaging, such as X-ray, positron emission tomography, and/or proton beam imaging and/or (2) beam targeting and treatment, such as positively charged particle based cancer treatment. As relative positions of objects in the treatment room are dynamically determined using the fiducial marking system, engineering and/or mathematical constraints of a treatment beamline isocenter is removed. In combination, a method and apparatus is described for determining a position of a tumor in a patient for treatment of the tumor using positively charged particles in a treatment room. More particularly, the method and apparatus use a set of fiducial markers and fiducial detectors to mark/determine relative position of static and/or moveable objects in a treatment room using photons passing from the markers to the detectors. Further, position and orientation of at least one of the objects is calibrated to a reference line, such as a zero-offset beam treatment line passing through an exit nozzle, which yields a relative position of each fiducially marked object in the treatment room. Treatment calculations are subsequently determined using the reference line and/or points thereon. The inventor notes that the treatment calculations are optionally and preferably performed without use of an isocenter point, such as a central point about which a treatment room gantry rotates, which eliminates mechanical errors associated with the isocenter point being an isocenter volume in practice. In combination, a method and apparatus for imaging a tumor of a patient using positively charged particles and X-rays, comprises the steps of: (1) transporting the positively charged particles from an accelerator to a patient position using a beam transport line, where the beam transport line comprises a positively charged particle beam path and an X-ray beam path; (2) detecting scintillation induced by the positively charged particles using a scintillation detector system; (3) detecting X-rays using an X-ray detector system; (4) positioning a mounting rail through linear extension/retraction to: at a first time and at a first extension position of the mounting rail, position the scintillation detector system opposite the patient position from the exit nozzle and at a second time and at a second extension position of the mounting rail, position the X-ray detector system opposite the patient position from the exit nozzle; (5) generating an image of the tumor using output of the scintillation detector system and the X-ray detector system; and (6) alternating between the step of detecting scintillation and treating the tumor via irradiation of the tumor using the positively charged particles. In combination, a tomography system is optionally used in combination with a charged particle cancer therapy system. The tomography system uses tomography or tomographic imaging, which refers to imaging by sections or sectioning through the use of a penetrating wave, such as a positively charge particle from an injector and/or accelerator. Optionally and preferably, a common injector, accelerator, and beam transport system is used for both charged particle based tomographic imaging and charged particle cancer therapy. In one case, an output nozzle of the beam transport system is positioned with a gantry system while the gantry system and/or a patient support maintains a scintillation plate of the tomography system on the opposite side of the patient from the output nozzle. In another example, a charged particle state determination system, of a cancer therapy system or tomographic imaging system, uses one or more coated layers in conjunction with a scintillation material, scintillation detector and/or a tomographic imaging system at time of tumor and surrounding tissue sample mapping and/or at time of tumor treatment, such as to determine an input vector of the charged particle beam into a patient and/or an output vector of the charged particle beam from the patient. In another example, the charged particle tomography apparatus is used in combination with a charged particle cancer therapy system. For example, tomographic imaging of a cancerous tumor is performed using charged particles generated with an injector, accelerated with an accelerator, and guided with a delivery system. The cancer therapy system uses the same injector, accelerator, and guided delivery system in delivering charged particles to the cancerous tumor. For example, the tomography apparatus and cancer therapy system use a common raster beam method and apparatus for treatment of solid cancers. More particularly, the invention comprises a multi-axis and/or multi-field raster beam charged particle accelerator used in: (1) tomography and (2) cancer therapy. Optionally, the system independently controls patient translation position, patient rotation position, two-dimensional beam trajectory, delivered radiation beam energy, delivered radiation beam intensity, beam velocity, timing of charged particle delivery, and/or distribution of radiation striking healthy tissue. The system operates in conjunction with a negative ion beam source, synchrotron, patient positioning, imaging, and/or targeting method and apparatus to deliver an effective and uniform dose of radiation to a tumor while distributing radiation striking healthy tissue. For clarity of presentation and without loss of generality, throughout this document, treatment systems and imaging systems are described relative to a tumor of a patient. However, more generally any sample is imaged with any of the imaging systems described herein and/or any element of the sample is treated with the positively charged particle beam(s) described herein. Charged Particle Beam Therapy Throughout this document, a charged particle beam therapy system, such as a proton beam, hydrogen ion beam, or carbon ion beam, is described. Herein, the charged particle beam therapy system is described using a proton beam. However, the aspects taught and described in terms of a proton beam are not intended to be limiting to that of a proton beam and are illustrative of a charged particle beam system, a positively charged beam system, and/or a multiply charged particle beam system, such as C4+ or C6+. Any of the techniques described herein are equally applicable to any charged particle beam system. Referring now to FIG. 1A, a charged particle beam system 100 is illustrated. The charged particle beam preferably comprises a number of subsystems including any of: a main controller 110; an injection system 120; a synchrotron 130 that typically includes: (1) an accelerator system 131 and (2) an internal or connected extraction system 134; a radio-frequency cavity system 180; a beam transport system 135; a scanning/targeting/delivery system 140; a nozzle system 146; a patient interface module 150; a display system 160; and/or an imaging system 170. An exemplary method of use of the charged particle beam system 100 is provided. The main controller 110 controls one or more of the subsystems to accurately and precisely deliver protons to a tumor of a patient. For example, the main controller 110 obtains an image, such as a portion of a body and/or of a tumor, from the imaging system 170. The main controller 110 also obtains position and/or timing information from the patient interface module 150. The main controller 110 optionally controls the injection system 120 to inject a proton into a synchrotron 130. The synchrotron typically contains at least an accelerator system 131 and an extraction system 134. The main controller 110 preferably controls the proton beam within the accelerator system, such as by controlling speed, trajectory, and timing of the proton beam. The main controller then controls extraction of a proton beam from the accelerator through the extraction system 134. For example, the controller controls timing, energy, and/or intensity of the extracted beam. The controller 110 also preferably controls targeting of the proton beam through the scanning/targeting/delivery system 140 to the patient interface module 150 or a patient with a patient positioning system. One or more components of the patient interface module 150, such as translational and rotational position of the patient, are preferably controlled by the main controller 110. Further, display elements of the display system 160 are preferably controlled via the main controller 110. Displays, such as display screens, are typically provided to one or more operators and/or to one or more patients. In one embodiment, the main controller 110 times the delivery of the proton beam from all systems, such that protons are delivered in an optimal therapeutic manner to the tumor of the patient. Herein, the main controller 110 refers to a single system controlling the charged particle beam system 100, to a single controller controlling a plurality of subsystems controlling the charged particle beam system 100, or to a plurality of individual controllers controlling one or more sub-systems of the charged particle beam system 100. Referring now to FIG. 42A and FIG. 42B, a multi-layer single-color scintillation detector element 4200, a species of the multi-layer scintillator 4030, is described where each scintillation layer uses the same scintillation material and/or emits the photons in a same wavelength range. As illustrated, the first scintillation layer 4111 is a first red photon emission layer 4210, the second scintillation layer 4114 is a second red photon emission layer 4220, and the third scintillation layer 4116 is a third red photon emission layer 4230. Again, for clarity of presentation, red photons are illustrative of any wavelength range common to all three of the first, second, and third photon emission layers 4210, 4220, 4230. Referring now to FIG. 42B, for a first energy beam, E1, a first intensity/magnitude response shape, R1, or first response curve 4241, such as a relative number of secondary photons, emitted from each of the first, second, and third red photon emission layers 4210, 4220, 4230, is illustrated. Generally, as the residual energy particle beam 267 traverses through the scintillation layers, the residual energy particle beam loses energy and slows down. Slower particles lose more energy per unit distance traversed than the faster particles resulting in still more lost energy and slowing of the particles, which results in a Bragg peak. The number of secondary photons produced is proportional to the amount of energy released by the charged particles into the scintillation material. Thus, as the charged particles progress into the multi-layer scintillator, more photons are generated per millimeter of travel and the shape of the response curve as a function of depth can be related to initial energy of the residual energy particle beam 267 via calibration. Again, energy of the residual energy particle beam 267 is used to generate an image, such as proton computed radiography (pRT) image and/or a proton computed tomography (pCT) image in conjunction with beam scanning, relative movement of the patient 230 relative to the scanning beam, and/or relative rotation of the patient 230 relative to the scanning beam. Referring now to FIG. 1B, an illustrative exemplary embodiment of one version of the charged particle beam system 100 is provided. The number, position, and described type of components is illustrative and non-limiting in nature. In the illustrated embodiment, the injection system 120 or ion source or charged particle beam source generates protons. The injection system 120 optionally includes one or more of: a negative ion beam source, a positive ion beam source, an ion beam focusing lens, and a tandem accelerator. The protons are delivered into a vacuum tube that runs into, through, and out of the synchrotron. The generated protons are delivered along an initial path 262. Optionally, focusing magnets 127, such as quadrupole magnets or injection quadrupole magnets, are used to focus the proton beam path. A quadrupole magnet is a focusing magnet. An injector bending magnet 128 bends the proton beam toward a plane of the synchrotron 130. The focused protons having an initial energy are introduced into an injector magnet 129, which is preferably an injection Lambertson magnet. Typically, the initial beam path 262 is along an axis off of, such as above, a circulating plane of the synchrotron 130. The injector bending magnet 128 and injector magnet 129 combine to move the protons into the synchrotron 130. Main bending magnets, dipole