Measuring radiation dose

Abstract

Provided herein are techniques relating to the use of radiation for medical purposes, and in particular, but not exclusively, to apparatuses, systems, and methods for monitoring, testing, and maintaining medical radiation equipment as part of a quality assurance procedure. For example, the techniques provide, in part, systems and methods for calculating a tissue phantom ratio (TPR) for characterizing a beam.

Description

[0001] This application claims priority to U.S. Provisional Patent Application Serial No. 63 / 396,444, filed on August 9, 2022, the entire contents of which are incorporated herein by reference. Technical Field

[0002] Provided herein are techniques related to the use of radiation for medical purposes, and particularly, but not exclusively, to apparatus, systems, and methods for monitoring, testing, and maintaining medical radiation equipment as part of a quality assurance program. Background Art

[0003] Medical radiation systems use radiation sources for imaging and therapeutic purposes, such as for radiotherapy. The radiation dose absorbed by the patient is a function of several variables, including the radiation beam energy, beam collimation, and the distance between the patient and the radiation source.

[0004] Radiation doses produced by medical radiation systems can be measured using a "phantom," typically a "water phantom" consisting of a tank filled with water. The water phantom closely approximates the radiation absorption and scattering properties of muscle and other soft biological tissues. The properties of the radiation beam, after entering the tank and passing through the water, can be measured using detectors located within the phantom (e.g., within the tank of the water phantom).

[0005] The tissue-to-phantom ratio (TPR) is often measured to characterize the radiation dose delivered by a beam. TPR is defined as the ratio of the dose at a given point in the phantom to the dose at the same point at a fixed reference depth. For example, a common form of TPR is the TPR calculated using radiation measurements recorded at 10 cm and 20 cm water levels in a water phantom. 20,10See, e.g., INTERNATIONAL COMMISSION ON RADIATION UNITS AND MEASUREMENT, "Determination of Absorbed Dose in a Patient Irradiated by Beams of X or Gamma Rays in Radiotherapy Procedures", ICRU Rep. 24, ICRU Publications, Bethesda, MD (1976), incorporated herein by reference. See also "Absorbed Dose Determination in External Beam Radiotherapy: An International Code of Practice for Dosimetry Based on Standards of Absorbed Dose to Water", Technical Reports Series No. 398, International Atomic Energy Agency, Vienna, 2000, incorporated herein by reference.

[0006] Current methods for measuring tissue-to-phantom ratio (TPR) require holding the detector in a fixed position and obtaining radiation measurements at multiple water levels provided between the detector and the radiation source in a water phantom. The water level is usually adjusted manually or automatically by a self-draining mechanism. The drainage process can be initially calibrated by a water sensor, which is usually mounted on the moving mechanism of the tank. In addition, a water reservoir system may be required to control the water level.

[0007] New or improved methods are needed to measure radiation dose from medical radiation systems. Summary of the invention

[0008] Accordingly, provided herein are embodiments of technology related to the use of radiation for medical purposes, and particularly, but not exclusively, to embodiments of technology related to apparatus, systems, and methods for monitoring, testing, and maintaining medical radiation equipment as part of a quality assurance program.

[0009] For example, in some embodiments, the technology provides a phantom. In some embodiments, the phantom includes a tank and the tank includes water. Water can also be simulated with a solid material (e.g., plastic). See, for example, Section 4.2.3 and Table 6 in "Absorbed Dose Determination in External Beam Radiotherapy: An International Code of Practice for Dosimetry Based on Standards of Absorbed Dose to Water", Technical Reports Series No. 398, International Atomic Energy Agency, Vienna, 2000, which is incorporated herein by reference. Therefore, in some embodiments, the phantom includes a solid water equivalent. The solid water phantom described herein provides advantages over phantoms including liquid water, for example, when the radiation dose is measured at any time during acceleration or deceleration of the phantom or during rotation or movement of the liquid water phantom, changes in the liquid water level are caused. The technology provided herein relates to embodiments of a phantom including liquid water ("water phantom") and embodiments of a phantom including a solid water equivalent ("solid phantom").

[0010] In some embodiments, the phantom is a water phantom. In some embodiments, the water phantom comprises: a tank body comprising a base, a first wall (e.g., a radiolucent wall) and a second wall (e.g., a radiolucent wall); a detector positioned within the tank body at a first distance from the first wall and at a second distance from the second wall; and water. In some embodiments, the first wall and / or the second wall comprises poly(methyl methacrylate). In some embodiments, the first wall is at a 90° angle to the second wall. In some embodiments, the detector has a cylindrical shape. In some embodiments, the detector has a first detection surface that is parallel (e.g., substantially and / or effectively parallel) to the first wall and a second detection surface that is parallel (e.g., substantially and / or effectively parallel) to the second wall. In some embodiments, the first distance is 10 cm and the second distance is 20 cm. Thus, in some embodiments, the water phantom can be used to calculate TPR 20,10 In some embodiments, TPR 20,10 For a field size of 10 cm × 10 cm and a source-chamber distance of 100 cm, at 20 and 10 g / cm 2The ratio of the tissue phantom to the water depth is used as a beam quality index. See, for example, "Absorbed Dose Determination in External Beam Radiotherapy: An International Code of Practice for Dosimetry Based on Standards of Absorbed Dose to Water", Technical Reports Series No. 398, International Atomic Energy Agency, Vienna, 2000, incorporated herein by reference, and particularly in Section 6.3.2, Table 12 and / or Figure 6 of this reference.

[0011] In some embodiments, the water phantom further comprises a component (e.g., an interface, a mounting component, etc.) configured to attach the water phantom to the patient support assembly. In some embodiments, the detector is positioned at the rotation axis of the water phantom. In some embodiments, the water phantom further comprises a movable arm operably engaged with the detector.

[0012] In some embodiments, the phantom is a solid phantom. In some embodiments, the solid phantom includes a solid water-equivalent material and the solid phantom includes a first outer surface and a second outer surface; a detector, the detector is positioned within the solid phantom, at a first distance from the first outer surface, and at a second distance from the second outer surface. In some embodiments, the solid phantom includes a hole, and the detector is placed in the hole. In some embodiments, the solid phantom includes a hole and a detector, the hole is positioned at a first distance from the first outer surface and at a second distance from the second outer surface, and the detector is placed in the hole. In some embodiments, the first outer surface is at a 90° angle to the second outer surface. In some embodiments, the detector has a cylindrical shape. In some embodiments, the detector has a first detection surface parallel to (e.g., substantially and / or effectively parallel to) the first outer surface and a second detection surface parallel to (e.g., substantially and / or effectively parallel to) the second outer surface. In some embodiments, the first distance is 10 cm and the second distance is 20 cm. Therefore, in some embodiments, the solid phantom can be used to calculate TPR 20,10 In some embodiments, the solid state phantom further comprises a component (e.g., an interface, a mounting component, etc.) configured to attach the solid state phantom to the patient support assembly. In some embodiments, the detector is positioned at the rotation axis of the solid state phantom. In some embodiments, the solid state phantom further comprises a movable arm operably engaged with the detector.

[0013] In some embodiments, the technology provides a system for measuring radiation dose. In some embodiments, the system includes a phantom (e.g., a water phantom or a solid phantom), the phantom includes a detector, and the system further includes an electrometer, a slip ring, and a computer. In some embodiments, the phantom detector is electrically or electronically connected to the electrometer. In some embodiments, the phantom detector and the electrometer are located on the same side of the slip ring. That is, the embodiment provides that the phantom detector outputs a signal to the electrometer and the signal does not pass through the slip ring between the phantom detector and the electrometer. Therefore, in some embodiments, the phantom detector and the electrometer are directly electrically connected. In some embodiments, the phantom detector is electrically or electronically connected to the electrometer through a cable connecting the detector and the electrometer. In some embodiments, the cable connecting the detector and the electrometer is a triaxial cable. In some embodiments, the electrometer is electrically or electronically connected to a microprocessor (e.g., a computer). In some embodiments, the electrometer outputs a signal, which is transmitted to the microprocessor (e.g., a computer). In some embodiments, the electrometer outputs a signal, which is transmitted to the microprocessor (e.g., a computer) through a slip ring. In some embodiments, the system further includes an analog-to-digital converter that converts the electrical (eg, analog) signal generated by the electrometer into a digital signal for communication with a microprocessor (eg, via a slip ring).

[0014] The technology further provides embodiments of the method. For example, in some embodiments, the technology provides a method for measuring a radiation dose provided by a medical radiation system. In some embodiments, the medical radiation system includes a radiation source (e.g., a static source) and a patient rotation system adapted to rotate about a rotation axis. In some embodiments, the method includes positioning a phantom (e.g., a water phantom or a solid phantom) on a patient support assembly of the patient rotation system. In some embodiments, the water phantom includes a liquid (e.g., water) and a detector immersed in the liquid. In some embodiments, the liquid is water, an aqueous solution, and / or a composition comprising water. In some embodiments, the solid phantom includes a solid water equivalent and the detector is positioned within the solid water equivalent. In some embodiments, the method further includes moving (e.g., rotating) the phantom relative to a radiation beam generated by the radiation source; detecting the radiation beam using a detector; and calculating a radiation dose of the radiation beam. In some embodiments, detecting the radiation beam occurs when the phantom moves (e.g., rotates). In some embodiments, the radiation beam is detected multiple times (e.g., once, twice, three times, four times, five times, six times, seven times, eight times, nine times, ten times, or more than ten times) while the phantom moves (e.g., rotates). In some embodiments, the method includes moving (e.g., rotating) the phantom, stopping the movement (e.g., rotating) of the phantom, and detecting radiation when the phantom is stationary. In some embodiments, the method includes moving (e.g., rotating) the phantom, stopping the movement (e.g., rotating) of the phantom, detecting radiation when the phantom is stationary, and moving (e.g., rotating) the phantom again. In some embodiments, the method includes repeatedly moving (e.g., rotating) the phantom, stopping the movement (e.g., rotating) of the phantom, and detecting radiation when the phantom is stationary multiple times (e.g., once, twice, three times, four times, five times, six times, seven times, eight times, nine times, ten times, or more than ten times).

[0015] For example, in some embodiments, the present technology provides a method for measuring a radiation dose provided by a medical radiation system, the medical radiation system comprising a radiation source (e.g., a static source) and a patient rotation system adapted to rotate about a rotation axis. In some embodiments, the method comprises positioning a phantom (e.g., a water phantom or a solid phantom) on a patient support assembly of the patient rotation system; moving the phantom relative to a radiation beam generated by the radiation source; detecting the radiation beam using a detector; and calculating a radiation dose of the radiation beam. In some embodiments, the phantom is a water phantom, comprising a tank containing a liquid and a detector immersed in the liquid (e.g., water, an aqueous solution, and / or a composition comprising water). In some embodiments, the phantom is a solid phantom, comprising a solid water equivalent material and a detector positioned within the solid phantom (e.g., in a hole provided in the solid phantom). In some embodiments, the phantom is positioned on the patient support assembly so that the rotation axis passes through the phantom. In some embodiments, the phantom is positioned on the patient support assembly such that a side wall or outer surface of the phantom faces the radiation source and the radiation beam passes through the side wall or outer surface. In some embodiments, the side wall or outer surface is orthogonal to the central axis of the radiation beam. In some embodiments, the side wall is transparent to the radiation beam. In some embodiments, the solid phantom comprises a solid water equivalent material that is transparent to the radiation beam.

[0016] In some embodiments, moving a phantom (e.g., a water phantom or a solid phantom) includes rotating the phantom by rotating a patient rotation system about a rotation axis. In some embodiments, moving the phantom includes translating the phantom by translating a patient support assembly relative to the patient rotation system. In some embodiments, the detector is movable within the phantom.

[0017] In some embodiments, detecting the radiation beam comprises positioning a detector to intercept the radiation beam by moving a phantom (e.g., a water phantom or a solid phantom) and / or moving the detector within the phantom. In some embodiments, detecting the radiation beam comprises detecting the radiation beam at multiple locations within the phantom (e.g., using multiple detectors and / or by moving the detector to multiple locations within the phantom).

[0018] In some embodiments, calculating the radiation dose of the radiation beam includes generating a three-dimensional intensity distribution of the radiation beam within a phantom (eg, a water phantom or a solid phantom).In some embodiments, the detector is positioned on the axis of rotation.

[0019] In some embodiments, the calculated radiation dose is a first radiation dose obtained for a first orientation of a phantom (e.g., a water phantom or a solid phantom), and the method further includes rotating the phantom to a second orientation different from the first orientation by rotating the patient rotation system about a rotation axis; detecting the radiation beam for the second orientation using the detector; calculating a second radiation dose for the radiation beam for the second orientation; and obtaining a tissue phantom ratio by comparing the second radiation dose with the first radiation dose. In some embodiments, the length of a first propagation path of the radiation beam inside the phantom for the first orientation is different from the length of a second propagation path of the radiation beam inside the phantom for the second orientation. In some embodiments, the length of the first propagation path is X cm; the length of the second propagation path is Y cm; and the tissue phantom ratio is TPR X,Y Measured value.

[0020] In some embodiments, X is 1 to 100 cm (e.g., 1, 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 90, 95, or 100 cm). In some embodiments, Y is 1 to 100 cm (e.g., 1, 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 90, 95, or 100 cm). In an exemplary embodiment, the length of the first propagation path is 10 cm (e.g., X); the length of the second propagation path is 20 cm (e.g., Y); and the tissue phantom ratio is TPR 20,10 Measured value.

[0021] In some embodiments, a solid phantom is used. In some embodiments, the solid phantom comprises a material suitable for measuring x-rays having a specific energy to be tested. In some embodiments, the phantom comprises a first hole at a depth of X cm from the outer surface of the phantom. In some embodiments, the phantom comprises a second hole at a depth of Y cm from the outer surface of the phantom. In some embodiments, the depth X of the first hole is 1 to 100 cm (e.g., 1, 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 90, 95, or 100 cm). In some embodiments, the depth Y of the second hole is 1 to 100 cm (e.g., 1, 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 90, 95, or 100 cm). In some embodiments, the solid phantom includes a hole (e.g., a single hole) at a depth of X cm from a first outer surface of the phantom and at a depth of Y cm from a second outer surface of the phantom. In some embodiments, the depth X of the hole from the first outer surface of the phantom is 1 to 100 cm (e.g., 1, 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 90, 95, or 100 cm), and the depth Y of the hole from the second outer surface of the phantom is 1 to 100 cm (e.g., 1, 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 90, 95, or 100 cm). In an exemplary embodiment, the solid phantom comprises a first hole at a depth of 10 cm from an outer surface of the phantom and / or a second hole at a depth of 20 cm from an outer surface of the phantom. In an exemplary embodiment, the solid phantom comprises a first hole at a depth of 10 cm from a first outer surface of the phantom and / or a second hole at a depth of 20 cm from a second outer surface of the phantom.

