Intensity modulated pixelated superficial radiation therapy system and method - Patents.com

Abstract

The x-ray therapy system includes an electron beam generator configured to generate an electron beam and an x-ray therapy head comprising an array of pixel source cells including sidewalls defining an x-ray transparent interior. The sidewalls include an x-ray absorbing material. The target element is positioned to generate x-ray photon radiation within the x-ray transparent pixel source cell interior when impacted by the electron beam. The electron beam control system includes a controller configured to control at least one of a direction and intensity of the electron beam to a particular one of the pixel source cells in response to a treatment plan, and then control at least one of a direction and intensity of the electron beam to at least one additional pixel source cell in response to the treatment plan. A method of treating a patient with x-ray photon radiation is also disclosed.

Description

[Technical field]

[0001] The present disclosure relates generally to radiation therapy, and more specifically to X-ray photon radiation therapy systems and methods. [Background technology]

[0002] Brachytherapy, including superficial radiotherapy, intraoperative radiotherapy, general brachytherapy, and intracavitary radiotherapy, involves the use of radiation, such as X-ray photons, as a treatment to induce apoptosis of target cells, particularly skin cancer lesions, keloids, in situ cancer lesions, and other infected cells in the epidermis, dermis, subcutaneous, and other organs and tissues of the body. During brachytherapy, care must be taken to avoid damage to healthy cells. During the administration of therapeutic X-ray photons, it is common to fabricate a shielding template made of a highly X-ray absorbing material with cutouts to allow the X-ray photons to penetrate and hit the treatment site only within the predetermined area exposed by the cutouts. The fabrication of such templates is time-consuming and imprecise. The cutouts must be of a size and contour to allow the X-ray photons to hit the cells of the target lesion. Otherwise, not all of the target cancer cells will be removed. Therefore, to ensure that the entire lesion is treated while providing some control over the exposure of surrounding tissue to the treatment beam, a treatment margin of up to 20% in some cases is permitted in the template notch design that exceeds the determined and targeted contours of the lesion. Creation of this treatment margin is subjective and complicated by the irregular surface and subsurface shapes of the lesion. Additionally, the template must be precisely positioned and attached prior to treatment, and template movement must be avoided. Summary of the Invention

[0003] An aspect of the present technology relates to an x-ray treatment system including an electron beam generator configured to generate an electron beam. The x-ray therapy system further includes an x-ray treatment head including a pixel source cell array including a plurality of pixel source cells. Each of the plurality of pixel source cells includes a sidewall defining an x-ray transparent interior of the pixel source cell. The sidewall includes an x-ray absorbing material. The pixel source cell further includes a target element that generates x-ray photon radiation within the x-ray transparent interior when impacted by the electron beam. The x-ray therapy system also includes an electron beam control system including a controller. The controller is configured to receive a treatment plan for a treatment site to be treated. The controller is also configured to select one or more pixel source cells from the plurality of pixel source cells based on the received treatment plan, the one or more pixel source cells describing a shape of the treatment site. The controller is further configured to determine at least one of a direction and an intensity of the electron beam delivered to each of the selected one or more pixel source cells based on the received treatment plan. The controller is also configured to send data to the electron beam generator and the X-ray therapy head, the data including the selected one or more pixel source cells and at least one of a direction and an intensity for each of the selected one or more pixel source cells.

[0004] It is understood that other configurations of the present technology will become readily apparent to those skilled in the art from the following detailed description, in which various configurations of the present technology are shown and described by way of example. As will be understood, the present technology is capable of other different configurations, and its several details are capable of modification in various other respects, all without departing from the scope of the present technology. Accordingly, the drawings and detailed description are to be regarded as illustrative in nature, and not as restrictive. [Brief description of the drawings]

[0005] It is to be understood, however, that the drawings show presently preferred embodiments, and that the invention is not limited to the arrangements and instrumentalities shown.

[0006] [Figure 1] FIG. 1 is a schematic diagram of an exemplary X-ray therapy system in accordance with an exemplary aspect of the present technique. [Diagram 2] FIG. 1 is a front view of an exemplary treatment head, in accordance with an exemplary aspect of the present technology; [Diagram 3] 1 is a perspective view of an exemplary pixel source cell array, in accordance with an exemplary aspect of the present technique; [Figure 3A] 1 is a partial perspective exploded view to reveal internal features of an exemplary pixel source cell array, in accordance with an exemplary aspect of the present technique. [Figure 4] 1 is a perspective view of an exemplary lesion contouring system of a pixel source cell array, in accordance with an exemplary aspect of the present technique; FIG. [Diagram 5] FIG. 1 is a side view of a mobile x-ray therapy system, in accordance with an exemplary aspect of the present technique. [Figure 6] FIG. 1 is a block diagram of components of an exemplary X-ray therapy system, in accordance with an exemplary aspect of the present technique. [Figure 7] FIG. 1 is a block diagram illustrating an exemplary method of performing X-ray therapy, in accordance with an exemplary aspect of the present technique. [Figure 8] 1 is a schematic perspective view of an alternative embodiment of a pixel source cell array, in accordance with an exemplary aspect of the present technique; [Figure 9A] FIG. 1 is a schematic diagram of a treatment head in a first stage of operation in accordance with an exemplary embodiment of the present technology. [Figure 9B] FIG. 1 is a schematic diagram of a lesion being treated in a first stage according to an exemplary embodiment of the present technology. [Figure 9C] FIG. 13 is a schematic diagram of a treatment head in a second stage of operation in accordance with an exemplary embodiment of the present technology. [Figure 9D] FIG. 1 is a schematic diagram of a lesion being treated in a second stage according to an exemplary embodiment of the present technology. [Figure 9E] FIG. 13 is a schematic diagram of a treatment head in a third stage of operation in accordance with an exemplary embodiment of the present technology. [Figure 9F] FIG. 13 is a schematic diagram of a lesion being treated in a third stage according to an exemplary embodiment of the present technology. [Figure 10A]1 is a schematic diagram of an exemplary multi-intensity pixel source x-ray hardening filter system, in accordance with an exemplary aspect of the present technique; [Figure 10B] 1 is a schematic diagram of a multi-intensity pixel source x-ray hardening filter system in a partially open position, in accordance with an exemplary embodiment of the present technique; [Figure 10C] 1 is a schematic bottom view of a multi-intensity pixelated source x-ray hardening filter system, in accordance with an exemplary embodiment of the present technique; [Figure 10D] 1 is a schematic diagram of a multi-intensity pixel source x-ray hardening filter system in a fully open position, in accordance with an exemplary embodiment of the present technique; [Figure 10E] 1 is a schematic bottom view of a multi-intensity pixelated source x-ray hardening filter system, in accordance with an exemplary embodiment of the present technique; DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0007] The detailed description set forth below is intended as a description of various configurations of the present technology and is not intended to represent the only configurations in which the present technology may be practiced. The accompanying drawings are incorporated herein and constitute a part of the detailed description. The detailed description may include specific details for the purpose of providing a thorough understanding of the present technology. However, the present technology is not limited to the specific details described herein and may be practiced without these specific details. In some instances, structures and components are shown in block diagram form to avoid obscuring the concepts of the present technology.

