The invention relates generally to the field of imaging systems, and more particularly to the imaging of objects. More specifically, the invention relates to an apparatus and method enabling analytical imaging of objects (for example, small animals and tissue) in differing modes, including bright-field, dark-field (e.g., luminescence and fluorescence), and x-ray and radioactive isotopes.
Electronic imaging systems are well known for enabling molecular imaging. An exemplary electronic imaging system (shown in
Applicants have recognized a need for an apparatus and method for enabling analytical imaging of an object in differing modes.
An object of the present invention is to provide an apparatus and method for enabling analytical imaging of an object.
Another object of the present invention is to provide such an apparatus and method for enabling analytical imaging of an object in differing modes.
These objects are given only by way of illustrative example, and such objects may be exemplary of one or more embodiments of the invention. Other desirable objectives and advantages inherently achieved by the disclosed invention may occur or become apparent to those skilled in the art. The invention is defined by the appended claims.
According to one aspect of the present invention, there is provided an imaging system for imaging an object. The imaging system includes a support member adapted to receive the object in an immobilized state. The system also includes first means for imaging the immobilized object in a first imaging mode to capture a first image, and second means for imaging the immobilized object in a second imaging mode, different from the first imaging mode, to capture a second image. The first imaging mode is selected from the group: x-ray mode and radio isotopic mode. The second imaging mode is selected from the group: bright-field mode and dark-field mode. A removable phosphor screen is employed when the first image is captured and not employed when the second image is captured. The phosphor screen is adapted to transduce ionizing radiation to visible light. The phosphor screen is adapted to be removable without moving the immobilized object. The system can further include means for generating a third image comprised of the first and second image.
The foregoing and other objects, features, and advantages of the invention will be apparent from the following more particular description of the embodiments of the invention, as illustrated in the accompanying drawings. The elements of the drawings are not necessarily to scale relative to each other.
The following is a detailed description of the preferred embodiments of the invention, reference being made to the drawings in which the same reference numerals identify the same elements of structure in each of the several figures.
Applicants have recognized that the complex pharmaceutical analyses of small objects/subjects (e.g., small animal and tissue) images are particularly enhanced by using different in-vivo imaging modalities. Using the known/current practices of bright-field, dark-field and radiographic imaging for the analysis of small objects/subjects (such as a mouse) can be expensive and may not provide the precision of co-registered images that is desired.
Using the apparatus and method of the present invention, precisely co-registered fluorescent, luminescent and/or isotopic probes within an object (e.g., a live animal and tissue) can be localized and multiple images can be accurately overlaid onto the simple bright-field reflected image or anatomical x-ray of the same animal within minutes of animal immobilization.
The present invention uses the same imaging system to capture differing modes of imaging, thereby enabling/simplifying multi-modal imaging. In addition, the relative movement of probes can be kinetically resolved over the time period that the animal is effectively immobilized (which can be tens of minutes). Alternatively, the same animal may be subject to repeated complete image analysis over a period of days/weeks required to assure completion of a pharmaceutical study, with the assurance that the precise anatomical frame of reference (particularly, the x-ray) may be readily reproduced upon repositioning the object animal. The method of the present invention can be applied to other objects and/or complex systems subject to simple planar imaging methodologies.
More particularly, using the imaging system of the present invention, an immobilized object can be imaged in several imaging modes without changing/moving the immobilized object. These acquired multi-modal images can then be merged to provide a co-registered image for analysis.
Imaging modes supported by the apparatus/method of the present invention include: x-ray imaging, bright-field imaging, dark-field imaging (including luminescence imaging, fluorescence imaging) and radioactive isotope imaging. Images acquired in these modes can be merged in various combinations for analysis. For example, an x-ray image of the object can be merged with a near IR fluorescence image of the object to provide a new image for analysis.
The apparatus of the present invention is now described with reference to
Imaging system 100 includes light source 12, optical compartment 14, a lens/camera system 18, and communication/computer control system 20 which can include a display device, for example, a computer monitor. Camera/lens system 18 can include an emission filter wheel for fluorescent imaging. Light source 12 can include an excitation filter selector for fluorescent excitation or bright field color imaging.
