Patent Grant
9950194
This disclosure relates generally to a patient positioning system for use in medical applications, such as proton therapy.
Some particle therapy systems use an accelerator to generate a particle beam for treating afflictions, such as tumors. In some particle therapy systems, particles are accelerated in orbits inside a cavity in the presence of a magnetic field, and are removed from the cavity through an extraction channel. A magnetic field regenerator generates a magnetic field bump near the outside of the cavity to distort the pitch and angle of some orbits so that they precess towards, and eventually into, the extraction channel. A beam, comprised of the particles (the “particle beam”), exits the extraction channel.
The particle beam is used to treat a patient. Typically, a tumor is targeted with the particle beam in order to destroy all or part of the tumor. Application of the particle beam to an appropriate site includes positioning the patient so that the beam can be applied to the target.
An example method for positioning a patient for treatment may comprise: associating fiducials with the patient; capturing an image of the fiducials and of an irradiation target while the patient is on a treatment couch, where the image is captured in a treatment room where treatment is to be performed; determining locations of the fiducials in the treatment room; determining locations of the fiducials in the image; determining a location of the irradiation target relative to a treatment system based on locations of the fiducials in the treatment room and in the image; and moving the treatment couch into a treatment position in the treatment room based on the location of the irradiation target. The example method may include one or more of the following features, either alone or in combination.
The image may be captured using an imaging system configured to capture internal images of the patient and of the fiducials. Determining the location of the fiducials in the treatment room may be performed using an imaging system that is configured to capture external images of the fiducials.
The image may comprise one or more of the following: an X-ray radiograph image, a computed tomography (CT) image that is captured by a CT imaging device, a magnetic resonance imaging (MRI) image that is captured by an MRI imaging device, a positron emission tomography (PET) image that is captured by a PET device, an image captured by a video surface imaging device, or an image captured by a SPECT/CT device. The image may comprise a three-dimensional (3D) image or a two-dimensional (2D) image.
The example method may further comprise treating the patient at the treatment position. Treating the patient may comprise irradiating the patient with protons using a treatment system comprising a particle accelerator system. The particle accelerator system may have an isocenter, and the isocenter may comprise the treatment position.
Determining the location of the irradiation target relative to the treatment system may comprise: determining, from the image, a location of the irradiation target relative to locations of the fiducials; determining locations of the fiducials relative to a reference coordinate system external to the image; and determining the location of the irradiation target relative to the treatment system based on the locations of the fiducials relative to the reference coordinate system and the location of the irradiation target from the image. The treatment system may have an isocenter. Moving the treatment couch into the treatment position may comprise moving the treatment couch so that the location of the irradiation target corresponds to the location of the isocenter. The reference coordinate system external to the image may be part of a real world space that includes the treatment system.
The example method may comprise securing the patient to the treatment couch relative to the fiducials; or securing the fiducials relative to the patient.
Moving the treatment couch into the treatment position may be performed using a robotic mechanism that moves the treatment couch automatically from an imaging position where the image is captured to the treatment position while the patient remains on the treatment couch. Moving the treatment couch may be performed manually while the patient remains on the treatment couch.
Associating fiducials with the patient may comprise arranging fiducials on the patient. Associating fiducials with the patient may comprise identifying anatomical landmarks on the patient, and designating the anatomical landmarks to be the fiducials. Associating fiducials with the patient may comprise arranging a frame over at least part of the patient, and securing the fiducials to the frame.
The example method may further comprise: determining an orientation of the irradiation target based on locations of the fiducials in the treatment room and in the image; and orienting the treatment based on the orientation of the irradiation target.
The example method may further comprise: tracking movement of the fiducials over time; and controlling movement of the treatment couch based on movement of the fiducials and/or controlling treatment based on movement of the fiducials. Capturing the image of the fiducials may comprise capturing the image at different times. The example method may further comprise: identifying movement of the fiducials based on different positions of the fiducials at different times; and controlling treatment based on the movement.
An example treatment system comprises: a treatment couch for holding a patient; fiducials associated with the patient; an imaging system to capture an image of the fiducials and of an irradiation target while the patient is on the treatment couch, where the image is captured in a treatment room where treatment is to be performed; a mechanism to move the treatment couch; and a computer system programmed to align locations of the fiducials to the fiducials in the image, and to determine a location of the irradiation target relative to a treatment system based on locations of the fiducials and based on the image. The movement of the treatment couch into a treatment position in the treatment room may be based on the location of the irradiation target. The example treatment system may include one or more of the following features, either alone or in combination.
The imaging system may be configured to capture internal images of the patient and of the fiducials. The imaging system may be a first imaging system and the treatment system may also comprise a second imaging system that is configured to capture external images of the fiducials.
The imaging system may comprise one or more of the following: an X-ray device to capture a radiograph image, a computed tomography (CT) device to capture a CT image, a magnetic resonance imaging (MRI) device to capture an MRI image, a positron emission tomography (PET) device to capture a PET image, an image captured by a video surface imaging device, or an image captured by a SPECT/CT device. The image may comprise a three-dimensional (3D) image or a two-dimensional (2D) image.
The example treatment system may comprise a particle accelerator system to treat the patient at the treatment position. Treating the patient may comprise irradiating the patient with protons output by the particle accelerator system. The particle accelerator system may have an isocenter, where the isocenter comprises the treatment position.
Determining the location of the irradiation target relative to the treatment system may comprise: determining, from the image, a location of the irradiation target relative to locations of the fiducials; determining locations of the fiducials relative to a reference coordinate system external to the image; and determining the location of the irradiation target relative to the treatment system based on the locations of the fiducials relative to the reference coordinate system and the location of the irradiation target from the image.
The treatment system may have an isocenter. Moving the treatment couch into the treatment position may comprise moving the treatment couch so that the location of the irradiation target corresponds to the location of the isocenter.
The reference coordinate system external to the image may be part of a real world space that includes the treatment system. The example system may comprise restraints to secure the patient to the treatment couch. The mechanism may comprise a robotic mechanism, which is configured to automatically move the treatment couch from an imaging position where the image is captured to the treatment position while the patient remains on the treatment couch.
The mechanism may be controllable to manually move the treatment couch while the patient remains on the treatment couch. The fiducials may be arranged on the patient. The fiducials may comprise anatomical landmarks on the patient. There may be a frame over at least part of the patient, and the fiducials may be secured to the frame.
The computer system may be programmed to perform operations comprising: determining an orientation of the irradiation target based on locations of the fiducials in the treatment room and in the image; and orienting the treatment based on the orientation of the irradiation target. The computer system may be programmed to perform operations comprising: tracking movement of the fiducials over time; and controlling movement of the treatment couch based on movement of the fiducials. The computer system may be programmed to perform operations comprising: tracking movement of the fiducials over time; and controlling treatment based on movement of the fiducials. Capturing the image of the fiducials may comprise capturing the image at different times; and the computer system may be programmed to perform operations comprising: identifying movement of the fiducials based on different positions of the fiducials at different times; and controlling treatment based on the movement.
Two or more of the features described in this disclosure, including those described in this summary section, may be combined to form implementations not specifically described herein.
Control of the various systems described herein, or portions thereof, may be implemented via a computer program product that includes instructions that are stored on one or more non-transitory machine-readable storage media, and that are executable on one or more processing devices (e.g., microprocessor(s), application-specific integrated circuit(s), programmed logic such as field programmable gate array(s), or the like). The systems described herein, or portions thereof, may be implemented as an apparatus, method, or electronic system that may include one or more processing devices and computer memory to store executable instructions to implement control of the stated functions.
The details of one or more implementations are set forth in the accompanying drawings and the description below. Other features, objects, and advantages will be apparent from the description and drawings, and from the claims.
Like reference symbols in the various drawings indicate like elements.