[0008] 1 shows a schematic diagram of an X-ray therapy system 100 in accordance with an exemplary embodiment of the present technique. The X-ray therapy system 100 includes a high voltage generator 104, a line 108, an electron beam generator 112, a focusing electromagnetic coil 116, a vacuum drift tube 118, an electron beam steering electromagnetic coil 120, a pixel cell source array 126, and a vacuum jacket 128.

[0009] The high voltage generator 104 may communicate with the electron beam generator 112 via line 108. A focusing electromagnetic coil 116 focuses the beam and passes it through a vacuum drift tube 118 to electron beam steering electromagnetic coils 120, which steer the beam 124 to a desired location on a pixel cell source array 126. A vacuum jacket 128 is provided to allow the electron beam 124 to travel to the pixel cell source array 126 without attenuation by the surrounding air.

[0010] A pixel cell source array 126 may be provided on a treatment head (e.g., treatment head 200 of FIG. 2). The pixel cell source array 126 is made up of individual pixel cells 130. The pixel source cell array 126 may be made up of a plurality of single pixel source cells 130 attached together or fabricated as a single monolithic structure to form a treatment head geometry. The pixel source cell array 126 may be in a variety of forms. These forms include planar arrays, curved arrays, and contoured arrays.

[0011] The pixel source array 126 may have between 3 and 15,000 pixel source cells 130, each with a diameter ranging from 250 micrometers to 2 cm. For example, the pixel source cell array 126 can have 3, 4, 5, 6, 7, 8, 9, 10, 20, 30, 40, 50, 60, 60, 80, 90, 100, 200, 300, 400, 500, 600, 700, 800, 900, 1000, 2000, 3000, 4000, 5000, 6000, 7000, 8000, 9000, 10000, 11000, 12000, 13000, 14000, or 15000 pixel source cells 130, and any lower and upper value range selected from these values. Each pixel source cell 130 may have a diameter of 0.25 mm, 0.5 mm, 0.75 mm, 1 mm, 2 mm, 3 mm, 4 mm, 5 mm, 6 mm, 7 mm, 8 mm, 9 mm, 10 mm, 11 mm, 12 mm, 13 mm, 14 mm, 15 mm, 16 mm, 17 mm, 18 mm, 19 mm, or 20 mm, or any larger or smaller value selected from these ranges.

[0012] The pixel source cell array 126 may be larger than the tumor to be treated. If the tumor is larger than the pixel source cell array 126, the pixel source cell array 126 may be rastered and moved to cover and encompass the entire lesion or target tissue surface to be treated. The number and dimensions of the pixel source cells 130 may depend on the desired resolution, with a greater number of pixel source cells 130 in a given area increasing the resolution and accuracy of the x-ray photon flux in covering the lesion contour while minimizing irradiation of healthy surrounding tissue. The pixel density of the pixel source cells 130 in the pixel source cell array 126 may be 1 to 25 pixels per square inch. The length of each pixel source cell 130 may be 1 mm to 100 cm. Thus, the dimensions of the pixel source cell array 126 may not be constant. In one embodiment, the entire pixel source cell array is 1 mm to 25 mm. 2 ~10cm 2 The dimensions of the axial length of the slit may be:

[0013] The pixel source cell array 126 may be large enough to irradiate the entire lesion with the x-ray photon flux emitted from the pixel source cell array 126. In some embodiments, an area larger than the pixel source cell array 126 may be treated by rastering the pixel source cell array 126. Rastering the pixel source cell array 126 may be performed, for example, by mounting the pixel source cell array 126 on a robotic arm and using appropriate positioning datums.

[0014] Each of the pixel cells 130 of the pixel source cell array 126 includes a substrate 132, a target 136, and an open interior 140. The target 136 may be provided on the substrate 132 mounted within the open interior 140 of each of the pixel cells 130. For example, the electron beam 124 may strike the target 136 of a single pixel cell 130 or a small group of pixel cells 130 to generate X-ray photons. The X-ray photons generated by the electron beam 124 striking the target 136 are confined by the walls of the pixel cell 130 to provide a pixelated, confined X-ray photon flux 144 aligned with an axis of the pixel cell 130.

[0015] The pixel source cells 130 may be individually targeted by the electron beam 124. In some examples, multiple pixel source cells 130 may be targeted with the electron beam 124 at one time, which is a subset of all pixel source cells in the pixel source cell array. The pixel source cells 130 are not limited to the geometries shown in the drawings (FIGS. 1-4, 8, 9A, 9C, and 9E) and may have any suitable cross-sectional geometry. For example, the pixel source cells 130 may have a cross-sectional geometry including at least one selected from the group consisting of a circle, a hexagon, a square, a rectangle, a triangle, a pentagon, an octagon, or a heptagon.

[0016] Any number of pixel source cells 130 may be incorporated into the array. The number, shape, and dimensions of the pixel source cells 130 are not limited to the numbers, shapes, and dimensions shown in the drawings (e.g., Figures 1-4, 8, 9A, 9C, and 9E) and may vary depending on clinical needs and applications.

[0017] X-ray therapy system 100 further includes image guidance system 148, line 152, treatment planning system (TPS) 156, line 158, central processing unit (CPU) 160, line 162, X-ray central control board 164, and line 166. Each of high voltage generator 104, image guidance system 148, TPS 156, CPU 160, and X-ray central control board 164 may represent an electronic device. The electronic device may include one or more programmable processors, one or more programmable logic circuits, and / or one or more storage devices that store instructions for the processes and logic flows executed by the programmable processors and programmable logic circuits.

[0018] The image guidance system 148 communicates to a CPU 160 via line 152. The CPU 160 communicates with the TPS 156 via line 158. The CPU 160 also communicates with an X-ray central control board 164 via line 162. The X-ray central control board 164 communicates with the high voltage generator 104 via line 166. With the aid of the image guidance system 148, the X-ray therapy system 100 is configured to deliver a precise, high resolution, intensity modulated, pixelated X-ray beam to the target treatment site.

[0019] For example, image guidance system 148 acquires anatomical and / or topological images of the target treatment area and transmits the acquired image data via line 152 to CPU 160. CPU 160 processes and transforms the image data. CPU 160 transmits the transformed image data via line 158 to TPS 156 and then via line 162 to X-ray central control board 164.

[0020] The TPS 156 generates a treatment plan by embedding image guidance data extracted from acquired images of a specified treatment site from the image guidance system 148. The treatment plan consists of the image guidance data, the activation sequence of selected pixel source cells 130 to cover the target treatment site, the desired intensity of each pixel source cell 130, and the total treatment dose for the target treatment site (a function of activation time to the target for each pixel source cell 130). The treatment plan is loaded onto the X-ray central control board 164 via the CPU 160.