As best shown in
Sample object stage 104 is disposed within a sample environment 108, which allows access to the object being imaged. Preferably, sample environment 108 is light-tight and fitted with light-locked gas ports for environmental control. Such environmental control might be desirable for controlled x-ray imaging or for support of particular specimens.
Imaging system 100 can include an access means/member 110 to provide convenient, safe and light-tight access to sample environment 108. Access means are well known to those skilled in the art and can include a door, opening, labyrinth, and the like. Additionally, sample environment 108 is preferably adapted to provide atmospheric control for sample maintenance or soft x-ray transmission (e.g., temperature/humidity/alternative gases and the like).
Sample object stage 104 is disposed within a sample environment 108, which allows is access to the object being imaged. Preferably, sample environment 108 is light-tight and fitted with light-locked gas ports for environmental control. Environmental control enables practical x-ray contrast below 8 Kev (air absorption) and aids in life support for biological specimens.
Accordingly, imaging system 100 further includes an access means/member 110 to provide convenient, safe and light-tight access to sample environment 19. Access means are well known to those skilled in the art and can include a door, opening, labyrinth, and the like. Additionally, sample environment 108 is preferably adapted to provide atmospheric control for sample maintenance or soft x-ray transmission (e.g., temperature/humidity/alterative gases and the like).
Imaging system 100 can be a unitary system. Alternatively, imaging system 100 can be a modular unit adapted to be used/mated with electronic imaging system such as electronic imaging system 10.
Sample object stage 104 includes a frame 120 to support and stretch a thin plastic support sheet 122. Support sheet 122 is selected so as to support a sample weight (i.e., the weight of a sample) and is optically clear and free of significant interfering fluorescence.
A phosphor plate 125 is mounted for motion toward and away from sample object stage 104. While those skilled in the art might recognize other configurations, in a preferred embodiment, phosphor plate 125 is mounted for translation to provide slidable motion (in the direction of arrow A) relative to frame 120, beneath the sample, in intimate contact with support sheet 122. As will be more particularly described below, in a first imaging position P1, phosphor plate 125 is in overlapping arrangement with sample object stage 104 (
Frame 100 and phosphor plate 125 are mounted for slidable motion relative to each other. Such motion can be accomplished using methods known to those skilled in the art, for example, frame 100 and phosphor plate 125 can be disposed on rails supported by a surface of an optical platen 126.
Sample support sheet 122 is preferably comprised of Mylar or polycarbonate and has a nominal thickness of about 0.1 mm.
A protective layer 128 (for example, reflective Mylar) of about 0.025 mm is provided to protect the phosphor surface of phosphor plate 125. Protective layer 128 promotes/increases the image-forming light output. In a preferred embodiment, protective layer 128 is reflective so as to prevent object reflection back into the image-forming screen, reducing the confusing the ionizing radiation image.
A phosphor layer 130 is provided to transduce ionizing radiation to visible light practically managed by a lens and a camera (such as a CCD camera). Phosphor layer 130 can have a thickness ranging from about 0.01 mm to about 0.1 mm, depending upon the application (i.e., soft x-ray, gamma-ray or fast electron imaging).
An optical layer 132 is provided for conditioning emitted light from phosphor layer 130. Optical layer 132 can have a thickness in the range of less than about 0.001 mm.
Particular information about phosphor layer 130 and optical layer 132 are disclosed in U.S. Pat. No. 6,444,988 (Vizard), commonly assigned and incorporated herein by reference.
A supporting glass plate 134 is provided. Glass plate 134 is spaced at a suitable mechanical clearance from an optical platen 126, for example, by an air gap/void 136. In the preferred embodiment, the surfaces of clear optical media (e.g., a lower surface of glass plate 134 and both surfaces of optical platen 126) are subject to anti-reflective coating to minimize reflections that may confuse the image of the object.
Referring now to
As indicated above, system 100 can be configured in several modes, including: x-ray imaging, bright-field imaging, dark-field imaging (including luminescence imaging, fluorescence imaging) and radioactive isotope imaging.