[0022] In some embodiments, holes are drilled to provide a correction chamber disturbance for the fluence. In some embodiments, holes are drilled by taking into account a priori corrections. As described herein, in exemplary embodiments, a solid phantom comprising one or more holes (e.g., each at a depth of 1 to 100 cm (e.g., 10 cm and / or 20 cm) from the first and / or second outer surface) can be rotated into place without worrying about liquid inertial forces causing the device material to sway.

[0023] In some embodiments, the length of one or more propagation paths and / or the depth of one or more holes can be varied from the nominal X and Y values ​​described herein (e.g., approximately ±10% (e.g., ±1% to 10% (e.g., ±1%, 2%, 3%, 4%, 5%, 6%, 7%, 8%, 9%, or 10%))), for example, to account for effective measurement points of the detector. Thus, in some embodiments, the technology provides a method comprising placing a phantom at a position relative to a detector that provides one or more effective measurement points at X and Y distances. In some embodiments, the technology provides a system comprising a phantom positioned at a position relative to a detector that provides one or more effective measurement points at X and Y distances.

[0024] In some embodiments, the technique uses a detector that provides a substantially symmetric response for measurements of the phantom in a first orientation and a second orientation. In some embodiments, a correction factor is determined for measurements made with the phantom in the first orientation of the phantom and for measurements made with the phantom in the second orientation.

[0025] In some embodiments, a first side wall or outer surface of a phantom (e.g., a water phantom or a solid phantom) facing the radiation source in a first orientation is orthogonal to the central axis of the radiation beam. In some embodiments, a second side wall or outer surface of the phantom facing the radiation source in a second orientation is orthogonal to the central axis of the radiation beam. In some embodiments, the radiation source is an imaging radiation source or a therapeutic radiation source.

[0026] In some embodiments, the axis of rotation is perpendicular to the radiation beam (eg, a central axis of the radiation beam). In some embodiments, the axis of rotation is a vertical axis.

[0027] In some embodiments, a phantom (e.g., a water phantom or a solid phantom) is securely attached to a patient support assembly. In some embodiments, the patient support assembly includes an interface for attaching the phantom at a fixed position on the patient support assembly. In some embodiments, the phantom is mounted to a seat member of a patient support assembly. In some embodiments, the phantom is mounted to an armrest of a patient support assembly. In some embodiments, the phantom is positioned on a horizontal surface of the patient support assembly. In some embodiments, the phantom is horizontally disposed on the patient support assembly such that a central axis of the radiation beam is parallel (e.g., substantially and / or effectively parallel) to a base of the phantom.

[0028] Additional embodiments of the present technology relate to systems. For example, in some embodiments, the present technology provides a system comprising a medical radiation system; a phantom (e.g., a water phantom or a solid phantom), the phantom comprising a base, a first wall (e.g., a radiolucent wall) or a first outer surface, and a second wall (e.g., a radiolucent wall) or a second outer surface; a detector, the detector being positioned within the phantom at a first distance from the first wall or the first outer surface, and positioned at a second distance from the second wall or the second outer surface. In some embodiments, the phantom is a water phantom, which comprises a tank (e.g., comprising a base, a first wall, and a second wall) and a liquid (e.g., water, an aqueous solution, and / or a composition comprising water). In some embodiments, the phantom is a solid phantom (e.g., comprising a solid water equivalent material, the solid water equivalent material comprising a base, a first outer surface, and a second outer surface). In some embodiments, the solid phantom comprises a plurality of holes. In some embodiments, the solid phantom comprises a detector placed within the hole. In some embodiments, a solid phantom includes a plurality of holes and a plurality of detectors, wherein each of the plurality of detectors is positioned in a hole.

[0029] In some embodiments, the system further comprises a source (eg, a static source). In some embodiments, the system further comprises a beam (eg, a beam generated by a source).

[0030] In some embodiments, the system further comprises a patient support assembly. In some embodiments, the patient support assembly comprises an interface configured to receive a phantom. In some embodiments, the patient support assembly is configured to operably engage the phantom. In some embodiments, the patient support assembly is configured to move the phantom. In some embodiments, the patient support assembly is configured to rotate the phantom.

[0031] In some embodiments, the system includes a phantom (e.g., a water phantom or a solid phantom), the phantom including a detector, and the system further includes an electrometer, a slip ring, and a computer. In some embodiments, the detector is electrically or electronically connected to the electrometer. In some embodiments, the detector is electrically or electronically connected to the electrometer via a cable connecting the detector and the electrometer. In some embodiments, the cable connecting the detector and the electrometer is a triaxial cable. In some embodiments, the electrometer is electrically or electronically connected to a microprocessor (e.g., a computer). In some embodiments, the electrometer outputs a signal that is transmitted to the microprocessor (e.g., a computer). In some embodiments, the electrometer outputs a signal that is transmitted to the microprocessor (e.g., a computer) via a slip ring. In some embodiments, the system further includes an analog-to-digital converter that converts an electrical (e.g., analog) signal generated by the electrometer into a digital signal for use in communicating with the microprocessor (e.g., via a slip ring).

[0032] Thus, in some embodiments, the system is a phantom system, comprising a phantom, the phantom comprising a detector; a slip ring; a microprocessor; and an electrometer, the electrometer being in electronic or electrical communication with the detector via a cable, and in electronic or electrical communication with the microprocessor via the slip ring. In some embodiments, the phantom is a water phantom. In some embodiments, the phantom is a solid-state phantom. In some embodiments, the cable is a triaxial cable. In some embodiments, the computer comprises an electrometer. In some embodiments, the phantom system further comprises an analog-to-digital converter in electrical communication with the electrometer. In some embodiments, the phantom system comprises a rotating subsystem, the rotating subsystem comprising a phantom and an electrometer. In some embodiments, the phantom system comprises a non-rotating subsystem, the non-rotating subsystem comprising a microprocessor.

[0033] In some embodiments, the present technology relates to a method of measuring a radiation dose provided by a medical radiation system including a patient rotation system and a radiation source, the patient rotation system being adapted to rotate about a rotation axis. For example, in some embodiments, the method includes positioning a phantom of a phantom system on a patient support assembly of the patient rotation system; moving the phantom relative to a radiation beam generated by the radiation source; detecting the radiation beam using a detector; generating an electrical signal characterizing the radiation beam by an electrometer; transmitting the electrical signal from the electrometer to a microprocessor through a slip ring; and calculating a radiation dose of the radiation beam using the signal. In some embodiments, the phantom is positioned on the patient support assembly so that the rotation axis passes through the phantom. In some embodiments, moving the phantom includes rotating the phantom by rotating the patient rotation system about the rotation axis. In some embodiments, detecting the radiation beam includes detecting the radiation beam at a plurality of locations within the phantom. In some embodiments, calculating the radiation dose of the radiation beam includes generating a three-dimensional intensity distribution of the radiation beam within the phantom. In some embodiments, the detector is positioned in line with the rotation axis.

[0034] In some embodiments, the calculated radiation dose is a first radiation dose obtained for a first orientation of the phantom, and the method further includes rotating the phantom to a second orientation different from the first orientation by rotating the patient rotation system about a rotation axis; detecting the radiation beam for the second orientation using the detector; generating a second electrical signal characterizing the radiation beam for the second orientation through the electrometer; transmitting the second electrical signal from the electrometer to the microprocessor through the slip ring; calculating a second radiation dose for the radiation beam for the second orientation; and obtaining a tissue phantom ratio by comparing the second radiation dose with the first radiation dose. In some embodiments, the length of a first propagation path of the radiation beam inside the phantom for the first orientation is different from the length of a second propagation path of the radiation beam inside the phantom for the second orientation. In some embodiments, the length of the first propagation path is X cm; the length of the second propagation path is Y cm; and the tissue phantom ratio is TPR X,Y Measurement values. In some embodiments, X is 1 to 100 cm (e.g., 1, 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 90, 95, or 100 cm). In some embodiments, Y is 1 to 100 cm (e.g., 1, 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 90, 95, or 100 cm). In an exemplary embodiment, the length of the first propagation path is 10 cm (e.g., X); the length of the second propagation path is 20 cm (e.g., Y); and the tissue phantom ratio is TPR 20,10 Measured value.

[0035] In some embodiments, the present technology relates to a method for measuring one or more radiation dose characteristics (e.g., radiation dose flux, cumulative radiation dose, radiation dose symmetry, radiation dose distribution shape, radiation dose penumbra, radiation dose spread) provided by a medical radiation system, the medical radiation system comprising a patient rotation system and a radiation source, the patient rotation system being adapted to rotate about a rotation axis. In some embodiments, measuring one or more radiation dose characteristics (e.g., radiation dose flux, cumulative radiation dose, radiation dose symmetry, radiation dose distribution shape, radiation dose penumbra, and / or radiation dose spread) comprises positioning a phantom of a phantom system on a patient support assembly of the patient rotation system; moving the phantom relative to a radiation beam generated by the radiation source; detecting the radiation beam using a detector; generating an electrical signal characterizing the radiation beam by an electrometer; transmitting the electrical signal from the electrometer to a microprocessor via a slip ring; and calculating one or more radiation dose characteristics (e.g., radiation dose flux, cumulative radiation dose, radiation dose symmetry, radiation dose distribution shape, radiation dose penumbra, radiation dose spread) of the radiation beam using the signal. In some embodiments, the phantom is positioned on the patient support assembly so that the axis of rotation passes through the phantom. In some embodiments, moving the phantom includes rotating the phantom by rotating the patient rotation system about the axis of rotation. In some embodiments, detecting the radiation beam includes detecting the radiation beam at multiple locations within the phantom. In some embodiments, calculating one or more radiation dose characteristics of the radiation beam includes generating a three-dimensional intensity distribution of the radiation beam within the phantom. In some embodiments, the detector is positioned in line with the axis of rotation.

[0036] In some embodiments, the one or more radiation dose characteristics are first radiation dose characteristics obtained for a first orientation of the phantom, and the method further includes rotating the phantom to a second orientation different from the first orientation by rotating the patient rotation system about a rotation axis; detecting the radiation beam for the second orientation using the detector; generating a second electrical signal characterizing the radiation beam for the second orientation through the electrometer; transmitting the second electrical signal from the electrometer to the microprocessor through the slip ring; calculating a second radiation dose characteristic (e.g., radiation dose flux, cumulative radiation dose, radiation dose symmetry, radiation dose distribution shape, radiation dose penumbra, radiation dose spread) for the radiation beam for the second orientation; and comparing the second radiation dose characteristic with the first radiation dose characteristic. In some embodiments, the second radiation dose characteristic is compared with the first radiation dose characteristic to provide a tissue phantom ratio. In some embodiments, the length of the first propagation path is X cm; and the length of the second propagation path is Y cm. In some embodiments, the tissue phantom ratio is TPR X,YIn some embodiments, X is 1 to 100 cm (e.g., 1, 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 90, 95, or 100 cm). In some embodiments, Y is 1 to 100 cm (e.g., 1, 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 90, 95, or 100 cm). In an exemplary embodiment, the length of the first propagation path is 10 cm (e.g., X); and the length of the second propagation path is 20 cm (e.g., Y). In some embodiments, the tissue phantom ratio is TPR 20,10 Measured value.

[0037] In some embodiments, a first side wall or outer surface of the phantom facing the radiation source in a first orientation is orthogonal to the central axis of the radiation beam. In some embodiments, a second side wall or outer surface of the phantom facing the radiation source in a second orientation is orthogonal to the central axis of the radiation beam. In some embodiments, the radiation source is one of an imaging radiation source or a therapeutic radiation source. In some embodiments, the axis of rotation is perpendicular to the radiation beam. In some embodiments, the axis of rotation is a vertical axis. In some embodiments, the phantom is securely attached to a patient support assembly. In some embodiments, the patient support assembly includes an interface for attaching the phantom at a fixed position on the patient support assembly. In some embodiments, the phantom is mounted to a seat member of a patient support assembly. In some embodiments, the phantom is mounted to an armrest of a patient support assembly. In some embodiments, the phantom is positioned on a horizontal surface of the patient support assembly. In some embodiments, the phantom is horizontally disposed on the patient support assembly so that the central axis of the radiation beam is parallel to the base of the phantom. In some embodiments, the phantom is a water phantom comprising a tank, water, and a detector. In some embodiments, the phantom is a solid phantom comprising a solid water equivalent material and a detector.

[0038] In some embodiments, the systems described herein further include a software component including instructions for rotating the phantom. In some embodiments, the systems further include a software component including instructions for activating the source to produce the beam. In some embodiments, the systems further include a software component including instructions for receiving data from the detector and using the data to calculate a tissue-to-pseudo ratio. In some embodiments, the tissue-to-pseudo ratio is TPR 20,10. In some embodiments, the first wall and / or the second wall comprises poly(methyl methacrylate). In some embodiments, the first wall is at a 90° angle to the second wall. In some embodiments, the first outer surface is at a 90° angle to the second outer surface. In some embodiments, the detector has a cylindrical shape. In some embodiments, the detector has a first detection surface that is parallel (e.g., substantially and / or effectively parallel) to the first wall or the first outer surface; and a second detection surface that is parallel (e.g., substantially and / or effectively parallel) to the second wall or the second outer surface. In some embodiments, a first distance between the first detection surface of the detector and the first wall or the first outer surface is 10 cm, and a second distance between the second detection surface of the detector and the second wall or the second outer surface is 20 cm.

[0039] In some embodiments, the method includes providing and / or using a correction factor to account for mass attenuation and / or density differences between materials. For example, relative to a density of 1.00 g / cm 3 The density of acrylic material is 1.18g / cm 3 .

[0040] Furthermore, the measurement point for the cylindrical phantom is located on the central axis of the phantom, and, therefore, when measuring the dose at a single point, the central axis is placed at the reference depth. Due to the dominant positive direction of the secondary electrons, the effective measurement point is closer to the source relative to the measurement point. Therefore, the depth-dose curve is shifted toward the source (e.g., to a shallower depth). For both cylindrical and spherical chambers, this shift is 0.6 rcav The photon beam and 0.5 rcav The electron beam is provided by , where rcav is the radius of the ionization chamber cavity.