[0021] The X-ray central control board 164 coordinates and controls the operation sequence of the X-ray therapy system 100. The X-ray central control board 164 controls the high voltage generator 104 based on the operation sequence of the X-ray therapy system 100. When controlled by the X-ray central control board 164, the high voltage generator 104 sets varying high voltage levels for each pixel source cell 130 in a treatment head (e.g., treatment head 200 of FIG. 2) while executing the treatment plan from the TPS 156.

[0022] For example, the x-ray central control board 164 controls the generation and deflection of the electron beam 124 toward each selected pixel source cell 130 according to the treatment plan loaded from the TPS 156. The electron beam 124 travels through a vacuum chamber 128 toward a designated pixel source cell 130. The electron beam 124 is generated in a selected high voltage range by the high voltage generator 104 and is delivered to the electron gun cathode 112 via the high voltage line 108 discretely for each pixel source cell 130 according to the treatment plan loaded from the TPS 156.

[0023] The X-ray central control board 164 sets the electron beam focal spot size (diameter) by controlling the magnetic field strength of the electron beam 124 using the focusing electromagnetic coil 116. The focused electron beam 124 is then sent through a vacuum drift tube 118 onto the electron beam steering electromagnetic coil 120. The electron beam steering electromagnetic coil 120 deflects the angle and vector of the electron beam 124 towards a selected pixel source cell 130 of a pixel source cell array 126 in a treatment head (e.g., treatment head 200 of FIG. 2). Upon striking an X-ray target 136 enclosed within the selected pixel source cell 130 and provided on a substrate 132, a collimated and well-defined X-ray photon flux emission is generated towards the designated treatment site. Collimation, X-ray beam geometry, and conformance are achieved by the high-Z cell wall structure of the pixel source 130. This sequence is repeated for each designated and selected pixel source cell 130 in a treatment head (e.g., treatment head 200 of FIG. 2) according to the treatment plan generated by the TPS 156 and sequence control by the X-ray central control board 164. The method of controlling the X-ray therapy system 100 is not limited to the method described herein and may include modified methods outside the scope of the present technology.

[0024] The X-ray therapy system 100 includes an electron beam source configured to generate an electron vortex beam. The electron beam control system includes a controller (e.g., image guidance system 148, CPU 160, TPS 156, X-ray central control board 164, high voltage generator 104), which is configured to control the electron beam generation system (e.g., electron beam generator 112, focusing electromagnetic coil 116, vacuum drift tube 118, electron beam steering electromagnetic coil 120) in response to a treatment plan of at least one of the electron beam direction and intensity to a particular one of the pixel source cells, and then in response to the treatment plan to control at least one of the electron beam direction and intensity to at least one additional pixel source cell. The steering of the electron beam is consistent with the treatment plan for a particular lesion treatment site.

[0025] The X-ray therapy system 100 employs laser-based image guidance (e.g., image guidance system 148), such as confocal imaging, to provide a treatment planning system (e.g., TPS 156) with the surface and subcutaneous anatomical features and topology of the tumor or lesion being treated, to better improve and plan the shape and intensity of the pixelated beam geometry to better cover the entire surface and depth of the lesion or tumor being treated, and to accurately plan the dose painting for each pixel source cell to more effectively treat the lesion or tumor.

[0026] The X-ray therapy system 100 allows for individual energization of pixel source cells 140 by control and steering of the electron beam as shown in FIG. 1. The electron beam 124 can be controlled to focus and steer the electron beam 124 with very small tolerances, for example, focal spot size range of 100um-2cm, and electron beam deflection range of 0.5-45 degrees. Also, the energy of the beam can be individually controlled from one pixel source cell to another. Selective control of the beam energy of each pixel source cell allows discrimination of the X-ray photon beam penetration at each single pixel source cell and adjusts the dose between corresponding irradiation areas of the target treatment site as a function of the beam on-time of each pixel source cell. Lesions have different thicknesses and grades at various subcutaneous depths, and individualized pixel source cell control of penetration and dose allows for increased efficacy and precision of treatment when greater penetration depth and enhanced dose at the treatment site are required for each target lesion. The X-ray therapy system 100 according to the present disclosure provides novel capabilities to treat each lesion with the precision and intensity required by the clinician, instead of delivering a blanket cohesive dose and treatment beam over the entire lesion, which is a compromise approach in most cases.

[0027] 2 shows a front view of a treatment head 200 in accordance with an exemplary aspect of the present technology. The treatment head 200 includes a housing 204 that contains a pixelated x-ray source cell array 208, a light source 212, and a laser beam emitter 216.

[0028] The shape of the housing 204 of the treatment head 200 is not limited to the shape shown in Figure 2 and may be other shapes. The pixelated X-ray cell source array 208 may include a structure similar or the same as the structure of the X-ray cell source array 126. The shape of the pixelated X-ray cell source array 208 may not be limited to the shape shown in Figure 2. The number of X-ray cell sources in the pixelated X-ray cell source array 208 is not limited to the number of X-ray cell sources shown in Figure 2 and may be less or more than this.

[0029] The light sources 212 are provided around the front surface of the treatment head 200. The light sources 212 include LED light sources that generate light to irradiate the target treatment area on the patient's body. The light sources 212 may be used to allow an operator to check whether the pixelated X-ray cell source array 208 covers the target treatment area. The shape and number of the light sources 212 are not limited to those shown in FIG. 2, but may include any shape or any number of light sources 212, as long as the light sources 212 irradiate light to the target treatment area and allow the operator to check whether the entire target treatment area is covered.

[0030] The laser beam emitter 216 may create a precise crosshair image of the center point of the treatment head 200 to allow the operator to confirm proper and accurate positioning and placement on the designated treatment site on the patient's body. The laser beam emitter 216 includes four laser beam emitters, however, the number of the laser beam emitters 216 may be less or more than the four shown in FIG. 2, as long as the laser beam emitters 216 are capable of creating a crosshair image of the center point of the treatment head 200.

[0031] 3 shows a perspective view of a pixel source cell array 300, in accordance with an exemplary embodiment of the present technology. The pixel source cell array 300 is made up of a plurality of individual pixel source cells 304.

[0032] 3A shows a close-up view of one of the pixel source cells 304 of the pixel source cell array 300 in accordance with an exemplary embodiment of the present technique. The pixel source cell 304 is shown partially in perspective to reveal internal features. Each pixel source cell 304 is comprised of an x-ray absorbing wall 308, an x-ray transparent interior 310, a target material 312, and one or more x-ray transparent substrate layers 316.

[0033] The x-ray absorbing walls 308 define an x-ray transparent interior 310. Provided within the x-ray transparent interior 310 of the pixel source cell 304 are a target material 312 and an x-ray transparent substrate layer 316, such that the target material 312 is supported by the x-ray transparent substrate layer 316.

