CA2359643A1 - Polarized light scattering spectroscopy of tissue - Google Patents
Polarized light scattering spectroscopy of tissue Download PDFInfo
- Publication number
- CA2359643A1 CA2359643A1 CA002359643A CA2359643A CA2359643A1 CA 2359643 A1 CA2359643 A1 CA 2359643A1 CA 002359643 A CA002359643 A CA 002359643A CA 2359643 A CA2359643 A CA 2359643A CA 2359643 A1 CA2359643 A1 CA 2359643A1
- Authority
- CA
- Canada
- Prior art keywords
- light
- probe
- tissue
- fiber optic
- polarized
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Classifications
-
- 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
- A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
- A61B5/0084—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for introduction into the body, e.g. by catheters
-
- 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
- A61B5/0075—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by spectroscopy, i.e. measuring spectra, e.g. Raman spectroscopy, infrared absorption spectroscopy
Abstract
The present invention relates to the use of polarized light to measure properties of tissue. More particularly, polarized light can be used to dete ct dysplasia in tissue as the polarization of backscattered light from such tissues is preserved while the contribution of diffusely scattered light fro m underlying tissues can be removed. A fiber optic system for delivery and collection of light can be used to measure tissues within the human body.</S DOAB>
Description
POLARIZED LIGHT SCATTERING SPECTROSCOPY OF TISSUE
RELATED APPLICATION
This application claims priority to U.S. Application No. 09/237,153, filed on January 25, 1999, the entire contents of which is incorporated herein by reference.
GOVERNMENT SUPPORT
The invention was supported, in whole or in part, by a grant number P41RR02954 from National Institute for Health. The Government has certain rights in the invention.
BACKGROUND OF THE INVENTION
More then 90% of cancer lesions are epithelial in origin. Several of the most common forms of epithelial cancers such as colorectal, esophageal, bladder, cervical and oral cancers have a well defined, detectable pre-cancer stage called dysplasia.
Dysplasia is characterized by sequential accumulation of mutations in defined oncogenes and tumor suppresser genes. If detected, the absolute majority of the dysplastic lesions are curable. Clinical efforts to detect and treat this pre-cancerous stage of epithelial cancer have been shown to reduce the mortality rate.
Diagnosis of epithelial dysplasia remains difficult because it typically does not form macroscopic structures such as polyps, and is usually only visible after cancer has developed. Standard methods of detecting epithelial dysplasia are based on random biopsies and pathologic examination of the stained biopsy material.
However, random biopsies have high sampling error. In many cases less than 1 %
of the epithelial surface at risk for dysplasia can be examined.
All types of epithelial dysplasia have several common characteristics, namely enlargement of epithelial cell nuclei with an increase in the nuclear to cytoplasmic ratio, nuclear hyperchromatism, and increased number and stratification of epithelial cells. Despite these well-characterized epithelial changes, classification has been difficult as demonstrated by high inter-observer disagreement, even among experienced pathologists.
SUMMARY OF THE INVENTION
Non-invasive, in-vivo methods of detecting epithelial dysplasia provide for surveillance of epithelial surfaces, and the pathological diagnosis of pre-cancerous conditions in humans.
Optical techniques are well suited to be a substitution for random biopsies, since they are non-invasive, do not require tissue removal, and can be performed in-vivo. Moreover, they are fast (can be applied in real time), are relatively non-expensive, are able to work on microscopic scale, and thus can find very small dysplastic sites. The latter are highly likely to be missed by random biopsies.
The present invention relates to light scattering spectroscopy of polarized light to provide information about scatterers in surface layers of turbid media such as tissue. This process need not utilize fluorescence or absorption spectral features, but rather scattering properties of surface tissues such as epithelial layers. It can characterize properties of large scatterers (cell nuclei) in human epithelium and provide histological information about human tissues and diagnose dysplasia in real time in human organs in-vivo.
The idea of light scattering spectroscopy of unpolarized light to determine features of epithelial tissue has been described in U.S. Serial No. 08/948,734 filed on October 10, 1997, and in International Application No. PCT/LJS98/21450 filed on October 9, 1998, which designated the United States, the entire contents of these applications being incorporated herein by reference. The major centers of light scattering in epithelium are cellular organelles such as mitochondria and nuclei with the refractive index higher than that of the surrounding cytoplasm. Light backscattered from surface epithelial cell nuclei has an oscillatory wavelength dependent component. The periodicity of this component increases with nuclear size, and its amplitude is related to the density of the nuclei. Thus, by analyzing the amplitude and frequency of the oscillatory component, the density and size distribution of epithelial nuclei can be determined. Normal nuclei have a characteristic diameter l=4-7 ~,m. In contrast, dysplastic nuclei can be as large as 20 ~,m. Nuclear size and density are important indicators of neoplastic precancerous changes in biological tissue. The ability to measure nuclear size distribution in vivo and in real time has valuable applications in clinical medicine. This enables the diagnosis of precancerous changes in various human organs such as esophagus, colon, bladder, oral cavity, cervix, etc. non-invasively and in-real-time.