Described herein are examples of systems to position a patient for medical treatment. In some implementations, the example systems are used to position the patient for treatment using radiotherapy, such as proton or ion therapy. In some implementations, the proton or ion therapy may be performed using a system such as that described below. However, the example systems described herein may be used to position a patient for any type of medical treatment, and are not limited to radiotherapy or to use with proton or ion therapy.
In this example, treatment couch 13 includes a platform on which a patient may be disposed. The platform also may include one or more restraints (not shown) for holding the patient in place during movement of the couch and during treatment. The platform may, or may not, be padded and/or have a shape (e.g., an indentation) that corresponds to the shape of part of the patient. For example, prior to treatment, the patient may be placed in a mold that confirms that the contours of the back half of the patient, and the resulting molded structure may be incorporated into the platform of the treatment couch. A mold, such as this, incorporated into the treatment couch may reduce patient motion during movement of the treatment couch and during treatment.
A movement mechanism may move the treatment couch automatically from one position in treatment space 12 to another position in treatment space 12. For example, the movement mechanism may include a robotic arm 16 that is controllable to move the patient in six degrees of freedom, as described below. In some implementations, a manual mechanism, such as a manually movable arm, may replace the robotic arm, and be used to manually position the treatment couch. In some implementations, the couch may not be robotic. In some implementations, movement of the treatment couch may include a combination of robotic and manual positioning. Movement of the treatment couch typically occurs while the patient remains in place on the couch. For example, the treatment couch, with the patient thereon, may be moved between imaging position 18 and treatment position 19. In the imaging position, an image of the patient is captured. As described in more detail below, that image is used to position the patient for treatment in the treatment position.
In this regard, the treatment system is configured to determine the location of an irradiation target, such as a tumor, and to position the patient so that the irradiation target is in an appropriate position for treatment to be applied by proton therapy system 15. To this end, the movement mechanism (such as robotic arm 16) is configured to move treatment couch 13 between an imaging position 18 and a treatment position 19, which are both within treatment space 12, typically while the patient remains on the treatment couch. Movement may be automatic (e.g., without manual intervention) or may include a manual component. Once the patient is on the couch for imaging, in some implementations the example systems described herein do not require the patient to move off of the couch until treatment is completed. The movement mechanism may be responsive to commands from a computer system (not shown in
In some implementations, the imaging system can be a three-dimensional (3D) imaging system. In some implementations, the imaging system can be a two-dimensional (2D) imaging system. In some implementations, imaging system 14 is a computed tomography (CT) system; however, in other implementations, different types of imaging systems may be used instead of, or in addition to, a CT system. For example, the imaging system may be, or include, one or more of the following types of imaging systems: a CT system, an X-ray device to capture a radiograph image, a magnetic resonance imaging (MRI) device to capture an MRI image, a positron emission tomography (PET) device to capture a PET image, a SPECT/CT device (where SPECT is Single-photon emission computed tomography), and/or a video surface imaging device, or any combination of these imaging devices (e.g., a combination of PET/CT, PET/MRI and/or SPECT/CT devices). In some implementations, images may be captured at different points in time so as to enable tracking of movement of a fiducial due, e.g., to patient movement, such as breathing or the like.
In some implementations, imaging system 14 includes an area (e.g., a hole) for receiving a patient and for capturing a 3D image of the patient. In the CT example, the image may include internal anatomical structures, such as organs, tumors, and bones, any of which may be an irradiation target (or fiducial, as described below). Imaging system 14 captures one or more images of the patient, or a selected part of the patient, typically the part of the patient where proton therapy is to be applied. These images are used to position the patient for treatment.
In some implementations, the treatment couch may include one or more fiducials arranged thereon. Examples of fiducials 20 are shown in
In some implementations, the fiducials may be secured directly to the treatment couch. In some implementations, the fiducials may be secured directly to the patient. In some implementations, the fiducials may be integrated in the treatment couch. In some implementations, a frame (shown in the figure) may be arranged over at least part of the patient, and the fiducials may be secured to the frame. In some implementations, the fiducials may be anatomical landmarks on or inside the patient. For example, the system may identify structural elements of a person's anatomy, such as teeth, bone, or the like, and designate those structural elements as fiducials. In some implementations, fiducials may be a combination of any two or more of the foregoing, e.g., anatomical structures and/or structural elements secured to the treatment couch, to the patient, to a frame, or the like.
The fiducials may have any appropriate shape; however, they are distinguishable from other structures on or in the patient and on or in the treatment couch. For example, the fiducials may be spherical, cubical, or polyhedral in shape. In some examples, the fiducials are fixed to the treatment couch rigidly, e.g., so that the fiducials do not move in response to movement of either the patient or the treatment couch. The arrangement of the fiducials may be dependent upon the location of the irradiation target, the type of treatment to be performed, the type of image to be captured, and so forth. Imaging system 14 captures images of the patient and fiducials. Those images are used to position the patient for treatment.
As noted above, in some implementations, robotic arm 16 moves treatment couch 13 from imaging position 18 to treatment position 19. There, the patient (not shown in
In some implementations, a second imaging system is associated with (e.g., part of or in communication with) the treatment system of
The fiducials are also arranged within a local 3D coordinate system. The location and orientation of this local 3D coordinate system are stored in computer memory. During movement of the treatment couch (and thus the patient), this local coordinate system is aligned to the treatment space 3D coordinate system.
Referring to
In the example of
In this example, the images are 3D in nature such that, either alone or in combination, the images provide information about the location of the fiducials and the location of the irradiation target in 3D space. The information may also be indicative of the relative positions of the fiducials and the irradiation target, and the angles and distances between individual fiducials and between individual fiducials and the radiation target. In some example implementations, this information is obtained (34) by identifying the fiducials and the irradiation target in the image, and by analyzing images to determine the locations of the fiducials and the size and location of the irradiation target based on the locations of the fiducials (and, in some cases, based on the size and/or shape of the fiducials). This information may be stored in memory, which may be on imaging system 14, on a computer system (not shown) associated with the treatment system, or elsewhere.
In some implementations, the treatment couch may be moved (35) from the imaging position towards the treatment position 19. For example, the treatment couch may be moved from a location near to the imaging system towards a location near to the proton therapy system. The treatment couch, however, is not yet in the treatment position, since the location of the irradiation target is not yet known to the computer system that controls the positioning of the treatment couch. Rather, the treatment couch is moved into a position where the second imaging system can detect the fiducials. In some implementations, in the imaging position, the treatment couch may already be in a position where the second imaging system can detect the fiducials; therefore, movement (35) may not be necessary. In any event, the treatment couch, in particular the portion of the treatment couch containing the fiducials, is moved into, or remains in, the field of view of the imaging apparatus in the second imaging system (which is used to detect the location of the fiducials in the real-world (3D coordinate) space.
In the example implementation shown in the figures, cameras (not shown) are used to determine (36) locations of the fiducials in the real-world treatment space. The cameras may include one or more appropriate imaging devices that are capable of capturing images of the fiducials, at least. This may be done by capturing images of the fiducials when the treatment couch is within the field of view of the cameras. The resulting images may be analyzed to determine the locations of the fiducials in the treatment space. For example, the treatment space may be part of, or define, a 3D coordinate system (e.g., an XYZ Cartesian coordinate system). The treatment space may be modeled in the computer system, with the various components of the treatment system at appropriate coordinates. Images of the fiducials taken by the cameras may be analyzed to identify where, in the 3D coordinate system, the fiducials are actually located. For example, the coordinates of the fiducials in the treatment room 3D coordinate space may be stored. This information may be stored in memory, which may be on second imaging system 14, on a computer system (not shown) associated with the treatment system, or elsewhere.