[0034] The X-ray absorbing wall 308 includes an X-ray absorbing material. For example, the X-ray absorbing material includes a high-Z material. As the term high-Z material is used herein, it generally refers to a material having an atomic number of at least 21. A suitable high-Z material may be at least one selected from the group consisting of stainless steel, molybdenum (Mo), tungsten (W), and tantalum (Ta). Other X-ray absorbing materials are possible. The X-ray absorbing wall 308 confines the X-ray photon flux within the pixel source cells, such that a pixelated and confined X-ray photon flux is generated by each pixel source cell.

[0035] The x-ray transparent interior 310 defined by the x-ray absorbing walls 308 of each pixel source cell 304 may be open or may be filled or covered with an x-ray transparent material (e.g., x-ray transparent substrate layer 316). The x-ray transparent substrate layer 316 must transmit the electron beam targeted within the selected pixel source cell 304. When the x-ray transparent substrate layer 316 is provided after the target element, the x-ray transparent substrate layer 316 should transmit the x-ray photon flux generated by the target material 312. The x-ray transparent substrate layer 316 may be at least one selected from the group consisting of diamond, beryllium (Be), silicon carbide (SiC), sapphire, aluminum (Al), ceramic alumina (Al2O3), or boron nitride (BN). Other substrate materials that are transparent to the electron beam may be used for the x-ray transparent substrate layer 316.

[0036] The x-ray transparent substrate layer 316 is disposed within the x-ray transparent interior 310 and supports a target element (e.g., target material 312) and enables the target material 312 to generate x-ray photon radiation when the target material 312 is bombarded by the electron beam. For example, the target material 312 may be supported by a single x-ray transparent substrate layer 316. In some embodiments, the x-ray transparent substrate layer 316 may support the target material 312 by sandwiching the target material 312 between two x-ray transparent substrate layers 316. However, in some other embodiments, the target element may be disposed between two or more x-ray transparent substrate layers 316.

[0037] The target material 312 may be positioned to contact the X-ray absorbing walls 308 of the pixel source cell 304 such that X-ray photons generated by the electron beam striking the target material 312 are emitted into and confined by the high-Z walls (e.g., X-ray absorbing walls 308) of the pixel source cell 304. The target material 312 may be positioned to receive the steered electron beam at a center of the target material 312, thereby generating a desired X-ray photon flux that is contained and collimated by the high-Z pixel source cell walls. For example, the target material 312 may be disposed within an X-ray transparent interior 310 defined by the X-ray absorbing walls 308. In some embodiments, the target material 312 may be disposed at an end of the pixel source cell 304.

[0038] The target material 312 is formed of a material that responds to the electron beam by generating X-ray photons. Suitable target materials include, for example, molybdenum, gold, or tungsten. Other materials that efficiently generate X-ray photons with relatively high efficiency when bombarded by the electron beam can be used for the target material 312. The target element can be a single large target element associated with the entire pixel source cell array, or multiple pixel source cells clustered together. The target elements can be discrete for each pixel source cell.

[0039] The pixel source cell 304 uses an x-ray absorbing wall 308, an x-ray transparent interior 310, a target material 312, and an x-ray transparent substrate layer 316 to provide a confined and precise x-ray beam covering a geometrically defined and limited surface area. The pixel source cell 304 achieves such technological improvement by directing a focused and steered electron beam to the target material 312, such that after the steered electron beam strikes the target material 312, the x-ray photon flux generated by the target material 312 is confined by the high-Z walls, which collimate and direct the resulting x-ray photon beam toward a defined surface area (e.g., a patient treatment site) without scattering beyond the pixel source cell's geometry. This further reduces the amount of healthy cells near the patient treatment site that are exposed to x-rays. By providing multiple pixel source cells in an array, control of the steered electron beam can be used to generate a predetermined shape and contour of the target treatment site in a pixelated manner.

[0040] 4 illustrates a perspective view of a lesion contouring system 400 for a pixel source cell array, in accordance with an exemplary aspect of the present technology. The lesion contouring system includes an array of pixel source cells 404, an open interior 412, a fiber optic laser emitter 416, a fiber optic cable 420, one or more fiber optic cable clusters 422 and 424, a suitable lesion contouring laser source 426, a lesion contouring central control board 432, and connections 438 and 442.

[0041] The pixel source cells 404 each include an open interior 412. The open interiors 412 allow for the emission of x-ray photons generated by a target material (e.g., target material 312 of FIG. 3). A fiber optic laser emitter 416 is provided along the periphery of each of the open interiors 412. The fiber optic laser emitter 415 generates a laser beam that is used to define an area to be illuminated by the x-ray photons emitted through the open interior 412 on the patient's treatment site. The fiber optic laser emitter 416 receives laser light through a fiber optic cable 420. The fiber optic cable 420 may be bundled into one or more fiber optic cable clusters 422 and 424. The laser light is generated by a suitable lesion contouring laser source 426. The lesion contouring central control board 432 directs the laser light to bundle 422 via connection 438, to bundle 424 via connection 442, and thereby to fiber optic cable 420 and fiber optic laser emitter 416 according to a treatment plan for the patient's treatment site.

[0042] By providing the operator with a representation of the contour of the targeted x-ray beam on the lesion (e.g., treatment site on the patient's body), the operator can verify the exact placement and edges of the treatment beam on the actual lesion in real time. This function is accomplished by a lesion contouring module (e.g., lesion contouring system 400). Lesion contouring system 400 projects light, such as a laser, to provide the operator with an indication of the positioning of the head and pixel source cell array. The optical fiber cluster of lesion contouring system 400 may be comprised of multiple optical fiber strands, which may be provided throughout the pixel source cell array, embedded between the edges of each pixel source cell to indicate the edge points of each pixel source cell, and may be individually controllable using lesion contouring system 400 according to a treatment plan provided by a treatment planning system.

[0043] 5 shows a side view of a mobile X-ray therapy system 500 in accordance with an exemplary aspect of the present technology. The mobile X-ray therapy system 500 includes a treatment head 504, a pixel source cell array 508, an articulating arm assembly 512, a positioning motor 516, a movable base support 520, a confocal imaging head 524, a confocal imaging head data and power cable 528, a treatment planning tablet 532, one or more base load casters 536, one or more base steering casters 540, a cool air intake louver 544, and a hot air exhaust louver 548.

[0044] The therapy head 504 includes a pixel source cell array 508. The structural relationship between the therapy head 504 and the pixel source cell array 508 may be similar to the structural relationship described using the therapy head 200 of FIG. 2. The pixel source cell array 508 may have the same or similar structure as any combination of pixel source cell arrays described with respect to FIGS. 1-4. The therapy head 504 is mounted on one end of an articulating arm assembly 512. The other end of the articulating arm assembly 512 is connected to a positioning motor 516. The positioning motor 516 is mounted on a movable base support 520.