To configure system 100 for x-ray imaging or isotope imaging, phosphor plate 125 is positioned in optical registration with sample object stage 104 (as shown in
To configure system 100 for bright-field imaging or dark-field imaging (including luminescence imaging and fluorescence imaging), phosphor plate 125 is removed from optical registration with sample object stage 104 (as shown in
The object is immobilized on sample object stage 104, and light emitted from the object (usually diffusive within the turbid constituents of a solid object) is projected to the object surface, which intimately bears upon the upper surface of sample support sheet 122.
For the purpose of optical imaging, the object surface is defined by a refractive boundary (e.g., the skin of an animal) that delineates the interior of the object (usually a heterogeneous, turbid media of higher index of refraction) and air. Light emanating from within an object (e.g., luminescent or transmitted) projects to the surface from which it scatters, defining the light that may be productively managed to create an image of the object. Conversely, light may be provided from beneath optical platen 126 and scattered from the object surface, thereby providing reflective light for imaging the same object.
For optical imaging, the definition of the object boundary may be moderated by matching the refractive index of the object boundary to support sheet 122 by introducing an index-matching fluid (e.g., water). The depth to which good focus can be achieved in optical imaging is dependent on minimizing the surface scatter of the object, and methods such as index matching and increasing wavelength (e.g., near-infrared, NIR imaging) are is well known in the art.
The depth to which good focus can be achieved in optical imaging is dependent on minimizing the surface scatter of the object, and methods such as index matching and increasing wavelength (e.g., near-infrared, NIR imaging) are well known in the art.
The emitted sample light can arise from luminescence, fluorescent or reflection, and the focal plane of the lens can be adjusted to the elevation of object surface. Alternatively, the “light” can be ionizing radiation passing through or emitted from the object, or passing into the phosphor and forming an image. Soft x-rays, consistent with thin objects or small animals, project an image through the diffusive phosphor onto the optical boundary, adding the depth of the (more than about 0.02 mm) to the depth of focus. More significant is the focal distance contributed by the phosphor support plate 134, which may be fractional millimeters, depending upon the thickness and index of the glass or plastic. The fractional-millimeter elevation of the best focal plane contributed by the phosphor support can provide a better coincidence between the phosphor focal plane and the focal plane used for optical imaging. For NIR optical imaging, the preferred/best focal plane may be located at millimeter depths into a nominally turbid object. The phosphor support plate 134 can be thicker to maximize the coincidence of the optical and phosphor imaging planes. Those skilled in the art will recognize how to tune the materials of the present invention to optimally co-locate the preferred optical and phosphor imaging planes. Currently described materials may be practically assembled to assure multi-modal focal plane co-location to accommodate the demands of a fast lens system.
Appropriately fast lens systems for dark-field and x-ray imaging applications will likely have sub-millimeter focal depths, necessitating the above considerations. Accordingly, for a particular embodiment, it may be desirable for multiple optical elements to enable the location of a common focal plane shared by differing modes of imaging.
Emitted gamma rays from a thick object (such as 99Tc emission from an animal organ) is distributed over the plane of the phosphor, diffusing the image by millimeters, and an appropriately thick phosphor screen (about 0.1 mm) may be preferred for increased detection efficiency. Consequently, the location of the focal plane at the supporting sheet is not critical to the resolution of the radio isotopic image. Better resolution and more precise planar projection of the emitting isotope can be achieved by gamma-ray collimation. Collimators of millimeter-resolution are available and capable of projecting isotopic location to millimeter resolution at the focal plane of the phosphor in the present invention.
Of particular relevance to the operation of the present invention is the thickness of the layers in the focal plane of the lens. For example, fast lenses, (which are essential elements for the practice of imaging low-light emissions) will have a focal depth of focus of about 0.5 mm for very fast lenses. For good resolution of objects of interest, less than about 0.2 mm of spatial resolution is desirable, and a megapixel CCD camera (cooled) imaging at 100 mm field is suitable. Generally, more resolution is desirable.
Precision registration of the multi-modal image can be accomplished using methods known to those skilled in the art. By placing the object on a thin, stretched optical support that allows phosphor plate 125 to be removed without displacement of the object, co-registered optical imaging is enabled by the same lens/camera system using epi-illumination methodologies at a sufficiently similar focal plane.