The actual locations of the fiducials in the 3D coordinate system are aligned (37) to the locations of the fiducials in the CT image. More specifically, the fiducials from the CT image are placed at the locations of the actual fiducials in the 3D coordinate system, and the other structures from the CT image are placed at appropriate locations in the 3D coordinate system relative to the fiducials. This may be done, e.g., in a virtual simulation (e.g., rendering) of the treatment space. For example, the actual locations of the fiducials may be identified in the simulation, and the fiducials from the CT image, along with other structures from the CT image, may be placed at appropriate points in the simulation. By placing the fiducials and other structures from the CT image in the 3D coordinate system, it is possible to locate the structures in the 3D coordinate system and, thus, in the real-world space of the treatment system. In addition, the local 3D coordinate system established during treatment planning is aligned to the 3D coordinate system of the real-world space, thereby facilitating detection of the location of the fiducials in the real-world space.
More specifically, the location of the fiducials in the real-world space (e.g., the 3D coordinate system) is known, and the fiducials and structures, including the irradiation target, from the CT image are mapped into the 3D coordinate system in the simulation. As part of the mapping, the fiducials from the CT image are aligned to the location of the fiducials in the real-world (3D coordinate) space. Furthermore, the location of the irradiation target relative to the fiducials in the CT image is known. For example, the distances and angles of the irradiation target relative to each fiducial are known. Given this information, it is possible to determine the location of the irradiation target in the real-world (3D coordinate) space based on the locations of the fiducials in the real-world (3D coordinate) space. Specifically, the location of the irradiation target in the real-world (3D coordinate) space is at the same distances and angles from the fiducials as the irradiation target is from the fiducials in the CT image. Accordingly, using the information from the CT image, and the locations of the fiducials in real-world space, the location of the irradiation target in real-world space can be determined. Thus, determining the location of the irradiation target relative to the treatment system includes: determining, from the CT image, a location of the irradiation target relative to locations of the fiducials in the CT image; determining locations of the fiducials relative to a reference point in the 3D coordinate space that is external to the CT image (e.g., relative to the reference coordinate system); and determining the location of the irradiation target relative to the treatment system based on the locations of the fiducials relative to the reference point (e.g., relative to the reference coordinate system) and the location of the irradiation target from the CT image. The location, as used herein, may, or may not, include the orientation of the fiducials and/or the target. In this context, the orientation includes, but is not limited to, angular position in space.
As noted above, in some implementations, the numbers of fiducials used enables a computer system to use triangulation to determine the location of the irradiation target. However, any appropriate process or processes may be used to determine the location of the irradiation target. Furthermore, the CT image models a shape of the irradiation target. The shape of the irradiation target may be regular (e.g., substantially spherical) or irregular. The fiducials may be used also to determine the shape of the irradiation target by determining locations of the surfaces of the irradiation target in the real-world (3D coordinate) space. More specifically, the distances and angles between various fiducials and irradiation target surfaces may be obtained from the CT image, and that information may be used, in the manner described above, to determine the locations of surfaces of the irradiation target in the real-world (e.g., 3D coordinate) space. This information may be provided to the computer system that controls the proton therapy system in order to control application of proton beam to the irradiation target.
In this regard, some proton therapy systems scan a proton beam across depth-wise cross-sections of an irradiation target. The shape of the irradiation target, and its location in real-world space, are used in determining where the proton beam is to be applied, both in the lateral and longitudinal directions. Some proton therapy systems scatter a proton beam across the irradiation target. In those systems, the shape of the irradiation target, and its location in real-world space, are also used in determining where the scattered proton beam is to be applied.
Referring to
In some implementations, movement may be controlled automatically and solely by the computer system that controls the treatment system. In some implementations, movement may be triggered manually, e.g., by a technician, and subsequently controlled by the computer system either automatically or interactively.
Once the treatment couch, and thus the irradiation target in the patient, is in the treatment position, treatment (39) may be performed. In this example implementation, treatment comprises irradiating the patient with protons using proton therapy system 15. In other implementations, a different type of particle therapy system may be used. In other implementations, treatment may be performed using systems other than particle therapy systems or non-radiotherapy systems.
In some implementations, the treatment couch may be moved during treatment based on the location of the irradiation target. In other implementations, the treatment couch is not movable during treatment. In this regard, in some implementations, images are captured at different points in time, and the treatment is controlled based on the captured images. For example, the location of an irradiation target may change when the patient breathes (e.g., in response to movement of the patient's chest). The rhythm of the patient's breathing may be detected, and treatment may be controlled so as to provide proton therapy only at particular times, e.g., in between breaths.
In some implementations, the location or orientation of the irradiation target may require further system adjustment. For example, in some implementations, there may be six degrees of freedom through which the position of the treatment couch, and thus the patient, may be controlled. The six degrees typically are expressed as forward/backward motion, up/down motion, left/right motion (i.e., translation in three perpendicular axes) combined with rotation about three perpendicular axes, called yaw, pitch, and roll. Movement of the patient couch in this manner may be advantageous, e.g., in the event of patient movement. For example, if patient movement is detected, or if the irradiation target is not at the expected location, the patient couch may be adjusted accordingly.
In some implementations, the second imaging system may regularly capture images of the patient. These images may be compared to prior images to determine if the patient has moved. If movement is detected, adjustments to the patient couch, such as those described above, may be made. In this way, the system may track patient motion and make appropriate adjustments. For example, the system may determine an orientation of the irradiation target, and make appropriate rotational and/or translational adjustments to the patient couch so that the particle beam impacts the correct area(s) of the irradiation target. In another example, the system may determine that fiducials have moved over time (e.g., by comparing two images taken at different times), and then make appropriate adjustments to the patient couch so that the irradiation target is at the appropriate position for treatment—in this example, the system isocenter.
Described below is an example of a particle accelerator for use in a system, such as proton therapy system 15. The example particle therapy system includes a particle accelerator—in this example, a synchrocyclotron—mounted on a gantry. The gantry enables the accelerator to be rotated around a patient position, as explained in more detail below. In some implementations, the gantry is steel and has two legs mounted for rotation on two respective bearings that lie on opposite sides of a patient. The particle accelerator is supported by a steel truss that is long enough to span a treatment area in which the patient lies and that is attached at both ends to the rotating legs of the gantry. As a result of rotation of the gantry around the patient, the particle accelerator also rotates.
In an example implementation, the particle accelerator (e.g., the synchrocyclotron) includes a cryostat that holds one or more superconducting coils, each for conducting a current that generates a magnetic field (B). In this example, the cryostat uses liquid helium (He) to maintain each coil at superconducting temperatures, e.g., 4° Kelvin (K). Magnetic yokes or smaller magnetic pole pieces are located inside the cryostat, and define a cavity in which particles are accelerated.
In this example implementation, the particle accelerator includes a particle source (e.g., a Penning Ion Gauge—PIG source) to provide a plasma column to the cavity. Hydrogen gas is ionized to produce the plasma column. A voltage source provides a radio frequency (RF) voltage to the cavity to accelerate pulses of particles from the plasma column.
As noted, in an example, the particle accelerator is a synchrocyclotron. Accordingly, the RF voltage is swept across a range of frequencies to account for relativistic effects on the particles (e.g., increasing particle mass) when accelerating particles from the plasma column. The magnetic field produced by running current through a superconducting coil causes particles accelerated from the plasma column to accelerate orbitally within the cavity. In other implementations, a particle accelerator other than a synchrocyclotron may be used. For example, a cyclotron, a synchrotron, a linear accelerator, and so forth may be substituted for the synchrocyclotron described herein.
In the example synchrocyclotron, a magnetic field regenerator (“regenerator”) is positioned near the outside of the cavity (e.g., at an interior edge thereof) to adjust the existing magnetic field inside the cavity to thereby change locations (e.g., the pitch and angle) of successive orbits of the particles accelerated from the plasma column so that, eventually, the particles output to an extraction channel that passes through the cryostat. The regenerator may increase the magnetic field at a point in the cavity (e.g., it may produce a magnetic field “bump” at an area of the cavity), thereby causing each successive orbit of particles at that point to precess outwardly toward the entry point of the extraction channel until it reaches the extraction channel. The extraction channel receives particles accelerated from the plasma column and outputs the received particles from the cavity as a particle beam.
