Modulation of beam energy for imaging and therapy with an energy regulator.

Abstract

In the radiation irradiation system of the present invention, a microwave source generates electromagnetic waves for accelerating an electron beam in an accelerator. The electromagnetic waves generated by the microwave source are adjusted to a first energy level by an energy adjuster. The accelerator generates a kilovolt (kV) imaging beam based on the first energy level. The electromagnetic waves generated by the microwave source are adjusted to a second energy level by the energy adjuster. The accelerator generates a megavolt (MV) treatment beam based on the second energy level.

Description

Related Applications

[0001] This application claims priority under 35 U.S.C. §119(e) to U.S. patent application Ser. No. 17 / 379,020, filed July 19, 2021, the entire text of which is incorporated herein by reference. [Technical Field]

[0002] The present invention relates to beam energy modulation for imaging and therapy using an energy conditioner. [Background technology]

[0003] In radiation therapy, a radiation delivery system can use a therapeutic radiation source to generate a treatment beam that delivers a therapeutic dose of radiation to a target, such as a tumor in a patient. The radiation source of a radiation delivery system may also operate in a mode (a mode with a different radiation dose) to deliver a diagnostic beam for the purpose of imaging a tumor in a patient. [Brief explanation of the drawings]

[0004] The present invention can be more fully understood from the following detailed description (embodiments of the invention) and the accompanying drawings illustrating various embodiments of the present disclosure.

[0005] [Figure 1A] 1 is an explanatory diagram illustrating a helical radiation irradiation system according to an embodiment of the present invention.

[0006] [Figure 1B] FIG. 1 is an illustration of a robotic radiation delivery system that can be used in accordance with embodiments of the present invention.

[0007] [Figure 1C] 1 is an explanatory diagram illustrating a C-arm gantry-based radiation delivery system according to an embodiment of the present invention.

[0008] [Figure 2]FIG. 1 is an explanatory diagram showing an example of a radiation irradiation system according to an embodiment of the present invention, which applies an energy adjuster that modulates electromagnetic waves to generate an imaging beam and a treatment beam.

[0009] [Figure 3A] FIG. 1 is an illustration of an example power variator including a Y-junction, according to an embodiment of the present invention.

[0010] [Figure 3B] 1 is an illustration of an example power variator including a T-junction, according to an embodiment of the present invention.

[0011] [Figure 4A] FIG. 1 is an illustrative diagram showing an example of a multi-X-ray target assembly including multiple radiation-generating targets with different energy characteristics, according to an embodiment of the present invention.

[0012] [Figure 4B] FIG. 1 illustrates a multi-X-ray target assembly according to an embodiment of the present invention, and illustrates an example of rearranging the multi-X-ray target assembly so that a therapeutic or imaging electron beam strikes a radiation-generating target with appropriate energy characteristics.

[0013] [Figure 5] FIG. 10 is a flow diagram illustrating a method for applying an energy conditioner to generate imaging and treatment beams according to an embodiment of the present disclosure.

[0014] [Figure 6] FIG. 1 is a block diagram illustrating an example of a computing device that may perform one or more processes (operations) described in this disclosure, in accordance with some embodiments of the present invention. DETAILED DESCRIPTION OF THE INVENTION

[0015] Below, this disclosure describes embodiments that use an energy conditioner to modulate the electromagnetic waves of a radiation delivery system. The radiation delivery system may utilize a single radiation source capable of producing both an imaging beam (also referred to as a diagnostic beam) and a therapeutic beam (also referred to as a medical treatment beam) at different energy levels.

[0016] In conventional radiation delivery systems, a therapeutic radiation source is used to generate a treatment beam that delivers a therapeutic dose of radiation to a target, such as a tumor in a patient. For example, a therapeutic radiation source may generate a megavoltage (MV) treatment beam. Conventional radiation delivery systems also use imaging radiation sources to generate imaging beams for acquiring image data related to the target. For example, an X-ray radiation source can generate a kilovoltage (kV) imaging beam. Thus, conventional radiation delivery systems require two different radiation sources (e.g., a therapeutic radiation source and an imaging radiation source) to deliver a therapeutic dose of radiation to a target using a treatment beam and acquire image data related to the target using an imaging beam, increasing costs.

[0017] In one aspect of the present invention, an energy conditioner is used to modulate the electromagnetic waves of a radiation delivery system so that a single radiation source can generate both an imaging beam and a treatment beam. Having such a radiation delivery system can ameliorate the above problems and other deficiencies. A radiation delivery system according to one aspect of the present invention includes a microwave source, such as a magnetron or klystron, that generates electromagnetic waves. The energy conditioner is operatively connected to the microwave source and can receive the electromagnetic waves from the microwave source and modulate the electromagnetic waves to correspond to the energy levels of the imaging beam or the treatment beam. The energy conditioner can modulate the electromagnetic waves to correspond to these energy levels without adjusting the output of the microwave source.