[0045] Although not shown in FIG. 5, the movable base support 520 may include an image guidance system (e.g., image guidance system 148 of FIG. 1), a CPU (e.g., CPU 160 of FIG. 1), a TPS (e.g., TPS 156 of FIG. 1), an X-ray central control board (e.g., X-ray central control board 164 of FIG. 1), and a high voltage generator (e.g., high voltage generator 104 of FIG. 1). The movable base support 520 further includes a confocal imaging head 524, which is connected to the movable base support 520 via a confocal imaging head data and power cable 528. For example, the confocal imaging head 524 may be part of an image guidance system and is used to acquire one or more anatomical and / or topological images of a treatment site on the patient's body. The acquired one or more anatomical and / or topological images are transmitted to the CPU in the movable base support 520 via the confocal imaging head data and power cable 528.

[0046] Further attached to the movable base support 520 is a treatment planning tablet 532. The treatment planning tablet 532 is a user interface that allows an operator to review one or more anatomical and / or topological images and input data and instructions (e.g., a treatment plan) for controlling the treatment head 504. For example, the treatment planning tablet 532 may be part of a TPS and receives one or more acquired anatomical and / or topological images from a CPU. The received one or more anatomical and / or topological images may be displayed on the treatment planning tablet 532 for review by an operator. The treatment planning tablet 532 may receive user input from an operator and generate a treatment plan based at least on the received one or more anatomical and / or topological images. The generated treatment plan is transmitted from the treatment planning tablet 532 via the CPU to the X-ray central control board. Based on the received treatment plan, the X-ray central control board selects one or more pixel source cells (not shown) from the pixel source cell array 508 that cover the treatment site and determines the intensity of the X-ray beam to be delivered to each of the selected one or more pixel source cells. The X-ray central control board then communicates the selected one or more pixel source cells and the corresponding intensity of the X-ray beam to the high voltage generator. Based on the communication from the X-ray central control board, the high voltage generator then communicates with the treatment head 504 and the pixel source cell array 508 to deliver a precise high resolution intensity modulated pixelated X-ray beam to the target treatment site.

[0047] The movable base support 520 may further include base loading casters 536 and base steering casters 540 to allow an operator to move the mobile X-ray therapy system 500 to a location as needed. The movable base support 520 further includes cool air intake louvers 514 and hot air exhaust louvers 548 to provide cooling air to the mobile X-ray therapy system 500.

[0048] In some embodiments, the X-ray therapy system 500 may be comprised of several interchangeable treatment heads that differ from each other by size, the number of pixel source cells in the array, the shape of the entire array, the shape and dimensions of each pixel source cell, the axis of each pixel source cell and therefore the direction of the X-ray photon flux emitted from each pixel source cell, and the arrangement of all pixel source cells in the array.

[0049] 6 is a block diagram of components of an X-ray therapy system 600 in accordance with an exemplary embodiment of the present technique. In particular, the block diagram illustrates components of the X-ray therapy system 600 and a method flow for controlling the X-ray therapy system 600 in accordance with an exemplary embodiment of the present technique.

[0050] X-ray therapy system 600 includes electron beam source 604, electron beam 606, focusing magnet 608, focused electron beam 610, steering magnet 612, directed electron beam 614, electron beam vacuum chamber 616, electron beam 618, pixel source cell array 620, high voltage generator 624, connections 626, system power bank 630, power line 628, X-ray central control board 640, power line 638, connections 642, connections 644, connections 646, CPU 648, power line 650, TPS 654, connections 656, image guidance system 660, connections 662, power line 664, and power line 670. Connections 626, 642, 644, 646, and 656 may provide bidirectional communication between the two components.

[0051] The system power bank 630 provides power to the high voltage generator 624 via power line 628, to the X-ray central control board 640 via power line 638, to the CPU 648 via power line 650, to the TPS 654 via power line 664, and to the image guidance system 660 via power line 670. The high voltage generator 624 provides power to the electron beam source 604 via connection 626.

[0052] The image guidance system 660 acquires one or more anatomical and / or topological images of a treatment site (e.g., a lesion) of the patient's body and generates image guidance data based on the acquired one or more anatomical and / or topological images. The image guidance data is communicated to the CPU 648 via connection 662. The CPU 648 also receives and provides information to the image guidance system 660 via connection 662. The CPU 648 communicates the image guidance data to the TPS 654 via connection 656. The TPS 654 generates a treatment plan based on the image guidance data. The generated treatment plan is communicated to the CPU 648 via connection 656. The CPU 648 generates instructions for controlling the electron beam source 604, the focusing magnets 608, and the steering magnets 612 based on the treatment plan and communicates the instructions to the X-ray central control board 640 via connection 644.

[0053] The X-ray central control board 640 processes these instructions and provides control signals to the focusing electromagnets 608 via connection 642 and to the steering electromagnets 612 via connection 646. The X-ray central control board 640 also provides control signals to the high voltage generator 624. The high voltage generator 624 provides a high voltage gain to the electron beam source 604 via connection 626 based on the control signals received from the X-ray central control board 640.

[0054] The electron beam source 604 generates an electron beam 606 based on control signals received from the X-ray central control board 640. That is, the electron beam generation and control in the electron beam source 604 is managed by the X-ray central control board 640 based on the treatment plan generated by the TPS 654. The electron beam 606 passes through a focusing magnet 608 which generates a focused electron beam 610. The focused electron beam 610 then enters a steering magnet 612. A directed electron beam 614 emerges and enters an electron beam vacuum chamber 616. The electron beam 618 then impinges on a pixel source cell array 620 from which an intensity modulated pixelated X-ray photon beam is generated to treat the lesion (e.g., treatment site). The CPU 648 operates and manages the X-ray therapy system 600 at a high level on the treatment site of the patient by controlling the modules, signals, and operational sequences of the system.

[0055] 7 shows a block diagram illustrating a method for intensity modulated pixelated superficial radiation therapy system 700 for X-ray therapy according to an exemplary embodiment of the present technology. The system 700 includes a treatment arm and head element control system 704, a main system control module 724, a TPS 744 (e.g., TPS 156 of FIG. 1, treatment planning tablet 532 of FIG. 5, TPS 654 of FIG. 6), an image guidance module 750 (e.g., image guidance system 148 of FIG. 1, image guidance system 660 of FIG. 6), an image guidance head 762 (e.g., confocal imaging head 524 of FIG. 5) connected and controlled by the image guidance module 750, and a lesion contouring module 780 (e.g., lesion contouring system 400 of FIG. 4).

[0056] The image guidance module 750 includes an imaging central control unit 754 and an imaging beam generator 758. The imaging central control unit 754 is connected to an image guidance head 762 via connection 760 and to the imaging beam generator via connection 759. For example, the image guidance head 762 receives image beams necessary to acquire one or more anatomical and / or topological images of a treatment site (e.g., a lesion) of a patient from the imaging beam generator 758 via connection 759. The acquired one or more anatomical and / or topological images are transmitted from the image guidance head 762 to the imaging central control unit 754 via connection 760. The imaging central control unit 754 communicates image guidance data of the acquired one or more anatomical and / or topological images to the CPU 728 of the main system module 724 via connection 770. The imaging beam generator 758 may receive instructions for controlling the image guidance head 762 from the CPU 728 of the main system module 724 via connection 774.