The superconducting (“main”) coils can produce relatively high magnetic fields. The magnetic field generated by a main coil may be within a range of 4 T to 20 T or more. For example, a main coil may be used to generate magnetic fields at, or that exceed, one or more of the following magnitudes: 4.0 T, 4.1 T, 4.2 T, 4.3 T, 4.4 T, 4.5 T, 4.6 T, 4.7 T, 4.8 T, 4.9 T, 5.0 T, 5.1 T, 5.2 T, 5.3 T, 5.4 T, 5.5 T, 5.6 T, 5.7 T, 5.8 T, 5.9 T, 6.0 T, 6.1 T, 6.2 T, 6.3 T, 6.4 T, 6.5 T, 6.6 T, 6.7 T, 6.8 T, 6.9 T, 7.0 T, 7.1 T, 7.2 T, 7.3 T, 7.4 T, 7.5 T, 7.6 T, 7.7 T, 7.8 T, 7.9 T, 8.0 T, 8.1 T, 8.2 T, 8.3 T, 8.4 T, 8.5 T, 8.6 T, 8.7 T, 8.8 T, 8.9 T, 9.0 T, 9.1 T, 9.2 T, 9.3 T, 9.4 T, 9.5 T, 9.6 T, 9.7 T, 9.8 T, 9.9 T, 10.0 T, 10.1 T, 10.2 T, 10.3 T, 10.4 T, 10.5 T, 10.6 T, 10.7 T, 10.8 T, 10.9 T, 11.0 T, 11.1 T, 11.2 T, 11.3 T, 11.4 T, 11.5 T, 11.6 T, 11.7 T, 11.8 T, 11.9 T, 12.0 T, 12.1 T, 12.2 T, 12.3 T, 12.4 T, 12.5 T, 12.6 T, 12.7 T, 12.8 T, 12.9 T, 13.0 T, 13.1 T, 13.2 T, 13.3 T, 13.4 T, 13.5 T, 13.6 T, 13.7 T, 13.8 T, 13.9 T, 14.0 T, 14.1 T, 14.2 T, 14.3 T, 14.4 T, 14.5 T, 14.6 T, 14.7 T, 14.8 T, 14.9 T, 15.0 T, 15.1 T, 15.2 T, 15.3 T, 15.4 T, 15.5 T, 15.6 T, 15.7 T, 15.8 T, 15.9 T, 16.0 T, 16.1 T, 16.2 T, 16.3 T, 16.4 T, 16.5 T, 16.6 T, 16.7 T, 16.8 T, 16.9 T, 17.0 T, 17.1 T, 17.2 T, 17.3 T, 17.4 T, 17.5 T, 17.6 T, 17.7 T, 17.8 T, 17.9 T, 18.0 T, 18.1 T, 18.2 T, 18.3 T, 18.4 T, 18.5 T, 18.6 T, 18.7 T, 18.8 T, 18.9 T, 19.0 T, 19.1 T, 19.2 T, 19.3 T, 19.4 T, 19.5 T, 19.6 T, 19.7 T, 19.8 T, 19.9 T, 20.0 T, 20.1 T, 20.2 T, 20.3 T, 20.4 T, 20.5 T, 20.6 T, 20.7 T, 20.8 T, 20.9 T, or more. Furthermore, a main coil may be used to generate magnetic fields that are within the range of 4 T to 20 T (or more, or less) that are not specifically listed above.
In some implementations, such as the implementation shown in
In some implementations, the return yoke and shield may be replaced by, or augmented by, an active return system. An example active return system includes one or more active return coils that conduct current in a direction opposite to current through the main superconducting coils. In some example implementations, there is an active return coil for each superconducting coil, e.g., two active return coils—one for each superconducting coil (referred to as a “main” coil). Each active return coil may also be a superconducting coil that surrounds the outside of a corresponding main superconducting coil.
Current passes through the active return coils in a direction that is opposite to the direction of current passing through the main coils. The current passing through the active return coils thus generates a magnetic field that is opposite in polarity to the magnetic field generated by the main coils. As a result, the magnetic field generated by an active return coil is able to dissipate at least some of the relatively strong stray magnetic field resulting from the corresponding main coil. In some implementations, each active return may be used to generate a magnetic field of between 2.5 T and 12 T or more.
Referring to
In an example operation, scanning magnet 108 is controllable in two dimensions (e.g., Cartesian XY dimensions) to direct the particle beam across a part (e.g., a cross-section) of an irradiation target. Ion chamber 109 detects the dosage of the beam and feeds-back that information to a control system to adjust beam movement. Energy degrader 110 is controllable to move material (e.g., one or more individual plates) into, and out of, the path of the particle beam to change the energy of the particle beam and therefore the depth to which the particle beam will penetrate the irradiation target. In this way, the energy degrader selects a depth-wise layer of an irradiation target to scan in two dimensions.
In some implementations, ion chamber 109 detects dosage (e.g., one or more individual doses) applied by the particle beam to positions on an irradiation target by detecting the numbers of ion pairs created within a gas caused by incident radiation. The numbers of ion pairs correspond to the dose provided by the particle beam. That information is fed-back to the computer system and stored in memory along with the time that the dose is provided. This information may be correlated to, and stored in association with, the location at which the dose was provided and/or
The processes described herein may be used with a single particle accelerator, and any two or more of the features thereof described herein may be used with the single particle accelerator. The particle accelerator may be used in any type of medical or non-medical application. An example of a particle therapy system that may be used is provided below. Notably, the concepts described herein may be used in other systems not specifically described.
Referring to
In some implementations, the steel gantry has two legs 408, 410 mounted for rotation on two respective bearings 412, 414 that lie on opposite sides of the patient. The accelerator is supported by a steel truss 416 that is long enough to span a treatment area 418 in which the patient lies (e.g., twice as long as a tall person, to permit the person to be rotated fully within the space with any desired target area of the patient remaining in the line of the beam) and is attached stably at both ends to the rotating legs of the gantry.
In some examples, the rotation of the gantry is limited to a range 420 of less than 360 degrees, e.g., about 180 degrees, to permit a floor 422 to extend from a wall of the vault 424 that houses the therapy system into the patient treatment area. The limited rotation range of the gantry also reduces the required thickness of some of the walls (which are not directly aligned with the beam, e.g., wall 430), which provide radiation shielding of people outside the treatment area. A range of 180 degrees of gantry rotation is enough to cover all treatment approach angles, but providing a larger range of travel can be useful. For example the range of rotation may be between 180 and 330 degrees and still provide clearance for the therapy floor space. In other implementations, rotation is not limited as described above.
The horizontal rotational axis 432 of the gantry is located nominally one meter above the floor where the patient and therapist interact with the therapy system. This floor is positioned about 3 meters above the bottom floor of the therapy system shielded vault. The accelerator can swing under the raised floor for delivery of treatment beams from below the rotational axis. The patient couch moves and rotates in a substantially horizontal plane parallel to the rotational axis of the gantry. The couch can rotate through a range 434 of about 270 degrees in the horizontal plane with this configuration. This combination of gantry and patient rotational ranges and degrees of freedom allow the therapist to select virtually any approach angle for the beam. If needed, the patient can be placed on the couch in the opposite orientation and then all possible angles can be used.