[0041] Some parts of this specification describe the implementation of the technology in terms of algorithms and symbolic representations of information operations. These algorithmic descriptions and representations are often used by technicians in the field of data processing to effectively convey the essence of their work to other technicians in the field. Although these operations are described functionally, computationally or logically, they should be understood to be implemented by computer programs or equivalent circuits, microcodes, etc. In addition, without loss of generality, it is sometimes convenient to refer to these operational arrangements as modules. The described operations and their associated modules can be embodied in software, firmware, hardware, or any combination thereof.

[0042] Certain steps, operations or processes described herein may be performed or implemented using one or more hardware or software modules, alone or in combination with other devices. In some embodiments, the software module is implemented using a computer program product that includes a computer-readable medium containing computer program code that can be executed by a computer processor to perform any or all of the steps, operations or processes described.

[0043] In some embodiments, the system includes a virtually provided computer and / or data storage (e.g., as a cloud computing resource). In a specific embodiment, the technology includes using cloud computing to provide a virtual computer system that includes components as described herein and / or performs the functions of a computer as described herein. Thus, in some embodiments, cloud computing provides infrastructure, applications, and software as described herein over a network and / or via the Internet. In some embodiments, computing resources (e.g., data analysis, computing, data storage, applications, file storage, etc.) are provided remotely over a network (e.g., the Internet; and / or a cellular network).

[0044] Embodiments of the technology may also relate to an apparatus for performing the operations herein. The apparatus may be specially constructed for the desired purpose and / or it may include a general-purpose computing device that is selectively activated or reconfigured by a computer program stored in a computer. Such a computer program may be stored in a non-transitory, tangible computer-readable storage medium or any type of medium suitable for storing electronic instructions, which may be connected to a computer system bus. In addition, any computing system mentioned in the specification may include a single processor or may be an architecture that employs a multi-processor design to increase computing power.

[0045] Other implementations will be apparent to persons skilled in the relevant arts based on the teachings contained herein. BRIEF DESCRIPTION OF THE DRAWINGS

[0046] The patent or application file contains at least one drawing printed in color. Copies of the patent or patent application publication with one or more color drawing(s) will be provided by the Office upon request and payment of the necessary fee.

[0047] These and other features, aspects and advantages of the present technology will be better understood with reference to the following drawings.

[0048] Figure 1A is a schematic diagram showing a perspective view of an example medical radiation system.

[0049] Figure 1B is a schematic diagram showing a top view of a medical radiation system.

[0050] Figure 1C is a schematic diagram showing a top view of a medical radiation system. A patient is positioned in the beam path.

[0051] Figure 1D is a schematic diagram showing a top view of a medical radiation system comprising two sources. A patient is positioned in the path of a beam generated by one of the two sources.

[0052] Figure 1E is a schematic diagram showing a top view of a medical radiation system comprising two sources. A patient is positioned in the path of a beam generated by one of the two sources.

[0053] Figure 1F is a schematic diagram showing a top view of a medical radiation system. A water phantom is placed in the path of the beam.

[0054] Figure 2 is a block diagram of an example method for measuring radiation dose provided by a medical radiation system.

[0055] Figure 3 is a schematic diagram showing a top view of an example system for performing three-dimensional radiation dose scanning.

[0056] Figure 4A and Figure 4B is a schematic diagram showing a top view of an example system for measuring tissue-to-pseudo ratio (TPR). Figure 4A is a schematic diagram of a phantom for TPR measurement in a first orientation and Figure 4B is a schematic diagram of the phantom in a second orientation.

[0057] Figure 5A and Figure 5B is a schematic diagram of an embodiment of a phantom system including a phantom, an electrometer, and a slip ring.

[0058] It should be understood that the drawings are not necessarily drawn to scale, nor are the objects in the drawings necessarily drawn in proportional relationship to each other. The drawings are intended to make the various embodiments of the devices, systems, and methods disclosed herein clear and understandable. In all drawings, the same reference numerals are used to refer to the same or similar parts as much as possible. In addition, it should be understood that the drawings are not intended to limit the scope of the present teachings in any way. DETAILED DESCRIPTION

[0059] Provided herein are embodiments of technology related to the use of radiation for medical purposes, and particularly, but not exclusively, to devices, systems, and methods for monitoring, testing, and maintaining medical radiation equipment as part of a quality assurance program.

[0060] In the detailed description of various embodiments, for the purpose of explanation, many specific details are set forth to provide a thorough understanding of the disclosed embodiments. However, it will be appreciated by those skilled in the art that these various embodiments may be practiced with or without these specific details. In other cases, structures and devices are shown in block diagram form. In addition, it will be readily appreciated by those skilled in the art that the particular order of presentation and execution methods is illustrative, and it is contemplated that the order may vary and still remain within the spirit and scope of the various embodiments disclosed herein.

[0061] All documents and similar materials cited in this application, including but not limited to patents, patent applications, articles, books, papers and Internet web pages, are expressly incorporated by reference in their entirety for any purpose. Unless otherwise defined, all technical and scientific terms used herein have the same meanings as generally understood by those of ordinary skill in the art to which the various embodiments described herein belong. When the definitions of terms in the incorporated references differ from the definitions provided in this teaching, the definitions provided in this teaching shall prevail. The section headings used herein are for organizational purposes only and should not be construed as limiting the subject matter described in any way.

[0062] definition

[0063] To facilitate understanding of the present technology, various terms and phrases are defined below. Additional definitions are set forth throughout the detailed description.

[0064] Throughout the specification and claims, unless the context clearly dictates otherwise, the following terms have the meanings clearly associated with them herein. As used herein, the phrase "in one embodiment" does not necessarily refer to the same embodiment, although it may refer to the same embodiment. In addition, as used herein, the phrase "in another embodiment" does not necessarily refer to a different embodiment, although it may refer to a different embodiment. Therefore, as described below, various embodiments of the present invention may be easily combined without departing from the scope or spirit of the present invention.

[0065] In addition, as used herein, unless the context clearly dictates otherwise, the term "or" is an inclusive "or" operator and is equivalent to the term "and / or". Unless the context clearly dictates otherwise, the term "based on" is not exclusive and allows for being based on additional factors that are not described. In addition, throughout the specification, the meaning of "a / an" and "the" includes plural references. The meaning of "in..." includes "in..." and "on...".

[0066] As used herein, the terms "about," "approximately," "substantially," and "significantly" are understood by those of ordinary skill in the art and will vary to some extent depending on the context in which they are used. If the use of these terms is not clear to one of ordinary skill in the art considering the context in which they are used, "about" and "approximately" mean plus or minus less than or equal to 10% of the particular term, and "substantially" and "significantly" mean plus or minus greater than 10% of the particular term.

[0067] As used herein, the disclosure of a range includes disclosure of all values ​​within the entire range and further divided ranges (including endpoints and subranges provided for the range). As used herein, the disclosure of a numerical range includes endpoints and each intermediate number with the same degree of accuracy therebetween. For example, for a range of 6-9, in addition to 6 and 9, numerals 7 and 8 are also contemplated, and for a range of 6.0-7.0, numerals 6.0, 6.1, 6.2, 6.3, 6.4, 6.5, 6.6, 6.7, 6.8, 6.9 and 7.0 are clearly contemplated.

[0068] As used herein, the suffix "-without" refers to embodiments of the technology that omit features of the base root of the word to which "-without" is appended. That is, the term "without X" as used herein means "without X," where X is a feature of the technology omitted from the "without X" technology. For example, a "calcium-free" composition does not include calcium, a "no mixing" process does not include a mixing step, etc.

[0069] Although the terms "first", "second", "third", etc. may be used in this article to describe various steps, elements, compositions, components, regions, layers and / or parts, unless otherwise specified, these steps, elements, compositions, components, regions, layers and / or parts should not be limited by these terms. These terms are used to distinguish a step, element, composition, component, region, layer and / or part from another step, element, composition, component, region, layer and / or part. Unless the context clearly indicates, the terms such as "first", "second" and other numerical terms used herein do not imply a sequence or order. Therefore, without departing from the technology, the first step, element, composition, component, region, layer or part discussed herein may be referred to as a second step, element, composition, component, region, layer or part.

[0070] As used herein, the words "presence" or "absence" (or alternatively, "existing" or "absent") are used in a relative sense to describe the amount or level of a particular entity (e.g., a component, function, element). For example, when an entity is referred to as being "present," it means that the level or amount of the entity is above a predetermined threshold; conversely, when an entity is referred to as being "absent," it means that the level or amount of the entity is below a predetermined threshold. The predetermined threshold may be a detectability threshold or any other threshold associated with a particular test for detecting the entity. When an entity is "detected," it is "present"; when an entity is "not detected," it is "absent."

[0071] As used herein, "increase" or "decrease" refers to a detectable (e.g., measured) positive or negative change in the value of a variable relative to a previously measured variable value, relative to a predetermined value, and / or relative to a standard control value, respectively. An increase is a positive change relative to a previously measured variable value, a predetermined value, and / or a standard control value of preferably at least 10%, more preferably 50%, still more preferably 2 times, even more preferably at least 5 times, and most preferably at least 10 times. Similarly, a decrease is a negative change of a previously measured variable value, a predetermined value, and / or a standard control value of preferably at least 10%, more preferably 50%, still more preferably at least 80%, and most preferably at least 90%. Other terms indicating a quantitative change or difference, such as "more" or "less", are used in the same manner as described above herein.

[0072] As used herein, "system" refers to a plurality of real and / or abstract components that operate together for a common purpose. In some embodiments, a "system" is an integrated assembly of hardware and / or software components. In some embodiments, each component of the system interacts with and / or is related to one or more other components. In some embodiments, a system refers to a combination of components and software used to control and guide methods. For example, a "system" or "subsystem" may include one or more or any combination of the following: mechanical devices, hardware, components of hardware, circuits, lines, logical designs, logical components, software, software modules, components of software or software modules, software processes, software instructions, software routines, software objects, software functions, software classes, software programs, files containing software, etc., to perform the functions of the system or subsystem. Therefore, the methods and devices of the embodiments, or some aspects or portions thereof, may take the form of program codes (e.g., instructions) embodied in tangible media such as floppy disks, CD-ROMs, hard drives, flash memory, or any other machine-readable storage medium, wherein when the program code is loaded into and executed by a machine such as a computer, the machine becomes a device for practicing the embodiments. In the case where the program code is executed on a programmable computer, the computing device generally includes a processor, a storage medium readable by the processor (e.g., volatile and non-volatile memory and / or storage element), at least one input device, and at least one output device. One or more programs can implement or utilize the process described in conjunction with the embodiment, for example, by using an application program interface (API), reusable controls, etc. Such programs are preferably implemented in a high-level process or object-oriented programming language to communicate with the computer system. However, if necessary, one or more programs can be implemented in assembly language or machine language. In any case, the language can be a compiled or interpreted language and combined with a hardware implementation.

[0073] As used herein, the term "computed tomography" is abbreviated as "CT" and refers to both tomographic and non-tomographic radiography. For example, the term "CT" refers to various forms of CT, including but not limited to x-ray CT, positron emission tomography (PET), single photon emission computed tomography (SPECT), and photon counting computed tomography. In general, computed tomography (CT) includes the use of an x-ray source and an x-ray detector panel that rotates around a patient and then reconstructs the image into different planes. In embodiments of CT described herein (e.g., devices, apparatus, methods, and systems provided for CT), the x-ray source is a static source and the patient rotates relative to the static source. The x-ray current used in CT describes the current flow from the cathode to the anode and is typically measured in milliamperes (mA).

[0074] As used herein, the term "constructed to [verb]" means that the identified element or assembly has a structure that is shaped, sized, arranged, connected, and / or configured to perform the identified verb. For example, a member that is "constructed to move" is movably connected to another element and includes an element that causes the member to move, or the member is otherwise configured to move in response to other elements or assemblies. Therefore, as used herein, "constructed to [verb]" describes structure rather than function. In addition, as used herein, "constructed to [verb]" means that the identified element or assembly is intended and designed to perform the identified verb.

[0075] As used herein, the term "associated" means that the elements are part of the same assembly and / or function together or interact with each other / with each other in some manner. For example, a car has four tires and four hubcaps. Although all elements are connected as part of the car, it is understood that each hubcap is "associated" with a specific tire.

[0076] As used herein, the term "coupled" refers to two or more parts that are fixed together by any suitable means. Therefore, in some embodiments, the expression that two or more parts or components are "coupled" should mean that these parts are directly or indirectly connected or operated together, such as through one or more intermediate parts or components. As used herein, "directly coupled" means that two elements are directly in contact with each other. As used herein, "fixed coupling" or "fixed" means that two parts are coupled so as to move as a whole while maintaining a constant orientation relative to each other. Therefore, when two elements are coupled, all parts of these elements are coupled. However, when describing that a specific part of a first element is coupled to a second element, for example, the first end of an axle is coupled to a first wheel, it means that a specific part of the first element is arranged closer to the second element than the other parts thereof. In addition, unless the upper object is otherwise substantially maintained in place, an object resting on another object that is held in place only by gravity will not be "coupled" to the lower object. That is, for example, a book on a table is not coupled to it, but a book glued to the table is coupled to it.

[0077] As used herein, the term "removably coupled" or "temporarily coupled" means that one component is coupled to another component in a substantially temporary manner. That is, the two components are coupled in a manner that connection or separation of the components is easy and does not damage the components. Thus, "removably coupled" components are easily uncoupled and recoupled without causing damage to the components.

[0078] As used herein, the term "operably coupled" means that a plurality of elements or components are coupled so that when a first element is moved from one position / configuration to another position, a second element also moves between positions / configurations, wherein each of the plurality of elements or components is movable between the first position and the second position, or between the first configuration and the second configuration. It is noteworthy that a first element is "operably coupled" to another element and vice versa.

[0079] As used herein, the term "rotatably coupled" refers to two or more components being coupled in a manner such that at least one component is able to rotate relative to another component.

[0080] As used herein, the term "translatably coupled" refers to two or more components being coupled in a manner such that at least one component is capable of translation relative to another component.

[0081] As used herein, the term "temporarily disposed" means that a first element or component is placed on a second element or component in a manner that allows the first element / component to be moved without decoupling or otherwise manipulating the first element. For example, a book is simply placed on a table, e.g., the book is not glued or fastened to the table, but is "temporarily disposed" on the table.