[0018] In one aspect of the invention, the energy conditioner can be a mechanical or electromechanical assembly configured to modulate electromagnetic waves. In one embodiment of the present invention, the energy conditioner can include a power variator, which can include two loads, a circulator, a junction, and a sliding short. In one embodiment of the invention, the junction may be either a Y junction or a T junction. In one aspect of the present invention, the sliding short may be a conventional mechanical sliding short or an electromagnetic design (electromagnetic short design) that allows for rapid adjustment of the short position through the use of a magnetically biased ferrite (electromagnetic ferrite).

[0019] In one embodiment of the present invention, the radiation delivery system may further include an accelerator (accelerating structure) operatively connected to the energy regulator to receive the modulated electromagnetic waves. The accelerator may accelerate the electron beam toward a radiation-emitting target (hereinafter also referred to as an "X-ray target") to generate a treatment beam and / or an imaging beam. The radiation delivery system of one embodiment of the present invention may also include an apparatus including multiple radiation-emitting targets, as described below.

[0020] In one aspect of the invention, the radiation delivery system also includes a controller operatively connected to the microwave source, the energy regulator, and the accelerator, the controller including a processor having processing logic that causes the energy regulator to modulate the electromagnetic waves, which causes the accelerator to generate the imaging beam and the treatment beam.

[0021] According to an aspect of the radiation delivery system of the present invention, by applying an energy adjuster to modulate electromagnetic waves to generate both an imaging beam and a treatment beam, it is not necessary to have both a therapeutic radiation source for generating a treatment beam and an imaging radiation source for generating an imaging beam, that is, a single radiation source can be used to generate both a treatment beam and an imaging beam, thereby reducing the cost of the radiation delivery system and improving the performance of the radiation delivery system.

[0022] FIG. 1A illustrates a helical irradiation system 800 according to an embodiment of the present disclosure. The helical radiation delivery system 800 includes a LINAC (linear accelerator) 850 mounted on a ring gantry 820. The LINAC 850 can be used to generate a radiation beam (i.e., a treatment beam) by directing an electron beam toward an X-ray radiation target. The treatment beam will deliver radiation toward a target area (i.e., a tumor). The treatment system further includes a multi-leaf collimator (MLC) 860 connected to the distal end of the LINAC 850. The MLC includes a housing containing multiple movable leaves, which can be moved to adjust the aperture of the MLC to enable treatment beam formation. In embodiments, the MLC 860 is a binary MLC including multiple leaves arranged in two opposing banks, where the leaves of the two opposing banks are interleaved and can be opened and closed to form an aperture. In some embodiments, the MLC 860 can be an electromagnetically actuated MLC, although the MLC 860 can also be any other type of MLC. The ring gantry 820 has a toroidal shape, and the patient 830 passes through the bore of the ring / toroid. The LINAC 850 is mounted around the periphery of the ring and rotates about an axis through its center to target radiation delivered from one or more angles around the patient. During treatment, the patient 830 can simultaneously move through the bore of the gantry on the treatment couch 840.

[0023] The helical radiation delivery system 800 includes an imaging system with a LINAC 850 as an imaging source and an X-ray detector 870. The LINAC 850 can be used to generate megavoltage X-ray images (MVCT) of a region of interest (ROI) of a patient 830. In this case, a series of X-ray beams are directed at the ROI and strike the X-ray detector 870 on the opposite side of the LINAC 850 to image the patient 830 and generate setup and pre-treatment images. In one embodiment, helical radiation delivery system 800 may also include a secondary imaging system consisting of a kV (kilovoltage) imaging source 810 mounted on a ring gantry 820 orthogonal to (e.g., 90 degrees away from) LINAC 850 and positioned to project an imaging x-ray beam toward a target region and project onto a detector imaging plane after passing through patient 130.

[0024] FIG. 1B illustrates a radiation therapy system 1200 used in accordance with an alternative embodiment described herein. As shown in FIG. 1B, the radiation therapy system 1200 includes a LINAC (linear accelerator) 1201 that functions as a therapeutic radiation source, and a multi-leaf collimator (MLC) 1205 connected to the distal end of the LINAC 1201 to form a treatment beam. In one embodiment, the LINAC 1201 is mounted and positioned at the end of a robotic arm 1202 with multiple (e.g., five or more) degrees of freedom to send beams from many angles and planes in a working area around the patient to irradiate a pathological anatomy (e.g., target). Treatments may involve beam paths with a single isocenter (isocentric point), beam paths with multiple isocenters (isocentric points), or beam paths with a non-isometric approach.