In some implementations, the accelerator uses a synchrocyclotron configuration having a high magnetic field superconducting electromagnetic structure. Because the bend radius of a charged particle of a given kinetic energy is reduced in direct proportion to an increase in the magnetic field applied to it, the high magnetic field superconducting magnetic structure permits the accelerator to be made smaller and lighter. The synchrocyclotron uses a magnetic field that is uniform in rotation angle and falls off in strength with increasing radius. Such a field shape can be achieved regardless of the magnitude of the magnetic field, so in theory there is no upper limit to the magnetic field strength (and therefore the resulting particle energy at a fixed radius) that can be used in a synchrocyclotron.
The synchrocyclotron is supported on the gantry so that the beam is generated directly in line with the patient. The gantry permits rotation of the synchrocyclotron about a horizontal rotational axis that contains a point (isocenter 440) within, or near, the patient. The split truss that is parallel to the rotational axis, supports the synchrocyclotron on both sides.
Because the rotational range of the gantry is limited in some example implementations, a patient support area can be accommodated in a wide area around the isocenter. Because the floor can be extended broadly around the isocenter, a patient support table can be positioned to move relative to and to rotate about a vertical axis 442 through the isocenter so that, by a combination of gantry rotation and table motion and rotation, any angle of beam direction into any part of the patient can be achieved. In some implementations, the two gantry arms are separated by more than twice the height of a tall patient, allowing the couch with patient to rotate and translate in a horizontal plane above the raised floor.
Limiting the gantry rotation angle allows for a reduction in the thickness of at least one of the walls surrounding the treatment room. Thick walls, typically constructed of concrete, provide radiation protection to individuals outside the treatment room. A wall downstream of a stopping proton beam may be about twice as thick as a wall at the opposite end of the room to provide an equivalent level of protection. Limiting the range of gantry rotation enables the treatment room to be sited below earth grade on three sides, while allowing an occupied area adjacent to the thinnest wall reducing the cost of constructing the treatment room.
In the example implementation shown in
The radiation therapy system described in this example is used for proton radiation therapy, but the same principles and details can be applied in analogous systems for use in heavy ion (ion) treatment systems.
As shown in
The two superconducting magnet coils are centered on a common axis and are spaced apart along the axis. The coils may be formed by of Nb3Sn-based superconducting 0.8 mm diameter strands (that initially comprise a niobium-tin core surrounded by a copper sheath) deployed in a twisted cable-in-channel conductor geometry. After seven individual strands are cabled together, they are heated to cause a reaction that forms the final (brittle) superconducting material of the wire. After the material has been reacted, the wires are soldered into the copper channel (outer dimensions 3.18×2.54 mm and inner dimensions 2.08×2.08 mm) and covered with insulation (in this example, a woven fiberglass material). The copper channel containing the wires is then wound in a coil having a rectangular cross-section. The wound coil is then vacuum impregnated with an epoxy compound. The finished coils are mounted on an annular stainless steel reverse bobbin. Heater blankets may be placed at intervals in the layers of the windings to protect the assembly in the event of a magnet quench.
The entire coil can then be covered with copper sheets to provide thermal conductivity and mechanical stability and then contained in an additional layer of epoxy. The precompression of the coil can be provided by heating the stainless steel reverse bobbin and fitting the coils within the reverse bobbin. The reverse bobbin inner diameter is chosen so that when the entire mass is cooled to 4 K, the reverse bobbin stays in contact with the coil and provides some compression. Heating the stainless steel reverse bobbin to approximately 50 degrees C. and fitting coils at a temperature of 100 degrees Kelvin can achieve this.
The geometry of the coil is maintained by mounting the coils in a “reverse” rectangular bobbin to exert a restorative force that works against the distorting force produced when the coils are energized. As shown in
Referring to
The superconducting coils are maintained at temperatures near absolute zero (e.g., about 4 degrees Kelvin) by enclosing the coil assembly (the coils and the bobbin) inside an evacuated annular aluminum or stainless steel cryostatic chamber 170 (the cryostat) that provides a free space around the coil structure, except at a limited set of support points 171, 173. In an alternate version (e.g.,
In some implementations, the temperature near absolute zero is achieved and maintained using one single-stage Gifford-McMahon cryo-cooler and three two-stage Gifford McMahon cryo-coolers. Each two stage cryo-cooler has a second stage cold end attached to a condenser that recondenses Helium vapor into liquid Helium. In some implementations, the temperature near absolute zero is achieved and maintained using a cooling channel (not shown) containing liquid helium, which is formed inside a superconducting coil support structure (e.g., the reverse bobbin), and which contains a thermal connection between the liquid helium in the channel and the corresponding superconducting coil.
In some implementations, the coil assembly and cryostatic chambers are mounted within and fully enclosed by two halves 181, 183 of a pillbox-shaped magnet yoke 100. The yoke 100 provides a path for the return magnetic field flux 184 and magnetically shields the volume 186 between the pole faces 144, 146 to prevent external magnetic influences from perturbing the shape of the magnetic field within that volume. The yoke also serves to decrease the stray magnetic field in the vicinity of the accelerator. In other implementations, the coil assembly and cryostatic chambers are mounted within and fully enclosed by a non-magnetic enclosure, and the path for return magnetic field flux is implemented using an active return system, an example of which is described above.
As shown in
Particle source 190 is fed from a supply 399 of hydrogen through a gas line 393 and tube 394 that delivers gaseous hydrogen. Electric cables 294 carry an electric current from a current source to stimulate electron discharge from cathodes 392, 390 that are aligned with the magnetic field.
In this example, the discharged electrons ionize the gas exiting through a small hole from tube 394 to create a supply of positive ions (protons) for acceleration by one semicircular (dee-shaped) radio-frequency plate that spans half of the space enclosed by the magnet structure and one dummy dee plate. Some implementations may use an interrupted particle source. In the case of an interrupted particle source all (or a substantial part, e.g., a majority) of the tube containing plasma is removed (not present) at the acceleration region.
As shown in
For the beam emerging from the centrally located particle source to clear the particle source structure as it begins to spiral outward, a large voltage difference may be applied across the radio frequency plates. 20,000 Volts is applied across the radio frequency plates. In some versions from 8,000 to 20,000 Volts may be applied across the radio frequency plates. To reduce the power required to drive this large voltage, the magnet structure is arranged to reduce the capacitance between the radio frequency plates and ground. This may be done by forming holes with sufficient clearance from the radio frequency structures through the outer yoke and the cryostat housing and making sufficient space between the magnet pole faces.
The high voltage alternating potential that drives the dee plate has a frequency that is swept downward during the accelerating cycle to account for the increasing relativistic mass of the protons and the decreasing magnetic field. The dummy dee does not require a hollow semi-cylindrical structure as it is at ground potential along with the vacuum chamber walls. Other plate arrangements could be used such as more than one pair of accelerating electrodes driven with different electrical phases or multiples of the fundamental frequency. The RF structure can be tuned to keep the Q high during the required frequency sweep by using, for example, a rotating capacitor having intermeshing rotating and stationary blades. During each meshing of the blades, the capacitance increases, thus lowering the resonant frequency of the RF structure. The blades can be shaped to create a precise frequency sweep required. A drive motor for the rotating condenser can be phase locked to the RF generator for precise control. One bunch of particles may be accelerated during each meshing of the blades of the rotating condenser.
The vacuum chamber in which the acceleration occurs is a generally cylindrical container that is thinner in the center and thicker at the rim. The vacuum chamber encloses the RF plates and the particle source and is evacuated by a vacuum pump. Maintaining a high vacuum reduces the chances that accelerating ions are not lost to collisions with gas molecules and enables the RF voltage to be kept at a higher level without arcing to ground.