[0082] As used herein, the term "corresponding" means that the size and shape of two structural components are similar to each other and are coupled with a minimum amount of friction. Therefore, the size of the opening that "corresponds" to a component is slightly larger than the component, so that the component can pass through the opening with a minimum amount of friction. If two components fit together "tightly", this definition can be modified. In this case, the difference between the sizes of the components is even smaller, so that the amount of friction increases. If the elements defining the opening and / or the components inserted into the opening are made of deformable or compressible materials, the opening can even be slightly smaller than the components inserted into the opening. With respect to surfaces, shapes and lines, two or more "corresponding" surfaces, shapes or lines generally have the same size, shape and profile.

[0083] As used herein, a "path of travel" or "path" when used in connection with a moving element includes the space through which the element moves when in motion. Thus, an inherently moving element has a "path of travel" or "path."

[0084] As used herein, the statement that two or more parts or components "engage" one another shall mean that the elements apply a force or bias to one another, either directly or through one or more intermediate elements or components. In addition, as used herein with respect to a moving part, the moving part may "engage" another element during movement from one position to another and / or may "engage" another element once in the described position. Therefore, it should be understood that the statements "when element A moves to the element A first position, element A engages element B" and "when element A is in the element A first position, element A engages element B" are equivalent statements and mean that element A either engages element B when moving to the element A first position and / or element A engages element B when it is in the element A first position.

[0085] As used herein, the term "operably engaged" means "engage and move." That is, when used relative to a first component that is configured to move a movable or rotatable second component, "operably engaged" means that the first component applies a force sufficient to cause the second component to move. For example, a screwdriver is placed in contact with a screw. When no force is applied to the screwdriver, the screwdriver is simply "coupled" to the screw. If an axial force is applied to the screwdriver, the screwdriver presses on the screw and "engages" the screw. However, when a rotational force is applied to the screwdriver, the screwdriver "operably engages" the screw and causes the screw to rotate. In addition, for electronic components, "operably engaged" means that one component controls another component by controlling a signal or current.

[0086] As used herein, the term "number" shall mean one or an integer greater than one (eg, a plurality).

[0087] As used herein, in the phrases “[x] moves between its first position and the second position” or “[y] is configured to move [x] between its first position and the second position”, “[x]” is the name of an element or component. In addition, when [x] is an element or component that moves between multiple positions, the pronoun “its” means “[x]”, i.e., the named element or component preceding the pronoun “its”.

[0088] As used herein, a "radial side / surface" of a circular or cylindrical body is a side / surface extending around or around a height line through its center or through its center. As used herein, an "axial side / surface" of a circular or cylindrical body is a side extending in a plane extending generally perpendicular to a height line through the center. That is, generally speaking, for a cylindrical soup can, a "radial side / surface" is the generally circular sidewall, and the "one or more axial sides / surfaces" are the top and bottom of the soup can.

[0089] As used herein, "diagnostic" tests include detecting or identifying a disease state or condition in a subject, determining the likelihood that a subject is infected with a given disease or condition, determining the likelihood that a subject with a disease or condition will respond to a treatment, determining the prognosis (or its likely progression or regression) of a subject with a disease or condition, and determining the effect of a treatment on a subject with a disease or condition. For example, diagnostics can be used to detect the presence or likelihood that a subject has cancer, or the likelihood that such a subject will respond favorably to a compound (e.g., a drug, such as a pharmaceutical) or other treatment.

[0090] As used herein, the term "disorder" generally refers to a disease, condition, injury, event, or change in health status.

[0091] As used herein, the term "treating" or "treatment" with respect to a condition refers to preventing the condition, slowing the onset or rate of development of the condition, reducing the risk of developing the condition, preventing or delaying the development of symptoms associated with the condition, reducing or ending symptoms associated with the condition, producing complete or partial regression of the condition, or some combination thereof. In some embodiments, "treatment" includes exposing a patient or a portion thereof (e.g., a tissue, organ, body part, or other local area of ​​the patient's body) to radiation (e.g., electromagnetic radiation, ionizing radiation).

[0092] As used herein, the term "beam" refers to a stream of radiation (e.g., electromagnetic waves and / or particle radiation). In some embodiments, the beam is generated by a source and is confined to a small solid angle. In some embodiments, the beam is collimated. In some embodiments, the beam is generally unidirectional. In some embodiments, the beam is divergent.

[0093] As used herein, the term "patient" or "subject" refers to a mammal that is identified and / or selected for imaging and / or treatment with radiation. Thus, in some embodiments, the patient or subject is exposed to a beam of radiation, such as a primary beam generated by a radiation source. In some embodiments, the patient or subject is a human. In some embodiments, the patient or subject is a veterinary or farm animal, livestock or pet, or an animal used in clinical research. In some embodiments, the subject or patient has cancer and / or the subject or patient has been identified as having cancer or at risk of developing cancer.

[0094] As used herein, the term "treatment volume" or "imaging volume" refers to a volume (e.g., tissue) of a patient that is selected for imaging and / or treatment with radiation. For example, in some embodiments, the "treatment volume" or "imaging volume" includes a tumor in a cancer patient. As used herein, the term "healthy tissue" refers to a volume (e.g., tissue) of a patient that is not and / or does not include the treatment volume. In some embodiments, the imaging volume is larger than the treatment volume and includes the treatment volume.

[0095] As used herein, the term "radiation source" or "source" refers to a device that produces radiation (e.g., ionizing radiation) in the form of photons (e.g., described as particles or waves). In some embodiments, the radiation source is a linear accelerator ("linear accelerator") that produces x-rays or electrons to treat cancer patients by contacting tumors with x-ray or electron beams. In some embodiments, the source produces particles (e.g., photons, electrons, neutrons, hadrons, ions (e.g., protons, carbon ions, other heavy ions)). In some embodiments, the source produces electromagnetic waves (e.g., x-rays and gamma rays with wavelengths ranging from about 1 pm to about 1 nm). Although it is understood that radiation can be described as having wave-particle duality, it is sometimes convenient to refer to radiation with waves and sometimes to refer to radiation with particles. Therefore, without limiting the technology and understanding the laws of quantum mechanics that stipulate that each particle or quantum entity is described as a particle or a wave, both descriptions will be used throughout.

[0096] As used herein, the term "radiation dose" refers to the amount of radiation energy deposited per unit mass provided by a radiation beam generated by a source, and may also refer to the characteristics of the radiation beam providing the radiation. Therefore, as used herein, the term "radiation dose" may be characterized by a plurality of radiation dose characteristics, including but not limited to radiation intensity, radiation spectral intensity, radiation dose flux (e.g., the instantaneous or average rate of radiation intensity as a function of time), cumulative radiation dose (e.g., the integrated amount of radiation provided over a period of time), radiation dose symmetry, radiation dose distribution shape, radiation dose penumbra, and / or radiation dose spread. The term "radiation dose" may also be characterized based on changes in radiation dose characteristics and / or measurement errors associated with the measurement of radiation dose characteristics.

[0097] As used herein, the term "static source" refers to a source that does not rotate around a patient during imaging or treatment using the source. In particular, a "static source" remains fixed relative to an axis passing through the patient while imaging or treating the patient. Although the patient may rotate around the axis to produce a relative motion between the static source and the rotating patient that is equivalent to the relative motion of the source rotating around the static patient, during imaging or treatment, the static source does not move with reference to a third object, a reference system (e.g., a treatment room in which the patient is located), or the patient's rotation axis, although the patient rotates relative to a third object, a reference system (e.g., a treatment room in which the patient is located), or the patient's rotation axis during imaging or treatment. Therefore, the static source is mounted on a mobile platform and when the mobile platform moves to transport the static source, the static source can therefore move relative to the ground and fixed objects on the ground. Therefore, the term "static source" can refer to a mobile "static source" provided that the mobile "static source" does not rotate around the rotation axis passing through the patient during imaging or treatment of the patient. In addition, the static source can translate and / or rotate around the patient to position the static source before or after imaging or treatment of the patient. Thus, the term "static source" can refer to a source that translates or rotates around a patient during non-imaging and non-therapeutic use of the patient, such as positioning the source relative to the patient when the patient is not undergoing imaging and / or therapy. In some embodiments, a "static source" is a photon source and is therefore referred to as a "static photon source." In some embodiments, a "static source" is a particle source and is therefore referred to as a "static particle source."

[0098] As used herein, the term "Z" refers to the atomic number (eg, the atomic number of an element and / or the atomic number of a material comprising an element). As used herein, "Z" of a material refers to the atomic number of one or more elements from which the material is made.

[0099] As used herein, the term "effective atomic number" or "Z eff” refers to the effective atomic number or average atomic number of a compound or material mixture (such as an alloy). eff Can be determined experimentally or estimated from calculations described by: Murty (1965) "Effective Atomic Numbers of Heterogeneous Materials" Nature 207(4995):398–99; Taylor (2008) "The effective atomic number of dosimetric gels" Australasian Physics & Engineering Sciences in Medicine 31(2):131–38; Taylor(2009) “Electron Interaction with Gel Dosimeters: Effective Atomic Numbers for Collisional, Radiative and Total Interaction Processes” Radiation Research 171(1):123–26; Taylor(2011) “Robust determination of effective atomic numbers forelectron interactions with TLD-100and TLD-100H thermoluminescent dosimeters" Nuclear Instruments and Methods in Physics Research Section B:BeamInteractions with Materials and Atoms 269(8):770–73; and Taylor (2012) “Robustcalculation of effective atomic numbers: The Auto-Z eff software” Medical Physics 39(4):1769–78, each of which is incorporated herein by reference. Auto-Z described by Taylor eff Free software for calculating the Z of a compound or material mixture eff .

[0100] As used herein, the term "solid water equivalent material" refers to a material that has characteristics similar to water in terms of interacting with an x-ray beam and transmitting (e.g., propagating) radiation through the material. In some embodiments, the "solid water equivalent material" is a plastic. In some embodiments, the solid water equivalent material has a density of approximately 0.90 to 1.20 g / cm 31.14, 1.15, 1.16, 1.17, 1.18, 1.19, or 1.20. In some embodiments, the solid water equivalent material has an average atomic number of 5.20 to 6.70 (e.g., 5.20, 5.21, 5.22, 5.23, 5.24, 5.25, 5.26, 5.27, 5.28, 5.29, 5.30, 5.31, 5.32, 5.33, 5.34, 5.35, 5.36, 5.37, 5.38, 5.39, 5.40, 5.41, 5.42, 5.43, 5.44, 5.45, 5.46, 5.47, 5.48, 5.49, 5.50, 5.51 , 5.52, 5.53, 5.54, 5.55, 5.56, 5.57, 5.58, 5.59, 5.60, 5.61, 5.62, 5.63, 5.64, 5.65, 5.66, 5.67, 5.68, 5.69, 5.70, 5.71, 5.72, 5.73, 5.74, 5.75, 5.76, 5.77, 5.78, 5.79, 5.80, 5.81, 5.82, 5.83, 5.84, 5.85, 5.86, 5.87, 5.88, 5.89, 5.90, 5.91 1, 5.92, 5.93, 5.94, 5.95, 5.96, 5.97, 5.98, 5.99, 6.00, 6.01, 6.02, 6.03, 6.04, 6.05, 6.06, 6.07, 6.08, 6.09, 6.10, 6.11, 6.12, 6.13, 6.14, 6.15, 6.16, 6.17, 6.18, 6.19, 6.20, 6.21, 6.22, 6.23, 6.24, 6.25, 6.26, 6.27, 6.28, 6.29, 6.30, 6. 6.54, 6.55, 6.56, 6.57, 6.58, 6.59, 6.60, 6.61, 6.62, 6.63, 6.64, 6.65, 6.66, 6.67, 6.68, 6.69, or 6.70).See, for example, Section 4.2.3 and Table 6 of "Absorbed Dose Determination in External Beam Radiotherapy: An International Code of Practice for Dosimetry Based on Standards of Absorbed Dose to Water", Technical Reports Series No. 398, International Atomic Energy Agency, Vienna, 2000, which is incorporated herein by reference. Without limitation, exemplary materials that are solid water equivalent materials are, for example, polystyrene and poly (methyl methacrylate). The characteristics of "solid water WT1", "solid water RMI-457", "plastic water" and "virtual water" are provided in Table 6 of "Absorbed Dose Determination in External Beam Radiotherapy: An International Code of Practice for Dosimetry Based on Standards of Absorbed Dose to Water", Technical Reports Series No. 398, International Atomic Energy Agency, Vienna, 2000, which is incorporated herein by reference. See also "Tissue Substitutes in Radiation Dosimetry and Measurement" (1989) INTERNATIONAL COMMISSION ON RADIATION UNITS AND MEASUREMENTS, Rep. 44, ICRU, Bethesda, Maryland; and Agostinelli (1992) "A new water-equivalent plastic for dosimetry calibration" Med. Phys. 19:774, each of which is incorporated herein by reference.

[0101] As used herein, the term "attenuation coefficient" or "linear attenuation coefficient" refers to a measure of the extent to which the radiant flux of a beam is reduced when the beam passes through a particular material, for example due to absorption and / or scattering. A "mass attenuation coefficient" of a material may be used, where the attenuation coefficient is normalized to the per unit density of the material, thereby providing a constant value for a given element or compound.

[0102] As used herein, the term "radio-lucent" refers to a material that would not interfere (e.g., would not substantially and / or would not effectively interfere) with the measurement if the material were replaced by another material (e.g., air or water) that was also in the beam. For example, air is radio-lucent compared to a vacuum, and acrylic is radio-lucent as a water wall because the measurement would be the same if the acrylic was replaced with water because the buildup and attenuation of the acrylic wall is not different enough from water to significantly change the measurement with mass attenuation correction applied.

[0103] As used herein, and when used with respect to transferring data or signals, "in electronic communication" includes both hardwired and wireless forms of communication.

[0104] As used herein, "in electrical communication" means that electrical current passes or is capable of passing between the identified elements. "In electrical communication" further depends on the position or configuration of the elements. For example, in a circuit breaker, a movable contact is "in electrical communication" with a fixed contact when the contacts are in a closed position. The same movable contact is not "in electrical communication" with a fixed contact when the contacts are in an open position. The term "in direct electrical communication" means that two elements are in electrical communication with each other without any intermediate elements other than a wire, cable, or other conductor connecting the two elements.

