WO2004044562A1 - Procede et appareil pour imagerie optique a resolution temporelle de tissus biologiques d'animaux - Google Patents

Procede et appareil pour imagerie optique a resolution temporelle de tissus biologiques d'animaux Download PDF

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Publication number
WO2004044562A1
WO2004044562A1 PCT/CA2003/001705 CA0301705W WO2004044562A1 WO 2004044562 A1 WO2004044562 A1 WO 2004044562A1 CA 0301705 W CA0301705 W CA 0301705W WO 2004044562 A1 WO2004044562 A1 WO 2004044562A1
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Prior art keywords
light
points
illumination
animal
imaging
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PCT/CA2003/001705
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English (en)
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William F. Long
Yves Berube-Lauziere
David J. Hall
Laura Mcintosh
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Art Advanced Research Technologies Inc.
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Priority to JP2005506631A priority Critical patent/JP2006505804A/ja
Priority to CA2505677A priority patent/CA2505677C/fr
Priority to EP03773381A priority patent/EP1563281A1/fr
Priority to AU2003283106A priority patent/AU2003283106A1/en
Publication of WO2004044562A1 publication Critical patent/WO2004044562A1/fr

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N21/6428—Measuring fluorescence of fluorescent products of reactions or of fluorochrome labelled reactive substances, e.g. measuring quenching effects, using measuring "optrodes"
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0062—Arrangements for scanning
    • A61B5/0064—Body surface scanning
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0073—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by tomography, i.e. reconstruction of 3D images from 2D projections
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/47—Scattering, i.e. diffuse reflection
    • G01N21/4795—Scattering, i.e. diffuse reflection spatially resolved investigating of object in scattering medium
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/47—Scattering, i.e. diffuse reflection
    • G01N21/49—Scattering, i.e. diffuse reflection within a body or fluid
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N21/6408—Fluorescence; Phosphorescence with measurement of decay time, time resolved fluorescence
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N21/645—Specially adapted constructive features of fluorimeters
    • G01N21/6456—Spatial resolved fluorescence measurements; Imaging
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N2021/178—Methods for obtaining spatial resolution of the property being measured
    • G01N2021/1785—Three dimensional
    • G01N2021/1787—Tomographic, i.e. computerised reconstruction from projective measurements
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N2021/6417—Spectrofluorimetric devices
    • G01N2021/6419—Excitation at two or more wavelengths
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N21/6428—Measuring fluorescence of fluorescent products of reactions or of fluorochrome labelled reactive substances, e.g. measuring quenching effects, using measuring "optrodes"
    • G01N2021/6439—Measuring fluorescence of fluorescent products of reactions or of fluorochrome labelled reactive substances, e.g. measuring quenching effects, using measuring "optrodes" with indicators, stains, dyes, tags, labels, marks
    • G01N2021/6441—Measuring fluorescence of fluorescent products of reactions or of fluorochrome labelled reactive substances, e.g. measuring quenching effects, using measuring "optrodes" with indicators, stains, dyes, tags, labels, marks with two or more labels
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N21/645—Specially adapted constructive features of fluorimeters
    • G01N2021/6463—Optics
    • G01N2021/6471—Special filters, filter wheel