[0057] The main system module 724 includes a CPU 728 (e.g., CPU 160 in FIG. 1, CPU 648 in FIG. 6), a central X-ray system control board 732 (e.g., X-ray central control board 164 in FIG. 1), a high voltage generator (HVG) 736 (e.g., high voltage generator 104 in FIG. 1, high voltage generator 624 in FIG. 6), and a system power bank 740 (e.g., system power bank 630 in FIG. 6). The CPU 728 is connected to the central X-ray system control board 732 via connection 730. The central X-ray system control board 732 is connected to the HVG 736 via connection 734. The HVG is connected to the system power bank 740 via connection 738. The system power bank 740 provides power to the system 700.

[0058] Upon receiving the image guidance data from the imaging central control unit 754, the CPU 728 transmits the imaging guidance data to the TPS 744 via connection 742. The TPS 744 may provide the image guidance data to an operator of the system 700. For example, the TPS 744 may include a display (not shown) for displaying the image guidance data and a user interface (not shown) for receiving user input from the operator. In some embodiments, the display may be a touch screen that functions as the user interface. The TPS 744 may receive a treatment plan from the operator via the user interface for the treatment area of ​​the patient imaged by the image guidance head 762. The TPS 744 transmits the treatment plan to the CPU 728.

[0059] Upon receiving the treatment plan from the TPS 744, the CPU 728 selects, based on the received treatment plan, one or more pixel source cells from a pixel source cell array (not shown) in the IMVB treatment head 708 to be used to emit x-rays through the treatment site. The CPU 728 determines an intensity of x-rays for each of the selected one or more pixel source cells based on the treatment plan. The CPU 728 may further determine an angle and / or direction of emission of the x-rays. The CPU 728 transmits control signals corresponding to the selected one or more pixel source cells, the corresponding intensity of the x-rays, and the angle and / or direction of emission of the x-rays to the central x-ray system control board 732 via connection 730.

[0060] The central x-ray system control board 732 sends control signals to the high voltage generator 736 via connection 734, to the IMVB treatment head 708 via connection 720, and to the lesion contouring central control board 788 of the lesion contouring module 780 via connection 789.

[0061] When the high voltage generator 736 receives a control signal from the central x-ray system control board 732, it determines a high voltage gain based on the received control signal and provides the determined high voltage gain to an electron beam source (not shown) in the IMVB treatment head 708.

[0062] Lesion contouring module 780 includes a lesion contouring laser source 784, a lesion contouring central control board 788, and a fiber optic cluster 792. Lesion contouring laser source 784 is connected to lesion contouring central control board 788 via connection 786. Lesion contouring central control board 788 is connected to fiber optic cluster 792 via connection 790.

[0063] The fiber optic cluster 792 includes a plurality of fiber optic cables (not shown) connected to the IMVB treatment head 708 via connection 794. The lesion contouring laser source 784 receives power from the system power bank 740 via connection 785. The lesion contouring laser source 784 provides laser light to the plurality of fiber optic cables. The lesion contouring central control board 788 selects one or more of the plurality of fiber optic cables for transmitting the laser light based on control signals received from the central x-ray system control board 732.

[0064] The treatment arm and head element control system 704 includes an IMVB treatment head 708, an articulating arm 712, and an arm actuator 716. The treatment head 708 is connected to the articulating arm 712 via connection 710. The articulating arm 712 is connected to the arm actuator 716 via connection 714.

[0065] Although not shown in FIG. 7, the IMVB treatment head 708 may include a pixel source cell array (e.g., pixel source cell array 126 of FIG. 1, pixelated x-ray source cell array 208 of FIG. 2, pixel source cell array 300 of FIG. 3, pixel source cell array 508 of FIG. 5, pixel source cell array 620 of FIG. 6). One or more pixel source cells selected from the pixel source cell array in the IMVB treatment head 708 based on a treatment plan may receive an electron beam from a high voltage generator 736. For example, the intensity of the electron beam delivered to each of the selected one or more pixel source cells may be set based on the treatment plan. In some embodiments, the intensity may be uniform across the one or more pixel source cells. In some other embodiments, the intensity may vary from pixel source cell to pixel source cell. Furthermore, in some other embodiments, the same intensity may be delivered to some of the one or more pixel source cells while different intensities may be delivered to other of the one or more pixel source cells.

[0066] The IMVB treatment head 708 may further include a fiber optic laser emitter (e.g., fiber optic laser emitter 416 of FIG. 4) (not shown). One or more fiber optic laser emitters corresponding to a selected one or more of the fiber optic cables may receive laser light from the lesion contouring laser source 784. The one or more fiber optic laser emitters form an outline on the patient's treatment site representing the perimeter of the area to be x-rayed.

[0067] The articulating arm 712 (e.g., articulating arm assembly 512 in FIG. 5) may be controlled by an arm actuator 716 according to control signals received from a central X-ray system control board 732 such that the IMVB treatment 708 is positioned over the treatment site on the patient.

[0068] FIG. 8 shows a schematic perspective view of an alternative embodiment of a pixel source cell array 802 of a treatment head 800 according to an exemplary aspect of the present technology. The treatment head 800 includes a pixel source cell array 802 made up of individual pixel source cells 806. The pixel source cell array 802 is attached to a target material 810. The target material 810 may include materials such as molybdenum, gold, or tungsten. The target material 810 may be mounted on a suitable target substrate 816. The suitable target substrate 816 may include materials such as diamond, beryllium (Be), silicon carbide (SiC), sapphire, aluminum (Al), ceramic alumina (Al203), or boron nitride (BN). Other substrate materials are possible. A focused and steered electron beam 824 strikes the target material 810. In response to the focused and steered electron beam 824 striking the target material 810, x-ray photons may be generated. X-ray photons generated from the target material 810 are confined by the walls of the individual pixel source cells 806, generating a confined X-ray photon flux 830. The X-ray photon flux 830 then irradiates the treatment area of ​​the patient.

[0069] 9A-9F show exemplary stages of a treatment operation performed using an X-ray therapy system according to exemplary aspects of the present technology. Specifically, FIGs. 9A and 9B show an exemplary first stage of the treatment operation, FIGs. 9C and 9D show an exemplary second stage of the treatment operation, and FIGs. 9E and 9F show an exemplary third state of the treatment operation according to exemplary aspects of the present technology.

[0070] FIG. 9A is a schematic diagram of a treatment head 904 during a first stage of a treatment operation, and FIG. 9B is a schematic diagram of a treatment site (e.g., a lesion) 908 of a patient being treated during a first stage of a treatment operation. The treatment head 904 may have the same or similar configuration as the treatment head 200 described in FIG. 2. A steering electromagnet (e.g., steering electromagnet 612 in FIG. 6) of an X-ray treatment system (e.g., a system described in FIGS. 1-7) steers an electron beam to a pixel source cell 916 according to a treatment plan. The pixel source cell 916 is one of the pixel source cells selected as a pixel source cell used to deliver X-ray photons to the treatment site based on the treatment plan. A fiber optic laser emitter 920 is irradiated according to the treatment plan to define the outline of an area irradiated by the X-ray photons. As shown in FIG. 9B, the fiber optic laser emitter 920 provides a laser spot 924 on the patient, which marks the outline of an area irradiated by the X-ray photons. The contour may encompass the entire treatment area 908. A corresponding flux of x-ray photons 918 generated by the electron beam transmitted through the pixel source cells 916 strikes a portion of the treatment area 908 in a first step.