magnets, turning magnets, or circulating magnets 132 are used to turn the protons along a circulating beam path 164. A dipole magnet is a bending magnet. The main bending magnets 132 bend the initial beam path 262 into a circulating beam path 164. In this example, the main bending magnets 132 or circulating magnets are represented as four sets of four magnets to maintain the circulating beam path 164 into a stable circulating beam path. However, any number of magnets or sets of magnets are optionally used to move the protons around a single orbit in the circulation process. The protons pass through an accelerator 133. The accelerator accelerates the protons in the circulating beam path 164. As the protons are accelerated, the fields applied by the magnets are increased. Particularly, the speed of the protons achieved by the accelerator 133 are synchronized with magnetic fields of the main bending magnets 132 or circulating magnets to maintain stable circulation of the protons about a central point or region 136 of the synchrotron. At separate points in time the accelerator 133/main bending magnet 132 combination is used to accelerate and/or decelerate the circulating protons while maintaining the protons in the circulating path or orbit. An extraction element of an inflector/deflector system is used in combination with a Lambertson extraction magnet 137 to remove protons from their circulating beam path 164 within the synchrotron 130. One example of a deflector component is a Lambertson magnet. Typically the deflector moves the protons from the circulating plane to an axis off of the circulating plane, such as above the circulating plane. Extracted protons are preferably directed and/or focused using an extraction bending magnet 142 and optional extraction focusing magnets 141, such as quadrupole magnets, and optional bending magnets along a positively charged particle beam transport path 268 in a beam transport system 135, such as a beam path or proton beam path, into the scanning/targeting/delivery system 140. Two components of a scanning system 140 or targeting system typically include a first axis controller 143, such as a vertical control, and a second axis controller 144, such as a horizontal control. In one embodiment, the first axis controller 143 allows for about 100 mm of vertical or y-axis scanning of the proton beam 268 and the second axis controller 144 allows for about 700 mm of horizontal or x-axis scanning of the proton beam 268. A nozzle system 146 is used for directing the proton beam, for imaging the proton beam, for defining shape of the proton beam, and/or as a vacuum barrier between the low pressure beam path of the synchrotron and the atmosphere. Protons are delivered with control to the patient interface module 150 and to a tumor of a patient. All of the above listed elements are optional and may be used in various permutations and combinations. Ion Extraction from Ion Source For clarity of presentation and without loss of generality, examples focus on protons from the ion source. However, more generally cations of any charge are optionally extracted from a corresponding ion source with the techniques described herein. For instance, C4+ or C6+ are optionally extracted using the ion extraction methods and apparatus described herein. Further, by reversing polarity of the system, anions are optionally extracted from an anion source, where the anion is of any charge. Herein, for clarity of presentation and without loss of generality, ion extraction is coupled with tumor treatment and/or tumor imaging. However, the ion extraction is optional used in any method or apparatus using a stream or time discrete bunches of ions. Ion Extraction from Accelerator Referring now to FIG. 1C, both: (1) an exemplary proton beam extraction system 215 from the synchrotron 130 and (2) a charged particle beam intensity control system 225 are illustrated. For clarity, FIG. 1C removes elements represented in FIG. 1B, such as the turning magnets, which allows for greater clarity of presentation of the proton beam path as a function of time. Generally, protons are extracted from the synchrotron 130 by slowing the protons. As described, supra, the protons were initially accelerated in a circulating path, which is maintained with a plurality of main bending magnets 132. The circulating path is referred to herein as an original central beamline 264. The protons repeatedly cycle around a central point in the synchrotron 136. The proton path traverses through a radio frequency (RF) cavity system 310. To initiate extraction, an RF field is applied across a first blade 312 and a second blade 314, in the RF cavity system 310. The first blade 312 and second blade 314 are referred to herein as a first pair of blades. In the proton extraction process, an RF voltage is applied across the first pair of blades, where the first blade 312 of the first pair of blades is on one side of the circulating proton beam path 264 and the second blade 314 of the first pair of blades is on an opposite side of the circulating proton beam path 264. The applied RF field applies energy to the circulating charged-particle beam. The applied RF field alters the orbiting or circulating beam path slightly of the protons from the original central beamline 264 to an altered circulating beam path 265. Upon a second pass of the protons through the RF cavity system, the RF field further moves the protons off of the original proton beamline 264. For example, if the original beamline is considered as a circular path, then the altered beamline is slightly elliptical. The frequency of the applied RF field is timed to apply outward or inward movement to a given band of protons circulating in the synchrotron accelerator. Orbits of the protons are slightly more off axis compared to the original circulating beam path 264. Successive passes of the protons through the RF cavity system are forced further and further from the original central beamline 264 by altering the direction and/or intensity of the RF field with each successive pass of the proton beam through the RF field. Timing of application of the RF field and/or frequency of the RF field is related to the circulating charged particles circulation pathlength in the synchrotron 130 and the velocity of the charged particles so that the applied RF field has a period, with a peak-to-peak time period, equal to a period of time of beam circulation in the synchrotron 130 about the center 136 or an integer multiple of the time period of beam circulation about the center 136 of the synchrotron 130. Alternatively, the time period of beam circulation about the center 136 of the synchrotron 130 is an integer multiple of the RF period time. The RF period is optionally used to calculated the velocity of the charged particles, which relates directly to the energy of the circulating charged particles. The RF voltage is frequency modulated at a frequency about equal to the period of one proton cycling around the synchrotron for one revolution or at a frequency than is an integral multiplier of the period of one proton cycling about the synchrotron. The applied RF frequency modulated voltage excites a betatron oscillation. For example, the oscillation is a sine wave motion of the protons. The process of timing the RF field to a given proton beam within the RF cavity system is repeated thousands of times with each successive pass of the protons being moved approximately one micrometer further off of the original central beamline 264. For clarity, the approximately 1000 changing beam paths with each successive path of a given band of protons through the RF field are illustrated as the altered beam path 265. The RF time period is process is known, thus energy of the charged particles at time of hitting the extraction material 330, described infra, is known. With a sufficient sine wave betatron amplitude, the altered circulating beam path 265 touches and/or traverses a extraction material 330, such as a foil or a sheet of foil. The foil is preferably a lightweight material, such as beryllium, a lithium hydride, a carbon sheet, or a material having low nuclear charge components. Herein, a material of low nuclear charge is a material composed of atoms consisting essentially of atoms having six or fewer protons. The foil is preferably about 10 to 150 microns thick, is more preferably about 30 to 100 microns thick, and is still more preferably about 40 to 60 microns thick. In one example, the foil is beryllium with a thickness of about 50 microns. When the protons traverse through the foil, energy of the protons is lost and the speed of the protons is reduced. Typically, a current is also generated, described infra. Protons moving at the slower speed travel in the synchrotron with a reduced radius of curvature 266 compared to either the original central beamline 264 or the altered circulating path 265. The reduced radius of curvature 266 path is also referred to herein as a path having a smaller diameter of trajectory or a path having protons with reduced energy. The reduced radius of curvature 266 is typically about two millimeters less than a radius of curvature of the last pass of the protons along the altered proton beam path 265. The thickness of the extraction material 330 is optionally adjusted to create a change in the radius of curvature, such as about ½, 1, 2, 3, or 4 mm less than the last pass of the protons 265 or original radius of curvature 264. The reduction in velocity of the charged particles transmitting through the extraction material 330 is calculable, such as by using the pathlength of the betatron oscillating charged particle beam through the extraction material 330 and/or using the density of the extraction material 330. Protons moving with the smaller radius of curvature travel between a second pair of blades. In one case, the second pair of blades is physically distinct and/or is separated from the first pair of blades. In a second case, one of the first pair of blades is also a member of the second pair of blades. For example, the second pair of blades is the second blade 314 and a third blade 316 in the RF cavity system 310. A high voltage DC signal, such as about 1 to 5 kV, is then applied across the second pair of blades, which directs the protons out of the synchrotron through an extraction magnet 137, such as a Lambertson extraction magnet, into a transport path 268. Control of acceleration of the charged particle beam path in the synchrotron with the accelerator and/or applied fields of the turning magnets in combination with the above described extraction system allows for control of the intensity of the extracted proton beam, where intensity is a proton flux per unit time or the number of protons extracted as a function of time. For example, when a current is measured beyond a threshold, the RF field modulation in the RF cavity system is terminated or reinitiated to establish a subsequent cycle of proton beam extraction. This process is repeated to yield many cycles of proton beam extraction from the synchrotron accelerator. In another embodiment, instead of moving the charged particles to the extraction material 330, the extraction material 330 is mechanically moved to the circulating charged particles. Particularly, the extraction material 330 is mechanically or electromechanically translated into the path of the circulating charged particles to induce the extraction process, described supra. In this case, the velocity or energy of the circulating charged particle beam is calculable using the pathlength of the beam path about the center 136 of the synchrotron 130 and from the force applied by the bending magnets 132. In either case, because the extraction system does not depend on any change in magnetic field properties, it allows the synchrotron to continue to operate in acceleration or deceleration mode during the extraction process. Stated differently, the extraction process does not interfere with synchrotron acceleration. In stark contrast, traditional extraction systems introduce a new magnetic field, such as via a hexapole, during the extraction process. More particularly, traditional synchrotrons have a magnet, such as a hexapole magnet, that is off during an acceleration stage. During the extraction phase, the hexapole magnetic field is introduced to the circulating path of the synchrotron. The introduction of the magnetic field necessitates two distinct modes, an acceleration mode and an extraction mode, which are mutually