Patent Application
20060072705
1. Field of the Invention
This invention relates generally to systems and methods for performing a radiation procedure, and more specifically, to systems and methods for obtaining images using a radiation machine.
2. Background of the Invention
Computed tomography is an imaging technique that has been widely used in the medical field. In a procedure for computed tomography, an x-ray source and a detector apparatus are positioned on opposite sides of a portion of a patient under examination. The x-ray source generates and directs a x-ray beam towards the patient, while the detector apparatus measures the x-ray absorption at a plurality of transmission paths defined by the x-ray beam during the process. The detector apparatus produces a voltage proportional to the intensity of incident x-rays, and the voltage is read and digitized for subsequent processing in a computer. By taking thousands of readings from multiple angles around the patient, relatively massive amounts of data are thus accumulated. The accumulated data are then analyzed and processed for reconstruction of a matrix (visual or otherwise), which constitutes a depiction of a density function of the bodily section being examined. By considering one or more of such sections, a skilled diagnostician can often diagnose various bodily ailments such as tumors, blood clots, etc.
When using computed tomography to examine bodily structures of a patient, a filter is generally placed between the patient and the x-ray source for modulating an intensity of an x-ray beam impinging on the patient during a CT scanning. Such filter is designed to reduce a dose to the patient modestly (reduce skin exposure by 30-40%) while having no detrimental effect on image quality. The cross-sectional shape of the filter, which is thin in the middle and thicker at its edges, is so configured such that the filter attenuates the beam more where the patient is the thinnest. Such arrangement compensates for differences in thicknesses over the cross-section of the patient's body so that an intensity of the x-ray beam exiting the patient is approximately uniform. Because existing filters are specially configured to provide an uniform image quality for an entire image of the patient's body, existing filters do not preferentially increase a dose (and hence improve an image quality) to a target region within the patient's body. In some cases, it may be desirable to obtain an image having a non-uniform image quality (e.g., it may be desirable to obtain good quality image for only a target region).
Also, there is a need to further reduce an overall dose of radiation delivered to a patient during a CT scan. Recently, some researchers have suggested the use of local tomography to reduce radiation dosage delivered to a patient. In this approach, the fan angle of the beam is reduced so that only a part of the patient is exposed to radiation during a CT scan. Although such technique substantially reduces radiation exposure to the patient, it is susceptible to substantial artifacts if highly attenuating structures are outside the region of interest. There are special local tomography reconstruction algorithms that can be used for reconstruction of images. However, these algorithms do not provide accurate CT numbers (Hounsfield Units). For the foregoing reason, local tomography is not suited to the use of CT scans for treatment planning applications, which requires an accurate determination of a density function of the bodily structure being examined.
For the foregoing, it would be desirable to have a method and a system for filtering radiation beam such that a dose to a target region can be increased to improve an image quality of the target region. It would also be desirable to have a method and a system for filtering radiation beam such that an overall dose of radiation delivered to a patient can be minimized or at least reduced during a radiation procedure.
In accordance with some embodiments of the invention, an apparatus for modulating an intensity of a radiation beam includes a filter having a size and a cross sectional shape such that an intensity of radiation beam filtered therethrough and passed through a patient will be substantially non-uniform.
In accordance with other embodiments of the invention, a method of modulating an intensity of a radiation beam includes directing a radiation beam towards a patient, and filtering the radiation beam such that an intensity of the radiation beam exiting the patient is substantially non-uniform.
In accordance with other embodiments of the invention, a radiation method includes generating an image using a radiation source, the image having an image of a target area and an image of non-target area, wherein a signal-to-noise ratio of the image of the target area is substantially higher than a signal-to-noise ratio of the image of the non-target area.
In accordance with other embodiments of the invention, an apparatus for modulating an intensity of a radiation beam generated by a radiation source includes a filter, and a positioner secured to the filter, the positioner configured to move the filter relative to the radiation source.
