Patent Application
20230317310
The present invention relates to an electron applicator and, more particularly, to a FLASH electron applicator with an integrated dosimeter.
A tumor is an abnormal growth of tissue that typically has an irregular shape. Tumors at or near the surface of the skin are often treated with a therapeutic electron beam. A radiotherapy linear accelerator is a medical device that generates and outputs a parallel or collimated electron beam. To avoid damaging healthy tissue adjacent to a tumor, the electron beam must be shaped to match the irregular shape of the tumor.
An electron applicator, is a device that attaches to the linear accelerator to further collimate and shape the electron beam. The electron applicator commonly has an elongated body with a proximate end that attaches to the accelerator and a distal end that is positioned close to the skin. The elongated body has an opening that extends from the proximate end to a partially-closed distal end where the shape of the opening at the distal end defines the final shape of the beam.
In addition, the irregular shape of a tumor may vary as the viewing angle of the tumor changes. Thus, if an electron beam is to be directed to a tumor from three different angles, three different beam shapes may be used where each beam shape matches the irregular shape of the tumor when viewed from that angle.
A common approach to forming different beam shapes for treating a single tumor from different angles is to fabricate multiple “cutouts”. The cutouts are casted to the desired shapes using low-melting-temperature lead alloys such as Cerrobend. The cutouts are then inserted into the distal end of the electron applicator per gantry angle as required to achieve the desired shape. The cutouts are expensive and time consuming to fabricate and require certain safety measures such as casting the Cerrobend under a vented hood.
FLASH is an emerging radiation therapy treatment modality where very high dose rates are used to reduce damage to healthy tissue. Conventional electron applicators are designed to treat at distances corresponding roughly with the treatment machine isocenter. To achieve a uniform (‘flat’) intensity distribution within the collimated area, the electron applicators are physically long, extending to within about 5 cm of the isocenter. In electron FLASH, to achieve the necessary high dose rates, it is advantageous to treat at shorter distances.
FLASH dose rates also present a challenge for accurate, real-time dosimetry. Conventional linear accelerators have ion chambers that monitor the radiation beam and serve as dosimeters that measure the dose. However, conventional ion chambers may have performance limitations associated with the very high dose per pulse delivered during FLASH radiotherapy. The ion chamber may experience high ion recombination, resulting in a non-linear response with respect to dose per pulse. This can lead to inaccurate dosimetry readings.
Note that the ion chamber may also serve as a patient safety device. It may be tied to the control system such that it can assert an interlock when the radiation beam is not correct, for example the beam current is too high or too low. Thus, in Flash radiotherapy, where the ion chamber may have accuracy limitations, it is advantageous to have a secondary dosimeter to confirm the dose is correct and provide redundant safety interlocks.
The electron applicator of the present invention accurately measures dose when delivered at FLASH dose rates, and easily, inexpensively, and accurately collimates a beam that substantially matches the shape of a tumor. The electron applicator includes a collimating body that has a proximate end, a distal end, and a first opening that extends from the proximate end to the distal end. The electron applicator also includes a radiation detector that can serve as a dosimeter and/or a monitoring device for patient safety. As a dosimeter, it may be used for dose measurements alone and/or it could be used to servo the dose. The dose servo acts to maintain a constant dose per pulse or dose rate across many beam pulses. The electron applicator may contain any supporting circuitry for dose measurements, beam intensity safety interlocks, or dose servo. The radiation detector is coupled to the proximate end of the electron applicator. The design is such that the detector subcomponent does not have to be removed from the gantry when interchanging the distal aperture (with cutouts) subcomponent. It is expected that a set of aperture subcomponents with varying diameters would be made available to cover the clinical range of radiation field widths and shapes.
A better understanding of the features and advantages of the present invention will be obtained by reference to the following detailed description and accompanying drawings which set forth an illustrative embodiment in which the principals of the invention are utilized.
The accompanying drawings described herein are used for providing further understanding of the present application and constitute a part of the present application. Exemplary embodiments of the present application and the description thereof are used for explaining the present application and do not constitute limitations on the present application.
In one embodiment of the present invention, two subcomponents comprise an electron collimator assembly. The first component, ‘upstream’ of the second component, houses a radiation monitoring device. The second component is a collimation cone, which manually attaches below the monitor component. The design is made such that any of several collimation cones can attach to the monitor component. The range of collimation cones would cover the expected useable radiation field diameters. The collimation cones are circular geometries, similar to x-ray stereotactic cones. Other embodiments can include other non-circular geometries. The cones would be fully enclosed on their sides, allowing for maximum collimation per physical length. In this way, the collimator can be kept short, allowing for the patient to be located closer to the linac gantry head (electron source), thereby taking advantage of higher dose rates available at short source-to-target distances.