Definitions

  • the invention relates to the field of optical imaging of turbid media such as biological tissues as part of animals. More specifically, the invention relates to time resolved optical data acquisition for use in optical imaging.
  • Imaging techniques such as positron emission tomography (PET) , magnetic resonance imaging (MRI) and ultrasound imaging are available that can non-invasively gather information from within biological tissues as a basis for image reconstruction. More recently, another imaging technique, namely optical imaging has been the subject of intense research and commercial development.
  • Optical imaging is based on the information that can be derived from the analysis of the signal resulting from the interaction of light with matter as it is propagated within an object.
  • Optical imaging of turbid medium can be performed using three different approaches namely continuous wave (CW) , time domain (TD) and frequency domain (FD) .
  • CW is the simplest and least expensive of the three techniques but provides only limited information with regards to the spatial distribution of internal optical attenuation of the object being imaged.
  • TD and FD by conveying information on the time required by photons to travel within the object (FD through the Fourier transform) are considered to be "time resolved” and can be used to calculate the spatial distribution of optical characteristics of the object, such as absorption and scatter coefficients, via well known photon diffusion equations (for a review paper on this topic, see the article by Hawrysz and Sevick-Muraca, Neoplasia, vol.2 No 5, pp388-417, 2000) X.
  • Optical imaging is particularly attractive in view of its non- invas veness which permits the acquisition of in vivo information without damaging biological tissues. Furthermore the technique may be useful to monitor drug distribution, detect the presence of abnormalities within organs, or map physiological activities within mammals.
  • widespread utilization of optical imaging systems has been impeded by some undesirable characteristics of existing systems. For example, optical imaging devices often require cumbersome arrangements of optical fibers that are used to transport the light to and from the object. Such systems have been described for example by Ntziachristos and Weissleder in patent application WO 02/41769 and by Hillman et al . Phys . Med. Biol, 46 (2001)1117-1130.
  • the type of arrangement for the optical components described in these references requires a time consuming alignment of the region of interest with the optic fibers used to illuminate the object and detect the optical signal. This type of arrangement is particularly problematic when imaging is performed on living tissues of mammals.
  • Ease of data acquisition and in particular ease of the positioning the object relative to the optic components is especially .important in applications requiring high throughput such as in clinical settings or in research that make use of small mammals such as mice.
  • ' commercially available optical imaging systems for imaging small mammals have been developed.
  • a bioluminescence imaging, system developed by Xenogen Corp. Biophotonics, vol.9, No.7 pp48-51, 2002
  • this imaging device suffers from certain . disadvantages.
  • it requires the presence of bioluminescent molecules which have a spatially restricted biodistribution profile therefore greatly reducing the flexibility in imaging desired region of interests (ROI) .
  • the technique is limited by the number . of luminescent molecules that are currently available.
  • the system does not allow time resolved data to be acquired.
  • a system and method for time resolved optical imaging of biological tissues as part of an animal The design of the optical components of the . present system allows a beam of light to be directionally propagated through air, that is to say through free-space optics, to impinge on desired points of illuminations in a region of interest (ROI) of the tissue.
  • ROI region of interest
  • Light re-emitted from the tissue is collected at collection points and directionally propagated through air (i.e. through free-space optics) towards a detector.
  • the fact that the light is propagated through air allows for a greater flexibility in scanning different ROI • by eliminating the need for cumbersome fiber optics arrangements. Thus there is no need for directly contacting the animal with optical components thereby leaving sufficient space to manipulate or access the animal.
  • a time resolved optical imaging method which comprises illuminating, at one or more wavelengths, a region of interest of an animal at a plurality of predetermined illumination points using a pulsed light beam.
  • the beam is propagated through air and directed by using appropriate .optical components to the illumination points.
  • a plurality of predetermined collection points are collected by optic components having a configuration enabling selective collection of light from well defined surface areas in the ROI.
  • the collected light is then directed to a detector to produce an optical signal that can be used to generate an optical image using reconstruction algorithms.
  • a system for collecting optical ' data for use in time resolved imaging comprising one or more light sources for providing a light beam at one or more wavelengths, illuminating optic components for directionally propagating the beam through air such that a region of interest of the biological tissue within an animal is illuminated at a plurality of illumination points thereby injecting light into the tissue, collecting optic components for collecting light re-emitted at a plurality of predetermined collection points in the region of interest and for directionally propagating through air the collected light and a time correlated detector for detecting the collected light.