[0025] By moving the robotic arm 1202, the LINAC 1201 can be positioned at multiple different nodes (predefined locations where the LINAC 1201 stops and delivers radiation) during treatment. At the nodes, the LINAC 1201 can deliver one or more radiation treatment beams to the target, where the shape of the radiation beam is determined by the position of the leaves in the MLC 1205. The nodes can be positioned in an approximately spherical distribution around the patient. The specific number of nodes, and the number of treatment beams applied to each node, may vary depending on the location and type of pathological anatomy to be treated.

[0026] In another embodiment, the robotic arm 1202, and the LINAC 1201 at its end, can move continuously between nodes while radiation is being delivered. The shape and two-dimensional intensity map of the radiation beam are determined by the rapid movement of leaves in the MLC 1205 while the LINAC 1201 operates continuously.

[0027] The radiation therapy system 1200 includes an imaging system 1210. The imaging system 1210 includes a processing unit 1230 connected to x-ray sources 1203A and 1203B (i.e., imaging sources) and to stationary x-ray detectors 1204A and 1204B. Alternatively, if the x-ray sources 1203A, 1203B and / or x-ray detectors 1204A, 1204B are movable, they may be repositioned to maintain alignment with the target or to image the target from different directions, and many x-ray images may be acquired to reconstruct a three-dimensional (3D) cone-beam computed tomography (CT). In one embodiment, the LINAC 1201 functions as the imaging source, and the power level of the LINAC is reduced to a level suitable for imaging.

[0028] The imaging system 1210 may perform computed tomography (CT), such as cone-beam CT or helical megavoltage computed tomography (MVCT), and the images generated by the imaging system 1210 may be two-dimensional (2D) or three-dimensional (3D). Two X-ray sources 1203A and 1203B may be mounted in fixed positions on the ceiling of the operating room and positioned to project X-ray imaging beams from two different angular positions (e.g., 90 degrees apart) to intersect at the machine isocenter (referred to herein as the treatment center, which provides a reference point for positioning the patient on the treatment couch 1206 during treatment) and project the imaging planes of the respective X-ray detectors 1204A and 1204B after passing through the patient. In one embodiment, the imaging system 1210 provides a volumetric image of the target and a surrounding volume of interest (VOI). In other embodiments, imaging system 1210 may include more than two or less than two x-ray sources and more than two or less than two detectors, any of which may be movable rather than fixed, and in still other embodiments, the positions of the x-ray sources and detectors may be interchanged. X-ray detectors 1204A and 1204B may be fabricated from a scintillation material (e.g., amorphous silicon) that converts X-rays into visible light. In this case, an array of CMOS (Complementary Metal Oxide Silicon) or CCD (Charge Coupled Device) imaging cells converts the light into a digital image, as is well known to those skilled in the art. This digital image can be compared to a reference image during an image registration process, in which the coordinate system of the digital image is transformed to that of the reference image. The reference image can be, for example, a digitally reconstructed radiograph (DRR), which is a virtual X-ray image created from a three-dimensional (3D) CT image and generated by simulating the X-ray image formation process through the CT image.

[0029] In one embodiment, radiation therapy system 1200, which is an IGRT (Image Guided Radiation Therapy) delivery system, also includes a secondary imaging system 1239. Secondary imaging system 1239 can be a CBCT (Cone Beam Computed Tomography) imaging system, or alternatively, other types of volumetric imaging systems. The secondary imaging system 1239 includes a rotating gantry 1240 (e.g., a ring) mounted on an arm and rail system (not shown). The arm and rail system moves the rotating gantry 1240 along one or more axes (e.g., along an axis extending from the head to the foot of the couch 1206). An imaging source 1245 and a detector 1250 are mounted on the rotating gantry 1240. The rotating gantry 1240 can rotate 360 ​​degrees about the axis extending from the head to the foot of the couch. Thus, the imaging source 1245 and the detector 1250 can be positioned at many different angles. In one embodiment, imaging source 1245 is an X-ray source and detector 1250 is an X-ray detector. In one embodiment, secondary imaging system 1239 includes two independently rotatable rings, where imaging source 1245 can be attached to the first ring and detector 1250 can be attached to the second ring. In one embodiment, the rotating gantry 1240 is stationary at the foot of the treatment couch to avoid collision with the robotic arm 1202 during delivery of the therapeutic radiation beam.

[0030] 1B, the image-guided radiation therapy system 1200 can be further coupled to a treatment delivery workstation 150 (a computer control system), which may be located remotely from the radiation therapy system 1200 in a different room than the treatment room in which the radiation therapy system 1200 and the patient are located. The treatment delivery workstation 150 includes a processing unit (which may be the processing unit 1230 or another processing unit) and memory that allows it to modify treatment delivery to the patient 1225 based on target movement detected according to one or more image registrations, as described herein.