Examples are now provided.
Referring to
It is noted that the first and/or second image can be enhanced using known image processing methods/means prior to be merged together. Alternatively, the merged image can be enhanced using known image processing methods/means. Often, false color is used to distinguish fluorescent signal from gray-scale x-rays in a merged image.
A phosphor plate suitable for use with the apparatus and method of the present invention is disclosed in U.S. Pat. No. 6,444,988 (Vizard), commonly assigned and incorporated herein by reference. A description of the phosphor plate described in Vizard is now provided.
Referring now to
The phosphor preferably used in phosphor layers 240 and 260 is Gadolinium Oxysulfide: Terbium whose strong monochromatic line output (544-548 nanometers (NM) is ideal for co-application with interference optics. This phosphor has technical superiority regarding linear dynamic range of output, sufficiently “live” or prompt emission and time reciprocity, and intrascenic dynamic range which exceed other phosphors and capture media. This phosphor layer preferably has a nominal thickness of 10-30 micrometers (μm) at 5-20 grams/square foot (g/ft2) of phosphor coverage, optimally absorbing 10-30 Kev x-rays. Thick phosphor layer 260 has a nominal thickness of 100 μm at 80 g/ft2 of phosphor coverage.
The duplex phosphor layers impart flexibility of usage for which the thick phosphor layer 260 may be removed to enhance the spatial resolution of the image. Thin phosphor layer 240 intimately contacts filter 220, whereas thick phosphor layer 260 may be alternatively placed on thin phosphor layer 240.
Interference filter 220 transmits light at 551 NM and below and reflects light above that wavelength. Filter 220 comprises layers of Zinc Sulfide-Cryolite that exhibits a large reduction in cutoff wavelength with increasing angle of incidence. The filter has a high transmission at 540-551 NM to assure good transmission of 540-548 NM transmission of the GOS phosphor. The filter also has a sharp short-pass cut-off at about 553 NM, that blue shifts at about 0.6 NM per angular degree of incidence to optimize optical gain.
Glass support 210 should be reasonably flat, clear, and free of severe defects. The thickness of support 210 can be 2 millimeters. The opposite side 280 of glass support 210 is coated with an anti-reflective layer (such as Magnesium Fluoride, green optimized) to increase transmittance and reduce optical artifacts to ensure that the large dynamic range of the phosphor emittance is captured.
Referring now to
The phosphor layer is removed from the PFTE support (box 340). The thin phosphor layer overcoated side is overlayed on interference filter 220 (box 360). Clean assembly of the thin phosphor layer 240 and filter 220 assures an optical boundary that optimizes management of screen light output into the camera of the lens/camera system. Optical coupling of layer 240 and filter 220 is not necessary, since performance reduction may result.
Layer 240 can be sealed around its periphery and around the periphery of filter 220 for mechanical stability and further protection of the critical optical boundary against environmental (e.g., moisture) intrusion (box 380).
Advantages of the present invention include: provides anatomical localization of molecular imaging agent signals in small animals, organs, and tissues; provides precise co-registration of anatomical x-ray images with optical molecular and radio isotopic images using one system; promotes improved understanding of imaging agent's biodistribution through combined use of time lapse molecular imaging with x-ray imaging; and allows simple switching between multi-wavelength fluorescence, luminescence, radio-isotopic, and x-ray imaging modalities without moving the object/sample.
The invention has been described in detail with particular reference to a presently preferred embodiment, but it will be understood that variations and modifications can be effected within the spirit and scope of the invention. The presently disclosed embodiments are therefore considered in all respects to be illustrative and not restrictive. The scope of the invention is indicated by the appended claims, and all changes that come within the meaning and range of equivalents thereof are intended to be embraced therein.
Reference is made to commonly assigned Provisional U.S. Patent Application No. 60/611,841 (Kodak Docket No. 88810/SLP), entitled “APPARATUS AND METHOD FOR MULTI-MODAL IMAGING”, and filed on Sep. 21, 2004 in the names of Vizard et al., and which is assigned to the assignee of this application, and incorporated herein by reference.
Number | Date | Country | |
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60611841 | Sep 2004 | US |