The electron collimator design is made such that the entire unit can be manually attached or detached from the linac gantry head. It can be installed when needed for electron FLASH treatments and removed for conventional mode treatments. It is noted that the proposed electron FLASH collimator could be used with conventional electron treatments, possibly offering improved radiation field penumbra and ergonomic advantages of smaller size and lighter weight. The geometric design and material composition allows for minimal radiation leakage outside the intended treatment area, minimal x-ray contamination, and lower weight than conventional electron applicators.
Different types of radiation monitor/dosimetry devices can be implemented. Some examples include: 1) a toroid, 2) a transmission foil, and 3) a capacitive-coupled detector. The toroid, a type of electric transformer, detects the accelerator electron beam passing through its hollow center. The transmission foil, which stretches across the collimator aperture, detects the accelerator electron beam passing through it. The capacitive-coupled detector is a multi-segmented device that senses the proximity of the accelerator beam to the sides of the collimator aperture.
Whereas known electron FLASH applicators in use today are typically not designed to support a beam monitoring device within its assembly, it has been discovered that having an independent, secondary detector is highly advantageous and required. This is because the standard ion chamber present in the linear accelerator may experience high ion recombination, resulting in a non-linear response with respect to dose per pulse. Hence, having the independent, secondary real-time dosimeter to monitor the dose addresses this issue.
In one embodiment, custom ‘cut-outs’ can be manually installed at the distal end of the cone component, to shape the radiation field to the treatment area. For low energy electron FLASH beams, it is possible and advantageous to make the cut-outs out of the same high density plastic used for the cones. The plastic cut-outs reduces x-ray contamination, and also advantageously allows for 3-D printing, additive manufacture, or easy machining of the cut-out.
As shown in
The minimum size of diameter D is determined by the size of the tumor as the diameter D must preferably be at least as large as the largest feature of the tumor from a particular view. The maximum size of diameter D is determined by the maximum amount of scattering that can be tolerated as wider openings tend to produce more scattering.
Collimating body 110 is fully enclosed on the sides to allow for maximum collimation per physical length. In this way, collimating body 110 can be kept short, allowing for a patient to be located closer to the gantry head (electron source) of a linear accelerator, thereby taking advantage of higher dose rates. The thickness of the material surrounding opening 116 is determined by the level of radiation leakage that is acceptable.
In the present embodiment, collimating body 110 is fabricated from a high-density polymer, such as polyethylene, but can alternately be fabricated in a conventional manner. Commercial electron applicators are made of metal which provide good radiation shielding, but also generate unwanted x-rays. Scattered electrons in a metal collimator interact with the metal in the collimator and generate unwanted x-rays. Thus, one advantage of a high-density polymer collimator over a conventional metal collimator is that x-ray contamination is substantially reduced.
Another advantage of a high-density polymer collimating body 110 is that it can be easily, inexpensively, and accurately formed by machining a block of the material. Alternately, molds can be used to form collimating body 110. In some embodiments the collimating body may be produced by additive manufacturing or 3D printing.
As further shown in
In the present embodiment, radiation detector 122 is implemented with a toroidal transformer 122T where the central axis of transformer 122T and opening 116 are aligned. In operation, a radiotherapy linear accelerator outputs a collimated electron beam as shown by arrow A in
Any of the radiation detector devices that would be incorporated into the electron applicator would respond in a stable, consistent, and calibratable manner to changes in the accelerator beam current. A change in the accelerator beam current (arrow A in
As additionally shown in
Cutout 130 is interchangeable with other cutouts such that one cutout can be removed and replaced with another cutout. The central axis of radiation detector 122, opening 116, and opening 132 are aligned. In operation, after the electron beam has passed through the center of detector 122, the beam passes through opening 116 in collimating body 110, and then through opening 132 in cutout 130 into a tumor.
In the present embodiment, cutout 130 is fabricated from a high-density polymer, such as polyethylene, but can alternately be formed from other materials. High-density polymer cutout 130 has several advantages over the metal openings in conventional electron applicators including the significant reduction in the amount of x-ray contamination.
Further, cutout 130 and opening 132 can be easily, inexpensively, and accurately formed by obtaining a layer of high-density polymer, which is thinner than the layer used to form collimating body 110, and then machining the layer of high-density polymer to form cutout 130 and opening 132.