[0031] FIG. 1C shows a C-arm radiation delivery system 1400. In one embodiment, the C-arm radiation delivery system 1400 can adjust the beam energy of the LINAC during treatment, allowing the LINAC to be used for both radiography and radiation therapy. In another embodiment, the C-arm radiation delivery system 1400 may incorporate an on-board kV imaging system for producing X-ray images and a separate LINAC for producing higher energy therapeutic radiation beams. The C-arm radiation delivery system 1400 includes a C-arm gantry 1410, a LINAC 1420, an MLC 1470 coupled to the distal end of the LINAC 1420 for beamforming, and a portal imaging detector 1450. The C-arm gantry 1410 is rotatable to an angle corresponding to a selected projection, and can thereby be used to acquire an X-ray image of a VOI (Volume of Interest) of a patient 1430 on a treatment couch 1440. In embodiments including a portal imaging system, the LINAC 1420 generates an x-ray beam that passes through a target in the patient 1430 and strikes the portal imaging detector 1450 to generate an x-ray image of the target. After the x-ray image of the target is generated, the beam energy of the LINAC 1420 can be increased to generate a radiation beam for treating the irradiated target area. In another embodiment, the kV imaging system can generate an x-ray beam that passes through a target in the patient 1430 to generate an x-ray image of the target. In some embodiments, the portal imaging system can acquire portal images during treatment delivery (irradiation). The portal imaging detector 1450 can measure the exit dose (exit radiation fluence) after the beam passes through the patient 1430. This allows internal or external fiducials (markers) or anatomical structures (e.g., tumors, bones, etc.) to be localized within the portal image.

[0032] Additionally, the kV imaging source or portal imaging apparatus and methods of operation described herein can also be used with other types of gantry-based systems, in which the gantry rotates the kV imaging source and LINAC about an axis that passes through the isocenter. Gantry-based systems include a ring gantry having a roughly torus shape, with the patient's body extending through the inner diameter (bore) of the ring / torus, and the kV imaging source and LINAC mounted on the outer periphery of the ring and rotating about an axis passing through the isocenter. Gantry-based systems may further include a C-arm gantry in which the kV imaging source and LINAC are cantilevered and rotated about an axis passing through the isocenter. In another embodiment, the kV imaging source and LINAC can be used in a robotic arm based system to which the kV imaging source and LINAC are attached as previously described. Aspects of the present disclosure may also be used in other such systems, such as gantry-based LINAC systems, static imaging systems associated with radiation therapy and radiosurgery, proton therapy systems using integrated image guidance, interventional radiology and intraoperative X-ray imaging systems, and the like.

[0033] 2 is an explanatory diagram illustrating an example of a radiation delivery system 200 that applies an energy conditioner to modulate electromagnetic waves to generate imaging beams and treatment beams in accordance with an embodiment of the present disclosure. In an embodiment, the radiation delivery system 200 may correspond to and include components of one of the radiation delivery systems of FIGS. 1A-1C described above.

[0034] The radiation delivery system 200 includes a microwave source 202 that generates electromagnetic waves. In some embodiments, the microwave source 202 may be a magnetron. In some embodiments, the microwave source 202 may be a klystron. In some embodiments, the microwave source 202 may be any other type of component capable of generating electromagnetic waves.

[0035] The radiation delivery system 200 can include an energy conditioner 204 operatively connected to the microwave source 202. The energy conditioner 204 can modulate the electromagnetic waves received from the microwave source 202. Energy conditioner 204 may be a mechanical or electromechanical assembly configured to modulate the electromagnetic waves. As previously described, energy conditioner 204 may modulate the energy level of the electromagnetic waves to correspond to an imaging beam, such as a kV imaging beam, or a treatment beam, such as a MV treatment beam. In embodiments, the energy regulator may include a power variator, which is described in more detail below in Figures 3A and 3B. In embodiments, the energy regulator 204 can vary the power level of the electromagnetic waves between 0 and 100% of the power of the microwave source 202. In some embodiments, the energy regulator 204 may be used to dynamically adjust the electromagnetic waves over a range of power levels during a radiation therapy session (treatment session).

[0036] The radiation delivery system 200 may include an accelerator 206 operatively connected to the energy conditioner 204 to receive the modulated electromagnetic waves. The accelerator may use the modulated electromagnetic waves to accelerate an electron beam toward an x-ray target (not shown) to generate various treatment and / or imaging beams, as previously described.

[0037] The radiation delivery system 200 may include a controller 208 operatively connected to the microwave source 202, the energy regulator 204, and the accelerator 206. The controller 208 may include a processor 210 that includes processing logic to control the microwave source 202, the energy regulator 204, and the accelerator 206. In an embodiment, processing device 210 may be provided by one or more general-purpose processing devices, such as a microprocessor, a central processing unit, etc. In an exemplary embodiment, processing device 210 may include a complex instruction set computing (CISC) microprocessor, a reduced instruction set computing (RISC) microprocessor, a very long instruction word (VLIW) microprocessor, or a processor implementing other instruction sets or a combination of instruction sets. Processing unit 210 may also be comprised of one or more special purpose processing units such as an application specific integrated circuit (ASIC), a field programmable gate array (FPGA), a digital signal processor (DSP), a network processor, or the like.