exclusive in time. The herein described system allows for acceleration and/or deceleration of the proton during the extraction step and tumor treatment without the use of a newly introduced magnetic field, such as by a hexapole magnet. Charged Particle Beam Intensity Control Control of applied field, such as a radio-frequency (RF) field, frequency and magnitude in the RF cavity system 310 allows for intensity control of the extracted proton beam, where intensity is extracted proton flux per unit time or the number of protons extracted as a function of time. Still referring FIG. 3, the intensity control system 225 is further described. In this example, an intensity control feedback loop is added to the extraction system, described supra. When protons in the proton beam hit the extraction material 330 electrons are given off from the extraction material 330 resulting in a current. The resulting current is converted to a voltage and is used as part of an ion beam intensity monitoring system or as part of an ion beam feedback loop for controlling beam intensity. The voltage is optionally measured and sent to the main controller 110 or to an intensity controller subsystem 340, which is preferably in communication or under the direction of the main controller 110. More particularly, when protons in the charged particle beam path pass through the extraction material 330, some of the protons lose a small fraction of their energy, such as about one-tenth of a percent, which results in a secondary electron. That is, protons in the charged particle beam push some electrons when passing through extraction material 330 giving the electrons enough energy to cause secondary emission. The resulting electron flow results in a current or signal that is proportional to the number of protons going through the target or extraction material 330. The resulting current is preferably converted to voltage and amplified. The resulting signal is referred to as a measured intensity signal. The amplified signal or measured intensity signal resulting from the protons passing through the extraction material 330 is optionally used in monitoring the intensity of the extracted protons and is preferably used in controlling the intensity of the extracted protons. For example, the measured intensity signal is compared to a goal signal, which is predetermined in an irradiation of the tumor plan. The difference between the measured intensity signal and the planned for goal signal is calculated. The difference is used as a control to the RF generator. Hence, the measured flow of current resulting from the protons passing through the extraction material 330 is used as a control in the RF generator to increase or decrease the number of protons undergoing betatron oscillation and striking the extraction material 330. Hence, the voltage determined off of the extraction material 330 is used as a measure of the orbital path and is used as a feedback control to control the RF cavity system. In one example, the intensity controller subsystem 340 preferably additionally receives input from: (1) a detector 350, which provides a reading of the actual intensity of the proton beam and/or (2) an irradiation plan 360. The irradiation plan provides the desired intensity of the proton beam for each x, y, energy, and/or rotational position of the patient/tumor as a function of time. Thus, the intensity controller 340 receives the desired intensity from the irradiation plan 350, the actual intensity from the detector 350 and/or a measure of intensity from the extraction material 330, and adjusts the amplitude and/or the duration of application of the applied radio-frequency field in the RF cavity system 310 to yield an intensity of the proton beam that matches the desired intensity from the irradiation plan 360. As described, supra, the protons striking the extraction material 330 is a step in the extraction of the protons from the synchrotron 130. Hence, the measured intensity signal is used to change the number of protons per unit time being extracted, which is referred to as intensity of the proton beam. The intensity of the proton beam is thus under algorithm control. Further, the intensity of the proton beam is controlled separately from the velocity of the protons in the synchrotron 130. Hence, intensity of the protons extracted and the energy of the protons extracted are independently variable. Still further, the intensity of the extracted protons is controllably variable while scanning the charged particles beam in the tumor from one voxel to an adjacent voxel as a separate hexapole and separated time period from acceleration and/or treatment is not required, as described supra. For example, protons initially move at an equilibrium trajectory in the synchrotron 130. An RF field is used to excite or move the protons into a betatron oscillation. In one case, the frequency of the protons orbit is about 10 MHz. In one example, in about one millisecond or after about 10,000 orbits, the first protons hit an outer edge of the target material 130. The specific frequency is dependent upon the period of the orbit. Upon hitting the material 130, the protons push electrons through the foil to produce a current. The current is converted to voltage and amplified to yield a measured intensity signal. The measured intensity signal is used as a feedback input to control the applied RF magnitude or RF field. An energy beam sensor, described infra, is optionally used as a feedback control to the RF field frequency or RF field of the RF field extraction system 310 to dynamically control, modify, and/or alter the delivered charge particle beam energy, such as in a continuous pencil beam scanning system operating to treat tumor voxels without alternating between an extraction phase and a treatment phase. Preferably, the measured intensity signal is compared to a target signal and a measure of the difference between the measured intensity signal and target signal is used to adjust the applied RF field in the RF cavity system 310 in the extraction system to control the intensity of the protons in the extraction step. Stated again, the signal resulting from the protons striking and/or passing through the material 130 is used as an input in RF field modulation. An increase in the magnitude of the RF modulation results in protons hitting the foil or material 130 sooner. By increasing the RF, more protons are pushed into the foil, which results in an increased intensity, or more protons per unit time, of protons extracted from the synchrotron 130. In another example, a detector 350 external to the synchrotron 130 is used to determine the flux of protons extracted from the synchrotron and a signal from the external detector is used to alter the RF field, RF intensity, RF amplitude, and/or RF modulation in the RF cavity system 310. Here the external detector generates an external signal, which is used in a manner similar to the measured intensity signal, described in the preceding paragraphs. Preferably, an algorithm or irradiation plan 360 is used as an input to the intensity controller 340, which controls the RF field modulation by directing the RF signal in the betatron oscillation generation in the RF cavity system 310. The irradiation plan 360 preferably includes the desired intensity of the charged particle beam as a function of time and/or energy of the charged particle beam as a function of time, for each patient rotation position, and/or for each x-, y-position of the charged particle beam. In yet another example, when a current from extraction material 330 resulting from protons passing through or hitting material is measured beyond a threshold, the RF field modulation in the RF cavity system is terminated or reinitiated to establish a subsequent cycle of proton beam extraction. This process is repeated to yield many cycles of proton beam extraction from the synchrotron accelerator. In still yet another embodiment, intensity modulation of the extracted proton beam is controlled by the main controller 110. The main controller 110 optionally and/or additionally controls timing of extraction of the charged particle beam and energy of the extracted proton beam. The benefits of the system include a multi-dimensional scanning system. Particularly, the system allows independence in: (1) energy of the protons extracted and (2) intensity of the protons extracted. That is, energy of the protons extracted is controlled by an energy control system and an intensity control system controls the intensity of the extracted protons. The energy control system and intensity control system are optionally independently controlled. Preferably, the main controller 110 controls the energy control system and the main controller 110 simultaneously controls the intensity control system to yield an extracted proton beam with controlled energy and controlled intensity where the controlled energy and controlled intensity are independently variable and/or continually available as a separate extraction phase and acceleration phase are not required, as described supra. Thus the irradiation spot hitting the tumor is under independent control of:                time;        energy;        intensity;        x-axis position, where the x-axis represents horizontal movement of the proton beam relative to the patient, and        y-axis position, where the y-axis represents vertical movement of the proton beam relative to the patient.         In addition, the patient is optionally independently translated and/or rotated relative to a translational axis of the proton beam at the same time. Beam Transport The beam transport system 135 is used to move the charged particles from the accelerator to the patient, such as via a nozzle in a gantry, described infra. Nozzle After extraction from the synchrotron 130 and transport of the charged particle beam along the proton beam path 268 in the beam transport system 135, the charged particle beam exits through the nozzle system 146. In one example, the nozzle system includes a nozzle foil covering an end of the nozzle system 146 or a cross-sectional area within the nozzle system forming a vacuum seal. The nozzle system includes a nozzle that expands in x/y-cross-sectional area along the z-axis of the proton beam path 268 to allow the proton beam 268 to be scanned along the x-axis and y-axis by the vertical control element and horizontal control element, respectively. The nozzle foil is preferably mechanically supported by the outer edges of an exit port of the nozzle or nozzle system 146. An example of a nozzle foil is a sheet of about 0.1 inch thick aluminum foil. Generally, the nozzle foil separates atmosphere pressures on the patient side of the nozzle foil from the low pressure region, such as about 10−5 to 10−7 torr region, on the synchrotron 130 side of the nozzle foil. The low pressure region is maintained to reduce scattering of the circulating charged particle beam in the synchrotron. Herein, the exit foil of the nozzle is optionally the first tracking plane 760. tracking sheet, or sheet of the charged particle beam state determination system 250, described infra. Tomography/Beam State In one embodiment, the charged particle tomography apparatus is used to image a tumor in a patient. As current beam position determination/verification is used in both tomography and cancer therapy treatment, for clarity of presentation and without limitation beam state determination is also addressed in this section. However, beam state determination is optionally used separately and without tomography. In another example, the charged particle tomography apparatus is used in combination with a charged particle cancer therapy system using common elements. For example, tomographic imaging of a cancerous tumor is performed using charged particles generated with an injector, accelerator, and guided with a delivery system that are part of the cancer therapy system, described supra. In various examples, the tomography imaging system is optionally simultaneously operational with a charged particle cancer therapy system using common elements, allows tomographic imaging with rotation of the patient, is operational on a patient in an upright, semi-upright, and/or horizontal position, is simultaneously operational with X-ray imaging, and/or allows use of adaptive charged particle cancer therapy. Further, the common tomography and cancer therapy apparatus elements are optionally operational in a multi-axis and/or multi-field