Scintillator Detector and Camera System and Method for Measuring Emission Uniformity and for Calibration of Radioactive Sources
Background and Summary of the Invention
This invention relates to the measurement and calibration of radioactive sources and, more particularly, to a scintillator-camera system therefor.
Radioactive sources, emitting x-rays, gamma rays, beta particles or other radiation, are used in many applications, including industrial radiography and gauging, medical therapy and heat and power sources. In many of these applications the umformity of radiation emission from the source is important. This is particularly true for low activity sources used for brachytherapy. In this case the radioactive source is placed on or inserted into the body to irradiate a tumor or lesion. Uniformity of emission is important, as is a calibration of the radiation emitted so that the radiation dose delivered to the patient can be accurately determined. Present methods for calibration of brachytherapy sources involve a variety of methods, including surrounding the source with multiple detectors, the use of multiple radiation probes or area detectors, such as film, and the use of well ionization chambers to measure the total radiation emitted from the source. These methods are cumbersome and, in many cases do not provide a complete determination of the emitted radiation patterns.
U.S. Patent No. 5,661,310, which is incorporated by reference, discloses a radiation dose mapping system and method. A dosimeter made of a suitable luminescent material is provided between an image sensor such as a camera that is hooked up to a computer-based controller and a stimulator including an infrared light source. An optical stimulator source filter for producing only a narrow-band infrared spectrum and an optical image filter for preventing light produced by the stimulator from being conveyed to the camera are provided between the stimulator and the dosimeter. The device permits mapping of spatially variable radiation
patterns for use in medical radiation treatments and does so without the requirement of chemical processing. The device is not adapted to permit analysis of circumferential, i.e., radial, or axial variations in a sample.
The method and system according to the present invention makes use of a scintillator observed by a camera. If the source to be calibrated is placed in a central hole in the scintillator, the emitted light will show variations in the radial emission pattern from the source. In one embodiment, a fiber optic scintillator, with the fibers parallel to the hole axis in the scintllator, will direct the emitted light toward the camera. Variations in the radial radiation emission from the source will be detected as variations in the radial pattern of the emitted light from the scintillator. Variations in the axial radiation from the source will be observed as the source is translated through the central hole in the scintillator.
According to one aspect of the present invention, a scintillator-camera system for determining uniformity of radiation emission from one or more radioactive sources includes a scintillation detector, the scintillation detector having a central hole in which a radioactive source is adapted to be inserted, the central hole having a hole axis extending in the first direction. A camera is arranged to view the scintillation detector and produce image data corresponding to light stimulated in the scintillation detector. The scintillation detector may be a solid plate, a granular phosphor, a columnar scintillator, or a fiber-optic plate having a plurality of scintillating fibers. If the scintillation detector is a fiber-optic plate, the fibers preferably all extend in a first direction.
According to another aspect of the present invention, a fiber-optic scintillation detector includes a scintillating body having a central hole in which a radioactive source is adapted to be inserted, the central hole having a hole axis extending in the first direction.
According to another aspect of the present invention, a method for determining uniformity of radiation emission from one or more radioactive
sources includes inserting a radioactive source in a central hole of a scintillation detector, the central hole having a hole axis extending in a first direction. Light stimulated in the scintillation detector by radioactive emissions from the radioactive source is detected with a camera.
Brief Description of the Drawings
The features and advantages of the present invention are well understood by reading the following detailed description in conjunction with the drawings in which like numerals indicate similar elements and in which: FIGS. 1A, IB, and 1C schematically show various imaging arrangement geometries for the detector system according to embodiments of the present invention;
FIG. 2A schematically shows a thin scintillator profiling system, with radiation shielding around the scintillator, according to an embodiment of the present invention;
FIG. 2B is a top view of a portion of the system of FIG. 2A; FIGS. 3 A and B schematically show embodiments of the scintillator wherein fibers run in a thickness direction of the plate, and wherein a solid scintillating material is cut in concentric rings, respectively.
Detailed Description of Preferred Embodiments
As seen in the embodiments of the system 10a, 10b, 10c according to the present invention shown in FIGS. 1A, IB, and 1C, observations of emitted light from a source S can be made by a camera 21 used with a single or multiple mirror system 23a, in a direct line with the scintillation detector or scintillator 22 with a transparent radiation shield 25 in the path, or by a fiber optic turning block 23c between the scintillator and the camera. Radiation shielding 25a and 25b such as lead or a high atomic number absorber such as a tungsten alloy can be used on both sides of the scintillator 22 to minimize scintillation light that may result when
the source S is not totally within the scintillator central hole, as shown, for example, by the large upper shield 25a and the lower cylindrical shield 25b, in FIG. 2A (shown from the top in FIG. 2B). For sources emitting lower energy photons, such as 125I, the camera-side shield may be a transparent absorber, such as leaded plastic or leaded glass 25b such as is shown in FIG. IB. For particle- emitting sources, such as 32P, the radiation shields should be free of high atomic number materials to avoid production of x-rays, and clear plastic shields, such as polyethylene provide good shielding results.