Epithelium covers surfaces of organs in the human body. The thickness of epithelium ranges from 20 ~.m (one cell layer) to a few hundred microns (multiple cell layers). Beneath epithelium there are layers of relatively acellular connective and muscular tissues. Since dysplasia is limited to the epithelium, it is important to differentiate between the signal associated with the epithelium and underlying tissues. The backscattered component which carnes information about surface epithelial nuclei is present in light reflected from mucosal tissues. However, it is ordinarily very small in amplitude, and easily masked by a background signal formed by diffuse scattering from the underlying tissue. To analyze that component the background signal must be removed. One can remove the diffuse background by modeling the general spectral features of the background. However, to make the approach more useful in practical medicine, and to be able to diagnose dysplasia in vivo, in real time, and in different organs, it is necessary to develop more robust method of removing or significantly reducing the diffuse component of the scattered light.
RELATED APPLICATION
This application claims priority to U.S. Application No. 09/237,153, filed on January 25, 1999, the entire contents of which is incorporated herein by reference.
GOVERNMENT SUPPORT
The invention was supported, in whole or in part, by a grant number P41RR02954 from National Institute for Health. The Government has certain rights in the invention.
BACKGROUND OF THE INVENTION
More then 90% of cancer lesions are epithelial in origin. Several of the most common forms of epithelial cancers such as colorectal, esophageal, bladder, cervical and oral cancers have a well defined, detectable pre-cancer stage called dysplasia.
Dysplasia is characterized by sequential accumulation of mutations in defined oncogenes and tumor suppresser genes. If detected, the absolute majority of the dysplastic lesions are curable. Clinical efforts to detect and treat this pre-cancerous stage of epithelial cancer have been shown to reduce the mortality rate.
Diagnosis of epithelial dysplasia remains difficult because it typically does not form macroscopic structures such as polyps, and is usually only visible after cancer has developed. Standard methods of detecting epithelial dysplasia are based on random biopsies and pathologic examination of the stained biopsy material.
However, random biopsies have high sampling error. In many cases less than 1 %
of the epithelial surface at risk for dysplasia can be examined.
All types of epithelial dysplasia have several common characteristics, namely enlargement of epithelial cell nuclei with an increase in the nuclear to cytoplasmic ratio, nuclear hyperchromatism, and increased number and stratification of epithelial cells. Despite these well-characterized epithelial changes, classification has been difficult as demonstrated by high inter-observer disagreement, even among experienced pathologists.
SUMMARY OF THE INVENTION
Non-invasive, in-vivo methods of detecting epithelial dysplasia provide for surveillance of epithelial surfaces, and the pathological diagnosis of pre-cancerous conditions in humans.
Optical techniques are well suited to be a substitution for random biopsies, since they are non-invasive, do not require tissue removal, and can be performed in-vivo. Moreover, they are fast (can be applied in real time), are relatively non-expensive, are able to work on microscopic scale, and thus can find very small dysplastic sites. The latter are highly likely to be missed by random biopsies.
The present invention relates to light scattering spectroscopy of polarized light to provide information about scatterers in surface layers of turbid media such as tissue. This process need not utilize fluorescence or absorption spectral features, but rather scattering properties of surface tissues such as epithelial layers. It can characterize properties of large scatterers (cell nuclei) in human epithelium and provide histological information about human tissues and diagnose dysplasia in real time in human organs in-vivo.