[0038] 3A is an illustration of an example of a power variator 300 including a Y-junction, according to an embodiment of the present disclosure. As previously described, the power variator 300 can be used to modulate electromagnetic waves to correspond to the energy levels of imaging and therapy beams.

[0039] In an embodiment, the power variator 300 may include a load 302a, a load 302b, a phase wand 304, a circulator 306, a Y-junction 310, a sliding short 308, or any combination thereof. A phase rod 304 is placed in the load 302b and can provide a reflection of the desired amplitude and phase. Circulator 306 is a passive device that allows electromagnetic waves that enter circulator 306 to exit through the port immediately following the port at which they entered. In some embodiments, circulator 306 may be a four-port circulator. In one embodiment, multiple circulators may be used.

[0040] The sliding short 308 is a mechanical or electromechanical assembly used to adjust the short position (e.g., electrical length) of the power variator 300. The sliding short 308 can be used to change the power level of the electromagnetic waves supplied to the accelerator. In some embodiments, the sliding short 308 may be an electromagnetically controlled short circuit in which the phase length of the electromagnetic wave is controlled by biasing of a ferrite material. In embodiments, the sliding short 308 may be a mechanical sliding short in which a plunger is mechanically moved within a rectangular waveguide to control the phase length of the electromagnetic wave. In some embodiments, other types of sliding shorts 308 may be used.

[0041] The Y-junction 310 is a junction operatively connected to the circulator 306, the load 302a, and the sliding short 308. The Y-junction 310 provides a waveguide junction that guides electromagnetic waves between the above components of the power variator 300. The Y-junction 310 may include three ports, each separated by the same or similar angles to form a "Y" shape.

[0042] 3B is an illustration of an example power variator 350 including a T-junction, according to an embodiment of the present disclosure. Power variator 350 may include similar components to power variator 300 as described above in FIG. 3A, but includes a T-junction 352 rather than a Y-junction. T-junction 352 can be a waveguide junction that guides electromagnetic waves between the load, sliding short, and circulator, as previously described. T-junction 352 includes three ports, two of which form a perpendicular axis with respect to the third port to form a "T" shape.

[0043] It should be noted that the Y-junction 310 shown in Figure 3A and the T-junction 352 shown in Figure 3B are shown for illustrative purposes only and are not intended to be limiting of the present invention. Embodiments of the present disclosure may use Y-junctions and / or T-junctions that have different appearances, geometric characteristics (shape, size, arrangement, etc.), or other characteristics than the Y-junctions and / or T-junctions illustrated in Figures 3A and 3B.

[0044] FIG. 4A is an illustration of an example multi-X-Ray target assembly 400 including multiple radiation-generating targets with different energy characteristics, according to an embodiment of the present disclosure. In some embodiments, the radiation delivery system can include a multi-X-ray target assembly 400 that includes multiple X-ray targets to maximize the X-ray production yield of each of the treatment and imaging beams. The multi-X-Ray target assembly 400 can include a treatment beam target (second target) 402 and an imaging beam target (first target) 404. Although the multi-X-Ray target assembly 400 is shown as having two X-Ray targets, embodiments of the present disclosure can include more than two X-Ray targets in the multi-X-Ray target assembly 400. Different X-Ray targets can be optimized for various beam energy levels contained in a single assembly. The positioning (arrangement) of the multi-X-Ray target assembly 400 can be adjusted to accelerate the modulated electromagnetic waves toward the appropriate X-Ray target based on the energy level of the modulated electromagnetic waves, as described below.

[0045] As previously mentioned, the electron beam 406 may be accelerated by the accelerator 206 towards the treatment beam target 402 to generate a treatment beam (e.g., a therapeutic photon beam) 408. The treatment beam target 402 is formed of a material with a high atomic number, which causes the treatment beam 408 to be generated when the electron beam 406 is accelerated towards the treatment beam target 402. In embodiments, the electron beam 406 accelerated toward the treatment beam target 402 may be modulated to an energy level corresponding to the treatment beam 408. For example, the electron beam 406 may be modulated to an energy level corresponding to a MV treatment photon beam.

[0046] FIG. 4B illustrates a multi-X-Ray target assembly 450 according to an embodiment of the present disclosure, showing an example of repositioning the multi-X-Ray target assembly 450 so that a therapeutic or imaging electron beam strikes a radiation-generating target with appropriate energy characteristics. 4B, accelerator 206 accelerates electron beam 452 at a diagnostic energy level having an energy level corresponding to imaging beam 454. In response to electron beam 452 having an energy level corresponding to imaging beam 454, multi-X-ray target assembly 450 positions imaging beam target 404 on the path of electron beam 452 by moving the target in a linear fashion (as viewed by the left arrow in the figure).