A lead or high-Z shield 25b on the camera side of the scintillator 22 is preferably arranged as shown in FIG. 1A. A leaded glass or leaded plastic shield
25b is preferably arranged against the scintillator 22 as shown in FIG. IB. The leaded glass or leaded plastic shield 25b shown in FIG. IB could, of course, be used with other embodiments such as the mirror embodiment shown in FIG. 1A and is not restricted to the straight-through imaging shown in FIG. IB. It is not necessary that the shielding 25b is on the scintillator 22, although it is preferred that the shielding is between the scintillator and the camera 21 to protect the camera, and close to the scintillator to minimize the shine of the source onto the face of the scintillator.
For sources emitting photons, gamma rays or x-rays, a useful scintillator 22 is a high-density fiber optic scintillating glass, such as Type IQI 302 (available from Industrial Quality, Inc., Gaithersburg, MD 20877) or a columnar cesium iodide (Csl scintillator available from Radiation Monitoring Devices, Inc., Watertown, MA). For sources emitting beta particles or positrons, a useful scintillator or imaging detector is a plastic scintillator 22. There are many variations available in plastic scintillators. One useful plastic scintillator is Type
BC400 (available from Saint Gobain Crystals & Detectors, Newbury, OH). The plastic scintillator may be used in the form of solid sheets, fiber optic plates in which fibers 22a run in the thickness direction of the plate (FIG. 3A), a bull's eye pattern form such as is shown in FIG. 3B and includes a plurality of concentric
rings 22b of scintillating plastic, or alternating rings of scintillating plastic and regular, non-scintillating plastic. The latter two methods offer improved circumferential or radial resolution. These embodiments of scintillators 22 are presently understood to tend to prevent radial progression of light in the glass or plastic and to scatter the light to a surface where it can be detected.
According to an aspect of the invention that will be described with reference to FIG. 2A, the radioactive source S, typically less than a millimeter in diameter and a few millimeters in length, is inserted into a central hole 35 in a thin fiber optic scintillator 22, as shown in FIGS. 1A, IB, and lC. The central hole 35 is parallel to the fiber axis so the light stimulated by the radioactive emission is directed along the fibers. The fiber optic scintillating glass can be Type IQI 302 (sold by Industrial Quality, Inc.) or columnar cesium iodide (Csl, available from Radiation Monitoring Devices, Watertown, MA) as examples. However, other scintillating detectors can be used. For beta emitting sources, such as 32P, a plastic scintillator (such as Type BC400 available from Saint Gobain
Crystals & Detectors, Newbury, OH) may be used. The light directed out of the fibers in the system shown in FIG. 2A is detected by a lens camera assembly 21 directly in line (FIG. IB) with the scintillator, through a mirror system (FIG. 1A) to move the camera and its electronics out of the radiation field, or through a fiber optic turning block (FIG. 1C).
The radioactive seed is placed in a guide catheter 37 (FIGS. 1A-1C) and fed through a hole 39 in a top radiation shield 25a, then through the scintillator 22 and into the bottom shield 25b. As the seed passes through the hole in the scintillator 22, the seed activity produces a light pattern in the scintillator. Any circumferential, i.e., radial, variations in the source activity will show as a skewed circumferential, i.e., radial pattern in the scintillator 22. Variations in the axial activity can be detected as different sections of the seed pass through the thin scintillator. A small portion of the circumferential or radial pattern may be obscured by the lower shield 25b, however the size and properties of the lower
shield are chosen to provide effective attenuation while permitting the outer extents of the scintillation pattern to be observed by the camera 21. An alternative shield for lower energy photons is a clear, leaded plastic or leaded glass to provide shielding and also permit observation by the camera 21. For particle emitting sources, beta or positron, the shield can be simple clear plastic. For this concept of the imaging system, a preferred scintillator is in the form of a thin fiber optic plate with the fibers running in the thickness direction. This allows a high spatial resolution of the scintillation pattern along the longitudinal direction of the source S by virtue of the scintillator thickness and in the circumferenital direction by virtue of the small fibers.
The final result obtained from this invention is a representation of the radiation emission pattern from a radioactive source. For brachytherapy applications, this radiation data can be related to radiation dose delivered to a patient, thereby making the radiation therapy more efficient and safer to use. The scintillator-camera system described here offers a rapid, complete characterization of the radiation pattern emitted by a radioactive source. The camera 21 can, of course, be associated with a computer for analysis and storage of information about the source and the reference to a camera is meant to encompass any suitable device capable of obtaining and recording or transmitting an image. While this invention has been illustrated and described in accordance with a preferred embodiment, it is recognized that variations and changes may be made therein without departing from the invention as set forth in the claims.