In accordance with other embodiments of the invention, a radiation method comprises placing a filter at a first position relative to a radiation source to obtain a first set of image data, and placing a filter at a second position relative to the radiation source to obtain a second set of image data.
In accordance with other embodiments of the invention, a computer program product that includes a medium is provided. The medium has a set of instruction, an execution of which by a processor causes a process to be performed, the process comprising sending a signal to move a filter relative to a radiation source.
Other aspects and features of the invention will be evident from reading the following detailed description of the preferred embodiments, which are intended to illustrate, not limit, the invention.
The drawings illustrate the design and utility of preferred embodiments of the present invention, in which similar elements are referred to by common reference numerals. In order to better appreciate how advantages and objects of the present invention are obtained, a more particular description of the present invention briefly described above will be rendered by reference to specific embodiments thereof, which are illustrated in the accompanying drawings. Understanding that these drawings depict only typical embodiments of the invention and are not therefore to be considered limiting of its scope, the invention will be described and explained with additional specificity and detail through the use of the accompanying drawings in which:
Various embodiments of the present invention are described hereinafter with reference to the figures. It should be noted that the figures are not drawn to scale and elements of similar structures or functions are represented by like reference numerals throughout the figures. It should also be noted that the figures are only intended to facilitate the description of specific embodiments of the invention. They are not intended as an exhaustive description of the invention or as a limitation on the scope of the invention. In addition, an aspect described in conjunction with a particular embodiment of the present invention is not necessarily limited to that embodiment and can be practiced in any other embodiments of the present invention.
Referring now to the drawings, in which similar or corresponding parts are identified with the same reference numeral,
In the illustrated embodiment, the control system 18 includes a processor 54, such as a computer processor, coupled to a gantry rotation control 40. The control system 18 may also include a monitor 56 for displaying data and an input device 58, such as a keyboard or a mouse, for inputting data. During a scan to acquire x-ray projection data (i.e., CT image data), the gantry 12 rotates about the patient 16. The rotation of the gantry 12 and the operation of the x-ray source 20 are controlled by the gantry rotation control 40, which provides power and timing signals to the x-ray source 20 and controls a rotational speed and position of the gantry 12 based on signals received from the processor 54. Although the control 40 is shown as a separate component from the gantry 12 and the processor 54, in alternative embodiments, the control 40 can be a part of the gantry 12 or the processor 54.
The system 10 also includes a filter 100 configured to modulate an intensity of a radiation beam. As shown in
As shown in
Attenuating portions of the radiation beam 150 going through non-target region more than the portion 152 of the radiation beam 150 going though the target region 160 is advantageous because it reduces radiation dose to non-target regions (e.g., regions 162, 164) where image quality is less critical, thereby reducing an overall dose of radiation to the patient 16. Since CT dose is characterized by a quantity (CT dose index) that averages dose over all regions of the patient 16, the CT dose index will decrease if part of the patient 16 is exposed to less radiation. Although, the above described technique will result in poorer CT image quality in the regions of the patient 16 outside of the volume of interest, in many cases, the image quality for non-target regions is less critical than that for the region of clinical interest, and the benefit of having a reduced overall dose of radiation delivered to the patient 16 outweighs the disadvantage of having poorer image quality for non-target regions.
In some embodiments, the filter 100 also allows the quality of the CT image at the target region 160 be enhanced for applications, such as radiation treatment planning and tumor targeting, where the clinical interest is focused on only a small anatomic volume. Particularly, through the use of the filter 100, more radiation dose can be delivered to the target region 160 to enhance a quality of an image of the target region 160 without exceeding a prescribed overall dose of radiation. This can be accomplished because radiation dose delivered to adjacent regions 162, 164 is reduced by the filter 100, thereby allowing more radiation dose be delivered to the target region 160. In some embodiments, a prescribed CT dose index can be maintained while using the filter 100, thereby allowing more radiation dose be delivered to the target region 160 to improve the CT image quality for the target region 160. Various techniques can be used to increase a radiation dose delivered to the target region 160. For example, the radiation source 20 can be configured to deliver a radiation beam having less energy in order to increase a radiation dose. As a result, the contrast and the signal-to-noise ratio in resulting images will increase, thereby making low contrast structures move visible. Such technique is particularly useful to obtain accurate delineation of anatomic structures, such as the prostate, which has low subject contrast.