The idea of light scattering spectroscopy of unpolarized light to determine features of epithelial tissue has been described in U.S. Serial No. 08/948,734 filed on October 10, 1997, and in International Application No. PCT/LJS98/21450 filed on October 9, 1998, which designated the United States, the entire contents of these applications being incorporated herein by reference. The major centers of light scattering in epithelium are cellular organelles such as mitochondria and nuclei with the refractive index higher than that of the surrounding cytoplasm. Light backscattered from surface epithelial cell nuclei has an oscillatory wavelength dependent component. The periodicity of this component increases with nuclear size, and its amplitude is related to the density of the nuclei. Thus, by analyzing the amplitude and frequency of the oscillatory component, the density and size distribution of epithelial nuclei can be determined. Normal nuclei have a characteristic diameter l=4-7 ~,m. In contrast, dysplastic nuclei can be as large as 20 ~,m. Nuclear size and density are important indicators of neoplastic precancerous changes in biological tissue. The ability to measure nuclear size distribution in vivo and in real time has valuable applications in clinical medicine. This enables the diagnosis of precancerous changes in various human organs such as esophagus, colon, bladder, oral cavity, cervix, etc. non-invasively and in-real-time.
Epithelium covers surfaces of organs in the human body. The thickness of epithelium ranges from 20 ~.m (one cell layer) to a few hundred microns (multiple cell layers). Beneath epithelium there are layers of relatively acellular connective and muscular tissues. Since dysplasia is limited to the epithelium, it is important to differentiate between the signal associated with the epithelium and underlying tissues. The backscattered component which carnes information about surface epithelial nuclei is present in light reflected from mucosal tissues. However, it is ordinarily very small in amplitude, and easily masked by a background signal formed by diffuse scattering from the underlying tissue. To analyze that component the background signal must be removed. One can remove the diffuse background by modeling the general spectral features of the background. However, to make the approach more useful in practical medicine, and to be able to diagnose dysplasia in vivo, in real time, and in different organs, it is necessary to develop more robust method of removing or significantly reducing the diffuse component of the scattered light.
The present invention provides a method of measuring scattering features of epithelial cells by using polarized light spectroscopy. Note that initially polarized light loses its polarization while traveling through a turbid medium (tissue is an example of turbid medium). On the other hand the light scattered backward after a single scattering preserves polarization. Thus, by removing the nonpolarized component of the scattered light, one is able to distinguish light scattered by epithelial cells. The residual spectrum can be further analyzed so that the size distribution of the nuclei and their density can be determined.
A preferred embodiment of the inventions includes a fiber optic light delivery and collection system for diagnoses of tissue. The fiber optic system can be housed in a probe housing proximal and distal ends where the distal end can be inserted into the various lumens of the human body for in vivo measurements of tissue. Polarizers can be used on the distal ends of both delivery and collection fibers. With optical fibers that preserve the polarization of light, the polarizers can be positioned at the proximal end of the probe. In a three fiber system, the probe can use a central delivery fiber and two off center collection fibers that collect two different polarization components of light returning from the tissue. The polarizers can be birefringent crystalline materials such as quartz, sapphire or calcite.
The calcite must be sealed from the working environment.
BRIEF DESCRIPTION OF THE DRAWINGS
Figure 1 illustrates a preferred embodiment of a polarization-based light scattering spectroscopic system.
Figures 2 A and B are reflectance spectra of the two-layered tissue phantom (polystyrene beads on top of gel containing blood and BaS04) for parallel and perpendicular polarizations (notice characteristic hemoglobin dips) respectively.
Figures 3 A-D illustrate differences of two polarizations for (A) 4.56 ~,m beads in water (relative refractive index n ~ 1.19), (B) 9.5 ~,m beads in water (n ~ 1.19), (C) 5.7 ~.m beads in glycol (n ~ 1.09), (D) 8.9 ~m beads in glycerol (n ~ 1.07) where the signals (dashed lines) are in good agreement with Mie -S-calculations (solid lines) and the absorption features of hemoglobin are completely removed.
Figure 4 is a spectrum of the polarized (residual) component of back-scattered light: experimental data vs. fit of the Mie calculations for the polarized back-scattering for T84 cancerous colonic cells where best fits provide the following sets of parameters: average size 10.2 ~,m, standard deviation 1.5 ~,m, relative refractive index 1.045, and the sizes and standard deviations are in agreement with those measured using light microscopy.
Figure S is a spectrum of the polarized (residual) component of back-scattered light: experimental data vs. fit of the Mie calculations for the polarized back-scattering for normal intestinal cells where best fits provide the following sets of parameters: average size 5.0 ~.m, standard deviation 0.5 Vim, relative refractive index 1.035, and the sizes and standard deviations are in agreement with those measured using light microscopy.
Figure 6 shows the nuclear size distribution for normal intestinal cells and T84 cancerous colonic cells where in each case, the solid line is the distribution extracted from the data, and the dashed line is the distribution measured using light microscopy.
Figure 7 schematically illustrates a fiber optic probe system for performing in vivo optical measurements of tissue in accordance with the invention.