[0105] The term "computer" as used herein generally includes a plurality of electrical and electronic components that provide power, operational control, and protection to the components and modules within the system. For example, a computer may include, among other things, a processing unit (e.g., a microprocessor, a microcontroller, or other suitable programmable device), a memory, an input unit, and an output unit. The processing unit may include, among other things, a control unit, an arithmetic logic unit ("ALC"), and a plurality of registers, and may be implemented using known computer architectures (e.g., a modified Harvard architecture, a von Neumann architecture, etc.). "Microprocessor" or "processor" refers to one or more microprocessors that may be configured to communicate in an independent and / or distributed environment, and may be configured to communicate with other processors via wired or wireless communications, wherein such one or more processors may be configured to run on one or more processor-controlled devices, which may be similar or different devices.

[0106] The term "memory" as used herein generally refers to any memory storage of a computer and is a non-transitory computer-readable medium. The memory may include, for example, a program storage area and a data storage area. The program storage area and the data storage area may include a combination of different types of memory, such as ROM, RAM (e.g., DRAM, SDRAM, etc.), EEPROM, flash memory, hard disk, SD card, or other suitable magnetic, optical, physical or electronic memory devices. The processing unit may be connected to the memory and execute software instructions that can be stored in the following: RAM of the memory (e.g., during execution), ROM of the memory (e.g., on a generally permanent basis), or another non-transitory computer-readable medium such as another memory or disk. "Memory" may include one or more processor-readable and accessible memory elements and / or components, which may be inside a processor-controlled device, outside a processor-controlled device, and may be accessed via a wired or wireless network. The software included in the implementation of the method disclosed herein may be stored in the memory. The software includes, for example, firmware, one or more applications, program data, filters, rules, one or more program modules, and other executable instructions. For example, a computer may be configured to retrieve and execute instructions related to the processes and methods described herein, among other things, from the memory.

[0107] Medical Radiation Systems

[0108] In some embodiments, the technology involves aligning components of a medical radiation system. In some embodiments, for example, Figures 1A to 1F As shown, the technology relates to a medical radiation system 100. In some embodiments, the medical radiation system 100 includes a patient rotation system 110 configured to rotate about a rotation axis. In some embodiments, the patient rotation system 110 includes a patient positioning system (e.g., including a patient positioning device or a configurable patient support assembly 120) mounted on a base 130. The base 130 is configured to rotate about an axis 131 of the base 130. In some embodiments, the base 130 is configured to rotate about a vertical symmetry axis of the base 130. In some embodiments, the patient positioning system, the patient positioning device, and / or the configurable patient support 120 are described in U.S. Patent Application Publication No. 20200268327 and U.S. Patent Application Serial No. 63 / 237,513, each of which is incorporated herein by reference.

[0109] The patient support assembly 120 is configured to support the patient 140 in an upright (e.g., standing, sitting, kneeling, perching) position during radiation therapy or imaging. Thus, embodiments provide that the configurable patient support assembly 120 is adjustable to support the patient 140 in an upright (e.g., standing, sitting, kneeling, perching) position or any other position in which the torso of the patient 140 is in a generally vertical or upright position (e.g., semi-standing position, crouching position). In some embodiments, the patient support assembly 120 includes support members such as a seat, backrest, headrest, armrest, shin rest, heel stop, foot support, and / or footrest to assist in supporting and / or securing the patient 140 in a given position. In some embodiments, for example, as described in U.S. patent application Ser. No. 63 / 237,513, which is incorporated herein by reference, the configurable patient support assembly 120 includes one or more configurable and movable components, such as a backrest (e.g., a configurable and movable backrest), a headrest (e.g., a configurable and movable headrest), an armrest (e.g., a configurable and movable armrest), a seat member (e.g., a configurable and movable seat member), a tibia support (e.g., a configurable and movable tibia support), a heel stop (e.g., a configurable and movable heel stop), and / or a foot support (e.g., a configurable and movable foot support). In some embodiments, one or more configurable and movable components of the configurable patient support include one or more powered components, such as, for example, a powered backrest (e.g., a backrest operably engaged with a backrest motor), a powered headrest (e.g., a headrest operably engaged with a headrest motor), a powered armrest (e.g., an armrest operably engaged with an armrest motor), a powered seat member (e.g., a seat member operably engaged with a seat member motor), a powered tibia support (e.g., a tibia support operably engaged with a tibia support motor), a powered heel stop (e.g., a heel stop operably engaged with a heel stop motor), and / or a powered foot support (e.g., a powered foot support operably engaged with a foot support motor). In some embodiments, the backrest motor is configured to move (e.g., translate and / or rotate) the backrest, the headrest motor is configured to move (e.g., translate and / or rotate) the headrest, the armrest motor is configured to move (e.g., translate and / or rotate) the armrest, the seat member motor is configured to move (e.g., translate and / or rotate) the seat member, the shin support motor is configured to move (e.g., translate and / or rotate) the shin support, the heel stop motor is configured to move (e.g., translate and / or rotate) the heel stop, and / or the foot support motor is configured to move (e.g., translate and / or rotate) the foot support. In some embodiments, the technology provides a configurable patient support 120 that is configured in a static configuration.In some embodiments, the technology provides a configurable patient support 120 that is configured to be dynamically configured (e.g., a configuration that moves to assist in patient movement, such as for patient entry and / or for patient exit). See, U.S. Patent Application Serial No. 63 / 237,513, which is incorporated herein by reference.

[0110] In some embodiments, the patient support assembly 120 is operably coupled to the base 130 such that the patient support assembly 120 rotates with the base 130 (e.g., about the axis 131). However, the patient support assembly 120 can be adjustably mounted to the base 130 to adjust the position and / or orientation of the patient support assembly 120 relative to the base 130. In some embodiments, the patient support assembly 120 is configured to move with six degrees of freedom, allowing translation in three vertical axes (e.g., two axes in the horizontal plane and a vertical axis) and rotation about three vertical axes (e.g., yaw, pitch, and roll). See, U.S. Patent Application Serial No. 63 / 237,513, which is incorporated herein by reference. In some embodiments, the patient support assembly 120 is capable of moving with less than six degrees of freedom.

[0111] In some embodiments, the medical radiation system 100 includes a first radiation source 150 configured to generate a beam 151 of electromagnetic radiation. In some embodiments, the first radiation source 150 is a kilovolt (kV) or megavolt (MV) x-ray radiation source. The first radiation source 150 can be a therapeutic radiation source or an imaging radiation source. In some embodiments, the medical radiation system further includes a second radiation source 152 configured to generate a second beam 153 of electromagnetic radiation. Therefore, in some embodiments, the medical radiation system 100 includes two radiation sources, such as a first radiation source as a therapeutic radiation source and a second radiation source as an imaging radiation source. In some embodiments, the radiation source 150 is a static source, such as a source that is not movable during normal operation (e.g., during radiotherapy). Therefore, the radiation source 150 can be translated, rotated, and / or rotated during a calibration or alignment procedure. In some embodiments, the first radiation source 150 is a static source and / or the second radiation source 152 is a static source. Therefore, the first radiation source 150 and / or the second radiation source 152 can be translated, rotated, and / or rotated during a calibration or alignment procedure.

[0112] In addition, embodiments provide that the radiation beam 151 from the first radiation source 150 is perpendicular to the rotation axis 131 of the base 130 (e.g., after an alignment procedure) and / or the radiation beam 153 from the second radiation source 152 is perpendicular to the rotation axis 131 of the base 130 (e.g., after an alignment procedure). In some embodiments, the radiation sources 150 are oriented so that the radiation beam 151 intersects the rotation axis 131. In some embodiments, the isocenter of the radiation beam intersects the rotation axis 131.

[0113] In some embodiments, the radiation source 150 is configured to direct the radiation beam 151 in the direction of the patient support assembly 120. Thus, when the patient 140 is positioned on the patient support assembly 120, the radiation source 150 is configured to direct the radiation beam 151 in the direction of the patient 140. In some embodiments, the medical radiation system 100 includes a detector 160 (e.g., a detection panel) disposed opposite the radiation source 150 to detect the radiation beam 151 passing through the patient 140. In some embodiments, the detector 160 is an imaging device that generates signals and / or data for generating an image generated by the radiation beam 151. In some embodiments, an additional (e.g., second) detector 162 is associated with a second radiation source 152 of the medical radiation system 100. In some embodiments, for example, as further described herein, the phantom 170 (e.g., a water phantom including a tank, a liquid, and a detector or a solid phantom including a solid water equivalent material (e.g., as Figure 3 -5)) is placed between the radiation source 150 and the detector 160 (e.g., a detection panel). In some embodiments, for example, as further described herein, the phantom 170 (e.g., a water phantom including a tank, a liquid, and a detector or a solid phantom including a solid water equivalent material (e.g., as Figure 3 -5)) is placed between a second radiation source 152 and a second detector 162 (e.g., a detection panel). Those skilled in the art will understand that the medical radiation system includes a detector, and the phantom described herein includes a detector, and the two detectors are different components of the present technology. The detector (e.g., detector 160) of the medical radiation system is placed relative to the source (e.g., radiation source 150), for example so that the detector and source of the medical radiation system are positioned on opposite sides of a patient positioned for imaging and / or treatment with the medical radiation system; and the detector of the phantom is present in a tank of a water phantom or in a solid phantom (e.g., in a hole of a solid phantom), for example so that the detector of the phantom can be placed at or near a medical radiation system location where the patient would otherwise be positioned (e.g., on a patient support assembly).

[0114] Phantom

[0115] The technology relates to a phantom for quality assurance validation of medical radiation systems. In some embodiments, the phantom is a water phantom. In some embodiments, the phantom is a solid phantom. In some embodiments, the water phantom includes a tank and a detector, the tank including water, and the detector is placed in the water. Water can also be simulated with a solid material (e.g., plastic). See, for example, Section 4.2.3 and Table 6 in "Absorbed Dose Determination in External Beam Radiotherapy: An International Code of Practice for Dosimetry Based on Standards of Absorbed Dose to Water", Technical Reports Series No. 398, International Atomic Energy Agency, Vienna, 2000, which is incorporated herein by reference. Therefore, in some embodiments, the phantom is a solid phantom including a solid water equivalent material. In some embodiments, the solid water equivalent material is specific to a specific beam quality or x-ray energy to be tested.

[0116] In some embodiments, the solid-state phantoms described herein provide advantages over phantoms that include a liquid (e.g., liquid water), for example, when measuring radiation dose during acceleration or deceleration of the phantom or at any time during rotation or movement of the liquid (e.g., liquid water), changes in the level of the liquid (e.g., liquid water) may be caused. Thus, in some embodiments, the solid-state phantom can be rotated to any measurement angle without the need to stabilize the phantom material before performing the measurement.

[0117] The technology provided herein relates to embodiments of a phantom that includes liquid water ("water phantom") and embodiments of a phantom that includes a solid water equivalent ("solid phantom").

[0118] In some embodiments, the technology provides a water phantom. In some embodiments, the water phantom includes a tank and a liquid retained within the volume of the tank. In some embodiments, the liquid is water, a composition comprising water, and / or an aqueous solution. In some embodiments, the tank includes a base (e.g., a tank surface that supports the weight of the liquid contained in the tank (e.g., resists the gravity acting on the liquid (e.g., water))) and one or more side walls that define a volume for containing the liquid (e.g., water, a composition comprising water, and / or an aqueous solution). In some embodiments, when viewed from the top, the tank has a polygonal (e.g., quadrilateral (e.g., rectangular)) shape. However, the technology is not limited to tanks having polygonal, quadrilateral, and / or rectangular shapes when viewed from the top. Therefore, embodiments provide tanks having other shapes when viewed from the top, such as "L" shape, cross shape, circular shape, etc.

[0119] In some embodiments, the sidewall of the tank comprises a material that is transparent and / or radiolucent to x-ray radiation. In some embodiments, the sidewall of the tank comprises a material having a low attenuation coefficient (e.g., a radiolucent or "radiolucent" material), such as a low attenuation coefficient relative to other materials in the beam path. In some embodiments, the sidewall of the tank transmits radiation similarly to water, so that the measurement is not disturbed by radiation passing through the sidewall. In some embodiments, the sidewall of the tank comprises a homogeneous material (e.g., a radiolucent or "radiolucent" material) having a low attenuation coefficient or having an attenuation coefficient similar to that of water or a liquid contained in the tank. In some embodiments, the material having a low attenuation coefficient is, for example, poly(methyl methacrylate), which is also known as acrylic glass and is commercially sold under the name PERSPEX.

[0120] In some embodiments, the tank includes a detector. In some embodiments, the detector is completely immersed in the liquid of the tank. In some embodiments, the detector is partially immersed in the liquid of the tank. In some embodiments, the detector is configured to measure the energy, intensity and / or dose of the radiation beam. In some embodiments, the detector is configured to measure one or more other characteristics of the radiation beam (e.g., shape, spectrum, wavelength, flux, photon count, etc.). In some embodiments, the detector includes an ion chamber.

[0121] In some embodiments, the detector is movable within the tank. In some embodiments, the detector is mounted to an adjustable arm fixed to the tank so that the position and / or orientation of the detector can be adjusted using the adjustable arm. In some embodiments, the tank includes more than one detector (e.g., in some embodiments, the tank includes 2, 3, 4, 5, 6, 7, 8 or more detectors). In some embodiments, the tank includes two detectors oriented at right angles to each other, such as when the tank is rotated 90°, the radiation beam is detected by the two detectors. In some embodiments, the tank includes two detectors oriented at 180° to each other, such as when the tank is rotated 180°, the radiation beam is detected by the two detectors. In some embodiments, the detector can be removed from the solid phantom, for example, for calibration, replacement, maintenance and / or repair.

[0122] In some embodiments, the tank includes a single cylindrical detector oriented in a vertical direction along the rotation axis of the tank, for example, so as to present a detection surface at a constant distance from the source (e.g., at a fixed position) along the radiation beam axis at all rotation angles of the tank. In this way, the distance between the radiation source and the detector remains constant when the tank rotates.

[0123] In some embodiments, the detector is movable within the tank, and the tank defines a measurement zone (or measurement volume), for example because the beam characteristics may be measured at one or more locations within the tank.

[0124] In some embodiments, the technology provides a solid phantom. In some embodiments, the solid phantom includes a solid water equivalent material. In some embodiments, the solid water equivalent material is a material described in: "Absorbed Dose Determination in External Beam Radiotherapy: An International Code of Practice for Dosimetry Based on Standards of Absorbed Dose to Water", Technical Reports Series No. 398, International Atomic Energy Agency, Vienna, 2000, incorporated herein by reference, and particularly in Section 4.2.3 and / or Table 6 of that reference.