Protons (or other ions) traverse a generally spiral orbital path beginning at the particle source. In half of each loop of the spiral path, the protons gain energy as they pass through the RF electric field. As the protons gain energy, the radius of the central orbit of each successive loop of their spiral path is larger than the prior loop until the loop radius reaches the maximum radius of the pole face. At that location a magnetic and electric field perturbation directs protons into an area where the magnetic field rapidly decreases, and the protons depart the area of the high magnetic field and are directed through an evacuated tube, referred to herein as the extraction channel, to exit the synchrocyclotron. A magnetic regenerator may be used to change the magnetic field perturbation to direct the protons. The protons exiting will tend to disperse as they enter an area of markedly decreased magnetic field that exists in the room around the synchrocyclotron. Beam shaping elements 507, 509 in the extraction channel 138 (
As the beam exits the extraction channel it is passed through a beam formation system 525 (
Stray magnetic fields exiting from the synchrocyclotron may be limited by both a magnet yoke (which also serves as a shield) and a separate magnetic shield 514 (e.g.,
Referring to
The gantry is driven to rotate by an electric motor mounted to one or both of the gantry legs and connected to the bearing housings by drive gears. The rotational position of the gantry is derived from signals provided by shaft angle encoders incorporated into the gantry drive motors and the drive gears.
At the location at which the ion beam exits the synchrocyclotron, the beam formation system 525 acts on the ion beam to give it properties suitable for patient treatment. For example, the beam may be spread and its depth of penetration varied to provide uniform radiation across a given target volume. The beam formation system may include active scanning elements as described herein.
All of the active systems of the synchrocyclotron (the current driven superconducting coils, the RF-driven plates, the vacuum pumps for the vacuum acceleration chamber and for the superconducting coil cooling chamber, the current driven particle source, the hydrogen gas source, and the RF plate coolers, for example), may be controlled by appropriate synchrocyclotron control electronics (not shown), which may include, e.g., one or more processing devices executing instructions from non-transitory memory to effect control.
As explained above, referring to system 602 of
The particle accelerator used in the example particle therapy systems and example scanning systems described herein may be a variable-energy particle accelerator, an example of which is described below
The energy of an extracted particle beam (the particle beam output from the accelerator) can affect the use of the particle beam during treatment. In some machines, the energy of the particle beam (or particles in the particle beam) does not increase after extraction. However, the energy may be reduced based on treatment needs after the extraction and before the treatment. Referring to
A target volume to be irradiated (an irradiation target) by a particle beam for treatment typically has a three-dimensional configuration. In some examples, to carry-out the treatment, the target volume is divided into layers along the irradiation direction of the particle beam so that the irradiation can be done on a layer-by-layer basis. For certain types of particles, such as protons, the penetration depth (or which layer the beam reaches) within the target volume is largely determined by the energy of the particle beam. A particle beam of a given energy does not reach substantially beyond a corresponding penetration depth for that energy. To move the beam irradiation from one layer to another layer of the target volume, the energy of the particle beam is changed.
In the example shown in
The energy variation for treating different layers of the target volume 924 can be performed at the accelerator 912 (e.g., the accelerator can vary the energy) so that, in some implementations, no additional energy variation is required after the particle beam is extracted from the accelerator 912. So, the optional energy degrader 920 in the treatment system 10 may be eliminated from the system. In some implementations, the accelerator 912 can output particle beams having an energy that varies between about 100 MeV and about 300 MeV, e.g., between about 115 MeV and about 250 MeV. The variation can be continuous or non-continuous, e.g., one step at a time. In some implementations, the variation, continuous or non-continuous, can take place at a relatively high rate, e.g., up to about 50 MeV per second or up to about 20 MeV per second. Non-continuous variation can take place one step at a time with a step size of about 10 MeV to about 90 MeV.
When irradiation is complete in one layer, the accelerator 912 can vary the energy of the particle beam for irradiating a next layer, e.g., within several seconds or within less than one second. In some implementations, the treatment of the target volume 924 can be continued without substantial interruption or even without any interruption. In some situations, the step size of the non-continuous energy variation is selected to correspond to the energy difference needed for irradiating two adjacent layers of the target volume 924. For example, the step size can be the same as, or a fraction of, the energy difference.
In some implementations, the accelerator 912 and the degrader 920 collectively vary the energy of the beam 914. For example, the accelerator 912 provides a coarse adjustment and the degrader 920 provides a fine adjustment or vice versa. In this example, the accelerator 912 can output the particle beam that varies energy with a variation step of about 10-80 MeV, and the degrader 920 adjusts (e.g., reduces) the energy of the beam at a variation step of about 2-10 MeV.
The reduced use (or absence) of the energy degrader, such as a range modulator, may help to maintain properties and quality of the output beam from the accelerator, e.g., beam intensity. The control of the particle beam can be performed at the accelerator. Side effects, e.g., from neutrons generated when the particle beam passes the degrader 920 can be reduced or eliminated.
The energy of the particle beam 914 may be adjusted to treat another target volume 930 in another body or body part 922′ after completing treatment in target volume 924. The target volumes 924, 930 may be in the same body (or patient), or in different patients. It is possible that the depth D of the target volume 930 from a surface of body 922′ is different from that of the target volume 924. Although some energy adjustment may be performed by the degrader 920, the degrader 912 may only reduce the beam energy and not increase the beam energy.
In this regard, in some cases, the beam energy required for treating target volume 930 is greater than the beam energy required to treat target volume 924. In such cases, the accelerator 912 may increase the output beam energy after treating the target volume 924 and before treating the target volume 930. In other cases, the beam energy required for treating target volume 930 is less than the beam energy required to treat target volume 924. Although the degrader 920 can reduce the energy, the accelerator 912 can be adjusted to output a lower beam energy to reduce or eliminate the use of the degrader 920. The division of the target volumes 924, 930 into layers can be different or the same. The target volume 930 can be treated similarly on a layer by layer basis to the treatment of the target volume 924.
The treatment of the different target volumes 924, 930 on the same patient may be substantially continuous, e.g., with the stop time between the two volumes being no longer than about 30 minutes or less, e.g., 25 minutes or less, 20 minutes or less, 15 minutes or less, 10 minutes or less, 5 minutes or less, or 1 minute or less. As explained herein, the accelerator 912 can be mounted on a movable gantry and the movement of the gantry can move the accelerator to aim at different target volumes. In some situations, the accelerator 912 can complete the energy adjustment of the output beam 914 during the time the treatment system makes adjustment (such as moving the gantry) after completing the treatment of the target volume 924 and before starting treating the target volume 930. After the alignment of the accelerator and the target volume 930, the treatment can begin with the adjusted, desired beam energy. Beam energy adjustment for different patients can also be completed relatively efficiently. In some examples, all adjustments, including increasing/reducing beam energy and/or moving the gantry are done within about 30 minutes, e.g., within about 25 minutes, within about 20 minutes, within about 15 minutes, within about 10 minutes or within about 5 minutes.
In the same layer of a target volume, an irradiation dose may be applied by moving the beam across the two-dimensional surface of the layer (which is sometimes called scanning beam) using a scanning unit 916. Alternatively, the layer can be irradiated by passing the extracted beam through one or more scatterers of the scattering unit 16 (which is sometimes called scattering beam).
Beam properties, such as energy and intensity, can be selected before a treatment or can be adjusted during the treatment by controlling the accelerator 912 and/or other devices, such as the scanning unit/scatterer(s) 916, the degrader 920, and others not shown in the figures. In example implementations, system 910 includes a controller 932, such as a computer, in communication with one or more devices in the system. Control can be based on results of the monitoring performed by the one or more monitors 918, e.g., monitoring of the beam intensity, dose, beam location in the target volume, etc. Although the monitors 918 are shown to be between the device 916 and the degrader 920, one or more monitors can be placed at other appropriate locations along the beam irradiation path. Controller 932 can also store a treatment plan for one or more target volumes (for the same patient and/or different patients). The treatment plan can be determined before the treatment starts and can include parameters, such as the shape of the target volume, the number of irradiation layers, the irradiation dose for each layer, the number of times each layer is irradiated, etc. The adjustment of a beam property within the system 910 can be performed based on the treatment plan. Additional adjustment can be made during the treatment, e.g., when deviation from the treatment plan is detected.