  • the system of the invention may advantageously be configured to acquire data for topographic or tomographic imaging.
  • Topographic imaging is achieved by maintaining constant the distance between collection points and illumination points. Synchronized. mirrors galvanometers are provided in the illumination and collection optics to achieve a constant distance between the illumination points and the detection points. Topographic data acquisition configurations ca be used to obtain 2 dimensional (2D) or 3 dimensional (3D) images .
  • ⁇ Tomographic imaging requires that light re-emitted from the animal be sampled at several different collection points/detection points configurations.
  • the system of the present invention advantageously provides moveable mirrors in the illumination and collection optics that are independently controllable thereby providing means to achieve a plurality of illumination points/ collection points configurations.
  • a method and system for optical imaging of biological tissue containing fluorescent molecules can be illuminated at an excitation wavelength while light re-emitted can be collected and detected at an emission wavelength.
  • the system also enables detection of both the emission wavelength and the excitation wavelength.
  • FIG. 1 is a flow chart diagram of an. embodiment of the method of the instant invention
  • FIG. 2 is perspective view of an embodiment of the system of the invention
  • FIG. 3 is as schematic representation of an embodiment of the system in which the source comprises a plurality of lasers
  • FIG. 4 schematically illustrates a raster scan pattern of illumination in a region of interest' at the surface of a mammal ;
  • FIG. 5 a schematic representation of an embodiment of the system of the invention in which the optical components are mounted on a gantry to be rotated around the mammal to acquire data for tomograph!c imaging;
  • FIG. 6 is a schematic representation of an embodiment of the system of the invention in which the optical components are fixed and the mammal is rotated to acquire data for tomographic imaging.
  • the invention relates to the field of optical imaging of turbid media such as biological tissues as parts of animals. . While the following description of the preferred embodiment provides examples that relate to imaging of small mammals such as mice, it will be appreciated that the method, can also be applied to larger animals and in particular to laboratory animals such as dogs, pigs and primates..
  • FIG. 1 an embodiment of the method of the present invention ' for collecting optical data for use in time resolved optical imaging is generally described.
  • pulsed light from a source of a selected intensity is directionally propagated in air (i.e. through free space optics) to illuminate a plurality of predetermined illumination points in a ROI of comprising biological tissue within an animal .
  • the light emanating from a plurality of collection points after diffusion through the tissue is selectively collected through free space optics at 4 and directionally propagated through free space at 6 towards a detector.
  • the collected light is finally measured at 8 using the detector to produce a time resolved optical signal.
  • Light emanating from points other than that being sampled is optically excluded from detection.
  • FIG. 2 A general schematic representation of the system of the present invention used for imaging small mammals is shown in FIG. 2.
  • the system comprises a light source 10 capable of generating a beam of light 12 at one or more wavelengths, illuminating optics for directionally propagating the beam of light through air, i.e. through free space optics, to desired ⁇ illumination points on the surface of the mammal 14, collecting optics for collecting the light 16 re-emitted from the mammal for directionally propagating the collected light to a detector 18, a moveable mammal supporting tray 20 mounted on a translational stage 22 and a computer 19 for controlling the source, the optics, the detector and the tray.
  • the illuminating optics comprises a moveable reflective mirror 24 which is preferably a mirror galvanometer.
  • the beam is reflected by the mirror galvanometer at an angle ⁇ and directed towards a thin angled mirror 26 which reflects the beam in a direction substantially perpendicular to the surface of the mammal being scanned.
  • the partial rotation of the mirror galvanometer will modify the angle ⁇ and direct the beam to a different point on the thin angled mirror and, consequently, to a different illumination point on the surface of the mammal.
  • Successive partial rotations of the mirror galvanometer 24 thus produces a line scan substantially parallel to the thin angled mirror.
  • Lens 28 is optionally provided and positioned between the mirror galvanometer and the thin angled mirror such that the mirror galvanometer is at the focal distance of the lens to provide telecentric imaging.
  • Filters such as. neutral density filter 29 may also be positioned between the source and mirror galvanometer 24 to adjust the intensity of the light beam.
  • the light source is preferably a variable intensity laser emitting light at a specific' wavelength.
  • a collection of lasers 31, such as diode lasers, each emitting light at different wavelengths may be used (FIG. 3) .
  • Appropriate filters such as filters 33 and 35 may be positioned between the source and the mammal and between the re-emitted light and the detector for the selection of wavelengths or to adjust the intensity of the light.
  • a switching or dichroic mirror system may be used for either sequential or simultaneous illumination of the mammal at different wavelengths.