[0125] In some embodiments, the solid phantom comprises a plurality of holes. In some embodiments, the solid phantom comprises 1 to 10 holes (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, or 10 holes). In some embodiments, holes are precisely machined (e.g., drilled) in the solid water equivalent material to securely hold the detector.

[0126] In some embodiments, the solid phantom includes a base (eg, a surface of the solid phantom that supports the weight of the solid phantom (eg, resists gravity acting on the solid phantom)) and one or more exterior surfaces that define a volume.

[0127] In some embodiments, the solid phantom has a polygonal (e.g., quadrilateral (e.g., rectangular)) shape when viewed from the top. However, the technology is not limited to solid phantoms having polygonal, quadrilateral, and / or rectangular shapes when viewed from the top. Therefore, embodiments provide solid phantoms having other shapes when viewed from the top, such as an "L" shape, a cross shape, a circle, etc.

[0128] In some embodiments, the solid phantom comprises a detector. In some embodiments, the solid phantom comprises a hole, and the hole comprises a detector. In some embodiments, the solid phantom comprises a plurality of holes, and one or more of the plurality of holes comprises a detector. In some embodiments, the solid phantom comprises 1 to 10 holes (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, or 10 holes), and each of the plurality of 1 to 10 holes (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, or 10 holes) comprises a detector. In some embodiments, the detector can be removed from the solid phantom, for example for calibration, replacement, maintenance, and / or repair. In some embodiments, a hole is precisely machined (e.g., drilled) in the solid water equivalent material to securely hold the detector. In some embodiments, the detector is securely fitted into a hole provided (e.g., by precise machining) in the solid water equivalent material of the solid phantom.

[0129] In some embodiments, the detector is configured to measure the energy, intensity, and / or dose of a radiation beam. In some embodiments, the detector is configured to measure one or more other characteristics of a radiation beam (e.g., shape, spectrum, wavelength, flux, photon count, etc.). In some embodiments, the detector comprises an ion chamber.

[0130] In some embodiments, the detector is movable within the solid phantom. In some embodiments, the detector is removable from a first hole in the solid phantom and insertable into a second hole in the solid phantom. In some embodiments, the solid phantom includes more than one detector (e.g., in some embodiments, the solid phantom includes 2, 3, 4, 5, 6, 7, 8, or more detectors). In some embodiments, the solid phantom includes a plurality of detectors and each detector is present in one of the plurality of holes in the solid phantom.

[0131] In some embodiments, the solid-state phantom includes two detectors oriented at right angles to each other, for example, such that the radiation beam is detected by the two detectors when the solid-state phantom is rotated 90°. In some embodiments, the solid-state phantom includes two detectors oriented at 180° to each other, for example, such that the radiation beam is detected by the two detectors when the solid-state phantom is rotated 180°.

[0132] In some embodiments, the solid-state phantom includes a single cylindrical detector oriented in a vertical direction along the rotation axis of the solid-state phantom (e.g., the solid-state phantom includes a hole and a detector present in the hole), for example, so as to present a detection surface at a constant distance from the source (e.g., at a fixed position) along the axis of the radiation beam at all rotation angles of the solid-state phantom. In this way, the distance between the radiation source and the detector remains constant when the solid-state phantom rotates.

[0133] In some embodiments, the detector is movable within the solid-state phantom (e.g., the detector is movable from a first hole in the solid-state phantom and is insertable into a second hole in the solid-state phantom), and the solid-state phantom defines a measurement area (or measurement volume), e.g., because beam characteristics can be measured at one or more locations within the solid-state phantom.

[0134] In some embodiments, a phantom (e.g., a water phantom or a solid phantom) includes a detector. In some embodiments, the detector includes an ion chamber. In some embodiments, the detector is configured to detect a megavoltage (e.g., therapeutic) x-ray beam. Without limitation, exemplary detectors used in embodiments of the present technology are, for example, FARMER-type detectors, such as the EXRADIN A12 and EXRADIN A19 commercially sold by Standard Imaging; the 30010 or 30012 ionization chambers commercially sold by PTW; the FC65-G ionization chamber commercially sold by Iba Dosimetry; and the SNC15c, SNC350p, or SNC600c commercially sold by Sun Nuclear. Without limitation, detectors (e.g., ionization chambers) are described in: “Absorbed Dose Determination in External Beam Radiotherapy: An International Code of Practice for Dosimetry Based on Standards of Absorbed Dose to Water”, Technical Reports Series No. 398, International Atomic Energy Agency, Vienna, 2000, incorporated herein by reference, and particularly in Section 4.2.1 and Tables 3 and 4.

[0135] method

[0136] In some embodiments, for example, Figure 2 As shown, the technology provides a method for measuring a radiation dose provided by a medical radiation system including a patient rotation system and a radiation source (e.g., a static source). For example, in some embodiments, the method 200 includes positioning 210 a phantom (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector) on a patient support assembly of the patient rotation system. In some embodiments, the method includes using a phantom system including a phantom (including a detector), an electrometer, and a slip ring, such as Figure 5A and Figure 5B Thus, in some embodiments, the method includes providing a phantom system including a phantom (including a detector), an electrometer, and a slip ring, such as Figure 5A and Figure 5B shown.

[0137] Furthermore, in some embodiments, the method comprises moving 220 the phantom relative to the radiation beam generated by the radiation source. In some embodiments, the method comprises detecting 230 the radiation beam. In some embodiments, the method comprises calculating 240 a radiation dose of the radiation beam.

[0138] In some embodiments, the method 200 can be used to measure radiation dose of a medical radiation system including a patient rotation system adapted to rotate about a rotation axis. A radiation therapy system 100, such as shown in FIG. 1 , is an example of such a medical radiation system. However, embodiments of the method 200 are not limited to use with the radiation therapy system 100 described herein. Thus, embodiments provide that the method 200 can be used to measure radiation dose of any medical radiation system (e.g., any radiation therapy system and / or any medical imaging system).

[0139] In some embodiments, positioning 210 a phantom (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector) on a patient support assembly includes attaching or mounting the phantom to a component of the patient support assembly. In some embodiments, the phantom is attached to a seat member of the patient support assembly. In some embodiments, the phantom is mounted to one or more armrests of the patient support assembly. For example, an embodiment provides that the phantom can be mounted to one or more armrests using an interface configured to hold a quality assurance device. In some embodiments, the phantom is secured to any other portion or component of the patient support assembly, for example, an embodiment provides that the phantom is secured to a portion or component that is generally configured to support or secure a patient. In some embodiments, a phantom system includes a phantom (including a detector), an electrometer, and a slip ring, such as Figure 5A and Figure 5B shown.

[0140] In some embodiments, a phantom (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector) is positioned on a patient support assembly such that the axis of rotation passes through the phantom and / or through the interior volume of the phantom. In some embodiments, the geometric center of the phantom is aligned with the axis of rotation. In some embodiments, the geometric center of the phantom is aligned with the isocenter of the medical radiation system. In some embodiments, method 200 further includes aligning the geometric center of the phantom with the axis of rotation. In some embodiments, the phantom is supported by a seat member of the patient support assembly, and the armrest of the patient support assembly is used to align the phantom. That is, in some embodiments, the seat member of the patient support assembly is used to support the weight of the phantom, and the armrest of the patient support assembly is used to align the phantom.

[0141] In some embodiments, a phantom (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector) is positioned on a horizontal surface of a patient support assembly (e.g., on a seat member). In some embodiments, the axis of rotation is a vertical axis (e.g., a substantially and / or effectively vertical axis), and the axis of rotation extends along a vertical dimension of the phantom. In some embodiments, the axis of rotation is perpendicular (e.g., substantially and / or effectively perpendicular) to the radiation beam. Thus, in some embodiments, the radiation beam travels (e.g., substantially and / or effectively travels) along a horizontal plane that is orthogonal (e.g., substantially and / or effectively orthogonal) to the vertical axis of rotation. In some embodiments, the phantom is horizontally disposed on the patient support assembly such that a central axis of the radiation beam is parallel (e.g., substantially and / or effectively parallel) to a base of the phantom. In some embodiments, the base of the phantom is defined as a surface of the tank that supports the weight of the phantom (e.g., resists gravity acting on the phantom).

[0142] In some embodiments, a phantom (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector) is positioned on a patient support assembly such that a side wall or outer surface of the phantom faces the radiation source, and the radiation beam passes through the side wall or outer surface and enters the phantom. In some embodiments, the position and orientation of the phantom is such that the side wall or outer surface facing the radiation source is orthogonal to the central axis of the radiation beam.

[0143] In some embodiments, moving 220 the phantom (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector) includes rotating the phantom, such as by rotating the patient rotation system around an axis of rotation. In some embodiments, moving 220 the phantom includes translating the phantom, such as by translating the patient support assembly relative to the patient rotation system. In some embodiments, moving 220 the phantom includes moving the patient support assembly relative to the patient rotation system (e.g., without displacing the axis of rotation of the patient rotation system). For example, in some embodiments, the patient support assembly is adapted to perform rotational movement (e.g., yaw, pitch, and / or roll) relative to a base of the patient rotation system. In some embodiments, moving the phantom includes moving the patient rotation system relative to a fixed radiation source (e.g., without displacing the axis of rotation of the patient rotation system). For example, in some embodiments, the patient rotation system is mounted to a translatable member (e.g., capable of moving in a vertical direction or in any other direction), thereby allowing the entire patient rotation system to translate in space. In some embodiments, the rotation phantom further includes a rotation phantom, an electrometer, and a cable. In some embodiments, the rotating phantom further comprises a first phantom side member of a rotating slip ring. Figure 5A and Figure 5B .

[0144] In some embodiments, a phantom (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector) is rotated in a continuous cycle. In some embodiments, the phantom is rotated in a discontinuous cycle. For example, in some embodiments, the phantom is rotated 90°, and then detecting 230 the radiation beam and calculating 240 the radiation dose of the radiation beam are performed before resuming the rotation of the phantom. In some embodiments, after the phantom is rotated at any angle (e.g., 10, 20, 30, 40, 50, 60, 70, 80, 90, 100, 110, 120, 130, 140, 150, 160, 170, 180, 190, 200, 210, 220, 230, 240, 250, 260, 270, 280, 290, 300, 310, 320, 330, 340, or 350°), the phantom is rotated at any angle. Detecting 230 the radiation beam and calculating 240 the radiation dose of the radiation beam are performed before 10, 20, 30, 40, 50, 60, 70, 80, 90, 100, 110, 120, 130, 140, 150, 160, 170, 180, 190, 200, 210, 220, 230, 240, 250, 260, 270, 280, 290, 300, 310, 320, 330, 340, or 350°. In some embodiments, the method includes waiting for a period of time after completing the step of rotating the phantom (e.g., water phantom), for example, after the rotation is stopped and the phantom is stationary, to allow the liquid (e.g., water) to stop moving, for example to stabilize the liquid (e.g., water) and thereby minimize and / or eliminate changes in the level of the liquid (e.g., water).

[0145] Alternatively, in some embodiments, the phantom is rotated continuously (e.g., without interrupting the rotation) while detecting 230 the radiation beam and / or calculating 240 the radiation dose of the radiation beam is performed. In some embodiments, the method includes detecting 230 the radiation beam during movement 220 (e.g., rotation and / or translation) of the phantom or detecting 230 the radiation beam within a relaxation time requirement of the liquid. Thus, in some embodiments, the method includes providing and / or using a solid-state phantom. Relative to a water phantom, embodiments of a solid-state phantom described herein provide an advantage in detecting the radiation beam while the phantom is rotated because the solid water equivalent material of the solid-state phantom remains at a constant level during rotation, while the water level of a water phantom may change due to acceleration of the phantom and the water in the phantom tank during rotation.

[0146] In some embodiments, detecting 230 the radiation beam includes detecting the radiation beam using a detector positioned within a phantom (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector). In some embodiments related to the water phantom, the detector is completely immersed in the liquid of the tank. In some embodiments related to the water phantom, the detector is partially immersed in the liquid of the tank. In some embodiments, detecting the radiation beam includes measuring a dose of the radiation beam. In some embodiments, the energy (e.g., average energy) and / or intensity of the radiation beam is calculated based on one or more dose measurements.

[0147] Thus, in some embodiments, the detector is configured to measure the dose of the radiation beam.In some embodiments, the detector is configured to measure one or more other characteristics of the radiation beam (eg, dose distribution).

[0148] In some embodiments, the detector is movable within a phantom (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector). In some embodiments associated with a water phantom, the detector is mounted to an adjustable arm fixed to the tank, such that the position and / or orientation of the detector can be adjusted using the adjustable arm. In some embodiments associated with a solid phantom, the detector can be moved between multiple holes (e.g., moved out of a first hole and inserted into a second hole). In some embodiments, detecting a radiation beam includes positioning the detector to intercept the radiation beam by moving the phantom and / or by moving the detector within the phantom. A radiation beam spreads out in space as it travels (e.g., due to divergence and / or scattering); therefore, in some embodiments, detecting a radiation beam includes detecting the radiation beam at multiple locations within the phantom to detect multiple rays of the beam as the rays diverge.

[0149] In some embodiments, more than one detector is provided in the phantom to detect the radiation beam when the phantom is rotated (for example, 2, 3, 4, 5, 6, 7 or 8 detectors are provided in the phantom to detect the radiation beam when the phantom is rotated). In some embodiments, two detectors are oriented at right angles to each other so that the radiation beam is detected when the phantom is rotated by 90°. In some embodiments, the two detectors are oriented relative to each other so that the radiation beam is detected when the phantom is rotated by 180°. In some embodiments, a single cylindrical detector is oriented in a vertical direction along the axis of rotation so as to present a detection surface at a constant distance from the source (for example, at a fixed position) along the axis of the radiation beam at all rotation angles of the phantom. In this way, the distance between the radiation source and the detector remains constant when the phantom is rotated.

[0150] In some embodiments, calculating 240 the radiation dose of the radiation beam comprises combining a plurality of measurements of the radiation beam from one or more detectors. In some embodiments, calculating the radiation dose of the radiation beam comprises generating a spatial distribution (e.g., a two-dimensional or three-dimensional distribution) of the intensity of the radiation beam within the phantom. In some embodiments, the detector is movable within the phantom, and the phantom defines a measurement zone (or measurement volume), e.g., because beam characteristics can be measured at one or more locations within the phantom.