raster beam mode. In conventional medical X-ray tomography, a sectional image through a body is made by moving one or both of an X-ray source and the X-ray film in relative to the patient during the exposure. By modifying the direction and extent of the movement, operators can select different focal planes, which contain the structures of interest. More modern variations of tomography involve gathering projection data from multiple directions by moving the X-ray source and feeding the data into a tomographic reconstruction software algorithm processed by a computer. Herein, in stark contrast to known methods, the radiation source is a charged particle, such as a proton ion beam or a carbon ion beam. A proton beam is used herein to describe the tomography system, but the description applies to a heavier ion beam, such as a carbon ion beam. Further, in stark contrast to known techniques, herein the radiation source is optionally stationary while the patient is rotated. Referring now to FIG. 2, an example of a tomography apparatus is described and an example of a beam state determination is described. In this example, the tomography system 200 uses elements in common with the charged particle beam system 100, including elements of one or more of the injection system 120, the accelerator 130, a positively charged particle beam transport path 268 within a beam transport housing 261 in the beam transport system 135, the targeting/delivery system 140, the patient interface module 150, the display system 160, and/or the imaging system 170, such as the X-ray imaging system. The scintillation material is optionally one or more scintillation plates, such as a scintillating plastic, used to measure energy, intensity, and/or position of the charged particle beam. For instance, a scintillation material of scintillation detector element 205 of a scintillation detector system 210 or scintillation plate is positioned behind the patient 230 relative to the targeting/delivery system 140 elements, which is optionally used to measure intensity and/or position of the charged particle beam after transmitting through the patient. Optionally, a second scintillation plate or a charged particle induced photon emitting sheet, described infra, is positioned prior to the patient 230 relative to the targeting/delivery system 140 elements, which is optionally used to measure incident intensity and/or position of the charged particle beam prior to transmitting through the patient. The charged particle beam system 100 as described has proven operation at up to and including 330 MeV, which is sufficient to send protons through the body and into contact with the scintillation material. Particularly, 250 MeV to 330 MeV are used to pass the beam through a standard sized patient with a standard sized pathlength, such as through the chest. The intensity or count of protons hitting the plate as a function of position is used to create an image. The velocity or energy of the proton hitting the scintillation plate is also used in creation of an image of the tumor 220 and/or an image of the patient 230. The patient 230 is rotated about the y-axis and a new image is collected. Preferably, a new image is collected with about every one degree of rotation of the patient resulting in about 360 images that are combined into a tomogram using tomographic reconstruction software. The tomographic reconstruction software uses overlapping rotationally varied images in the reconstruction. Optionally, a new image is collected at about every 2, 3, 4, 5, 10, 15, 30, or 45 degrees of rotation of the patient. Herein, the scintillation material or scintillator, of the scintillation detection system, is any material that emits a photon when struck by a positively charged particle or when a positively charged particle transfers energy to the scintillation material sufficient to cause emission of light. Optionally, the scintillation material emits the photon after a delay, such as in fluorescence or phosphorescence. However, preferably, the scintillator has a fast fifty percent quench time, such as less than 0.0001, 0.001, 0.01, 0.1, 1, 10, 100, or 1,000 milliseconds, so that the light emission goes dark, falls off, or terminates quickly. Preferred scintillation materials include sodium iodide, potassium iodide, cesium iodide, an iodide salt, and/or a doped iodide salt. Additional examples of the scintillation materials include, but are not limited to: an organic crystal, a plastic, a glass, an organic liquid, a luminophor, and/or an inorganic material or inorganic crystal, such as barium fluoride, BaF2; calcium fluoride, CaF2, doped calcium fluoride, sodium iodide, NaI; doped sodium iodide, sodium iodide doped with thallium, NaI(Tl); cadmium tungstate, CdWO4; bismuth germanate; cadmium tungstate, CdWO4; calcium tungstate, CaWO4; cesium iodide, CsI; doped cesium iodide; cesium iodide doped with thallium, CsI(Tl); cesium iodide doped with sodium CsI(Na); potassium iodide, KI; doped potassium iodide, gadolinium oxysulfide, Gd2O2S; lanthanum bromide doped with cerium, LaBr3(Ce); lanthanum chloride, LaCl3; cesium doped lanthanum chloride, LaCl3(Ce); lead tungstate, PbWO4; LSO or lutetium oxyorthosilicate (Lu2SiO5); LYSO, Lu1.8Y0.2SiO5(Ce); yttrium aluminum garnet, YAG(Ce); zinc sulfide, ZnS(Ag); and zinc tungstate, ZnWO4. In one embodiment, a tomogram or an individual tomogram section image is collected at about the same time as cancer therapy occurs using the charged particle beam system 100. For example, a tomogram is collected and cancer therapy is subsequently performed: without the patient moving from the positioning systems, such as in a semi-vertical partial immobilization system, a sitting partial immobilization system, or the a laying position. In a second example, an individual tomogram slice is collected using a first cycle of the accelerator 130 and using a following cycle of the accelerator 130, the tumor 220 is irradiated, such as within about 1, 2, 5, 10, 15 or 30 seconds. In a third case, about 2, 3, 4, or 5 tomogram slices are collected using 1, 2, 3, 4, or more rotation positions of the patient 230 within about 5, 10, 15, 30, or 60 seconds of subsequent tumor irradiation therapy. In another embodiment, the independent control of the tomographic imaging process and X-ray collection process allows simultaneous single and/or multi-field collection of X-ray images and tomographic images easing interpretation of multiple images. Indeed, the X-ray and tomographic images are optionally overlaid and/or integrated to from a hybrid X-ray/proton beam tomographic image as the patient 230 is optionally in the same position for each image. In still another embodiment, the tomogram is collected with the patient 230 in the about the same position as when the patient's tumor is treated using subsequent irradiation therapy. For some tumors, the patient being positioned in the same upright or semi-upright position allows the tumor 220 to be separated from surrounding organs or tissue of the patient 230 better than in a laying position. Positioning of the scintillation material, in the scintillation detector system 210, behind the patient 230 allows the tomographic imaging to occur while the patient is in the same upright or semi-upright position. The use of common elements in the tomographic imaging and in the charged particle cancer therapy allows benefits of the cancer therapy, described supra, to optionally be used with the tomographic imaging, such as proton beam x-axis control, proton beam y-axis control, control of proton beam energy, control of proton beam intensity, timing control of beam delivery to the patient, rotation control of the patient, and control of patient translation all in a raster beam mode of proton energy delivery. The use of a single proton or cation beamline for both imaging and treatment eases patient setup, reduces alignment uncertainties, reduces beam state uncertainties, and eases quality assurance. In yet still another embodiment, initially a three-dimensional tomographic X-ray and/or proton based reference image is collected, such as with hundreds of individual rotation images of the tumor 220 and patient 230. Subsequently, just prior to proton treatment of the cancer, just a few 2-dimensional control tomographic images of the patient are collected, such as with a stationary patient or at just a few rotation positions, such as an image straight on to the patient, with the patient rotated about 45 degrees each way, and/or the X-ray source and/or patient rotated about 90 degrees each way about the y-axis. The individual control images are compared with the 3-dimensional reference image. An adaptive proton therapy is optionally subsequently performed where: (1) the proton cancer therapy is not used for a given position based on the differences between the 3-dimensional reference image and one or more of the 2-dimensional control images and/or (2) the proton cancer therapy is modified in real time based on the differences between the 3-dimensional reference image and one or more of the 2-dimensional control images. Charged Particle State Determination/Verification/Photonic Monitoring Still referring to FIG. 2, the tomography system 200 is optionally used with a charged particle beam state determination system 250, optionally used as a charged particle verification system. The charged particle state determination system 250 optionally measures, determines, and/or verifies one of more of: (1) position of the charged particle beam, such as a treatment beam 269, (2) direction of the treatment beam 269, (3) intensity of the treatment beam 269, (4) energy of the treatment beam 269, (5) position, direction, intensity, and/or energy of the charged particle beam, such as a residual charged particle beam 267 after passing through a sample or the patient 230, and/or (6) a history of the charged particle beam. For clarity of presentation and without loss of generality, a description of the charged particle beam state determination system 250 is described and illustrated separately in FIG. 3 and FIG. 4A; however, as described herein elements of the charged particle beam state determination system 250 are optionally and preferably integrated into the nozzle system 146 and/or the tomography system 200 of the charged particle treatment system 100. More particularly, any element of the charged particle beam state determination system 250 is integrated into the nozzle system 146, a dynamic gantry nozzle, and/or tomography system 200. The tomography system detects secondary electrons, resultant from the positively charged particles, and/or uses a scintillation material of a scintillation detector element 205, scintillation plate, or scintillation detector system 210. The nozzle system 146 or the dynamic gantry nozzle provides an outlet of the charged particle beam from the vacuum tube initiating at the injection system 120 and passing through the synchrotron 130 and beam transport system 135. Any plate, tracking plane, sheet, fluorophore, or detector of the charged particle beam state determination system is optionally integrated into the nozzle system 146. For example, an exit foil of the nozzle is optionally a first sheet 252 of the charged particle beam state determination system 250 and a first coating 254 is optionally coated onto the exit foil, as illustrated in FIG. 2. Similarly, optionally a surface of the scintillation material is a support surface for a fourth coating 292, as illustrated in FIG. 2. The charged particle beam state determination system 250 is further described, infra. Referring now to FIG. 2, FIG. 3, and FIG. 4A, four tracking planes and/or four sheets, such as a first tracking plane 260 or a first sheet 252, a second tracking plane 270 or second sheet, a third tracking plane 280 or third sheet, and a fourth tracking plane 290 or fourth sheet are used to illustrate detection sheets and/or photon emitting sheets upon transmittance of a charged particle beam. Each sheet is optionally coated with a photon emitter, such as a fluorophore, such as the first sheet 252 is optionally coated with a first coating 254. Without loss of generality and for clarity of presentation, the four tracking planes are each illustrated as units, where the light emitting layer is not illustrated. Thus, for example, the second tracking plane 270 optionally refers to a support sheet, a light emitting sheet, and/or a support sheet coated by a light emitting element. The four tracking planes are