Figures 8A and 8B show the distal end of a probe of a preferred embodiment of the invention.
Figures 9A-9C illustrate another preferred embodiment of a fiber optic probe in accordance with the invention.
The foregoing and other objects, features and advantages of the invention will be apparent from the following more particular description of preferred embodiments of the invention, as illustrated in the accompanying drawings in which like reference characters refer to the same parts throughout the different views. The drawings are not necessarily to scale, with emphasis being placed upon illustrating the principles of the invention.
DETAILED DESCRIPTION OF THE INVENTION
To determine properties of epithelial cells, one can correlate measured spectrum of the backscattered light with a model or representation. Using Mie theory, which provides the exact solution for the problem of light scattering by spherical objects of arbitrary sizes, the sizes and relative refractive indexes of the scatterers can be determined.
For polarized incident light, light scattered by a spherical particle with diameter d has components which are polarized parallel and perpendicular to the plane of scattering. For a plane polarized wave incident in direction so, light scattered into direction s will have components which are polarized parallel (p) and perpendicular (s) to the plane of scattering. Intensities Ip and IS of these components are related to the intensities of the incident light Ip~°~ and ISO°> as follows:
l S( z In~s~ - 4 ~ 'z z ~~ In~so~ (1) Kd Sz~S,So~lz o Is~s~ - 4 Kzdz In~so~ (2) where k is the wavenumber of the incident light, S~ and Sz are scattering amplitudes which can be calculated numerically using Mie theory, and sl and sz are unit vectors defining propagation of the incident and scattered light. Scattering amplitudes are functions of a scattering angle ~ =cos' (s~so ) and are normalized so that integral (IS, (~)Iz + ISz (~) z ) sin ~d~ equals the total elastic scattering cross section.
Now consider an experiment in which linearly polarized incident light, intensity Io, is distributed over solid angle OSZo and scattering is collected over solid angle X52. The polarization, so , of the incident light can be decomposed into a component sP , in the scattering plane (i.e. the plane formed by s and "so ), and a perpendicular component ss . By means of analyzers, we detect two orthogonal components of the scattered light intensity, III having polarization sa and I1 having perpendicular polarization sa . The scattered intensity components are then given by III = ~~d2 f d"s f dsolo(so~S2(so,s~cos~pcos~po+S,~"so,"s)sin~psin~po z nn n~
(3) 11 = ~~d2 f ds~dsolo(so)lSz~so,s)cos~psin~po-S,(so,s)sin~pcos~po~2 nn n~
(4) If the incident light is completely collimated (OS2o =0), light scattered directly backward will be polarized parallel to the incident light polarization. In this case we can orient one of the analyzers parallel to the incident polarization direction ( so ~ s~ ) . If the solid angles of the incident and collected light are sufficiently small and approximately equal, both III and Il will be present. However, the analyzer can still be positioned such that ( eo ~ sq ) . Thus, in this case the collected light will still be highly polarized, and l~l » Il . For this case the expression for the residual intensity, I;. - Il can be simplified:
_ _ 4I a~
III 11 ~ kd2 f Re(S; ~8)SZ (a~~ sin 9d,~ , (5) with ~ o = ~~ .
2 ~c _g_ Consider a system of two layers of scattering media such as epithelial tissue in which a thin layer of large scattered (d»~,) covers a highly turbid layer of underlying tissue. Each of these layers gives rise to a different type of scattering.
This two layer system represents optical properties of many human tissues with the first layer correlated with epithelium and second layer correlated with other tissue layers beneath epithelium. The upper layer is optically thin so that it does not allow multiple scattering. Small portions of incident linearly polarized light is backscattered by the particles in the upper layer. The rest of the signal penetrates to the second layer that is optically thick. Light propagating through the second layer is randomized by means of multiple scattering. This diffusive light, if not absorbed in the second layer, returns to the surface. Thus, emerging light has two contributions: one from light backscattered by the particles of the first layer, Ib, and the other being diffusely reflected from the second layer, Id. Ib has high degree of linear polarization that is parallel to the polarization of the incident light: hb»Ilb.
As a result of multiple scatterings in the second layer, diffusely reflected light is depolarized and Ipd=Ila. Therefore, the residual intensity of the emerging light h -Il~Ipb-I1b 1S dominated by the contribution from the upper layer and is substantially free from both absorption and scattering from the tissue below.