[0151] Dose scanning system and method

[0152] In some embodiments, for example, Figure 3 As shown, the technology provides a system for performing dose scanning (e.g., full three-dimensional (3D) dose scanning). In some embodiments, dose scanning can be used to measure dose spread, debug linear accelerators (linacs), and / or perform quality assurance and / or maintenance procedures for medical radiation systems. In some embodiments, dose scanning provides a characterization of the three-dimensional intensity distribution of a radiation beam. Embodiments provide for scanning a range of beam field sizes. In some embodiments, data obtained by these measurements is used to construct a three-dimensional map of the radiation beam.

[0153] In some embodiments, the system includes a phantom 310 (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector). In some embodiments, the phantom 310 is positioned on a patient support assembly of a patient rotation system configured to rotate about a rotation axis 320. In some embodiments, the phantom 310 is positioned so that a segment of the rotation axis 320 is positioned within a side wall or outer surface of the phantom 310. That is, in some embodiments, the side wall or outer surface of the phantom 310 facing the radiation source 350 is parallel (e.g., substantially and / or effectively parallel) to the rotation axis 320 passing through a plane along the side wall or outer surface.

[0154] exist Figure 3 In the exemplary embodiment shown, the first beam 330 and the second beam 340 are shown as being incident on a phantom 310 (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector). As an example, for example Figure 3As shown, the first beam 330 and the second beam 340 have different areas projected onto the phantom 310. For example, the beam 330 may have a size of 10 cm by 10 cm, and the beam 340 may have a size of 30 cm by 30 cm (e.g., corresponding to the size of the semi-minor axis and the semi-major axis of the ellipse defined by the beam area incident on the phantom 310). In this example, the larger sidewall or outer surface of the phantom 310 may be 100 cm long. The technology is not limited to a phantom 310 having a sidewall or outer surface of 100 cm and / or a beam having an area of ​​10 cm by 10 cm and 30 cm by 30 cm. Therefore, the technology involves beams and phantoms having any other length or area. In some embodiments, the phantom and the radiation source 350 are arranged so that the beam area is contained within the phantom. That is, embodiments provide that the dimensions (eg, height and / or width) of the beam area projected onto the phantom do not exceed one or more dimensions (eg, height and / or width) of the sidewall or outer surface of the phantom upon which the beam is incident.

[0155] In some embodiments, the first beam 330 and the second beam 340 are generated asynchronously. In some embodiments, the first beam 330 and the second beam 340 are generated simultaneously (e.g., substantially and / or effectively simultaneously). In some embodiments, the first beam 330 and the second beam 340 are generated by the same source. In some embodiments, the first beam 330 and the second beam 340 are generated by different sources (e.g., the first beam 330 is generated by a first source, and the second beam 340 is generated by a second source). In some embodiments, a beam shaping system is provided to adjust the size and / or shape of the radiation beam (e.g., in one or two dimensions).

[0156] In some embodiments, the system includes a detector (e.g., a detector of a water phantom or a solid phantom). In some embodiments, the detector is positioned inside the phantom 310. In some embodiments, the detector moves within the phantom to obtain a three-dimensional distribution of the radiation beam. In some embodiments, the detector moves along a vertical axis, a horizontal axis, and / or a depth axis to detect the beam intensity at multiple points within the phantom 310. In some embodiments, the detector translates along a vertical axis, a horizontal axis, and / or a depth axis to detect the beam intensity at multiple points within the phantom 310. In some embodiments, the detector rotates along a vertical axis, a horizontal axis, and / or a depth axis (e.g., to provide pitch, roll, and / or yaw rotation) to detect the beam intensity at multiple points within the phantom 310.

[0157] In some embodiments, the patient support assembly is moved to obtain a three-dimensional distribution of the radiation beam. In some embodiments, the patient support assembly is moved along a vertical axis, a horizontal axis, and / or a depth axis to detect the beam intensity at multiple points within the phantom 310. In some embodiments, the patient support assembly is translated along a vertical axis, a horizontal axis, and / or a depth axis to detect the beam intensity at multiple points within the phantom 310. In some embodiments, the patient support assembly is rotated along a vertical axis, a horizontal axis, and / or a depth axis (e.g., to provide pitch, roll, and / or yaw rotation) to detect the beam intensity at multiple points within the phantom 310.

[0158] Some embodiments combine a moving detector with a moving patient support assembly to detect beam intensity in three dimensions. For example, in some embodiments, the detector translates along a vertical axis, a horizontal axis, and / or a depth axis and / or rotates around a vertical axis, a horizontal axis, and / or a depth axis, and the patient support assembly translates along a vertical axis, a horizontal axis, and / or a depth axis and / or rotates around a vertical axis, a horizontal axis, and / or a depth axis. As an example, the detector can move in two dimensions (e.g., any two of translation along a vertical axis, translation along a horizontal axis, translation along a depth axis, rotation around a vertical axis, rotation around a horizontal axis, and / or rotation around a depth axis) while the patient support assembly moves in a third dimension (e.g., any one of translation along a vertical axis, translation along a horizontal axis, translation along a depth axis, rotation around a vertical axis, rotation around a horizontal axis, and / or rotation around a depth axis); or, alternatively, the detector can move in one dimension (e.g., any one of translation along a vertical axis, translation along a horizontal axis, translation along a depth axis, rotation around a vertical axis, rotation around a horizontal axis, and / or rotation around a depth axis) while the patient support assembly moves in two dimensions (e.g., any two of translation along a vertical axis, translation along a horizontal axis, translation along a depth axis, rotation around a vertical axis, rotation around a horizontal axis, and / or rotation around a depth axis).

[0159] Tissue phantom ratio measurement system and method

[0160] In some embodiments, for example, Figure 4A and Figure 4BAs shown, the technology provides a system for performing tissue phantom ratio measurements. In some embodiments, a phantom 410 (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector) is positioned on a patient support assembly of a patient rotation system configured to rotate about a rotation axis 420. In some embodiments, the phantom 410 is positioned so that the rotation axis 420 intersects the interior volume of the phantom 410 (e.g., the rotation axis 420 passes through the phantom 410). In some embodiments, a detector is placed within the phantom 410 on the rotation axis 420 to detect a radiation beam 430. Therefore, in some embodiments, the detector is positioned within the phantom at a position having a distance from the source 440 that is constant (e.g., substantially and / or effectively constant) when the phantom rotates about the rotation axis.

[0161] Figure 4A A phantom 410 (eg, a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector) is shown in a first orientation, wherein a beam 430 reaches the detector after traveling a first distance inside the phantom 410 . Figure 4B The phantom 410 is shown in a second orientation (e.g., rotated 90° clockwise relative to the first orientation) in which the beam 430 reaches the detector after traveling a second distance inside the phantom 410, wherein the second distance is longer than the first distance. In both the first orientation of the phantom 410 and the second orientation of the phantom 410, the sidewall or outer surface of the phantom 410 facing the radiation source 440 is orthogonal to the central axis of the beam 430. In some embodiments, the phantom is rotated by any other angle between the first orientation and the second orientation (e.g., the phantom is rotated by 10, 20, 30, 40, 50, 60, 70, 80, 90, 100, 110, 120, 130, 140, 150, 160, 170, 180, 190, 200, 210, 220, 230, 240, 250, 260, 270, 280, 290, 300, 310, 320, 330, 340, or 350°).

[0162] In some embodiments, beam 430 contacts the detector and the detector detects beam 430. Thus, embodiments provide that the length of the propagation path of beam 430 is defined as the distance the beam travels inside a phantom 410 (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector). As used herein, the term "propagation path" refers to the straight-line distance between a side wall or outer surface of the phantom facing radiation source 440 and a detector within the phantom. In some embodiments, for example, Figure 4A and Figure 4BAs shown, the length of the propagation path of the beam 430 inside the phantom 410 in the first orientation (e.g., 10 cm) is different from the length of the propagation path of the beam 430 inside the phantom 410 in the second orientation (e.g., 20 cm). An embodiment of the method includes measuring the dose of the beam and / or calculating the quality of the beam (e.g., energy, intensity, flux, attenuation, absorbed dose) using the phantom in the first orientation, measuring the dose of the beam and / or calculating the quality of the beam (e.g., energy, intensity, flux, attenuation, absorbed dose) using the phantom in the second orientation, and comparing the first measured value or calculated quality with the second measured value or calculated quality to calculate a tissue phantom ratio (TPR) that characterizes the travel of the beam 430 through the phantom 410. The TPR measurement can be a function of the beam energy or intensity and is an indicator of beam quality.

[0163] In some embodiments, a method comprises calculating a TPR 20,10 In some embodiments, TPR is calculated 20,10 Embodiments using the systems and / or phantoms 410 described herein are included, such as phantoms (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector) having dimensions and a detector positioned within the phantom (e.g., such as Figure 4A and Figure 4B ) such that the first propagation path length is 10 cm and the second propagation path length is 20 cm. In some embodiments, the ratio of the measurements at 20 cm and 10 cm provides a measure of the quality of the radiation (eg, the average energy of the beam).

[0164] This technique is not limited to calculating TPR 20,10 or using a method having a Figure 4A and Figure 4B The phantom of the dimensions and detector placement shown (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector). Thus, the technique provides that other propagation path lengths can be measured by changing the dimensions of the phantom 410, by using different rotation angles, or by changing the location of the detector inside the phantom 410.

[0165] In some embodiments, the described techniques provide methods, apparatus, and systems for measuring x-ray dose and / or calculating average beam energy or beam quality for isocenter dose. In some embodiments, the described techniques provide methods, apparatus, and systems for measuring x-ray beam quality and expressing x-ray beam quality as a tissue phantom ratio (TPR). In some embodiments, measuring x-ray beam quality and expressing x-ray beam quality as a tissue phantom ratio (TPR) (e.g., for isocenter dose) includes applying translational and / or rotational offsets of a patient rotation system to measure beams of different propagation lengths (e.g., 10 and 20 cm). The rotational and / or translational movement of the phantom allows different measurements to be performed without a technician or other operator having to access the medical radiation system or repeatedly rearranging the measurement setup. In some embodiments, the present method allows for efficient positioning of a measurement system (e.g., a phantom (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector)) for measuring radiation dose of a medical radiation system. In some embodiments, a microprocessor (e.g., executing instructions provided by software) controls the measurement of beam characteristics, movement of the phantom (e.g., translation and / or rotation), and calculation of the TPR. In some embodiments, the microprocessor outputs the TPR value to a user. In some embodiments, the microprocessor outputs the TPR value to a user after the electrometer processes the signal, and the processed charge signal and / or processed current signal from the ion chamber is transmitted to the user via a slip ring.

[0166] Phantom system

[0167] In some embodiments, for example, Figure 5A and Figure 5B As shown, the technology provides a phantom system 500 for measuring radiation dose. In some embodiments, the phantom system 500 includes a phantom 501 (e.g., a water phantom or a solid phantom), the phantom includes a detector, and the phantom system further includes an electrometer 502, a slip ring 503, and a microprocessor 504. In some embodiments, the microprocessor or computer includes the electrometer. In some embodiments, the electrometer is a device with a very high input impedance (e.g., at least about 10 14 ohms) so that it resolves very small signals (e.g., less than 1 pC and / or 1 nA). In some embodiments, the electrometer 502 can be removed from the phantom system 500, for example, for calibration, replacement, maintenance, and / or repair of the electrometer.

[0168] In some embodiments, the phantom 501 detector is in electrical or electronic communication with the electrometer 502. In some embodiments, the phantom 501 detector is in electrical or electronic communication with the electrometer 502 via a cable 505 connecting the detector and the electrometer 502. In some embodiments, the cable 505 connecting the detector and the electrometer 502 is a triaxial cable. In some embodiments, the electrometer 502 is in electrical or electronic communication with a microprocessor 504 (e.g., a computer). In some embodiments, the electrometer 502 outputs a signal that is transmitted to the microprocessor 504 (e.g., a computer). In some embodiments, the electrometer 502 outputs a signal that is transmitted to the microprocessor 504 (e.g., a computer) via a slip ring 503. In some embodiments, the slip ring 503 includes a first phantom-side component that rotates with the phantom 501 and the electrometer 502; and includes a second user-side component that does not rotate with the phantom 501 and the electrometer 502. The first phantom-side component of the slip ring 503 and the second user-side component of the slip ring 503 are in electrical or electronic communication with each other. In some embodiments, the first phantom-side component of the slip ring 503 is in electrical or electronic communication with the electrometer 502 via a cable 507; and the second user-side component of the slip ring 503 is in electrical or electronic communication with the microprocessor 504 via a cable 506. In some embodiments, the system 500 further includes an analog-to-digital converter (ADC) that converts an electrical (e.g., analog) signal generated by the electrometer 502 into a digital signal for communication with the microprocessor 504 (e.g., via the slip ring 503).

[0169] In some embodiments, the method includes positioning a phantom 501 (e.g., a water phantom including a tank, water, and a detector; or a solid phantom including a solid water equivalent material and a detector) of a phantom system 500 on a patient support assembly of a patient rotation system. In some embodiments, an electrometer 502 and a cable 505 (e.g., a triaxial cable) of the phantom system 500 are also positioned on a patient support assembly of the patient rotation system. In some embodiments, the method includes rotating the patient rotation system about a rotation axis 590 such that the phantom 501, the electrometer 502, and the cable 505 (e.g., a triaxial cable) of the phantom system 500 rotate about the rotation axis 590. The first phantom-side component of the slip ring 503 also rotates about the rotation axis 590 while maintaining electrical or electronic communication with the second user-side component of the slip ring 503. During rotation of the patient rotation system about the rotation axis 590 (and therefore during rotation of the phantom 501, the electrometer 502, and the cable 505 (e.g., a triaxial cable)), the microprocessor 504 and the cable 506 do not rotate about the rotation axis 590. The second user-side component of the slip ring 503 also does not rotate about the rotation axis 590. Figure 5A .

[0170] In some embodiments, for example, Figure 5B As shown, the technology provides a phantom system 500 for measuring a radiation dose provided by a beam 551 generated by a static source 550. In some embodiments, the method includes rotating the patient rotation system about a rotation axis 590 so that a phantom 501, an electrometer 502, and a cable 505 (e.g., a triaxial cable) of the system 500 rotate about the rotation axis 590; and generating a beam 551 from the static source 550. Thus, in some embodiments, the method includes contacting a detector of the phantom 501 with the beam 551 while the phantom 501 rotates.