representative of n tracking planes, where n is a positive integer. Referring now to FIG. 2 and FIG. 3, the charged particle beam state verification system 250 is a system that allows for monitoring of the actual charged particle beam position in real-time without destruction of the charged particle beam. The charged particle beam state verification system 250 preferably includes a first position element or first beam verification layer, which is also referred to herein as a coating, luminescent, fluorescent, phosphorescent, radiance, or viewing layer. The first position element optionally and preferably includes a coating or thin layer substantially in contact with a sheet, such as an inside surface of the nozzle foil, where the inside surface is on the synchrotron side of the nozzle foil. Less preferably, the verification layer or coating layer is substantially in contact with an outer surface of the nozzle foil, where the outer surface is on the patient treatment side of the nozzle foil. Preferably, the nozzle foil provides a substrate surface for coating by the coating layer. Optionally, a binding layer is located between the coating layer and the nozzle foil, substrate, or support sheet. Optionally, the position element is placed anywhere in the charged particle beam path. Optionally, more than one position element on more than one sheet, respectively, is used in the charged particle beam path and is used to determine a state property of the charged particle beam, as described infra. Still referring to FIG. 2 and FIG. 3, the coating, referred to as a fluorophore, yields a measurable spectroscopic response, spatially viewable by a detector or camera, as a result of transmission by the proton beam. The coating is preferably a phosphor, but is optionally any material that is viewable or imaged by a detector where the material changes, as viewed spectroscopically, as a result of the charged particle beam hitting or transmitting through the coating or coating layer. A detector or camera views secondary photons emitted from the coating layer and determines a position of a treatment beam 269, which is also referred to as a current position of the charged particle beam or final treatment vector of the charged particle beam, by the spectroscopic differences resulting from protons and/or charged particle beam passing through the coating layer. For example, the camera views a surface of the coating surface as the proton beam or positively charged cation beam is being scanned by the first axis controller 143, vertical control, and the second axis controller 144, horizontal control, beam position control elements during treatment of the tumor 220. The camera views the current position of the charged particle beam or treatment beam 269 as measured by spectroscopic response. The coating layer is preferably a phosphor or luminescent material that glows and/or emits photons for a short period of time, such as less than 5 seconds for a 50% intensity, as a result of excitation by the charged particle beam. The detector observes the temperature change and/or observe photons emitted from the charged particle beam traversed spot. Optionally, a plurality of cameras or detectors are used, where each detector views all or a portion of the coating layer. For example, two detectors are used where a first detector views a first half of the coating layer and the second detector views a second half of the coating layer. Preferably, at least a portion of the detector is mounted into the nozzle system to view the proton beam position after passing through the first axis and second axis controllers 143, 144. Preferably, the coating layer is positioned in the proton beam path 268 in a position prior to the protons striking the patient 230. Referring now to FIG. 1 and FIG. 2, the main controller 110, connected to the camera or detector output, optionally and preferably compares the final proton beam position or position of the treatment beam 269 with the planned proton beam position and/or a calibration reference, such as a calibrated beamline, to determine if the actual proton beam position or position of the treatment beam 269 is within tolerance. The charged particle beam state determination system 250 preferably is used in one or more phases, such as a calibration phase, a mapping phase, a beam position verification phase, a treatment phase, and a treatment plan modification phase. The calibration phase is used to correlate, as a function of x-, y-position of the first axis controller 143 and the second axis controller 144 response the actual x-, y-position of the proton beam at the patient interface. During the treatment phase, the charged particle beam position is monitored and compared to the calibration and/or treatment plan to verify accurate proton delivery to the tumor 220 and/or as a charged particle beam shutoff safety indicator. Referring now to FIG. 5, a position verification system 179 and/or a treatment delivery control system 112, upon determination of a tumor shift, an unpredicted tumor distortion upon treatment, and/or a treatment anomaly optionally generates and or provides a recommended treatment change 1070. The treatment change 1070 is optionally sent out while the patient 230 is still in the treatment position, such as to a proximate physician, through a communication system to a remote physician located outside of the treatment room and not in a direct line of sight of the patient in the treatment position, such as no line of sight through a window between a control room and the patient in the treatment room, and/or over the internet to a remote physician, for physician approval 1072, receipt of which allows continuation of the now modified and approved treatment plan. Referring now to FIG. 43A and FIG. 43B, a multi-layer multi-color scintillation detector element 4300, a species of the multi-layer scintillator 4030, is described where at least two z-axis layers differ in wavelength ranges of emitted secondary photons. As illustrated, the first scintillation layer 4111 is the first red (R) photon emission layer 4210, the second scintillation layer 4114 is a green (G) photon emission layer 4320, and the third scintillation layer 4116 is a blue (B) photon emission layer 4330. Again, for clarity of presentation, red, green, and blue photons are illustrative of a set of wavelength ranges of the respective first, second, and third photon emission layers 4210, 4220, 4230 and emission wavelengths include ultraviolet and infrared light. Use of different scintillation materials emitting light in differing wavelength regions is optionally and preferably used to enhance resolution of a depth of penetration and/or an original energy of the residual energy particle beam 267 through reduction of cross-talk between layers. To clarify, in the case of a standard camera using a Bayer matrix, elements covered by filters are used to detect red, green, or blue light, where standard detector arrays provide x/y-plane resolution and the standard Bayer matrix yields z-axis resolution of position the charged particle beam. Optionally and preferably, one or more two-dimensional detector arrays are optically coupled to a set of transmission filters with out of emission band blocking elements are keyed, respectively, to wavelengths of emissions from a set emission layers with corresponding emission elements in the multi-layer scintillator 4030. Referring still to FIG. 43A and FIG. 43B, the multi-layer multi-color scintillation detector element 4300 is further described. For clarity of presentation and without loss of generality, a blue (B) emission scintillation layer, such as the third emission layer 4330 has a greater responsivity, photons emitted per millimeter of beam travel, than a green (G) emission scintillation layer, such as the second emission layer 4320, which has a greater responsivity than a red (R) emission scintillation layer, such as the first red (R) photon emission layer 4210 described in the second example. Thus, in a first case of a red scintillator used in each of the first, second, and third scintillation layers, the first response curve 4241, described in the first example, is generated. Similarly, in a second case of a green scintillator used in each of the first, second, and third scintillation layer, a second response curve 4242 is generated. Similarly, in a third case of a blue scintillator used in each of the first, second, and third scintillation layer, a third response curve 4243 is generated. Referring now to FIG. 43B, for a given depth, the more responsive blue emission scintillation layer yields a higher signal than the less responsive green emission scintillation layer, which yields a greater response than the still less responsive red emission scintillation layer. Further, the spread between the exemplary response curves increases with depth of penetration of the charged particles into the multi-layer scintillator 4030 as a greater lost energy, resultant in the higher response, slows the charged particles more resulting in a still greater loss of energy of the charged particle, as described supra. Thus, three unique response curves are generated; in this example, all of the response curves having a non-linear shape. Referring still to FIG. 43A and FIG. 43B and referring now to FIG. 43C, the multi-layer multi-color scintillation detector element 4300 is further described. In FIG. 43C, the first response of the first red (R) photon emission layer 4210 at the first depth is plotted with both the second response of the green photon emission layer 4320 at the second depth and the third response of the blue photon emission layer 4330 at the third depth. By effectively using the first point of the first response curve 4241, the second point of the second response curve 4242, and the third point of the third response curve 4243, relative to the first, second, and third response curves, an amplified response curve with a greater slope and an enhanced curve shape is generated, which is referred to herein as a first multi-color response curve 4251. The first multi-color response curve is combined and compared with additional multi-color response curves, as further described infra. Referring now to FIG. 44, a stacked detector element 4400 of the beam state, position and/or residual energy, determination system 4000 is described. The stacked detector element includes multiple sub-stacks, where each sub-stack is a unit block of two or more scintillation layers of different wavelength of emission. As illustrated, for clarity of presentation and without loss of generality, the stacked detector element 4400 comprises four repeating sub-stacks with three scintillation layers per sub-stack. As illustrated, the first sub-stack 4301 is a first set of red, green, and blue scintillation layers, such as the multi-layer multi-color scintillation detector element 4300. A second sub-stack 4302, a third sub-stack 4303, and a fourth sub-stack 4304 are repeating units of the first sub-stack 4301, where the set of sub-stacks are optionally close packed along the z-axis and/or as illustrated have a small gap between each sub-stack. More generally, the sub-stack comprises any number of scintillation layers and any number of scintillation colors where the scintillation colors are ordered in any order along the z-axis of the charged particles. Further, the stacked detector element 4400 optionally contains different types of sub-stacks, such as 2, 3, 4, or more color sub-stacks. Still further, each layer of a given sub-stack type is optionally any thickness, such as thicker or thinner than a neighboring layer along the z-axis. Still referring to FIG. 44, a set of response curves 4250 are plotted for a first residual charged particle beam 267 at a first energy, E1, that transmits through the stacked detector element 4400. As illustrated, a first member of the set of response curves is the first multi-color response curve 4251, described supra, related to the charged particles passing through the first sub-stack 4301. As the charged particles penetrate into the second sub-stack 4302, the charged particles continue to lose energy, which results in a second multi-color response curve 4252 comprising larger element-by-element responses compared to responses from the first sub-stack 4302. More particularly, the red scintillator response is larger from the second sub-stack 4302 than from the first sub-stack 4301. Larger responses from the green and blue scintillation materials also