In some implementations, the accelerator 912 is configured to vary the energy of the output particle beam by varying the magnetic field in which the particle beam is accelerated. In an example implementation, one or more sets of coils receives variable electrical current to produce a variable magnetic field in the cavity. In some examples, one set of coils receives a fixed electrical current, while one or more other sets of coils receives a variable current so that the total current received by the coil sets varies. In some implementations, all sets of coils are superconducting. In other implementations, some sets of coils, such as the set for the fixed electrical current, are superconducting, while other sets of coils, such as the one or more sets for the variable current, are non-superconducting. In some examples, all sets of coils are non-superconducting.
Generally, the magnitude of the magnetic field is scalable with the magnitude of the electrical current. Adjusting the total electric current of the coils in a predetermined range can generate a magnetic field that varies in a corresponding, predetermined range. In some examples, a continuous adjustment of the electrical current can lead to a continuous variation of the magnetic field and a continuous variation of the output beam energy. Alternatively, when the electrical current applied to the coils is adjusted in a non-continuous, step-wise manner, the magnetic field and the output beam energy also varies accordingly in a non-continuous (step-wise) manner. The scaling of the magnetic field to the current can allow the variation of the beam energy to be carried out relatively precisely, although sometimes minor adjustment other than the input current may be performed.
In some implementations, to output particle beams having a variable energy, the accelerator 912 is configured to apply RF voltages that sweep over different ranges of frequencies, with each range corresponding to a different output beam energy. For example, if the accelerator 912 is configured to produce three different output beam energies, the RF voltage is capable of sweeping over three different ranges of frequencies. In another example, corresponding to continuous beam energy variations, the RF voltage sweeps over frequency ranges that continuously change. The different frequency ranges may have different lower frequency and/or upper frequency boundaries.
The extraction channel may be configured to accommodate the range of different energies produced by the variable-energy particle accelerator. For example the extraction channel may be large enough to support the highest and lowest energies produced by the particle accelerator. That is, the extraction channel may be sized or otherwise configured to receive and to transmit particles within that range of energies. Particle beams having different energies can be extracted from the accelerator 912 without altering the features of the regenerator that is used for extracting particle beams having a single energy. In other implementations, to accommodate the variable particle energy, the regenerator can be moved to disturb (e.g., change) different particle orbits in the manner described above and/or iron rods (magnetic shims) can be added or removed to change the magnetic field bump provided by the regenerator. More specifically, different particle energies will typically be at different particle orbits within the cavity. By moving the regenerator, it is possible to intercept a particle orbit at a specified energy and thereby provide the correct perturbation of that orbit so that particles at the specified energy reach the extraction channel. In some implementations, movement of the regenerator (and/or addition/removal of magnetic shims) is performed in real-time to match real-time changes in the particle beam energy output by the accelerator. In other implementations, particle energy is adjusted on a per-treatment basis, and movement of the regenerator (and/or addition/removal of magnetic shims) is performed in advance of the treatment. In either case, movement of the regenerator (and/or addition/removal of magnetic shims) may be computer controlled. For example, a computer may control one or more motors that effect movement of the regenerator and/or magnetic shims.
In some implementations, the regenerator is implemented using one or more magnetic shims that are controllable to move to the appropriate location(s).
As an example, table 1 shows three example energy levels at which example accelerator 912 can output particle beams. The corresponding parameters for producing the three energy levels are also listed. In this regard, the magnet current refers to the total electrical current applied to the one or more coil sets in the accelerator 912; the maximum and minimum frequencies define the ranges in which the RF voltage sweeps; and “r” is the radial distance of a location to a center of the cavity in which the particles are accelerated.
Details that may be included in an example particle accelerator that produces charged particles having variable energies are described below. The accelerator can be a synchrocyclotron and the particles may be protons. The particles may be output as pulsed beams. The energy of the beam output from the particle accelerator can be varied during the treatment of one target volume in a patient, or between treatments of different target volumes of the same patient or different patients. In some implementations, settings of the accelerator are changed to vary the beam energy when no beam (or particles) is output from the accelerator. The energy variation can be continuous or non-continuous over a desired range.
Referring to the example shown in
In some examples, the variation is non-continuous and the variation step can have a size of about 10 MeV or lower, about 15 MeV, about 20 MeV, about 25 MeV, about 30 MeV, about 35 MeV, about 40 MeV, about 45 MeV, about 50 MeV, about 55 MeV, about 60 MeV, about 65 MeV, about 70 MeV, about 75 MeV, or about 80 MeV or higher. Varying the energy by one step size can take no more than 30 minutes, e.g., about 25 minutes or less, about 20 minutes or less, about 15 minutes or less, about 10 minutes or less, about 5 minutes or less, about 1 minute or less, or about 30 seconds or less. In other examples, the variation is continuous and the accelerator can adjust the energy of the particle beam at a relatively high rate, e.g., up to about 50 MeV per second, up to about 45 MeV per second, up to about 40 MeV per second, up to about 35 MeV per second, up to about 30 MeV per second, up to about 25 MeV per second, up to about 20 MeV per second, up to about 15 MeV per second, or up to about 10 MeV per second. The accelerator can be configured to adjust the particle energy both continuously and non-continuously. For example, a combination of the continuous and non-continuous variation can be used in a treatment of one target volume or in treatments of different target volumes. Flexible treatment planning and flexible treatment can be achieved.
A particle accelerator that outputs a particle beam having a variable energy can provide accuracy in irradiation treatment and reduce the number of additional devices (other than the accelerator) used for the treatment. For example, the use of degraders for changing the energy of an output particle beam may be reduced or eliminated for all or part of the treatment. The properties of the particle beam, such as intensity, focus, etc. can be controlled at the particle accelerator and the particle beam can reach the target volume without substantial disturbance from the additional devices. The relatively high variation rate of the beam energy can reduce treatment time and allow for efficient use of the treatment system.
In some implementations, the accelerator, such as the synchrocyclotron of
Each set of coils may be a split pair of annular coils to receive electrical current. In some situations, both sets of coils are superconducting. In other situations, only one set of the coils is superconducting and the other set is non-superconducting or normal conducting (also discussed further below). It is also possible that both sets of coils are non-superconducting. Suitable superconducting materials for use in the coils include niobium-3 tin (Nb3Sn) and/or niobium-titanium. Other normal conducting materials can include copper. Examples of the coil set constructions are described further below.
The two sets of coils can be electrically connected serially or in parallel. In some implementations, the total electrical current received by the two sets of coils can include about 2 million ampere turns to about 10 million ampere turns, e.g., about 2.5 to about 7.5 million ampere turns or about 3.75 million ampere turns to about 5 million ampere turns. In some examples, one set of coils is configured to receive a fixed (or constant) portion of the total variable electrical current, while the other set of coils is configured to receive a variable portion of the total electrical current. The total electrical current of the two coil sets varies with the variation of the current in one coil set. In other situations, the electrical current applied to both sets of coils can vary. The variable total current in the two sets of coils can generate a magnetic field having a variable magnitude, which in turn varies the acceleration pathways of the particles and produces particles having variable energies.
Generally, the magnitude of the magnetic field generated by the coil(s) is scalable to the magnitude of the total electrical current applied to the coil(s). Based on the scalability, in some implementations, linear variation of the magnetic field strength can be achieved by linearly changing the total current of the coil sets. The total current can be adjusted at a relatively high rate that leads to a relatively high-rate adjustment of the magnetic field and the beam energy.