Expressions (3)-(S) relate Id -li to the scattering amplitudes Sl and S2. The amplitudes depend on the wavelength of the light being scattered ~,=~/k, the scatter's size d and the ratio of its refractive index to that of the surrounding medium, relative refractive index h. Therefore, the spectrum of the residual intensity varies with the scatterer's size and relative refractive index. Thus, sizes and refractive indexes of the scatterers can be found by fitting the representation of the Mie theory using equations (3)-(S) to the residual intensity spectrum.
A system 10 that measures excised tissue samples in vitro is illustrated in Figure 1. This system 10 delivers collimated polarized light on tissue 12 and separates two orthogonal polarizations of back-scattered light. The difference of these two components provides information about light scattered in the epithelial layer only. Since linearly polarized light is depolarized faster than circularly polarized light while passing through a random medium, linear polarization was used. The system provides light from a broad-band source 14 (250 W tungsten lamp, Model 66181, Oriel Instruments, Inc., Stratford, CT) is collimated and then refocused with a small solid angle onto the sample using a fiber 16, a lens 18 and an aperture 20. A broadband polarizer 22 linearly polarizes the beam, before it is delivered to the surface of a scattering medium through beamsplitter 24. The light beam strikes the surface of the sample with an angle ~ 1 S ° relative to the normal in order to avoid specular reflectance. The diameter of the beam is 2mm. The reflected light is collected in a narrow cone ( 0.015 radian) with apertures 26 and mirror 28 and two polarizations, parallel Id and orthogonal Ii to the initial polarization, are separated by a broadband polarizing beam sputter cube 28 which also acts as our analyzer (Melles Griot, Inc.). The output from this analyzer is delivered through lenses 30 and ZOO~,m optical fibers 32, 34 (Ocean Optics, Inc., Dunedin, FL) into two channels of a multichannel spectroscope 36 (quadruple spectroscope, Model SQ200, Ocean Optics, Inc., Dunedin, FL). This enables the spectra of both components to be measured simultaneously in the range from 300 nm to 1200 or optionally in the range from 400 nm to 900 nm.
The beams are not perfectly collinear, and when they pass through the polarizer and analyzer cubes this gives rise to a small amount of distortion.
Furthermore, the beamsplitter has different reflectivities for s and p polarizations. A
diffusely reflective white surface was used as standard to correct for wavelength non-uniformity, and to calibrate the signals in the two channels. Il~~,) and I~~ (~,~ were each normalized to the corresponding background spectra, Ii (~,~
and I~~B (~.) were each normalized to the corresponding background spectra, I~~
~~.~ and Il ~~.) taken with the white diffusing surface. This removed spectral non-uniformities in the light source. Thus, the experiments actually measured the normalized residual intensity, DI:
01- III _ 11 I$ IB
II
(5) Measurements on simple single- and two-layer systems were conducted to determine operational parameters. The single layer system included polystyrene beads of various sizes ranging from 0.5~.m to 10~,m (Polyscience, Inc.) embedded in de-ionized water, glycol, or glycerol. The thickness of these layers was varied so that the optical thickness i ranged from 0.1 to 5 a photon propagating through a medium with i=1, undergoes one scattering event on average). The beads of large sizes 4-10 ~m were used to represent cell nuclei. Since the relative refractive index of the polystyrene beads in water is about 1.2 (absolute refractive index is about n=1.59) and is substantially higher than that of the cell nuclei relative to the cytoplasm which is in the range from 1.03 to 1.1, glycol (na 1.45) and glycerol (na 1.48) were used instead of water to decrease the relative refractive index of the beads and, therefore, better approximate biological conditions.
In the single layer measurements the component of the backscattered light with the same state of polarization as the incoming light (denoted by I~ was almost 100 times larger than the component with the polarization orthogonal to the polarization of the incoming light (denoted by li). This establishes that single scattering from large spheroidal particles preserves polarization.
In the measurements with two layer models the first layer consisted of polystyrene beads embedded in water, glycol, or glycerol and was prepared as in the single layer measurements. The second layer included a gel containing solution of BaS04 powder which provided scattering properties of the second layer and human blood. Hemoglobin content of the blood provided absorptive properties to the model. This physical model simulated epithelium and underlying tissues.
Adjusting concentrations of the BaS04 powder and blood, the scattering and absorption properties, can be made similar to those of a biological tissue, since in the optical spectral region hemoglobin is known to be the major absorber.
Figures 2A and 2B shows spectra of the parallel h and orthogonal I1 polarized components of the light reflected from a two layer system. In this measurement, the first layer contained beads embedded in glycol. The beads had an average diameter of 4.56 ~.m. Standard deviation of their sizes was 0.03 p,m.