result, which combined with the material responsivity differences results in a distinct shape of the second response curve 4252 relative to a shape of the first response curve 4251. Similarly, passage of the charged particles through the third sub-stack 4303 and the fourth sub-stack 4304 results in a third multi-color response curve 4253 and a fourth multi-color response curve 4254 with a third and fourth distinct shape, respectively. Similarly, the set of response curves 4250 are also plotted for a second residual charged particle beam 267 at a second lower energy, E2, that terminates, such as in a Bragg peak, within the stacked detector element 4400. More particularly, a fifth, sixth, seventh, and eighth multi-color response curve 4255, 4256, 4257, 4258 are illustrated for the lower second energy, relative to the first higher energy, E1, residual charged particle beam. The lower energy beam, E2 versus E1, results in: (1) a larger response for a given depth and (2) in a larger curvature shape in each sub-stack, relative to the first residual charged particle beam due to a larger loss of energy, as described supra. If the set of emission layers is limited to one scintillation material, the response signals reduce to a Bragg peak with gaps along the z-axis. For example, referring still to FIG. 44, if only the first red emission scintillation layer of each sub-stack is plotted, the points fit a Bragg peak curve, with loss of the benefit of different responsivities of differing scintillation materials/colors. As further described infra, initial energy of the residual charged particle beam 267 is determined using any 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, or more points from the union of the response curves with or without a Bragg peak-like sudden stoppage of the charged particles within the stacked detector element 4400 or the multi-layer scintillator 4030. Still referring to FIG. 44, as a given response curve, which changes for changing initial energy levels of the residual charged particle beam 267 is based on scintillator material types as a function of depth, once calibrated the initial energy of the residual charged particle beam 267 is determined using:                a response at any given depth;        a difference in response between any two depths;        2, 3, or more responses in a given sub-stack;        responses from single layers in 2, 3, or more sub-stacks;        responses from 2, 3, or more sub-stacks;        responses from a common scintillator material at two or more depths;        responses from a common scintillator material in 2, 3, or more sub-stacks;        a shape of a response curve of a given sub-stack;        a shape of a response curve comprising points from 2, 3, or more sub-stacks; and/or        a shape of a response curve from two or more scintillation layers.         Still referring to FIG. 44, the inventor notes that error is reduced in determination of the initial energy of the residual charged particle beam 267 using:                an increasing number of points in a given response curve from a given sub-stack;        an increasing number of points from two or more sub-stacks;        an increasing number of points from two or more layers of the multi-layer scintillator 4030;        using two or more scintillation materials with different responsivities due to the change in response being large;        a gap, along the z-axis, between two or more layers, which increases the change in response between the two or more layers;        a beam slowing material, such as other scintillation layers, between two or more scintillation layers.         Reduction in error of determination of the initial energy of the residual charged particle beam 267, by way of additional data points, increases precision and/or accuracy of an image generated using the residual energies, such as a proton computed radiography (pRT) image; a proton computed tomography (pCT) image; and/or a positively charged particle radiography and/or tomography image. Still referring to FIG. 44, shapes of the set of response curves 4250, shapes of combinations of members of the set of response curves 4250, and/or individual members of the set of response curves are optionally used, after calibration, to determine a full Bragg peak profile, including a position of the Bragg peak, even without observation of the Bragg peak for a given scintillation color. The inventor notes that the set of response curves represents multiple Bragg peak profiles, one for each scintillation color utilized in the multi-layer scintillator. The inventor further notes that multiple Bragg peaks enhances accuracy and/or resolution of the energy of the residual charged particle beam 760 as a result of the rapid drop off of a given Bragg peak relative to a thickness of a given scintillation layer and the opportunity to catch multiple points, a very sensitive and accurate measurement, of a Bragg peak falloff from different scintillation layers given multiple Bragg peaks occurring for different colors across junctions of layers in the set of layers in the multi-layer scintillator detector element 4110. Dual Particle Accelerator Referring now to FIGS. 45-49, use of a single synchrotron to accelerate multiple treatment beams, comprising positive and/or negative ions and/or particles, such as an electron, is described. Referring now to FIG. 45, a dual accelerator 4510, such as the synchrotron 130, in a multi-beam type treatment system 4500 is used to accelerate cations 4520, such as H+ or C6+ and, by reversing the polarity of the main bending magnets 132, or a portion thereof as described infra, the synchrotron 130 is used to accelerate anions 4530 and/or an atomic particle, such as an electron, e−. Herein, for clarity of presentation and without loss of generality, H+, C6+ and e− are used as examples of any atomic anion, cation, or particle with a positive or negative charge. Herein, carbon stripped of all electrons is referred to as C6+, a carbon atom stripped of all electrons, and/or a carbon charge state of six. Similarly, C4+ or C6+ are referred to as multiply charged carbon atoms. Thus, more generally, the synchrotron 130 is used to accelerate any multiply charged cation having a mass-to-charge ratio, m/Q, where m is mass, such as an atomic mass, of the atom and Q is the charge of the cation, such as C6+ has a mass-to-charge ratio of 12/6 or 2 and H+ has a mass-to-charge ratio of 1/1 or 1. Referring now to FIG. 46, a multiple particle accelerator system 4600, which is an example of the charged particle beam system 100, is illustrated with multiple injector systems, such as a first injector system 4610, a second injector system 4620, and a third injector system 4630, such as used to inject a proton, a carbon atom stripped of all electrons, and an electron, respectively. Referring now to FIG. 47, a cross-section of a single turning magnet 4700, such as the main bending magnet 132, of the synchrotron 130 and/or the beam transport system 135 is provided. The turning magnet 4700 includes a first magnet half 4701 and a second magnet half 4702 and a gap 4710 running therebetween through which protons circulate in the synchrotron 130 and/or are transported through the beam transport system 135. The gap 4710 is preferably a flat gap, allowing for a magnetic field across the gap 4710 that is more uniform, even, and intense. In use, a magnetic field runs sequentially from a first magnet core 4720, across the gap 4710, through a second magnet core 4730, through a second magnet return yoke 4732, and through a first magnet return yoke 4722 to arrive back at the first magnet core 4720, or vise-versa. An insulator 4795 is optionally used to direct the magnetic field through the gap 4710. Still referring to FIG. 47, coils generating the magnetic field loop, described in the preceding paragraph, are described. Herein, winding coils refer to: (1) optionally and preferably, a first magnet coil 4750 wound around the first magnet core 4720 and a second magnet coil 4760 wound around the second magnet core 4730 and (2) optionally and preferably, a first correction coil 4770 and a second correction coil 4780, described infra, which are also wound around the first magnet core 4720 and second magnet core 4730, respectively. The first and second correction coils 4770, 4780 are optionally used in a position inside, outside, on top, or on the bottom relative to their respective first and second magnet coils 4750, 4760. Alternatively, positions of the first and second correction coils 4770, 4780 and the first and second magnet coils 4750, 4760 are reversed compared to their illustrated positions in FIG. 47. Still referring to FIG. 47, the first and second correction coils 4770, 4780 supplement the first and second magnet coils 4750, 4760. More particularly, the first and second correction coils 4770, 4780 have correction coil power supplies that are separate from winding coil power supplies used with the first and second magnet coils 4750, 4760. The correction coil power supplies typically operate at a fraction of the power required compared to the main winding coil power supplies, such as about 1, 2, 3, 5, 7, or 10 percent of the power and more preferably about 1 or 2 percent of the power used with the main magnet winding coils. The smaller operating power applied to the correction coils allows for more accurate and/or precise control of the correction coils. The correction coils are used to adjust for imperfection in the turning magnets. Optionally, separate correction coils are used for each turning magnet allowing individual tuning of the magnet field for each turning magnet, which eases quality requirements in the manufacture of each turning magnet. As further described infra, the first and second correction coils 4770, 4780 are optionally used to accelerate electrons and/or guide transport of electrons, such as used to directly treat and/or indirectly treat, via generation of secondary X-rays, the tumor 220 of the patient 230. Still referring to FIG. 47, the charged particle beam moves through the gap 4710 with an instantaneous velocity, v. Current running through the first and second magnet coils 4750, 4760 results in a magnetic field, B, running through the single turning magnet 4700. In a first example, at a first time, in conjunction with use of the first injector 4610 injecting a positively charged cation, such as a proton, current flows in a first direction around/through the winding coils resulting in a first magnetic field, B1, running in a first direction, which pushes the positively charged particle inward toward a central point of the synchrotron 130, which turns the charged particle beam in an arc. In a second example, at a second time, in conjunction with use of the third injector 4630 injecting a negatively charged particle, such as an electron, current flows in a second direction, opposite the first direction, around/through the winding coils resulting in a second magnetic field, B2, running in a second direction, which pushes the negatively charged particle beam inward toward a central point of the synchrotron 130, which again turns the charged particle beam in an arc, such as through the synchrotron 130 and/or along the beam transport system 135. Thus, referring still to FIG. 47 and referring now to FIG. 48, at the first time, the cation, such as the proton, is accelerated by the synchrotron 130 and delivered via the beam transport system 135 and at the second time, an electron is accelerated by the synchrotron 130 and delivered via the beam transport system 135 to the patient 230. As illustrated, the proton, having a large mass and a larger mass-to-charge ratio than the electron, penetrates further into the patient 230 and treats the tumor 220 at first greater treatment depth than a second treatment depth of the tumor 220 by the lower mass and more scattering electron. Referring now to FIG. 49, three beam types are used, a proton beam, an electron beam, and a C6+ beam to treat the tumor 220 of the patient 230, such as at various relative depths based on charge, mass, energy, ion/particle cross-section, absorbance, and/or scattering. The inventor notes that the proton beam is illustrative of any ion having a charge-to-mass ratio of one, the C6+ is illustrative of any ion having a charge-to-mass ration of two, and the electron is illustrative of any particle having a negative charge and that a single synchrotron 130 is used to accelerate all treatment beams. The inventor