[0047] The imaging beam target 404 is formed of a material having a low atomic number and generates an imaging beam (e.g., an imaging photon beam) 454 when the electron beam 452 is accelerated toward the imaging beam target 404. In an embodiment, the imaging beam target 404 may be thinner than the treatment beam target 402 to reduce attenuation of the generated imaging beam 454.

[0048] FIG. 5 is a flow diagram of a method 500 for generating imaging and therapy beams using an energy conditioner, according to an embodiment of the present disclosure. Method 500 is performed at least in part by processing logic comprised of hardware (e.g., circuitry, dedicated logic, programmable logic, processor, processing device, central processing unit (CPU), system-on-chip (SoC), etc.), software (e.g., instructions executed / implemented on a processing device), firmware (e.g., microcode), or a combination thereof. In embodiments, each portion of method 500 may be performed by one or more components of a radiation delivery system such as those described above in FIGS. 1A-2.

[0049] Method 500, referenced in Figure 5, illustrates example functions used in various embodiments. Although specific functional blocks ("blocks") are disclosed in method 500, such blocks are exemplary. That is, embodiments may involve various other blocks or variations of the blocks described in method 500. The blocks of method 500 may be performed in an order different from the order presented, and not all of the blocks of method 500 may be performed.

[0050] The method 500 begins at block 510, where a microwave source generates electromagnetic waves for accelerating an electron beam in an accelerator of a radiation delivery system.

[0051] At block 520, the energy adjuster adjusts the electromagnetic wave to a first energy level. In an embodiment, the first energy level may correspond to the energy level of the imaging beam.

[0052] In block 530, the accelerator generates a kilovoltage (kV) imaging beam based on a first energy level. In some embodiments, the kV imaging beam may have an energy level between 50 and 1000 kV. Also, in embodiments, the imaging beam may be a MV energy beam having an energy level greater than 1000 kV. In some embodiments, multiple imaging beams having different energy levels may be used.

[0053] At block 540, processing logic of the processing device generates a three-dimensional model and / or two-dimensional projections (images) using one or more images captured by the kV imaging beam. The processing logic may generate a three-dimensional model based on two or more images (two-dimensional images) captured by the kV imaging beam.

[0054] In block 550, the energy adjuster adjusts the electromagnetic wave to a second energy level. In an embodiment, the second energy level may correspond to the energy level of the treatment beam.

[0055] In block 560, the accelerator generates a megavoltage (MV) treatment beam based on the second energy level. In embodiments, the MV treatment beam may have an energy level between 1 and 20 MV. In some embodiments, multiple treatment beams with different energy levels may be used.

[0056] In some embodiments, blocks 520-560 may be performed repeatedly to alternate between one or more imaging beams and one or more treatment beams during a treatment session. In some embodiments, blocks 520-560 may be performed during a single rotation of a gantry of a radiation delivery system. In some embodiments, blocks 520-560 may be performed during multiple rotations in the case of helical reconstruction.

[0057] FIG. 6 is a block diagram of an example computing device 600 capable of performing one or more of the operations described herein, according to some embodiments. The computing device 600 may be connected to other computing devices by a LAN, an intranet, an extranet, and / or the Internet. The computing device may operate as a server machine in a client-server network environment and as a client in a peer-to-peer (P2P) network environment. A computing device may be provided by a personal computer (PC), a set-top box (STB), a server, a network router, a switch, a bridge, or any machine that executes a set of instructions (sequential or otherwise) that specify operations to be performed by that machine. Further, although only a single computing device is illustrated, the term "computing device" is intended to include a collection of computing devices that individually or collectively execute a set (or sets) of instructions to perform the methods described herein.

[0058] The computing device 600 illustrated herein may include a processing unit (e.g., a general-purpose processor, a programmable logic device (PLD), etc.) 602, a main memory 604 (e.g., a synchronous dynamic random access memory (DRAM), a read-only memory (ROM)), a static memory 606 (e.g., a flash memory, and a data storage device 618), which may communicate with each other via a bus 630.

[0059] The processing unit 602 may be provided by one or more general-purpose processing units, such as a microprocessor, a central processing unit, or the like. As specific examples, the processing unit 602 may comprise a complex instruction set computing (CISC) microprocessor, a reduced instruction set computing (RISC) microprocessor, a very long instruction word (VLIW) microprocessor, or a processor implementing other instruction sets or combinations of instruction sets. The processing unit 602 may also include one or more application-specific processing units, such as an application-specific integrated circuit (ASIC), a field-programmable gate array (FPGA), a digital signal processor (DSP), a network processor, or the like. The processing unit 602 may also be configured to perform the operations and steps described herein in accordance with one or more aspects of the present disclosure.