  • a unique multi- wavelengths source of light may also be, used. In the latter case, ranges of wavelengths or specific wavelengths may .be selected by using filters, gratings or the like, as is well known by persons skilled in the art.
  • the preferred intensity of the source is determined by Maximum Permissible Exposure (MPE) limits for biological tissues as established by regulatory instances.
  • MPE Maximum Permissible Exposure
  • Standards for safe exposure are outlined, for example, in American National Standard for the safe use of lasers (ANSI Z 136.1-2000).
  • a laser emitting in the near infrared (NIR) should preferably be adjusted at- a power of about 200 mW or less for non-invasive imaging of biological tissues such as that comprising humans and small mammals.
  • Tray 20 supports the mammal while it is being imaged.
  • the mammal is preferably anesthetized for the duration of the data collection to reduce movements to a minimum.
  • parts of or the whole animal could be mechanically restrained to reduce movements.
  • the tray can be heated to maintain the body temperature of the mammal.
  • the tray can be displaced longitudinally on a translational stage 22 to position the mammal such that a plurality of line scans parallel to each other can be generated. This stepwise process is repeated a selected number of times to produce a raster scan of a region of interest (ROI) .
  • the raster scan can alternatively be achieved by longitudinally displacing the thin angled mirror 26.
  • FIG. 3 illustrates an example of a raster scan pattern at the surface of a mammal.
  • the user defined ROI 40 delimits the area to be scanned which comprises the predetermined illumination points 42.
  • the arrangement of the optic components also permits other scanning patterns to be performed. It will be appreciated that the ROI may consist of the whole animal.
  • the collecting optics which comprise collecting lens 34, reflective mirror 36 which is preferably a'mirror galvanometer and lens 38.
  • Collecting lens 34 is located above the ROI and above the thin angled mirror. The angular position of the mirror 36 relative to the incoming light and the detector determines which collection point is being sampled since only part of the light (corresponding to a given collection point) impinging on the mirror is reflected at the proper angle to reach the detector. Selective detection of the light from a given collection point may be further enhanced by optically coupling the mirror galvanometer with lenses and/or pinholes.
  • the overall arrangement of the optics which permits propagation of the light through air, allows for easy positioning and manipulation of the animal. Furthermore, since the system does not rely on optic fibers, a plurality of ROIs can be scanned without manipulating the animal simply by moving the tray so that a new ROI is brought in the focus of the optics. The movements of the tray can be controlled externally using the computer.
  • part of the light Upon impinging on the surface of the mammal, part of the light penetrates the skin and part is reflected at the air/skin boundary.
  • the photons that are propagated within the mammal are absorbed and scattered, thereby producing a large number of photon paths.
  • absorption may arise as a result of the presence of natural (endogenous) or exogenous chromophores while scattering is triggered by the presence of macromolecular structures such as proteins, lipids and the like which create refractive index inhomogeneities.
  • the fraction of the light that is not absorbed ultimately exits the mammal by diffusing, through the skin barrier at various distances from the illumination point.
  • the time resolved method used in the system of the present invention is time domain (TD) .
  • the source is briefly pulsed and the optical signal is detected as a function of time to generate a temporal point • spread function (TPSF) .
  • the source is preferably a laser source capable of generating pulses characterized by a width in the picoseconds range.
  • Time domain detectors such as time gated intensified CCDs (ICCDs) , time correlated single photon counting devices (TCSPC s) , ultrafast semiconductor detectors (avalanche and PIN photodiodes) , photomultipliers and streak cameras can be used.
  • ICCDs time gated intensified CCDs
  • TCSPC s time correlated single photon counting devices
  • ultrafast semiconductor detectors avalanche and PIN photodiodes
  • photomultipliers and streak cameras can be used.
  • a TCSPC device is used in the system of the present invention.
  • TCSPC s are capable of measuring the time taken by a photon to reach the detector as it travels through the illuminating optic, the tissue and the collecting optic. Time measurement is provided by a "clock" circuitry electronically coupling the source and the detector. Such circuits are well known in the art. TCSPC s are very sensitive and advantageously allows the use of low power sources to minimize damage to the tissue being scanned.
  • Attenuation measurements similar to measurements obtained using continuous wave can be generated using the system and method of the present invention by integrating the TPSF.
  • the efficiency of detection is a function, inter alia, of the power of the light source and the distance from the illumination point at which the light is collected.
  • the intensity of the source may be adjusted so that the flux of photons reaching the detector is optimized for the characteristics of the detector.
  • the probability of detecting a photon for each illumination light pulse be approximately 1% in order to avoid distortions caused by electronics dead-time losses in the temporal profile being measured as is well known by a person skilled in the art .