Optical thickness of the first layer was z ~ 0.8. The second layer was optically thick and its scattering and absorptive properties were comparable to those of a biological tissue. The spectrum of Il is dominated by characteristic hemoglobin absorption bands. At the same time, characteristic spectral features of light scattered by 4.56 ~m beads in the first layer, namely apparent ripple structure, and hemoglobin absorption in the second layer are seen in the spectrum of Ia.
The residual spectrum dI is shown in Figure 3A. No hemoglobin absorption features are seen and the diffusive background coming from the second layer was completely removed. The ripple structure characteristic of scattering from spheres is evident. The comparison with Mie theory representation for scatterers with d =
4.56 ~m , ~d=0.03~Cm and n=1.035 correspond with the ~tm shown in Figure 3B
shows high degree of accuracy. The residual spectra obtained in measurements with other bead sizes (5.7~,m, 8.9~m, and 9.S~,m) embedded in any of the media used (water, glycol, and glycerol) had no measurable diffusive background component and agreed with Mie theory. Figure 3B shows the agreement between the theory and the measurements for 9.5 ~.m beads.
Similarly, the results of the measurements for 5.7 ~m and 8.9 ~m beads in glycerol and glycol are shown in Figures 3(C) and (D) respectively. Mie theory corresponds with the measured values in these cases as well. The high frequency ripple structure decreases as the relative refractive index gets smaller. The law frequency oscillations remain evident. Measurements showed that the instrument was able to detect signal from the bead solution of as low optical thickness as 0.05.
Small disagreements seen in the spectrum can result from imperfect calibration of the instrument for the wavelength dependence of the optical elements used. The beams are not perfectly collinear and so there arises some imperfections in the polarized signals from the two channels when the beam passes through the polarizer and the analyzer elements. Further, the beam sputter used has different reflectivities for the s and the p polarized beams. However, using just a white standard, signals in the two channels were corrected for any wavelength non-uniformity and further used for calibration of signals.
Measurements with cell monolayers were conducted and the results are described in connection with Figures 4-6. A layer of gel containing solution of BaS04 powder and human blood under the monolayers is used to represent underlying tissue. The concentrations of the BaS04 powder and blood, were adjusted to match optical properties of the biological tissue. Three types of cells were measured: normal intestinal cells, T84 cancer colonic cells and the fibroblasts.
The measurements were similar to the measurements with beads. Nuclei of cells, however, had relative refractive indexes smaller then those of beads as well as larger size distributions which substantially eliminate the ripple structure. Fitting of the observed residual spectrum to Mie theory was performed. Three parameters in the f tting procedure were average size of the nuclei, standard deviation in size (a Gaussian size distribution was assumed), and relative refractive index.
For normal intestinal cells, the best fit was obtained using d=S.O~,m,Od=O.S~m, and n=1.045 (Figure 4). For the fibroblast cells, d-7.0 ~,m, ~d=1.0 ~,m and n=1.051 were obtained. For the T84 colon cancer cells the corresponding values were d=9.8 ~,m Od=1.5 Vim, and n=1.04 (Figure 5).
In order to check these results, the distribution of the average size of the cell nuclei was measured using light microscopy. The sizes and their standard deviations were in agreement with the parameters from Mie theory. A histogram showing the size distributions obtained for the normal T84 cells are shown in Figure 6.
The accuracy of the average size is estimated to be 0.1 ~,m, and the accuracy in n as 0.001. Note the larger value of n obtained for cancerous cells, which is in agreement with the hyperchromaticity of cancer cell nuclei observed in conventional histopathology of stained tissue sections.
The backscattered signal can be described by Mie theory if the average size of the nuclei d, standard deviation in sizes Od, and relative refractive index n are varied. Note that in Mie theory, dependence on d and n does not always come as a (n-I)d product. Thus, the residual spectra have enough information to extract d and n simultaneously.
The size distributions for monolayers were compared to light microscopy and were in a good agreement for all three lines of cells. The accuracy of size and standard deviation extraction was approximately 0.1 ~,m which makes the method useful in differentiating nuclei of different cell types, including cancerous and non-cancerous cells of the same organ.
Ability to detect cell nuclear enlargement and changes in refractive index of the nucleus (which can be related to the amount of DNA and protein in the nucleus) has valuable applications in clinical medicine.
