Patent Application
20250004145
This invention relates to devices for radiographic imaging, including X-ray/gamma ray, neutron or other particle imaging, where a scintillator is used to convert high-energy particles or photons to optical photons.
Detectors for imaging ionizing radiation traditionally comprise a 2-D scintillator and an optical detector such as a CCD or a CMOS array, in which the scintillator converts the incident radiation (“incident radiation” here can include X-rays, Gamma rays, neutrons, protons, alpha particles or beta particles as examples) into optical photons that are subsequently detected by the optical detector. A wide variety of scintillators are in use for this purpose, with different properties utilized for various specific applications. For imaging purposes, these scintillators are typically 2-D planar films or crystals and there exists a trade-off in the thickness versus the spatial resolution that can be achieved. Specifically, in order to stop a higher proportion of the incident radiation a thicker layer of scintillator is desired, however this results in a reduced spatial resolution due to internal light spread within the scintillator layer itself.
Most of these detectors integrate the optical photons that originate within the scintillator over a period of exposure time to form an image. These integrating detectors form an image by integrating all of the optical light photons that interact with each pixel, which limits the spatial resolution based on the energy and light spread within the scintillator layer. This type of imaging detector is the most common.
Some detectors have been developed that utilize a photon-counting approach in which individual absorbed photons or particles are detected during a relatively short exposure time. Within the scintillator each incident photon or particle that is absorbed produces a burst of optical photons that are emitted in 4π. Each of these “scintillation events” can be seen in the detector as bright spots in the image, and typically these bright spots will be circular or ellipsoidal in nature with a diameter covering a plurality of the detector pixels. Scintillation events can also be streaks depending on the type of radiation. It then becomes possible to perform centroiding of each event to find the center, which corresponds to the location that the original photon or particle was absorbed. With this method, the spatial resolution can be greatly enhanced. Many of these individual images (each consisting of many bright spots) can be processed with the centroiding approach and then summed to form the final image.
The common Anger camera is another example of a photon-counting detector typically used for gammas and neutrons. Here the scintillator can be made relatively thicker so sensitivity is increased. The detector uses Anger logic to roughly approximate the location of the incident events. The resulting spatial resolution is quite poor, typically not better than 0.25-0.5 mm (1-2 line-pairs/mm).
While there are working scintillator-based devices that function for the imaging of X-rays, gamma-rays, and neutrons, all of these detectors heretofore known suffer from a number of disadvantages, including as examples: (a) current detectors suffer from an inherent trade-off between detection efficiency and spatial resolution; (b) current detectors are planar or 2D detectors that offer no measurement of the depth of interaction of the incident radiation; (c) while photon-counting detectors utilizing thin scintillator screens can perform centroiding for enhanced spatial resolution, they still are subject to the trade-off between detection efficiency and spatial resolution; (d) photon counting Anger cameras make it possible to increase efficiency with a thicker scintillator, however the Anger logic used to determine event locations results in poor spatial resolution.
Embodiments of the present invention provide a new type of photon-counting detector for high-resolution imaging, comprising a thick transparent scintillator and multiple lens-based cameras that view the individual scintillation events from two or more angles. Embodiments can provide very precise locations of each individual event. Each camera provides a separate view of the scintillator volume, and where these views intersect a 3D volume is delineated within which the scintillation events can very precisely be determined. Each scintillation event is a burst of optical photons in a sphere or oval and the center of each spot can be determined by centroiding to greatly enhance spatial resolution.
Prior to use, a grid consisting of a known array of points can be placed in the volume to calibrate the entire volume of space where the scintillator is then placed.
Embodiments of the invention can provide various advantages, including as examples: (a) providing a scintillator-based photon-counting detector that can very precisely locate each scintillation event within a scintillator volume; (b) providing a radiographic imaging detector that does not suffer from the inherent trade-off between detection efficiency and spatial resolution; (c) providing a radiographic imaging detector that can provide high-resolution of both low-energy and high-energy gamma rays or neutrons; (d) providing a radiographic imaging detector that allows gamma/neutron discrimination; (e) providing a radiographic imaging detector that allows scattered gammas/neutrons to be identified and excluded from the image; (f) providing a radiographic imaging detector that allows the user to select or exclude events based on their depth of interaction within the scintillator volume; (g) providing a radiographic imaging detector that can provide dual energy imaging with one detector; (h) providing a radiographic imaging detector that provides energy resolution for each detected particle based on the total integrated light combined from all cameras.
Embodiments can provide a radiographic imaging detector with an unprecedented combination of detection efficiency and spatial resolution. Embodiments of the invention can impact radiographic imaging of all energy ranges, and can be particularly useful for high-energy particles that are difficult to detect. Embodiments of the invention provide a new type of detector that can have widespread use in a range of applications for imaging ionizing radiation, including as examples X-rays, gamma rays, neutrons (of a wide range of energies), protons, alpha particles, beta particles, muons and possibly others.
Reference numerals in the drawings correspond to the following elements:
incident radiation 5; camera view 35; object imaged 10; calibration grid or fixture 40; incident radiation after object 15; x dimension of scintillator 45; transparent scintillator volume 20; y dimension of scintillator 50; lens-coupled cameras 25; z dimension of scintillator 55; scintillation events 30; x,y image frame 60; radiation source 65; collimator 70; incident radiation after collimator 75.