As shown in
In any of the embodiments described herein the filter 100 can be used with a radiation source that delivers a fan beam, in which case, the filter 100 has length in a z-direction that is relatively short (
As shown in
After a first set of image data has been obtained at the first gantry rotational position, the radiation source 20 is then rotated to a second gantry rotational position. When the gantry 12 has moved the radiation source 20 to the second gantry rotational position (shown in dashed lines), the filter 200 is moved to a second position by the positioner 140 such that the thinner portion of the filter 200 is placed between a portion of a radiation beam that is directed towards the target region 160. Particularly, when the radiation source 20 is at the second gantry rotational position, the filter 200 is moved to a center position because the target region 160 is aligned with the center 230 of rotation. At the center position, the filter 200 provides less attenuation effect on a portion 322 of a radiation beam 320 that is directed towards the target region 160, and more attenuation effect on a portions 324, 326 of the radiation beam 320 that is not directed towards the target region 160. This in turn results in an attenuated radiation beam 330 exiting the patient 16 having a substantially non-uniform intensity. In the illustrated example, a portion 332 of the attenuated radiation beam 330 exiting from the target region 160 of the patient 16 has a higher intensity than the rest (e.g., portions 332, 334) of the attenuated radiation beam 330, thereby creating an image of the target region 160 that has a relatively higher SNR than that of images of the adjacent tissue regions.
Although, only two gantry rotational positions are shown, it should be understood that during an image acquisition session, the radiation source 20 can be placed at more than two gantry rotational positions to collect more than two sets of image data. For examples, the radiation source 20 can be rotated to positions that are between the two gantry rotational positions shown. The filter 200 can be, accordingly, positioned relative to the radiation source 20 in synchronization with the gantry rotational positions. In some cases, the filter 200 can be positioned relative to the radiation source 20 in a sinusoidal manner (i.e., the relative position between the filter 200 and the radiation source 20 varies in a sinusoidal manner). The range of positions at which the radiation source 20 can be placed varies. In some embodiments, the gantry 12 makes a 360° rotation around the patient 16 during an image data acquisition. Alternatively, if a full fan detector is used, the system 300 may acquire data while the gantry 12 rotates 180° plus the fan angle. Other angles of rotation may also be used, depending on the particular system being employed.
It should be noted that instead of using the filter 100 or 200 for fan beam CT or cone beam CT, any of the embodiments of the filter can be used with other imaging techniques, such as Spiral CT, laminar tomography, or the like, to reduce radiation dose to a patient and/or to enhance an image quality of a target region. As such, the configuration of the filter should not be limited to those described herein, and the filter can be variously sized and shaped to suit the need of a particular imaging technique.
Computer System Architecture
The computer system 1200 may be coupled via the bus 1202 to a display 1212, such as a cathode ray tube (CRT), for displaying information to a user. An input device 1214, including alphanumeric and other keys, is coupled to the bus 1202 for communicating information and command selections to processor 1204. Another type of user input device is cursor control 1216, such as a mouse, a trackball, or cursor direction keys for communicating direction information and command selections to processor 1204 and for controlling cursor movement on display 1212. This input device typically has two degrees of freedom in two axes, a first axis (e.g., x) and a second axis (e.g., y), that allows the device to specify positions in a plane.
One aspect of the invention is related to the use of computer system 1200 for sending timing signals to control a movement of a filter (e.g., filter 200). According to one embodiment of the invention, such use is provided by computer system 1200 in response to processor 1204 executing one or more sequences of one or more instructions contained in the main memory 1206. Such instructions may be read into the main memory 1206 from another computer-readable medium, such as storage device 1210. Execution of the sequences of instructions contained in the main memory 1206 causes the processor 1204 to perform the process steps described herein. One or more processors in a multi-processing arrangement may also be employed to execute the sequences of instructions contained in the main memory 1206. In alternative embodiments, hard-wired circuitry may be used in place of or in combination with software instructions to implement the invention. Thus, embodiments of the invention are not limited to any specific combination of hardware circuitry and software.