[0071] FIG. 9C is a schematic diagram of the treatment head 904 during a second stage of the treatment operation, and FIG. 9D is a schematic diagram of a treatment site (e.g., lesion) 908 of a treated patient during the second stage of the treatment operation. During the second stage as shown in FIG. 9C, the steering electromagnet of the X-ray therapy system steers the electron beam to another pixel source cell 930 according to the treatment plan. The pixel source cell 930 is another one of the pixel source cells selected as the pixel source cell to be used to deliver X-ray photons to the treatment site based on the treatment plan. This causes a corresponding X-ray photon flux 932 to strike another portion of the lesion 908, as shown in FIG. 9D.

[0072] FIG. 9E is a schematic diagram of the therapy head 904 during a third stage of the therapy operation, and FIG. 9F is a schematic diagram of the treatment site (e.g., lesion) 908 of the treated patient during the third stage of the therapy operation. In the third stage as shown in FIG. 9E, the steering electromagnet of the X-ray therapy system steers the electron beam to yet another pixel source cell 940. The pixel source cell 940 is yet another one of the pixel source cells that is selected as the pixel source cell to be used to deliver X-ray photons to the treatment site based on the treatment plan. This causes a corresponding X-ray photon flux 942 to strike yet another portion of the treatment site 908, as shown in FIG. 9F. This process continues until all of the treatment site 908 is irradiated by the X-ray photon flux. The position of the X-ray photon flux can be carefully controlled by the pixel cell source array with minimal contact with healthy tissue and without the use of a shield template.

[0073] 10A shows a schematic diagram of a discrete pixel source cell x-ray hardening multi-filter system 1000 in accordance with an exemplary embodiment of the present technique. The x-ray hardening multi-filter system 1000 includes three or more hardening filter layers 1012, 1016, and 1020. The hardening filter layers 1012, 1016, and 1020 may be made of aluminum (Al) or other metallic materials to provide x-ray beam hardening functionality.

[0074] The discrete pixel source cell x-ray hardening multi-filter system 1000 provides three or more layers of x-ray multi-filtering for each pixel source cell 1021 element in a pixel source cell array (e.g., pixel source cell array 126 in FIG. 1, pixel source cell array 300 in FIG. 3, pixel source cell array 508 in FIG. 5) in a treatment head (e.g., treatment head 200 in FIG. 2, treatment head 504 in FIG. 5, treatment head 904 in FIG. 9) of the x-ray therapy system 100 of the present disclosure. The discrete pixel source cell x-ray hardening multi-filter system 1000 may provide one default filtering and beam hardening layer 1020 for all pixel source cells 1021 in the pixel source cell array of the treatment head. Two or more additional active filter layers may be embedded in the pixel source cells 1021 on the distal end of the pixel source cells 1021. The two or more additional active filter layers may be made of different materials and have different thicknesses to provide different filtering for each pixel source cell, thus providing different degrees of beam penetration to the target treatment site and tissue.

[0075] Filter layers 1012, 1016 may each be composed of one or more segments to allow for opening and closing of filter layers 1012, 1016, such as by actuator 1008. Filter layer 1012 may be composed of two segments 1024, 1028 that divide filter layer 1012 in half, as shown in Figures 10C and 10E. Filter layer 1016 may be composed of two segments 1032, 1036 that divide filter layer 1012 in half, as shown in Figures 10C and 10E.

[0076] FIG. 10B shows the segments 1032, 1036 of the filter layer 1016 in a partially open position and the filter layer 1012 in a closed position at the bottom of the pixel source cell 1021. The actuator 1008 may move the segments 1032, 1036 between the open and closed positions and vertically within the pixel source cell 1021. The actuator 1008 may also be a sensor for determining the position of the segments of the filter layer 1012, 1016. Each segment of the filter layer 1012, 1016 may have its own actuator 1008. Each actuator 1008 may have a line 1004 for operating the actuator and communicating the position of the segment. FIG. 10D shows all the segments 1024, 1028, 1032, 1036 of the filter layer 1012, 1016 in an open position near the wall of the pixel source cell 1021.

[0077] The discrete pixel source cell x-ray hardening multi-filter system 1000 may close the first filter 1016 to add it to the default filtering layer 1020, thus increasing the beam hardening and penetration to the treated tissue or lesion. The discrete pixel source cell x-ray hardening multi-filter system 1000 may also close the third layer 1012 to increase the total beam hardening filter mass and density, thus further increasing the beam transmission for each particular pixel source cell 1021 element. This configuration of the discrete pixel source cell x-ray hardening multi-filter system 1000 may be another embodiment to provide per pixel filtering regulation required by the treatment plan, controlling the intensity of the x-ray photons and the area where the x-ray photons are delivered at the individual pixel source cell level.

[0078] Reference to an element in the singular is not intended to mean only one, unless specifically stated otherwise, but rather one or more. For example, "a" module may refer to one or more modules. The term "a," "an," "the," or "said" preceding an element does not, without further constraints, preclude the presence of additional identical elements.

[0079] Phrases such as an aspect, this aspect, another aspect, some aspects, one or more aspects, an implementation, this implementation, another implementation, some implementations, one or more implementations, an embodiment, this embodiment, another embodiment, some embodiments, one or more embodiments, a configuration, this configuration, another configuration, some configurations, one or more configurations, the technology, this disclosure, the disclosure, other variations, and the like are for convenience and do not imply that the disclosure of such a phrase(s) is essential to the technology or that such disclosure applies to all configurations of the technology. The disclosure of such a phrase(s) may apply to all configurations, or to one or more configurations. The disclosure of such a phrase(s) may provide one or more examples. Phrases such as an aspect or some aspects may refer to one or more aspects, and vice versa, and this is equally true for other aforementioned phrases.

[0080] It is understood that the particular order or hierarchy of steps, operations, or processes disclosed is illustrative of an example approach. It is understood that the particular order or hierarchy of steps, operations, or processes may be performed in different orders, unless expressly stated otherwise. Some of the steps, operations, or processes may be performed simultaneously. If there are accompanying method claims, the various steps, operations, or process elements are presented in a sample order, and are not intended to be limited to the particular order or hierarchy presented. They may be performed serially, linearly, in parallel, or in different orders. It may be understood that the instructions, operations, and systems described may generally be integrated into a single software / hardware product or packaged into multiple software / hardware products.