The method of tissue diagnosis can be implemented either in a diagnostic device in which light can be delivered to points on the surface of the tissue, and collected and analyzed at each of those points on the surface of the tissue, and collected and analyzed at each of those points. In an in vivo system optical fibers are used to deliver and collect light. The fiber probe can be inserted in the endoscope biopsy channel or any similar device (depending on the type of the procedure and organ under study). Polarizer and analyzer can be placed at the tip of the probe in front of the delivery and collection fibers. Such an instrument can be used during routine endoscopic procedures to detect precancerous changes in-vivo in real time.
Such a probe system 40 is shown generally in Figure 7. This system 40 includes a broadband light source 42 that is optically coupled to a delivery fiber 44 extending through probe 50. As schematically shown in Figure 7, the probe 50 can be inserted through a channel in an endoscope 48, however the probe 50 can be constructed to be used separately. In a preferred embodiment described hereinafter, the light from source is directed through a polarizer at the distal end of probe 50.
However, in another embodiment using polarization preserving optical fibers, a polarizer 26 can be used at the proximal end of probe fiber 44 to direct polarized light 46 through the fiber. Similarly, the proximal ends of collection fibers 65, 66 can employ polarizing elements 65, 66 respectively to transmit selected polarization components into the multichannel fiber spectrometer 54. The data can then be processed by computer 56, stored in computer 56, stored in computer memory and displayed on display 60 as needed.
The probe system can include a fiber optic probe having a distal end incorporating polarizers as seen in Figure 8A and 8B.
Figures 8A and 8B show the distal end of a probe 100 for the use of polarized light for in vivo diagnosis. Figure 8A shows a fiber optic device that is divided into three sections, the inner delivery fiber and two sets of collection fibers 150 and 152 that collect different polarization components. The cross-section of Figure 8B shows fibers 156 delivering light onto the tissue 140. They have to pass through a polarizer 120 which is also seen in the cross-section view of Figure 8B.
The polarizing element is divided into at least two parts or elements 122, 126.
Optical fibers 152 are arranged to collect the back reflected light from the tissue surface.
The backscattered light has two polarization components, corresponding to the parallel and the perpendicular components to the incident light. The two are differentiated by two different birefringent analyzers shown by two sectioned ring elements 122, 126. A first element 122 allows the parallel component to pass through while the second element 126 allows perpendicular component. A portion of element 122 polarizes light exiting fiber 156. As the fibers have low numerical apertures to collect light over very small angles, it is necessary to extend the distance 136 between the fiber ends and the aperture surface 142 opening to the tissue surface 140. It can be as long as Smm. To avoid spurious internal reflections a glass block 130 is shown having refractive index n2 lower than that of the shield 132 with refractive index n~. The shield I32 can be coated with an absorbing element so that light hitting the boundaries is refracted out and then absorbed by the absorbing coating on the outer wall of the shield 132. The glass element 130 is beveled to avoid specular reflections from the tissue surface as it is described to increase the relative signal strength of the back-scattering. The light having the two orthogonal WO 00/42912 PCT/i1S00/01967 polarizations is separated and coupled to two spectrometer channels for detection and analysis.
Another preferred embodiment of a fiber optic probe 160 is illustrated in Figures 9A-9C. In this embodiment, delivery 156 and collection 162 fibers are housed in flexible tube 164 that is attached to a distal annular housing 166.
Housing 166 includes a fiber retainer 106 and a polarizer 168 which can be a birefringent crystal such as calcite, quartz or sapphire. Delivery fiber 156 delivers light from source 42 to polarizer 168 which delivers ordinary ray 170 through aperture 175 and window 178. Light returning through aperture 175 has ordinary 170 and extraordinary 172 components. The perpendicular component is collected by fibers 162 and the parallel component is collected by fibers 161. The delivery fiber 156 is positioned along the optical axis 176 of the crystal 168. Fibers 161, 156 are aligned along the aperture 175 of absorbing plate 178.
While this invention has been particularly shown and described with references to preferred embodiments thereof, it will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the spirit and scope of the invention as defined by the appended claims.
A preferred embodiment of the inventions includes a fiber optic light delivery and collection system for diagnoses of tissue. The fiber optic system can be housed in a probe housing proximal and distal ends where the distal end can be inserted into the various lumens of the human body for in vivo measurements of tissue. Polarizers can be used on the distal ends of both delivery and collection fibers. With optical fibers that preserve the polarization of light, the polarizers can be positioned at the proximal end of the probe. In a three fiber system, the probe can use a central delivery fiber and two off center collection fibers that collect two different polarization components of light returning from the tissue. The polarizers can be birefringent crystalline materials such as quartz, sapphire or calcite.