further notes that the synchrotron 130 optionally accelerates: (1) two or more cation types having a same charge-to-mass ratio and/or (2) accelerates a cation of any charge-to-mass ratio. Referring again to FIG. 46, FIG. 47, and FIG. 49, a multiple beam type treatment system 4900 is described using 2, 3, 4, 5 or more beam types of cations, anions, and/or particles at any 1, 2, 3, 4 or more charge-to-mass ratios. As illustrated, at a first time, t1, the first injector system 4610 and the synchrotron 130 accelerate a proton to a first energy that penetrates a first depth 4910 and/or a first total pathlength into the tumor 220 of the patient 230. As illustrated, at a second time, t2, the third injector system 4630 and the synchrotron 130 accelerate an electron to a second energy that penetrates a second depth 4920 and/or a second total pathlength into the tumor 220 of the patient 230. Due to the scattering of the lighter weight electron in tissue, as illustrated the proton penetrates a greater depth into the patient 230 and the electron is used to treat a surface tumor, a near surface tumor, and/or a section of a tumor near the surface of the skin, such as less than 10, 5, 4, 3, 2, or 1 millimeter from the surface of the skin. Similarly, at a third time, t3, the second injector system 4620 and the synchrotron 130 accelerate C6+ to a third energy that penetrates a third depth 4930 and/or a third total pathlength into the tumor 220 of the patient 230. As the C6+ has a larger mass-to-charge ratio compared to the proton, equation 1,r=E·m·sqrt(2)/(qB)  (eq. 1)requires, for a given synchrotron setting, the C6+ has a lower energy than the proton and penetrates to a shallower depth than the proton, where r is a bending radius, E is energy, m is mass, q is charge, and B is a magnetic field. As size/performance of the synchrotron 130 increases to pass the proton through the patient 230, such as in proton tomography, the depth of penetration of the C6+ increases, eventually to the point of doing carbon tomography, where a carbon cation, or other cation with an atomic mass of 2, 3, 4, 5, 6, or more has enough energy to pass through the patient. The inventor notes that a proton accelerator configured to pass protons just to an opposite side of a patient, designated here as one unit, still has the capability of accelerating a larger mass and/or a larger mass-to-charge ratio particle into the person at an effective treatment depth, such as less than 0.75, 0.50, 0.25, or 0.10 of the way through a patient having a thickness of 1.00 unit. Referring again to FIG. 47, use of the first and second correction coils 4770, 4780 and a current controller 4790 to accelerate electrons with and/or preferably without use of the first and second magnet coils 4560, 4570 is described. More particularly, the smaller first and second correction coils 4770, 4780, such as with less than 10, 5, 2, or 1 percent of a maximum current passing through the first and second magnet coils 4560, 4570 when accelerating a cation, are still capable of turning the smaller mass electron and thus are optionally used to accelerate and guide the electron to the body for tumor treatment. The inventor notes that the electrons are optionally used to generate X-rays, such as by striking a heavy metal, such as tungsten, where the resultant secondary X-rays are guided, also referred to in the art as collimated, into the tumor 220 of the body 230. The tungsten or X-ray generating material, upon being struck by an electron, is optionally and preferably removable and replaceably placed proximate the patient 230, such as within 1, 2, 3, 5, or 10 cm of the patient. The current controller 4790 optionally uses a first switch 4792 to turn on/off the first and/or second magnet coils 4750, 4560, and/or uses a second switch 4794 to turn on/off the first and/or second correction coils 4770, 4780. Additionally, the current controller 4790 is optionally used to change/reverse polarity of the first and second correction coils 4770, 4780 to go from a first mode of correction of the first and second magnet coils 4560, 4570, such as for turning guiding protons or cations, to a second mode of turning/guiding electrons. Thus, the first and second correction coils 4770, 4780 in combination with the current controller 4790 allows the synchrotron to accelerate protons or cations and then switch to accelerating electrons with the same alignment of the rotatable gantry support 1210 and/or position of the nozzle system 146 relative to the patient 230. Still yet another embodiment includes any combination and/or permutation of any of the elements described herein. The main controller, a localized communication apparatus, and/or a system for communication of information optionally comprises one or more subsystems stored on a client. The client is a computing platform configured to act as a client device or other computing device, such as a computer, personal computer, a digital media device, and/or a personal digital assistant. The client comprises a processor that is optionally coupled to one or more internal or external input device, such as a mouse, a keyboard, a display device, a voice recognition system, a motion recognition system, or the like. The processor is also communicatively coupled to an output device, such as a display screen or data link to display or send data and/or processed information, respectively. In one embodiment, the communication apparatus is the processor. In another embodiment, the communication apparatus is a set of instructions stored in memory that is carried out by the processor. The client includes a computer-readable storage medium, such as memory. The memory includes, but is not limited to, an electronic, optical, magnetic, or another storage or transmission data storage medium capable of coupling to a processor, such as a processor in communication with a touch-sensitive input device linked to computer-readable instructions. Other examples of suitable media include, for example, a flash drive, a CD-ROM, read only memory (ROM), random access memory (RAM), an application-specific integrated circuit (ASIC), a DVD, magnetic disk, an optical disk, and/or a memory chip. The processor executes a set of computer-executable program code instructions stored in the memory. The instructions may comprise code from any computer-programming language, including, for example, C originally of Bell Laboratories, C++, C #, Visual Basic® (Microsoft, Redmond, Wash.), Matlab® (MathWorks, Natick, Mass.), Java® (Oracle Corporation, Redwood City, Calif.), and JavaScript® (Oracle Corporation, Redwood City, Calif.). Herein, any number, such as 1, 2, 3, 4, 5, is optionally more than the number, less than the number, or within 1, 2, 5, 10, 20, or 50 percent of the number. Herein, an element and/or object is optionally manually and/or mechanically moved, such as along a guiding element, with a motor, and/or under control of the main controller. The particular implementations shown and described are illustrative of the invention and its best mode and are not intended to otherwise limit the scope of the present invention in any way. Indeed, for the sake of brevity, conventional manufacturing, connection, preparation, and other functional aspects of the system may not be described in detail. Furthermore, the connecting lines shown in the various figures are intended to represent exemplary functional relationships and/or physical couplings between the various elements. Many alternative or additional functional relationships or physical connections may be present in a practical system. In the foregoing description, the invention has been described with reference to specific exemplary embodiments; however, it will be appreciated that various modifications and changes may be made without departing from the scope of the present invention as set forth herein. The description and figures are to be regarded in an illustrative manner, rather than a restrictive one and all such modifications are intended to be included within the scope of the present invention. Accordingly, the scope of the invention should be determined by the generic embodiments described herein and their legal equivalents rather than by merely the specific examples described above. For example, the steps recited in any method or process embodiment may be executed in any order and are not limited to the explicit order presented in the specific examples. Additionally, the components and/or elements recited in any apparatus embodiment may be assembled or otherwise operationally configured in a variety of permutations to produce substantially the same result as the present invention and are accordingly not limited to the specific configuration recited in the specific examples. Benefits, other advantages and solutions to problems have been described above with regard to particular embodiments; however, any benefit, advantage, solution to problems or any element that may cause any particular benefit, advantage or solution to occur or to become more pronounced are not to be construed as critical, required or essential features or components. As used herein, the terms “comprises”, “comprising”, or any variation thereof, are intended to reference a non-exclusive inclusion, such that a process, method, article, composition or apparatus that comprises a list of elements does not include only those elements recited, but may also include other elements not expressly listed or inherent to such process, method, article, composition or apparatus. Other combinations and/or modifications of the above-described structures, arrangements, applications, proportions, elements, materials or components used in the practice of the present invention, in addition to those not specifically recited, may be varied or otherwise particularly adapted to specific environments, manufacturing specifications, design parameters or other operating requirements without departing from the general principles of the same. Although the invention has been described herein with reference to certain preferred embodiments, one skilled in the art will readily appreciate that other applications may be substituted for those set forth herein without departing from the spirit and scope of the present invention. Accordingly, the invention should only be limited by the Claims included below. Still referring to FIG. 22, a sixth input to the automated radiation treatment plan development system 2200 comprises information related to collapse and/or shifting of the tumor 220 of the patient 230 during treatment. For instance, the radiation treatment plan 2210 is automatically updated, using the automated radiation treatment plan development system 2200, during treatment using an input of images of the tumor 220 of the patient 230 collected concurrently with treatment using the positively charged particles. For instance, as the tumor 220 reduces in size with treatment, the tumor 220 collapses inward and/or shifts. The auto-updated radiation treatment plan is optionally auto-implemented, such as without the patient moving from a treatment position. Optionally, the automated radiation treatment plan development system 2200 tracks dosage of untreated voxels of the tumor 220 and/or tracks partially irradiated, relative to the prescribed dosage 2221, voxels and dynamically and/or automatically adjusts the radiation treatment plan 2210 to provide the full prescribed dosage to each voxel despite movement of the tumor 220. Similarly, the automated radiation treatment plan development system 2200 tracks dosage of treated voxels of the tumor 220 and adjusts the automatically updated tumor treatment plan to reduce and/or minimize further radiation delivery to the fully treated and shifted tumor voxels while continuing treatment of the partially treated and/or untreated shifted voxels of the tumor 220. Automated Adaptive Treatment Referring now to FIG. 23, a system for automatically updating the radiation treatment plan 2300 and preferably automatically updating and implementing the radiation treatment plan is illustrated. In a first task 2310, an initial radiation treatment plan is provided, such as the auto-generated radiation treatment plan 2126, described supra. The first task is a startup task of an iterative loop of tasks and/or recurring set of tasks, described herein as comprising tasks two to four. In a second task 2320, the tumor 220 is treated using the positively charged particles delivered from the synchrotron 130. In a third