[0081] The present disclosure is provided to enable those skilled in the art to implement the various aspects described herein. In some instances, well-known structures and components are shown in block diagram form to avoid obscuring the concepts of the present technology. The present disclosure provides various examples of the present technology, and the present technology is not limited to these examples. Various modifications of these aspects will be readily apparent to those skilled in the art, and the principles described herein may be applied to other aspects.

[0082] All structural and functional equivalents of the elements of the various embodiments described throughout the disclosure that are known or that later become known to those of ordinary skill in the art are expressly incorporated herein by reference and are intended to be encompassed by the claims. Furthermore, nothing disclosed herein is intended to be dedicated to the public, regardless of whether such disclosure is expressly recited in the claims.

[0083] The title, background, brief description of the drawings, abstract, and drawings are incorporated into this disclosure and are provided as illustrative examples of the disclosure, not as a limiting description. This disclosure is submitted with the understanding that it will not be used to limit the scope or meaning of the claims. Furthermore, in the detailed description, it will be seen that the description provides illustrative examples, and that various features have been grouped together in various implementations for the purpose of streamlining the disclosure. The method of disclosure should not be interpreted as reflecting an intention that the claimed subject matter requires more features than are expressly recited in each claim. Rather, the claims reflect inventive subject matter in less than all features of a single disclosed structure or operation. The claims are hereby incorporated into the detailed description, with each claim standing on its own as separately claimed subject matter.

[0084] The claims are not intended to be limited to the embodiments described herein, but are to be accorded the full scope consistent with the claims literally, including all legal equivalents. Nonetheless, no claim is intended to cover subject matter that does not comply with the requirements of applicable patent law, and may not be construed in such a manner.

Claims

1. 1. An x-ray therapy system comprising: an electron beam generator configured to generate an electron beam; an x-ray therapy head comprising a pixel source cell array including a plurality of pixel source cells, each of the plurality of pixel source cells comprising a sidewall defining an x-ray transparent interior of the pixel source cell, the sidewall comprising an x-ray absorbing material, the pixel source cell further comprising a target element that generates x-ray photon radiation within the x-ray transparent interior when the pixel source cell is impacted by the electron beam; and an electron beam control system comprising a controller, the controller comprising: receiving a treatment plan for a treatment area to be treated; selecting one or more pixel source cells from the plurality of pixel source cells based on the received treatment plan, the one or more pixel source cells describing a shape of the treatment area; determining at least one of a direction and an intensity of the electron beam to be delivered to each of the selected one or more pixel source cells based on the received treatment plan; and transmitting data to the electron beam generator and the X-ray therapy head, the data including the selected one or more pixel source cells and the determined at least one of the direction and the intensity for each of the selected one or more pixel source cells.

2. 10. The x-ray therapy system of claim 1, wherein the target element comprises at least one selected from the group consisting of molybdenum, gold, and tungsten.

3. The x-ray therapy system of claim 2 , wherein the target element is provided on a substrate.

4. The substrate may be made of diamond, beryllium (Be), silicon carbide (SiC), sapphire, aluminum (Al), ceramic alumina (Al ２ 0 ３ 4. The X-ray therapy system of claim 3, further comprising at least one selected from the group consisting of: SiO 2 (SiO 2 );

5. 10. The x-ray therapy system of claim 1, wherein the x-ray absorbing material comprises at least one selected from the group consisting of stainless steel, molybdenum (Mo), tungsten (W), and tantalum (Ta).

6. The x-ray therapy system of claim 1 , wherein each of the pixel source cells includes the target element within the x-ray transparent interior.

7. 7. The x-ray therapy system of claim 6, wherein the entire periphery of the target element provided within the x-ray transparent interior contacts the sidewall of the pixel source cell.

8. The x-ray therapy system of claim 1 , wherein the target element is attached to the pixel source cell array at a proximal end of the pixel source cell.

9. 10. The x-ray therapy system of claim 1, wherein the pixel source cells have a cross-sectional geometric shape comprising at least one selected from the group consisting of a circle, a hexagon, a square, a rectangle, a triangle, a pentagon, an octagon, or a heptagon.

10. 10. The x-ray therapy system of claim 1, further comprising a laser emitter disposed at a distal end of a plurality of said pixel source cells.

11. the controller selecting one or more laser emitters to form a shape that matches a contour of the treatment area; the shape formed by the selected one or more laser emitters corresponds to a perimeter of the selected one or more pixel source cells; 11. The x-ray therapy system of claim 10, wherein the controller is configured to turn on the selected one or more laser emitters when the x-ray therapy head is brought over the treatment site.

12. the substrate comprises a first substrate and a second substrate; The x-ray therapy system of claim 3 , wherein the target element is sandwiched between the first substrate and the second substrate.

13. 10. The x-ray therapy system of claim 1 further comprising a plurality of hardening filters.

14. 14. The x-ray therapy system of claim 13, wherein at least one of the plurality of hardening filters includes at least two segments that can be separated.

15. 15. The x-ray therapy system of claim 14, further comprising an actuator configured to position the at least two segments in an open position and a closed position.

16. The x-ray therapy system of claim 14, further comprising a sensor configured to determine a position of the at least two segments.

17. 15. The x-ray therapy system of claim 14, wherein two of the plurality of hardening filters each include two segments that can be separated, a separation opening between the segments of one hardening filter positioned orthogonally to a separation opening between the segments of the other hardening filter.

18. 1. A method of treating a target area of ​​a patient with x-ray photon radiation, comprising:

1. An X-ray therapy system, comprising: an electron beam generator configured to generate an electron beam; an x-ray therapy head comprising a pixel source cell array including a plurality of pixel source cells, each of the plurality of pixel source cells comprising a sidewall defining an x-ray transparent interior of the pixel source cell, the sidewall comprising an x-ray absorbing material, the pixel source cell further comprising a target element that generates x-ray photon radiation within the x-ray transparent interior when the pixel source cell is impacted by the electron beam; and an electron beam control system comprising a controller, the controller comprising: receiving a treatment plan for the treatment area to be treated; selecting one or more pixel source cells from the plurality of pixel source cells based on the received treatment plan, the one or more pixel source cells describing a shape of the treatment area; determining at least one of a direction and an intensity of the electron beam to be delivered to each of the selected one or more pixel source cells based on the received treatment plan; transmitting data to the electron beam generator and the X-ray therapy head, the data including the selected one or more pixel source cells and the determined at least one of the direction and the intensity for each of the selected one or more pixel source cells; positioning the pixel source cell array relative to a treatment site on a patient; controlling at least one of the direction and intensity of the electron beam to selectively strike a target element portion associated with a first pixel source cell to generate a constrained flux of x-ray photons that irradiates a corresponding portion of the treatment site; controlling at least one of the direction and intensity of the electron beam to selectively strike target element portions associated with second pixel source cells to generate a constrained flux of x-ray photons that irradiates different corresponding portions of the treatment site.

19. The method of claim 18 , wherein the first pixel source cell and the second pixel source cell are different.

20. 20. The method of claim 18, further comprising increasing the energy of the electron beam for certain ones of the pixel source cells associated with an increase in thickness of a treatment site.

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