  • the illumination duration (which is provided by the number of light pulses) directed at a given point on the mammal may* vary in order to provide a sufficient number of detected photons to produce an adequate signal and yet keep the duration as short as possible to reduce the acquisition time.
  • the power of the beam should be adjusted so that approximately 8 x 105 photons per second are detected. It will be appreciated that the selection of the appropriate frequency is based on, among other factors, the characteristics of the optical components, of the detector, of the tissue to be imaged and of the type of optical data that is desired.
  • the TPSF may also be generated by using a time gated intensified charged coupled device (ICCD) .
  • ICCD time gated intensified charged coupled device
  • This type of detector can provide spatial resolution enabling simultaneous detection of optical signals emanating from different collection points.
  • the light collected at any given collection points can be divided into constituent wavelengths to produce two or more beams which can be directed to different detection positions of the ICCD.
  • the intensity of the source should ⁇ be adjusted accordingly while remaining below levels that could cause tissue damage.
  • the system and the mammal are placed in an enclosure such as a box 50.
  • the box is preferably light tight to prevent any stray light from interfering with the measurements.
  • the interior of the box can be accessed through door 56.
  • optical signals are obtained from a plurality of illumination/detection points within the ROI.
  • the configuration of the illumination/detection points may vary depending of the type of image to be reconstructed.
  • topographic and tomographic images can be generated with the system and method of the present invention and both require different illumination/detection configurations .
  • the position of the collection points relative to the illumination points is determined prior to the start of the acquisition and is a function of the desired depth of imaging in the region of interest. For planes of imaging that are close to the surface of the skin, the collection points are located near the illumination points since the deeper a photon travels, the lower is the probability of that photon being re-emitted near the illumination points, and conversely.
  • collection points are maintained at a fixed distance from illumination points so as to gather information from substantially the ⁇ same depth across the ROI.
  • the mirror galvanometers comprised in the illuminating and the collecting optic may be synchronized to achieve rapid scanning with ' a constant illumination/detection points distance.
  • Tomographic data is obtained when the illumination and collection points are permuted so as to generate a plurality of illumination to collection points distances thereby obtaining information from different depths.
  • tomographic images can be generated.
  • the two mirror galvanometers 24 and 26 are preferably controlled independently in order to obtain multi-perspective data.
  • the mirror galvanometer in the illumination optic directs the light at a desired illumination point
  • the mirror galvanometer in the collection optic may be programmed to sample light at a plurality of different collection points.
  • the illumination and collection optics are mounted on a movable gantry system 52 which turns around the animal (FIG. 5) .
  • the tray preferably exhibits an "I" shape. This particular shape facilitates- data acquisition as the illumination and collection optics is rotated around the region of interest (for example: torso region) while allowing the animal to be comfortably supported. With this configuration, angular displacements of an amplitude substantially equals to 360 degrees are possible.
  • the mammal may be rotated instead of the gantry. The mammal may be maintained on the tray by attaching its legs to the tray. Rotation around the cranio-caudal axis of the body by 360° is possible. This design configuration can reduce weight, volume and complexity compared to the moveable gantry system.
  • the mammal can be rotated along the cranio-caudal axis while sitting.
  • the animal is positioned on the stage such that the region of interest is kept straight by softly supporting its head.
  • These designs allow the animal to be scanned over almost 360°.
  • the optics may be modified to adapt it to the different tomographic configurations.
  • mirror 54 in the "sitting" configuration provides a convenient way of directionally propagating the light.
  • the system may also comprise means to determine the volumetric profile of the animal.
  • the volumetric profile can be determined by scanning the animal with a laser beam directed substantially perpendicularly to the animal . By simultaneously acquiring an image of the laser beam at the surface of the animal with a video camera placed at an angle to the laser path, the volumetric profile may be determined. The animal may be scanned by moving the tray. It will be appreciated that the volumetric profile thus obtained provides spatial information useful for image reconstruction and display.
  • exogenous molecules may be introduced in the
  • exogenous chromophores as well as fluorophores may be used.
  • biodistribution of such contrast agents can be followed using the method and system of the present invention.
  • biodistribution can be followed over time thereby producing pharmacokinetics data.
  • the optics as well as the source can be arranged to illuminate and detect light at one or more wavelengths as is described supra. This property can be exploited to follow the pharmacokinetics of two or more fluorophores and/or chromophores.
  • the source and associated optics can be arranged to illuminate at an excitation wavelength of a fluorophore while the detector and associated optics can be arranged to detect light at an emission wavelength of the fluorophore.