Embodiments of the invention comprise a radiographic imaging detector that comprises a thick transparent scintillator and two or more lens-coupled cameras that focus through the volume of the scintillator. Other embodiments comprise relatively thin scintillators or scintillator films.
An example embodiment of the present invention is illustrated in a top view in
The detector comprises a transparent scintillator 20 and two or more lens-coupled cameras 25.
The cameras or other imaging devices can be controlled as is known to those skilled in the art. The locations and calibrations can be determined using a determination system, which can comprise, as examples, a programmed computer, a special purpose computer, digital or analog circuitry, applications on general purpose computing devices such as personal computers, tablets, or smart phones, or other systems known to those skilled in the art. The determination system can be mounted close to the detector system, or at a distance with data communicated using wired or wireless communication. The determination can be done near the time of acquiring the images or signals, or after time has elapsed in a post-processing system, or a combination thereof.
An example embodiment is shown in
Other example embodiments can include more cameras (not shown). For example, three cameras 25 placed 60° apart can provide three views of each scintillation event 30. This provides increased precision in locating the exact position of each event 30.
Another example embodiment (not shown) includes mirrors placed in between the camera or cameras 25 and the scintillator 20. The views 35 can thus easily be adjusted to achieve the desired imaging volume. In addition, in this embodiment it is possible to use mirrors to focus two or more views on a single sensor array.
This photon-counting detector works with the cameras 25 operating in continuous framing mode, with the cameras' 25 acquisition times synchronized so that the cameras 25 acquire image frames at the exact same time. It can be important that they are synchronized so that they are looking at the scintillation events 30 simultaneously from two or more views 35, depending on how many cameras are employed. Prior to imaging an unknown object, a calibration grid 40 or something else with points that have known positions can be placed within the volume and imaged there in order to calibrate the volume where the scintillator 20 will subsequently be placed. Once the calibration is complete, anything viewed within that volume can be located in 3-dimensional space with x, y, z coordinates, with the cameras remaining stationary.
A transparent scintillator 20 can then be placed in the calibrated volume, inside a light-tight box. The camera frame rates can be set at a speed such that the desired number of scintillation events 30 are visible within the volume in each frame. If there are too many events 30 in each frame it can become difficult to resolve individual events 30 that occur close to each other. Also, events 30 farther away from the cameras 25 can be obscured by events in the foreground. The frame rate can be chosen specifically for each application depending on the flux of incident radiation 5. For example, the desired number of events 30 can be in the range from 1-100 or more.
In each frame, there can be some number of events 30 within the scintillator 20 volume that are viewed 35 by both cameras 25, or multiple cameras. These events 30 will have known locations in terms of x, y, z coordinates. Each event 30 can be centroided to find its precise location, which can enhance spatial resolution. The z coordinate 55 can be used to select the events 30 that are desired to form the image. For example, it is possible to exclude the events 30 closer to the front face of the scintillator 20, if desired. These would normally be associated with lower-energy incident radiation 5, 15, since they do not penetrate as far into the scintillator volume. Or conversely, one can make separate images with the front events making one image and the events near the rear in another image. With the desired z range defined, the x, y coordinates can then be used to form an x, y image frame 60 for each frame.
The scintillation events 30 can also be integrated in order to quantify the total light emitted from each event 30. This can provide another way to filter or select the desired events 30 to be used to form the image.
Forming an image of an object 10 can require many such frames 60 to be acquired. This can require a plethora of images 60 and thousands to millions of events 30 to form the final image (for example). In general, the more events 30 that make up the image, the better the object 10 will be resolved. To form a final image, the pixels in the x, y frame 60 where an event 30 was registered can be given an arbitrary value (e.g., 100) and then the complete set of image frames 60 can be summed. With the x, y, z coordinate data now determined in each frame, algorithms can be used to compile this information into 2D images of the object 10. These resulting images can provide unprecedented spatial resolution of the object 10.
Embodiments of this invention provide an apparatus that can detect X-rays, gammas, neutrons or other radiation with great precision within the scintillator. This results in an image with greatly enhanced spatial resolution. Because it is a photon-counting detector, it can be more amenable to applications where the incoming flux is not too high relative to the shortest exposure time of the detector. It is simply a matter of getting the desired number of events within each frame. Although with high-speed cameras or other 2D detectors such as SiPM arrays (silicon photo-multiplier arrays) it is feasible to also use this detector in applications with higher flux. Also, with more cameras, e.g., 3, 4, or more, this will also make it more amenable to applications where higher flux is observed.
Although the description above contains many specificities, these should not be construed as limiting the scope of the invention but as merely providing illustrations of some of the presently preferred embodiments of this invention. Many other variations are possible. For example, as mentioned above, more cameras can be utilized. The examples in the figures depict an embodiment with two cameras. Having more cameras can provide greater precision in locating the coordinates of each event.
Thus the scope of the invention should be determined by the appended claims and their legal equivalents, rather than by the examples given.
| Number | Date | Country | |
|---|---|---|---|
| 63333709 | Apr 2022 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | PCT/US23/65835 | Apr 2023 | WO |
| Child | 18826757 | US |