[0171] Thus, the phantom system 500 includes a rotating subsystem including a phantom 501, an electrometer 502, and a cable 505 (e.g., a triaxial cable); and the phantom system 500 includes a non-rotating subsystem including a microprocessor 504. In some embodiments, the rotating subsystem includes an ADC. In some embodiments, the rotating subsystem includes a microprocessor or computer, which includes an electrometer. Thus, in some embodiments, data is transmitted from inside the rotating subsystem (e.g., from the phantom side of the system) to outside the rotating subsystem (to the user side) via a slip ring 503. In addition, the charge and / or current output from the detector are small enough that they are transmitted from the detector to the electrometer via a special cable (e.g., a triaxial cable). Only the post-electrometer signal (e.g., an analog charge or current measurement or a digitized version thereof) passes through the slip ring to the user side (e.g., outside the radiation shelter).

[0172] Although the disclosure herein is directed to certain exemplary embodiments, it should be understood that these embodiments are presented by way of example and not limitation.

[0173] For all purposes, all publications and patents mentioned in the above description are incorporated herein by reference in their entirety. Various modifications and variations of the use of the described compositions, methods and techniques will be apparent to those skilled in the art without departing from the scope and spirit of the described technology. Although the technology has been described in conjunction with specific exemplary embodiments, it should be understood that the claimed invention should not be unduly limited to these specific embodiments. In fact, various modifications of the described modes for implementing the present invention that are apparent to those skilled in the art are intended to fall within the scope of the appended claims.

Claims

1. A method of measuring a radiation dose provided by a medical radiation system comprising a patient rotation system and a radiation source, the patient rotation system being adapted to rotate about a rotation axis, the method comprising: positioning a phantom on a patient support assembly of the patient rotation system; moving the phantom relative to a radiation beam generated by the radiation source; detecting the radiation beam using a detector; as well as A radiation dose of the radiation beam is calculated.

2. The method according to claim 1, wherein: The phantom is positioned on the patient support assembly such that the axis of rotation passes through the phantom.

3. The method according to claim 1 or 2, wherein: The phantom is positioned on the patient support assembly such that a side wall or outer surface of the phantom faces the radiation source and the radiation beam passes through the side wall or outer surface.

4. The method according to claim 3, wherein: The side walls or outer surfaces are orthogonal to a central axis of the radiation beam.

5. The method according to claim 3 or 4, wherein: The side walls or outer surfaces are transparent to the radiation beam.

6. The method according to any one of claims 1 to 5, wherein: Moving the phantom includes rotating the phantom by rotating the patient rotation system about the rotation axis.

7. The method according to any one of claims 1 to 6, wherein: Moving the phantom includes translating the phantom by translating the patient support assembly relative to the patient rotation system.

8. The method according to any one of claims 1 to 7, wherein: The detector is movable within the phantom.

9. The method according to claim 8, wherein: Detecting the radiation beam includes positioning the detector to intercept the radiation beam by moving the phantom and moving the detector within the phantom.

10. The method according to claim 8 or 9, wherein: Detecting the radiation beam includes detecting the radiation beam at a plurality of locations within the phantom.

11. The method according to any one of claims 1 to 10, wherein: Calculating a radiation dose of the radiation beam includes generating a three-dimensional intensity distribution of the radiation beam within the phantom.

12. The method according to any one of claims 1 to 11, wherein: The detector is positioned in line with the axis of rotation.

13. The method according to claim 12, wherein: The calculated radiation dose is a first radiation dose obtained for a first orientation of the phantom, and wherein the method further comprises: rotating the phantom to a second orientation different from the first orientation by rotating the patient rotation system about the rotation axis; detecting the radiation beam directed to the second orientation using the detector; calculating a second radiation dose for the second oriented radiation beam; and A tissue phantom ratio is obtained by comparing the second radiation dose to the first radiation dose.

14. The method according to claim 13, wherein: The length of a first propagation path of the radiation beam inside the phantom for the first orientation is different from the length of a second propagation path of the radiation beam inside the phantom for the second orientation.

15. The method according to claim 14, wherein: The length of the first propagation path is 10 cm, and wherein the length of the second propagation path is 20 cm, so that the tissue phantom ratio is TPR 20,10 Measured value.

16. The method according to any one of claims 13 to 15, wherein: A first side wall or outer surface of the phantom facing the radiation source in the first orientation is orthogonal to a central axis of the radiation beam.

17. The method according to claim 16, wherein: A second side wall or outer surface of the phantom facing the radiation source in the second orientation is orthogonal to the central axis of the radiation beam.

18. The method according to any one of claims 1 to 17, wherein: The radiation source is one of an imaging radiation source or a therapeutic radiation source.

19. The method according to any one of claims 1 to 18, wherein: The axis of rotation is perpendicular to the radiation beam.

20. The method according to any one of claims 1 to 19, wherein: The axis of rotation is a vertical axis.

21. The method according to any one of claims 1 to 20, wherein: The phantom is securely attached to the patient support assembly.

22. The method according to any one of claims 1 to 21, wherein: The patient support assembly includes an interface for attaching the phantom at a fixed location on the patient support assembly.

23. The method according to any one of claims 1 to 22, wherein: The phantom is mounted to a seat member of the patient support assembly.

24. The method according to any one of claims 1 to 22, wherein: The phantom is mounted to an armrest of the patient support assembly.

25. The method according to any one of claims 1 to 24, wherein: The phantom is positioned on a horizontal surface of the patient support assembly.

26. The method according to any one of claims 1 to 25, wherein: The phantom is horizontally disposed on the patient support assembly such that a central axis of the radiation beam is parallel to a base of the phantom.

27. The method according to any one of claims 1 to 25, wherein: The phantom is a water phantom including a tank, water and a detector.

28. The method according to any one of claims 1 to 25, wherein: The phantom is a solid-state phantom including a solid water equivalent material and a detector.

29. A water phantom, comprising: a tank body, the tank body comprising a base, a first wall and a second wall; a detector positioned within the tank at a first distance from the first wall and at a second distance from the second wall; as well as water.

30. The water phantom according to claim 29, wherein: The first wall and / or the second wall comprises poly(methyl methacrylate).

31. The water phantom according to claim 29, wherein: The first wall forms an angle of 90° with the second wall.

32. The water phantom of claim 29, wherein: The detector has a cylindrical shape.

33. The water phantom according to claim 29, wherein: The detector has a first detection surface parallel to the first wall and a second detection surface parallel to the second wall.

34. The water phantom according to claim 29, wherein: The first distance is 10 cm and the second distance is 20 cm.

35. The water phantom of claim 29, further comprising a component configured to attach the water phantom to a patient support assembly.

36. The water phantom of claim 29, wherein: The detector is positioned at the axis of rotation of the water phantom.

37. The water phantom of claim 29, further comprising a movable arm operably engaged with the detector.

38. A solid body phantom, comprising: a solid water equivalent material, the solid water equivalent material comprising a first outer surface and a second outer surface; as well as A detector is positioned within the solid water equivalent material at a first distance from the first outer surface and at a second distance from the second outer surface.

39. The solid phantom according to claim 38, wherein: The first outer surface forms an angle of 90° with the second outer surface.

40. The solid phantom of claim 38, wherein: The detector has a cylindrical shape.

41. The solid phantom of claim 38, wherein: The detector has a first detection surface parallel to the first outer surface and a second detection surface parallel to the second outer surface.

42. The solid phantom of claim 38, wherein: The first distance is 10 cm and the second distance is 20 cm.

43. The solid phantom of claim 38, further comprising a component configured to attach the solid phantom to a patient support assembly.

44. The solid phantom of claim 38, wherein: The detector is positioned at the axis of rotation of the solid state phantom.

45. The solid phantom of claim 38, wherein: The solid water equivalent material includes a hole, and the detector is positioned in the hole.

46. ​​A system comprising: Medical radiation systems; as well as A water phantom, the water phantom comprising: a tank body, the tank body comprising a base, a first wall and a second wall; a detector positioned within the tank at a first distance from the first wall and at a second distance from the second wall; and water.

47. A system comprising: Medical radiation systems; as well as A solid body phantom, the solid body phantom comprising: a solid water equivalent material, the solid water equivalent material comprising a first outer surface and a second outer surface; as well as A detector is positioned within the solid water equivalent material at a first distance from the first outer surface and at a second distance from the second outer surface.

48. A system according to any one of claims 46 or 47, wherein: The medical radiation system includes an x-ray source.

49. The system of any one of claims 46 or 47, further comprising a patient support assembly.

50. The system of claim 49, wherein: The patient support assembly includes an interface configured to receive the water phantom or the solid phantom.

51. The system of claim 49, wherein: The patient support assembly is configured to operably engage the water phantom or the solid state phantom.

52. The system of claim 49, wherein: The patient support assembly is configured to move the water phantom or the solid phantom.

53. The system of claim 49, wherein: The patient support assembly is configured to rotate the water phantom or the solid phantom.

54. The system of any one of claims 46 or 47, further comprising a beam.

55. The system of any one of claims 46 or 47, further comprising a software component including instructions for rotating the water phantom or the solid phantom.

56. The system of any of claims 46 or 47, further comprising a software component including instructions for activating a source to produce a beam.

57. The system of any of claims 46 or 47, further comprising a software component including instructions for receiving data from the detector and using the data to calculate a tissue phantom ratio.

58. The system of claim 57, wherein: The tissue phantom ratio is TPR 20,10 .

59. The system of claim 46, wherein: The first wall and / or the second wall comprises poly(methyl methacrylate).

60. The system of any one of claims 46 or 47, wherein: The first wall or the first outer surface forms an angle of 90° with the second wall or the second outer surface.

61. The system of any one of claims 46 or 47, wherein: The detector has a cylindrical shape.

62. The system of any one of claims 46 or 47, wherein: The detector has a first detection surface parallel to the first wall or the first outer surface and a second detection surface parallel to the second wall or the second outer surface.

63. The system of any one of claims 46 or 47, wherein: The first distance is 10 cm and the second distance is 20 cm.

64. A phantom system for measuring radiation dose, the system comprising: A phantom including a detector; Slip rings; microprocessor; as well as An electrometer is electronically or electrically connected to the detector via a cable and is electronically or electrically connected to the microprocessor via the slip ring.

65. The phantom system of claim 64, wherein: The phantom is a water phantom.

66. The phantom system of claim 64, wherein: The phantom is a solid-state phantom.

67. The phantom system of claim 64, wherein: The cable is a triaxial cable.

68. The phantom system of claim 64, wherein: A computer includes the electrometer.

69. The phantom system of claim 64, further comprising an analog-to-digital converter in electrical communication with the electrometer.

70. The phantom system of claim 64, comprising a rotation subsystem comprising the phantom and an electrometer.

71. The phantom system of claim 64, comprising a non-rotating subsystem comprising the microprocessor.

72. A method of measuring a radiation dose provided by a medical radiation system comprising a patient rotation system and a radiation source, the patient rotation system being adapted to rotate about a rotation axis, the method comprising: positioning a phantom of a phantom system on a patient support assembly of the patient rotation system; moving the phantom relative to a radiation beam generated by the radiation source; detecting the radiation beam using a detector; generating, by an electrometer, an electrical signal representative of the radiation beam; transmitting an electrical signal from the electrometer to a microprocessor via a slip ring; as well as The signal is used to calculate a radiation dose of the radiation beam.

73. The method of claim 72, wherein: The phantom is positioned on the patient support assembly such that the axis of rotation passes through the phantom.

74. The method of claim 72, wherein: Moving the phantom includes rotating the phantom by rotating the patient rotation system about the rotation axis.

75. The method of claim 72, wherein: Detecting the radiation beam includes detecting the radiation beam at a plurality of locations within the phantom.

76. The method of claim 72, wherein: Calculating a radiation dose of the radiation beam includes generating a three-dimensional intensity distribution of the radiation beam within the phantom.

77. The method of claim 72, wherein: The detector is positioned in line with the axis of rotation.

78. The method of claim 72, wherein: The calculated radiation dose is a first radiation dose obtained for a first orientation of the phantom, and wherein the method further comprises: rotating the phantom to a second orientation different from the first orientation by rotating the patient rotation system about the rotation axis; detecting the radiation beam directed to the second orientation using the detector; generating, by the electrometer, a second electrical signal representative of the radiation beam for the second orientation; transmitting the second electrical signal from the electrometer to a microprocessor through the slip ring; calculating a second radiation dose for the second oriented radiation beam; and A tissue phantom ratio is obtained by comparing the second radiation dose to the first radiation dose.

79. The method of claim 78, wherein: The length of a first propagation path of the radiation beam inside the phantom for the first orientation is different from the length of a second propagation path of the radiation beam inside the phantom for the second orientation.

80. The method of claim 78, wherein: The length of the first propagation path is 10 cm, and wherein the length of the second propagation path is 20 cm, so that the tissue phantom ratio is TPR 20,10 Measured value.

81. The method of claim 72, wherein: A first side wall or outer surface of the phantom facing the radiation source in the first orientation is orthogonal to a central axis of the radiation beam.

82. The method of claim 72, wherein: A second side wall or outer surface of the phantom facing the radiation source in the second orientation is orthogonal to the central axis of the radiation beam.

83. The method of claim 72, wherein: The radiation source is one of an imaging radiation source or a therapeutic radiation source.

84. The method of claim 72, wherein: The axis of rotation is perpendicular to the radiation beam.

85. The method of claim 72, wherein: The axis of rotation is a vertical axis.

86. The method of claim 72, wherein: The phantom is securely attached to the patient support assembly.

87. The method of claim 72, wherein: The patient support assembly includes an interface for attaching the phantom at a fixed location on the patient support assembly.

88. The method of claim 72, wherein: The phantom is mounted to a seat member of the patient support assembly.

89. The method of claim 72, wherein: The phantom is mounted to an armrest of the patient support assembly.

90. The method of claim 72, wherein: The phantom is positioned on a horizontal surface of the patient support assembly.

91. The method of claim 72, wherein: The phantom is horizontally disposed on the patient support assembly such that a central axis of the radiation beam is parallel to a base of the phantom.

92. The method of claim 72, wherein: The phantom is a water phantom including a tank, water and a detector.

93. The method of claim 72, wherein: The phantom is a solid-state phantom including a solid water equivalent material and a detector.

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