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Abstract

L'invention concerne un procédé et un système permettant de collecter des données optiques, destinés à être utilisés en imagerie optique à résolution temporelle, selon lesquels de la lumière pulsée est propagée de manière directionnelle à travers des optiques en espace libre (24, 26, 28, 29) afin d'arriver sur une pluralité de points d'illumination situés à la surface d'un tissu biologique (14) de type tissus de petits animaux. La lumière renvoyée par le tissu est collectée et propagée de manière directionnelle à travers des optiques en espace libre (34, 36, 38) vers un détecteur (18) afin que soient produits des signaux optiques à résolution temporelle utiles à des fins de reconstructions d'images optiques.
PCT/CA2003/001705 2002-11-11 2003-11-10 Procede et appareil pour imagerie optique a resolution temporelle de tissus biologiques d'animaux WO2004044562A1 (fr)

Priority Applications (4)

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JP2005506631A JP2006505804A (ja) 2002-11-11 2003-11-10 動物の一部としての生物学的組織の時間分解光学撮像用の方法および装置
CA2505677A CA2505677C (fr) 2002-11-11 2003-11-10 Procede et appareil pour imagerie optique a resolution temporelle de tissus biologiques d'animaux
EP03773381A EP1563281A1 (fr) 2002-11-11 2003-11-10 Procede et appareil pour imagerie optique a resolution temporelle de tissus biologiques d'animaux
AU2003283106A AU2003283106A1 (en) 2002-11-11 2003-11-10 Method and apparatus for time resolved optical imaging of biological tissues as part of animals

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IBPCT/IB02/04698 2002-11-11
IB0204698 2002-11-11
US31785602A 2002-12-12 2002-12-12
US50535203P 2003-09-22 2003-09-22
US60/505,352 2003-09-22
US10/665,297 2003-09-22

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WO2007144542A1 (fr) * 2006-06-14 2007-12-21 Quidd Dispositif d'imagerie optique
CN102048525A (zh) * 2011-01-26 2011-05-11 浙江大学 一种生物体荧光三维成像***及应用
EP2804524A4 (fr) * 2012-01-19 2016-01-27 Technion Res & Dev Foundation Système et méthode d'imagerie de vaisseau

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EP0760477A2 (fr) * 1995-08-29 1997-03-05 Hamamatsu Photonics K.K. Procédé et appareil pour mesurer dans un milieu diffusant
JP2002051662A (ja) * 2000-08-08 2002-02-19 Japan Science & Technology Corp 小動物用体温保持装置
WO2002027300A1 (fr) * 2000-09-27 2002-04-04 Amersham Biosciences Uk Ltd Mesure de temps de declin de fluorescence
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WO2002056765A2 (fr) * 2001-01-12 2002-07-25 General Hospital Corporation Systeme et procede permettant l'etalonnage et la mise en image simultanes d'un milieu
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WO2007144542A1 (fr) * 2006-06-14 2007-12-21 Quidd Dispositif d'imagerie optique
FR2902307A1 (fr) * 2006-06-14 2007-12-21 Quidd Soc Par Actions Simplifi Dispositif d'imagerie optique
CN102048525A (zh) * 2011-01-26 2011-05-11 浙江大学 一种生物体荧光三维成像***及应用
EP2804524A4 (fr) * 2012-01-19 2016-01-27 Technion Res & Dev Foundation Système et méthode d'imagerie de vaisseau
US10646160B2 (en) 2012-01-19 2020-05-12 Technion Research & Development Foundation Limited Vessel imaging system and method
US11850065B2 (en) 2012-01-19 2023-12-26 Technion Research & Development Foundation Limited Vessel imaging system and method

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AU2003283106A1 (en) 2004-06-03
CA2505677C (fr) 2011-11-01

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