In the example reflected in Table 1 above, the ratio between values of the current and the magnetic field at the geometric center of the coil rings is: 1990:8.7 (approximately 228.7:1); 1920:8.4 (approximately 228.6:1); 1760:7.9 (approximately 222.8:1). Accordingly, adjusting the magnitude of the total current applied to a superconducting coil(s) can proportionally (based on the ratio) adjust the magnitude of the magnetic field.
The scalability of the magnetic field to the total electrical current in the example of Table 1 is also shown in the plot of
In some implementations, the scalability of the magnetic field to the total electrical current may not be perfect. For example, the ratio between the magnetic field and the current calculated based on the example shown in table 1 is not constant. Also, as shown in
In some implementations, settings of the accelerator, such as the current applied to the coil sets, can be chosen based on the substantial scalability of the magnetic field to the total electrical current in the coil sets.
Generally, to produce the total current that varies within a desired range, any appropriate combination of current applied to the two coil sets can be used. In an example, the coil set 42a, 42b can be configured to receive a fixed electrical current corresponding to a lower boundary of a desired range of the magnetic field. In the example shown in table 1, the fixed electrical current is 1760 Amperes. In addition, the coil set 40a, 40b can be configured to receive a variable electrical current having an upper boundary corresponding to a difference between an upper boundary and a lower boundary of the desired range of the magnetic field. In the example shown in table 1, the coil set 40a, 40b is configured to receive electrical current that varies between 0 Ampere and 230 Amperes.
In another example, the coil set 42a, 42b can be configured to receive a fixed electrical current corresponding to an upper boundary of a desired range of the magnetic field. In the example shown in table 1, the fixed current is 1990 Amperes. In addition, the coil set 40a, 40b can be configured to receive a variable electrical current having an upper boundary corresponding to a difference between a lower boundary and an upper boundary of the desired range of the magnetic field. In the example shown in table 1, the coil set 40a, 40b is configured to receive electrical current that varies between −230 Ampere and 0 Ampere.
The total variable magnetic field generated by the variable total current for accelerating the particles can have a maximum magnitude greater than 4 Tesla, e.g., greater than 5 Tesla, greater than 6 Tesla, greater than 7 Tesla, greater than 8 Tesla, greater than 9 Tesla, or greater than 10 Tesla, and up to about 20 Tesla or higher, e.g., up to about 18 Tesla, up to about 15 Tesla, or up to about 12 Tesla. In some implementations, variation of the total current in the coil sets can vary the magnetic field by about 0.2 Tesla to about 4.2 Tesla or more, e.g., about 0.2 Tesla to about 1.4 Tesla or about 0.6 Tesla to about 4.2 Tesla. In some situations, the amount of variation of the magnetic field can be proportional to the maximum magnitude.
The variable reactive element 1306 can be a rotating capacitor that has multiple blades 1310 rotatable by a motor (not shown). By meshing or unmeshing the blades 1310 during each cycle of RF sweeping, the capacitance of the RF structure changes, which in turn changes the resonant frequency of the RF structure. In some implementations, during each quarter cycle of the motor, the blades 1310 mesh with the each other. The capacitance of the RF structure increases and the resonant frequency decreases. The process reverses as the blades 1310 unmesh. As a result, the power required to generate the high voltage applied to the dee plate 103 and necessary to accelerate the beam can be reduced by a large factor. In some implementations, the shape of the blades 1310 is machined to form the required dependence of resonant frequency on time.
The RF frequency generation is synchronized with the blade rotation by sensing the phase of the RF voltage in the resonator, keeping the alternating voltage on the dee plates close to the resonant frequency of the RF cavity. (The dummy dee is grounded and is not shown in
The variable reactive element 1308 can be a capacitor formed by a plate 1312 and a surface 1316 of the inner conductor 1300. The plate 1312 is movable along a direction 1314 towards or away from the surface 1316. The capacitance of the capacitor changes as the distance D between the plate 1312 and the surface 1316 changes. For each frequency range to be swept for one particle energy, the distance D is at a set value, and to change the frequency range, the plate 1312 is moved corresponding to the change in the energy of the output beam.
In some implementations, the inner and outer conductors 1300, 1302 are formed of a metallic material, such as copper, aluminum, or silver. The blades 1310 and the plate 1312 can also be formed of the same or different metallic materials as the conductors 1300, 1302. The coupling device 1304 can be an electrical conductor. The variable reactive elements 1306, 1308 can have other forms and can couple to the dee plate 100 in other ways to perform the RF frequency sweep and the frequency range alteration. In some implementations, a single variable reactive element can be configured to perform the functions of both the variable reactive elements 1306, 1308. In other implementations, more than two variable reactive elements can be used.
The control of the gantry, the patient support, the active beam shaping elements, and the synchrocyclotron to perform a therapy session is achieved by appropriate therapy control electronics (not shown).
Control of the particle therapy system described herein and its various features may be implemented using hardware or a combination of hardware and software. For example, a system like the ones described herein may include various controllers and/or processing devices located at various points. A central computer may coordinate operation among the various controllers or processing devices. The central computer, controllers, and processing devices may execute various software routines to effect control and coordination of testing and calibration.
System operation can be controlled, at least in part, using one or more computer program products, e.g., one or more computer program tangibly embodied in one or more non-transitory machine-readable media, for execution by, or to control the operation of, one or more data processing apparatus, e.g., a programmable processor, a computer, multiple computers, and/or programmable logic components.
A computer program can be written in any form of programming language, including compiled or interpreted languages, and it can be deployed in any form, including as a stand-alone program or as a module, component, subroutine, or other unit suitable for use in a computing environment. A computer program can be deployed to be executed on one computer or on multiple computers at one site or distributed across multiple sites and interconnected by a network.
Actions associated with implementing all or part of the operations of the particle therapy system described herein can be performed by one or more programmable processors executing one or more computer programs to perform the functions described herein. All or part of the operations can be implemented using special purpose logic circuitry, e.g., an FPGA (field programmable gate array) and/or an ASIC (application-specific integrated circuit).
Processors suitable for the execution of a computer program include, by way of example, both general and special purpose microprocessors, and any one or more processors of any kind of digital computer. Generally, a processor will receive instructions and data from a read-only storage area or a random access storage area or both. Elements of a computer (including a server) include one or more processors for executing instructions and one or more storage area devices for storing instructions and data. Generally, a computer will also include, or be operatively coupled to receive data from, or transfer data to, or both, one or more machine-readable storage media, such as mass PCBs for storing data, e.g., magnetic, magneto-optical disks, or optical disks. Non-transitory machine-readable storage media suitable for embodying computer program instructions and data include all forms of non-volatile storage area, including by way of example, semiconductor storage area devices, e.g., EPROM, EEPROM, and flash storage area devices; magnetic disks, e.g., internal hard disks or removable disks; magneto-optical disks; and CD-ROM and DVD-ROM disks.
Any “electrical connection” as used herein may imply a direct physical connection or a connection that includes intervening components but that nevertheless allows electrical signals to flow between connected components. Any “connection” involving electrical circuitry mentioned herein, unless stated otherwise, is an electrical connection and not necessarily a direct physical connection regardless of whether the word “electrical” is used to modify “connection”.
Any two more of the foregoing implementations may be used in an appropriate combination in an appropriate particle accelerator (e.g., a synchrocyclotron). Likewise, individual features of any two more of the foregoing implementations may be used in an appropriate combination.
Elements of different implementations described herein may be combined to form other implementations not specifically set forth above. Elements may be left out of the processes, systems, apparatus, etc., described herein without adversely affecting their operation. Various separate elements may be combined into one or more individual elements to perform the functions described herein.
The example implementations described herein are not limited to use with a particle therapy system or to use with the example particle therapy systems described herein. Rather, the example implementations can be used in any appropriate system that directs accelerated particles to an output.
Other implementations not specifically described herein are also within the scope of the following claims.
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| Number | Date | Country | |
|---|---|---|---|
| 20160067525 A1 | Mar 2016 | US |