[0060] Computing device 600 may further include a network interface device 608 capable of communicating with a network 620. Computing device 600 may also include a video display device 610 (e.g., a liquid crystal display (LCD) or a cathode ray tube (CRT)), an alphanumeric input device 612 (e.g., a keyboard), a cursor control device 614 (e.g., a mouse), and an audio signal generator 616 (e.g., a speaker). In one embodiment, video display device 610, alphanumeric input device 612, and cursor control device 614 may be combined into a single component or device (e.g., an LCD touch panel).

[0061] The data storage device 618 may include a computer-readable storage medium (e.g., a non-transitory computer-readable storage medium) 628 on which may be stored one or more sets of instructions including an energy modulation procedure 625 for performing the operations described herein in accordance with one or more aspects of the present disclosure. When executed by computing device 600, such instructions may reside, completely or at least partially, within primary memory 604 and / or processing unit 602, where primary memory 604 and processing unit 602 also constitute computer-readable media. Additionally, the instructions may also be transmitted to or received over network 620 via network interface unit 608.

[0062] Although computer-readable storage medium 628 is illustratively shown to be a single medium, the term "computer-readable storage medium" should be considered to include a single medium or multiple media (e.g., centralized or distributed databases and / or associated caches and servers) that store one or more sets of instructions. The term "computer-readable storage medium" also includes any medium capable of storing, encoding, or transmitting sets of instructions for execution by a machine, thereby causing the machine to perform the methods described herein. Thus, the term "computer-readable storage medium" includes, but is not limited to, solid-state memory, optical media, and magnetic media.

[0063] It should be noted that the methods and apparatus described herein are not limited to use in medical diagnostic imaging and treatment. In alternative embodiments, the methods and apparatus described herein may be used in applications outside of the medical technology field, such as industrial imaging and non-destructive testing of materials. In such applications, for example, "treatment" may generally refer to the performance of an operation controlled by a treatment planning system, which may include the application of a beam (e.g., radiation, sound, etc.). Also, "target" may refer to a non-anatomical object or region, rather than an anatomical object or region.

[0064] Although the foregoing description provides several examples of particular systems, components, methods, etc. to facilitate understanding of embodiments of the present invention, those skilled in the art may practice at least some embodiments of the present disclosure without the description of these examples. In addition, details of well-known components and methods may be omitted or shown in simple block diagram form in order to facilitate understanding of the present invention. Therefore, the disclosed content is merely exemplary, and one example may differ from other examples and still be included within the scope of the present invention.

[0065] The use of the phrase "one embodiment" or "an embodiment" herein means that a particular feature, structure, or characteristic described in connection with the embodiment is included in at least one embodiment. Thus, the appearances of the phrase "in one embodiment" or "an embodiment" in various places in this specification do not necessarily refer to the same embodiment.

[0066] Although the operations of the methods described herein are shown in a particular order, the order of the operations of each method may be changed, certain operations may be performed in reverse order, or at least some operations may be performed simultaneously with other operations. Different operations may be directed or sub-operations may be performed intermittently or alternately.

[0067] The above description of the embodiments of the present invention, including the description of the abstract concepts thereof, is not intended to limit the present invention. The embodiments and specific examples described in this specification are provided for the purpose of explaining the present invention, and various equivalent modifications can be made within the scope recognized by those skilled in the art. As used herein, the words "example" or "exemplary" are used to serve as an example or illustration. Any aspect or feature described as "example" or "exemplary" should not be construed as superior to other aspects or features. Use of the word "example" or "exemplary" is intended to present concepts in a concrete manner. The term "or" as used herein is intended to be construed as an inclusive "or" rather than an exclusive "or." That is, unless otherwise specified or clear from the context, the phrase "X includes A or B" refers to any of the natural inclusive permutations. That is, if X includes A, if X includes B, or if X includes both A and B, then in all of the foregoing cases, the condition "X includes A or B" is satisfied. Furthermore, the articles "a" and "an," as used in this specification and the appended claims, shall be construed to mean "one or more" unless the singular form is clear from the context, unless otherwise specified. Furthermore, when terms such as "first," "second," "third," and "fourth" are used in the specification, these terms are used as labels to distinguish different elements and do not necessarily dictate an order according to the numerical designation.