One of the advantages of the present invention is that a computer numerical control (CNC) router or similar device can be used to machine opening 132 in a thin layer of high-density polymer to match the irregular shape of a tumor that is much more accurate than the opening that can be formed with an electron applicator that uses a multi-leaf collimator (MLC).
Further, the fabrication of opening 132 in a high-density polymer cutout is substantially easier and cheaper than the process for forming openings in a conventional metal electron applicator. Alternately, cutout 130 can be 3D printed, or formed from molds. The minimum thickness T of cutout 130 is defined by the minimum thickness required to block the electron beam from passing though the regions surrounding opening 132 which, in turn, is defined by the energy of the electron beam.
As further shown in
Collimating body 110 is interchangeable with other collimating bodies such that housing 140 can accommodate different collimating bodies. For example, a collimating body 110 that has a diameter D of 10 cm can be removed from housing 140 and replaced with a collimating body 110 that has a diameter D of 4 cm without removing housing 140 from the linear accelerator. Thus, changing opening 116 from a first diameter D to a second diameter D is simple.
Similarly, housing 140 can accommodate different cutouts 130. For example, a cutout 130 that has a first opening that substantially matches the irregular shape of a tumor can be removed from housing 140 and replaced with a cutout 130 that has a second opening that substantially matches the irregular shape of the tumor from a different angle.
Another of the advantages of the present invention is that electron applicator 100, being largely made from plastic, is substantially lighter than conventional electron applicators. In addition, housing 140 is fabricated to easily attach to a linear accelerator. As a result, electron applicator 100 can be installed when needed for electron FLASH treatments, and removed for conventional mode treatments. A further advantage of the present invention is that dosimeter 120 provides a real-time, accurate measure of the dose.
The length L of opening 116 in collimating body 100 is defined by the treatment protocol. For example, conventional radiotherapy utilizes a 100 cm source-to-skin (SSD) measure, while FLASH radiotherapy works better with a shorter 70 cm (or less) SSD. Thus, the applicator-to-skin distance, thickness of cutout 130, length L of collimating body 110, thickness of radiation detector 122, and thickness of housing 140 have a total thickness of approximately 70 cm or less.
Within the limits of the 70 cm protocol, a longer length L increases the flatness of the beam and also increases the intensity of the beam by reducing scatter and generating a more parallel beam. In addition, as the diameter D increases, the length L increases to provide the same beam quality. Further, reducing the distance between cutout 130 and the skin reduces the penumbra and provides a sharper falloff of the radiation field.
An alternative embodiment is shown in
By utilizing the real-time dosimeter incorporated with interchangeable collimator for electron FLASH radiation therapy as described in the various embodiments above, tumors can be treated as follows. First, a high dose of FLASH radiation is generated. This high does FLASH radiation is collimated to form a beam of electrons. This beam of electrons is sent through an electron applicator. Within the electron applicator is a dosimeter that measures the dose in real-time. The electron applicator also shapes the beam to substantially match the shape of the tumor.
Reference has now been made in detail to the various embodiments of the present disclosure, examples of which are illustrated in the accompanying drawings. While described in conjunction with the various embodiments, it will be understood that these various embodiments are not intended to limit the present disclosure. On the contrary, the present disclosure is intended to cover alternatives, modifications and equivalents, which may be included within the scope of the present disclosure as construed according to the claims.
Furthermore, in the preceding detailed description of various embodiments of the present disclosure, numerous specific details are set forth in order to provide a thorough understanding of the present disclosure. However, it will be recognized by one of ordinary skill in the art that the present disclosure may be practiced without these specific details or with equivalents thereof. In other instances, well-known methods, procedures, components, and circuits have not been described in detail so as not to unnecessarily obscure aspects of various embodiments of the present disclosure.
The drawings showing various embodiments in accordance with the present disclosure are semi-diagrammatic and not to scale and, particularly, some of the dimensions are for the clarity of presentation and are shown exaggerated in the drawing Figures. Similarly, although the views in the drawings for the ease of description generally show similar orientations, this depiction in the Figures is arbitrary for the most part. Generally, the various embodiments in accordance with the present disclosure can be operated in any orientation.
The above embodiments are merely used for illustrating rather than limiting the technical solutions of the present invention. Although the present application is described in detail with reference to the foregoing embodiments, those of ordinary skill in the art should understand that the technical solutions recorded in the foregoing embodiments may still be modified or equivalent replacement may be made on part or all of the technical features therein. These modifications or replacements will not make the essence of the corresponding technical solutions be departed from the scope of the technical solutions in the embodiments of the present invention.