The term “computer-readable medium” as used herein refers to any medium that participates in providing instructions to the processor 1204 for execution. Such a medium may take many forms, including but not limited to, non-volatile media, volatile media, and transmission media. Non-volatile media includes, for example, optical or magnetic disks, such as the storage device 1210. Volatile media includes dynamic memory, such as the main memory 1206. Transmission media includes coaxial cables, copper wire and fiber optics, including the wires that comprise the bus 1202. Transmission media can also take the form of acoustic or light waves, such as those generated during radio wave and infrared data communications.
Common forms of computer-readable media include, for example, a floppy disk, a flexible disk, hard disk, magnetic tape, or any other magnetic medium, a CD-ROM, any other optical medium, punch cards, paper tape, any other physical medium with patterns of holes, a RAM, a PROM, and EPROM, a FLASH-EPROM, any other memory chip or cartridge, a carrier wave as described hereinafter, or any other medium from which a computer can read.
Various forms of computer-readable media may be involved in carrying one or more sequences of one or more instructions to the processor 1204 for execution. For example, the instructions may initially be carried on a magnetic disk of a remote computer. The remote computer can load the instructions into its dynamic memory and send the instructions over a telephone line using a modem. A modem local to the computer system 1200 can receive the data on the telephone line and use an infrared transmitter to convert the data to an infrared signal. An infrared detector coupled to the bus 1202 can receive the data carried in the infrared signal and place the data on the bus 1202. The bus 1202 carries the data to the main memory 1206, from which the processor 1204 retrieves and executes the instructions. The instructions received by the main memory 1206 may optionally be stored on the storage device 1210 either before or after execution by the processor 1204.
The computer system 1200 also includes a communication interface 1218 coupled to the bus 1202. The communication interface 1218 provides a two-way data communication coupling to a network link 1220 that is connected to a local network 1222. For example, the communication interface 1218 may be an integrated services digital network (ISDN) card or a modem to provide a data communication connection to a corresponding type of telephone line. As another example, the communication interface 1218 may be a local area network (LAN) card to provide a data communication connection to a compatible LAN. Wireless links may also be implemented. In any such implementation, the communication interface 1218 sends and receives electrical, electromagnetic or optical signals that carry data streams representing various types of information.
The network link 1220 typically provides data communication through one or more networks to other devices. For example, the network link 1220 may provide a connection through local network 1222 to a host computer 1224 or to medical equipment 1226 such as a radiation beam source or a switch operatively coupled to a radiation beam source. The data streams transported over the network link 1220 can comprise electrical, electromagnetic or optical signals. The signals through the various networks and the signals on the network link 1220 and through the communication interface 1218, which carry data to and from the computer system 1200, are exemplary forms of carrier waves transporting the information. The computer system 1200 can send messages and receive data, including program code, through the network(s), the network link 1220, and the communication interface 1218.
Although particular embodiments of the present inventions have been shown and described, it will be understood that it is not intended to limit the present inventions to the preferred embodiments, and it will be obvious to those skilled in the art that various changes and modifications may be made without departing from the spirit and scope of the present inventions. For example, the operations performed by the processor 54 can be performed by any combination of hardware and software within the scope of the invention, and should not be limited to particular embodiments comprising a particular definition of “processor”. In addition, the term “image” as used in this specification includes image data that may be stored in a circuitry or a computer-readable medium, and should not be limited to image data that is displayed visually. The specification and drawings are, accordingly, to be regarded in an illustrative rather than restrictive sense. The present inventions are intended to cover alternatives, modifications, and equivalents, which may be included within the spirit and scope of the present inventions as defined by the claims.