task 2330, changes in the tumor shape and/or changes in the tumor position relative to surrounding constituents of the patient 230 are observed, such as via any of the imaging systems described herein. The imaging optionally occurs simultaneously, concurrently, periodically, and/or intermittently with the second task while the patient remains positioned by the patient positioning system. The main controller 110 uses images from the imaging system(s) and the provided and/or current radiation treatment plan to determine if the treatment plan is to be followed or modified. Upon detected relative movement of the tumor 220 relative to the other elements of the patient 230 and/or change in a shape of the tumor 230, a fourth task 2340 of updating the treatment plan is optionally and preferably automatically implemented and/or use of the radiation treatment plan development system 2200, described supra, is implemented. The process of tasks two to four is optionally and preferably repeated n times where n is a positive integer of greater than 1, 2, 5, 10, 20, 50, or 100 and/or until a treatment session of the tumor 220 ends and the patient 230 departs the treatment room 922. Automated Treatment Referring now to FIG. 24, an automated cancer therapy treatment system 2400 is illustrated. In the automated cancer therapy treatment system 2400, a majority of tasks are implemented according to a computer based algorithm and/or an intelligent system. Optionally and preferably, a medical professional oversees the automated cancer therapy treatment system 2400 and stops or alters the treatment upon detection of an error but fundamentally observes the process of computer algorithm guided implementation of the system using electromechanical elements, such as any of the hardware and/or software described herein. Optionally and preferably, each sub-system and/or sub-task is automated. Optionally, one or more of the sub-systems and/or sub-tasks are performed by a medical professional. For instance, the patient 230 is optionally initially positioned in the patient positioning system by the medical professional and/or the nozzle system 146 inserts are loaded by the medical professional. Optional and preferably automated, such as computer algorithm implemented, sub-tasks include one or more and preferably all of:                receiving the treatment plan input 2200, such as a prescription, guidelines, patient motion guidelines 2230, dose distribution guidelines 2220, intervening object 2210 information, and/or images of the tumor 220;        using the treatment plan input 2200 to auto-generate a radiation treatment plan 2126;        auto-positioning 2122 the patient 230;        auto-imaging 2124 the tumor 220;        implementing medical profession oversight 2138 instructions;        auto-implementing the radiation treatment plan 2320/delivering the positively charged particles to the tumor 220;        auto-reposition the patient 2321 for subsequent radiation delivery;        auto-rotate a nozzle position 2322 of the nozzle system 146 relative to the patient 230;        auto-translate a nozzle position 2323 of the nozzle system 146 relative to the patient 230;        auto-verify a clear treatment path using an imaging system, such as to observe presence of a metal object or unforeseen dense object via an X-ray image;        auto-verify a clear treatment path using fiducial indicators 2324;        auto control a state of the positively charge particle beam 2325, such as energy, intensity, position (x,y,z), duration, and/or direction;        auto-control a particle beam path 2326, such as to a selected beamline and/or to a selected nozzle;        auto implement positioning a tray insert and/or tray assembly;        auto-update a tumor image 2410;        auto-observe tumor movement 2330; and/or        generate an auto-modified radiation treatment plan 2340/new treatment plan.         Treatment Beam Progression Referring now to FIGS. 25-32, treatment beam progression is described. More particularly, reduction in systematic errors by control of order and/or position of treatment of tumor voxels is described. Referring now to FIG. 25 and FIG. 26, row-by-row voxel treatment of a tumor, the tumor not illustrated for clarity of presentation, is compared with non-row treatment of a tumor, referred to herein as a controlled beam progression treatment and/or a controlled random beam position treatment system. Referring now to FIG. 25, a first voxel of the tumor is treated, then second, third, fourth, fifth, and sixth voxels are sequentially treated with the treatment beam 269. Subsequently, second, third, fourth, . . . , nth rows are treated until all voxels in an x/y-plane of the tumor are treated, the first nine treatment voxels are illustrated. In stark contrast, referring now to FIG. 26, the treatment beam 269 over time will treat all of the x/y-plane pixels, but in a random order as a function of x-axis position and y-axis position. Referring now to FIGS. 25-32, for clarity of presentation and without loss of generality, the beam is illustrated as a function of time moving along a first axis, such as the x-axis, relative to a second axis, such as the y-axis. However, the beam is optionally scanned along and/or moved randomly along the x-axis, the y-axis, the z-axis, any pair of axes, and/or along all three axes as a function of time. Further, the x, y, and z-axes are optionally treated at m, n, or o positions, where m, n, and o are positive integers. Systematic Beam Position Errors A charged particle cancer therapy system uses a complex instrument in a complex setting. Many changes to the beam output as a function of time versus a planned treatment result, such as during scanning the beam position, delivering an intended beam energy, and/or delivering an intended beam energy. Many known factors impact precision and accuracy of the beam state, where various calibration and/or control systems minimize precision and accuracy error. However, physics dictates that absolute control of the treatment beam state in terms of precision and accuracy is not possible. Further, unknown parameters may lead to errors, such as systematic errors, in the beam state accuracy and precision. Two known and controlled errors are illustrated in the following examples. In a seventh example, the rolling floor 1320 forms a continuous loop in the cantilevered three hundred sixty degree rotatable gantry system. In an eighth example, an actual position of the cantilevered rotatable gantry system is monitored, determined, and/or confirmed using the fiducial indicators 2040, described, infra, such as a fiducial source and/or a fiducial detector/marker placed on any section of the gantry 490, patient positioning system 1350, and/or patient 230. Floor Force Directed Gantry System Referring now to FIG. 17, a wall mounted gantry system 1700 is illustrated, where a wall mounted gantry 499 is bolted to a first wall 1710, such as a first buttress, with a first set of bolts 1714, optionally using a first mounting element 1712, and mounted to a second wall 1720, such as a second buttress 1720, such a through a second mounting element 1722, with a second set of bolts 1714. The inventor notes that in this design, forces, such as a first force, F1, and a second force, F2, are directed outward into the first wall 1710 and the second wall 1720, respectively, where at least twenty percent of resolved force is along the x-axis as illustrated. Thus, the wall mounted gantry system 499 must be designed to overcome tensile stress on the bolts, greatly increasing mounting costs of the wall mounted gantry system 499. Further, the wall mounted gantry 499 design thus requires that the walls of the building are specially designed to withstand the multi-ton horizontal forces resultant from the wall mounted gantry 499. Further, as the wall mounted gantry 1700 must rotate about an axis of rotation to function, the wall mounted gantry 1700 cannot be connected to front and back walls, but rather can only be mounted to side walls, such as the first wall 1710 and the second wall 1720 as illustrated. Thus, when the wall mounted gantry 499 rotates, the center of mass of the wall mounted gantry 499 necessarily moves into a position that is not between the end mounting points, such as the first mounting element 1712 and the second mounting element 1722. With movement of the center of mass of the wall mounted gantry 499 outside of the supports, the gantry must be configured with additional systems to prevent the wall mounted gantry system 499 from tipping over. In stark contrast, referring now to FIG. 18, in a floor mounted gantry system 1800 the gantry 490 is optionally and preferably designed to rest directly onto a support, such as the floor 1310, with no requirement of a wall mounted system. As illustrated, the mass of the gantry 490 results in only downward forces, such as a third force, F3, into ground or a first pier 1810 and as a fourth force, F4, into ground and/or a second pier 1820. Generally, in the floor mounted gantry system, the center of mass of the gantry 490 is inside a footprint of the piers, such as the first pier 1810 and the second pier 1820 and maintains a footprint inside the piers even as the gantry rotates due to use of additional piers into or out of FIG. 18 and/or due to use of the counter mass in the counterweighted gantry system 1100. Referring now to FIG. 19, an example of the gantry superstructure 1600 is illustrated incorporating the gantry 490, the gantry support arm 498, the counterweight system 1120, the rotatable beamline section 138, and the rolling floor system 1300. The rotatable gantry support 1210 is illustrated with the optional hybrid cancer treatment-imaging system 1400. Further, the first pier 1810 and the second pier 1820 of the floor mounted gantry system 1800 are illustrated, which are representative of any number of underfloor gantry support elements designed to support the gantry 490, where the underfloor gantry support elements are out of a rotation path of the gantry support arm 498 and the rotatable beamline section 138. Referenced Charged Particle Path Referring now to FIG. 20, a charged particle reference beam path system 2000 is described, which starkly contrasts to an isocenter reference point of a gantry system, as described supra. The charged particle reference beam path system 2000 defines voxels in the treatment room 922, the patient 230, and/or the tumor 220 relative to a reference path of the positively charged particles and/or a transform thereof. The reference path of the positively charged particles comprises one or more of: a zero vector, an unredirected beamline, an unsteered beamline, a nominal path of the beamline, and/or, such as, in the case of a rotatable gantry and/or moveable nozzle, a translatable and/or a rotatable position of the zero vectors. For clarity of presentation and without loss of generality, the terminology of a reference beam path is used herein to refer to an axis system defined by the charged particle beam under a known set of controls, such as a known position of entry into the treatment room 922, a known vector into the treatment room 922, a first known field applied in the first axis controller 143, and/or a second known field applied in the second axis controller 144. Further, as described, supra, a reference zero point or zero point 1002 is a point on the reference beam path. More generally, the reference beam path and the reference zero point optionally refer to a mathematical transform of a calibrated reference beam path and a calibrated reference zero point of the beam path, such as a charged particle beam path defined axis system. The calibrated reference zero point is any point; however, preferably the reference zero point is on the calibrated reference beam path and as used herein, for clarity of presentation and without loss of generality, is a point on the calibrated reference beam path crossing a plane defined by a terminus of the nozzle of the nozzle system 146. Optionally and preferably, the reference beam path is calibrated, in a prior calibration step, against one or more system position markers as a function of one or more applied fields of the first known field and the second known field and optionally energy and/or flux/intensity of the charged particle beam, such as along the treatment beam path 269. The reference beam path is optionally and preferably implemented with a fiducial marker system and is further described infra.