Claims

1. 1. A radiation irradiation system comprising a linear accelerator (LINAC), The linear accelerator a microwave source that generates electromagnetic waves; an energy conditioner operatively connected to the microwave source, the energy conditioner including a power variator that modulates electromagnetic waves generated by the microwave source, the power variator including a Y-junction operatively connected to a circulator, the Y-junction being a waveguide junction that guides electromagnetic waves between the circulator and a load; an accelerator operatively connected to the energy conditioner, the accelerator generating a kilovoltage (kV) imaging beam and a megavoltage (MV) treatment beam based on the modulated electromagnetic waves; a control device operatively connected to the microwave source, the energy regulator, and the accelerator, the control device causing the energy regulator to perform modulation of electromagnetic waves, thereby causing the accelerator to generate the kV imaging beam and the MV treatment beam.

2. 10. The radiation delivery system of claim 1, wherein the power variator includes an electromagnetic shunt design that allows for rapid adjustment of the shunt position through the use of a magnetically biased electromagnetic ferrite.

3. 10. The radiation delivery system of claim 1, wherein the power variator includes a mechanical sliding short that adjusts the short position of the power variator.

4. 10. The radiation delivery system of claim 1, further comprising a multi-x-ray target assembly including a first target for a kV imaging beam and a second target for a kV therapy beam.

5. 10. The radiation delivery system of claim 1, further comprising a processor for generating two-dimensional projections using the kV imaging beam.

6. 10. The radiation delivery system of claim 1, further comprising a processing unit for generating a three-dimensional model based on a plurality of two-dimensional images taken using the kV imaging beam.

7. 10. The radiation delivery system of claim 1, wherein the kV imaging beam and the MV therapy beam are delivered during a single rotation or multiple rotations of the gantry.

8. 8. The radiation irradiation system according to claim 7, wherein the gantry includes any one of a ring-type gantry, a C-arm-type gantry, and a robot arm.

9. 2. The radiation delivery system of claim 1, wherein the kV imaging beam and the MV treatment beam are delivered alternately.

10. 10. The radiation delivery system of claim 1, wherein the kV imaging beam has a first energy level of 50-1000 kV and the MV treatment beam has a second energy level of 1-20 MV.

11. A method for controlling a radiation irradiation system, comprising: generating electromagnetic waves by a microwave source of the radiation irradiation system for accelerating an electron beam in an accelerator of the radiation irradiation system; b) adjusting the electromagnetic waves generated by the microwave source to a first energy level by an energy adjuster of the radiation delivery system, the energy adjuster including a power variator that modulates the electromagnetic waves generated by the microwave source, the power variator including a Y-junction operatively connected to a circulator, the Y-junction providing a waveguide junction that guides the electromagnetic waves between the circulator and a load; c. generating, with the accelerator, a kilovoltage (kV) imaging beam based on the first energy level; d. adjusting the electromagnetic waves generated by the microwave source to a second energy level by the energy adjuster; e. generating a megavoltage (MV) therapeutic beam based on the second energy level with the accelerator; A method comprising:

12. 12. The method of claim 11, wherein the power variator includes an electromagnetic shunt design that allows for rapid adjustment of the shunt position through the use of a magnetically biased electromagnetic ferrite.

13. 12. The method of claim 11, wherein the power variator includes a mechanical sliding short that adjusts a short position on the power variator.

14. 12. The method of claim 11, wherein the electromagnetic waves generated by the microwave source are dynamically adjusted by the energy adjuster during a treatment session.

15. 12. The method of claim 11, further comprising generating, by a processing unit, a three-dimensional model based on a plurality of two-dimensional images captured using the kV imaging beam.

16. 12. The method of claim 11, wherein the kV imaging beam and the MV therapy beam are delivered during a single rotation or multiple rotations of the gantry.

17. A non-transitory computer-readable storage medium storing instructions that, when executed by a processor of a radiation delivery system, cause the radiation delivery system to: a) A microwave source of the radiation irradiation system generates electromagnetic waves for accelerating an electron beam in an accelerator of the radiation irradiation system. b) adjusting the electromagnetic waves generated by the microwave source to a first energy level with an energy conditioner of the radiation delivery system, wherein the energy conditioner includes a power variator that modulates the electromagnetic waves generated by the microwave source, and the power variator includes a Y-junction operatively connected to a circulator, the Y-junction providing a waveguide junction that guides the electromagnetic waves between the circulator and a load. c) generating a kilovoltage (kV) imaging beam based on the first energy level with the accelerator; d) adjusting the electromagnetic waves generated by the microwave source to a second energy level with the energy adjuster. e) generating a megavoltage (MV) therapeutic beam based on the second energy level with the accelerator;

18. 20. The non-transitory computer-readable storage medium of claim 17, further causing the processing device to generate a three-dimensional model based on a plurality of two-dimensional images captured using the kV imaging beam.

19. 20. The non-transitory computer-readable storage medium of claim 17, further causing the processing unit to generate a two-dimensional projection using the kV imaging beam.

20. 20. The non-transitory computer-readable storage medium of claim 17, wherein the electromagnetic waves generated by the microwave source are dynamically adjusted by the energy regulator during a treatment session.

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