The calcite must be sealed from the working environment.
BRIEF DESCRIPTION OF THE DRAWINGS
Figure 1 illustrates a preferred embodiment of a polarization-based light scattering spectroscopic system.
Figures 2 A and B are reflectance spectra of the two-layered tissue phantom (polystyrene beads on top of gel containing blood and BaS04) for parallel and perpendicular polarizations (notice characteristic hemoglobin dips) respectively.
Figures 3 A-D illustrate differences of two polarizations for (A) 4.56 ~,m beads in water (relative refractive index n ~ 1.19), (B) 9.5 ~,m beads in water (n ~ 1.19), (C) 5.7 ~.m beads in glycol (n ~ 1.09), (D) 8.9 ~m beads in glycerol (n ~ 1.07) where the signals (dashed lines) are in good agreement with Mie -S-calculations (solid lines) and the absorption features of hemoglobin are completely removed.
Figure 4 is a spectrum of the polarized (residual) component of back-scattered light: experimental data vs. fit of the Mie calculations for the polarized back-scattering for T84 cancerous colonic cells where best fits provide the following sets of parameters: average size 10.2 ~,m, standard deviation 1.5 ~,m, relative refractive index 1.045, and the sizes and standard deviations are in agreement with those measured using light microscopy.
Figure S is a spectrum of the polarized (residual) component of back-scattered light: experimental data vs. fit of the Mie calculations for the polarized back-scattering for normal intestinal cells where best fits provide the following sets of parameters: average size 5.0 ~.m, standard deviation 0.5 Vim, relative refractive index 1.035, and the sizes and standard deviations are in agreement with those measured using light microscopy.
Figure 6 shows the nuclear size distribution for normal intestinal cells and T84 cancerous colonic cells where in each case, the solid line is the distribution extracted from the data, and the dashed line is the distribution measured using light microscopy.
Figure 7 schematically illustrates a fiber optic probe system for performing in vivo optical measurements of tissue in accordance with the invention.
Figures 8A and 8B show the distal end of a probe of a preferred embodiment of the invention.
Figures 9A-9C illustrate another preferred embodiment of a fiber optic probe in accordance with the invention.
The foregoing and other objects, features and advantages of the invention will be apparent from the following more particular description of preferred embodiments of the invention, as illustrated in the accompanying drawings in which like reference characters refer to the same parts throughout the different views. The drawings are not necessarily to scale, with emphasis being placed upon illustrating the principles of the invention.
DETAILED DESCRIPTION OF THE INVENTION
To determine properties of epithelial cells, one can correlate measured spectrum of the backscattered light with a model or representation. Using Mie theory, which provides the exact solution for the problem of light scattering by spherical objects of arbitrary sizes, the sizes and relative refractive indexes of the scatterers can be determined.
For polarized incident light, light scattered by a spherical particle with diameter d has components which are polarized parallel and perpendicular to the plane of scattering. For a plane polarized wave incident in direction so, light scattered into direction s will have components which are polarized parallel (p) and perpendicular (s) to the plane of scattering. Intensities Ip and IS of these components are related to the intensities of the incident light Ip~°~ and ISO°> as follows:
l S( z In~s~ - 4 ~ 'z z ~~ In~so~ (1) Kd Sz~S,So~lz o Is~s~ - 4 Kzdz In~so~ (2) where k is the wavenumber of the incident light, S~ and Sz are scattering amplitudes which can be calculated numerically using Mie theory, and sl and sz are unit vectors defining propagation of the incident and scattered light. Scattering amplitudes are functions of a scattering angle ~ =cos' (s~so ) and are normalized so that integral (IS, (~)Iz + ISz (~) z ) sin ~d~ equals the total elastic scattering cross section.
Now consider an experiment in which linearly polarized incident light, intensity Io, is distributed over solid angle OSZo and scattering is collected over solid angle X52. The polarization, so , of the incident light can be decomposed into a component sP , in the scattering plane (i.e. the plane formed by s and "so ), and a perpendicular component ss . By means of analyzers, we detect two orthogonal components of the scattered light intensity, III having polarization sa and I1 having perpendicular polarization sa . The scattered intensity components are then given by III = ~~d2 f d"s f dsolo(so~S2(so,s~cos~pcos~po+S,~"so,"s)sin~psin~po z nn n~
(3) 11 = ~~d2 f ds~dsolo(so)lSz~so,s)cos~psin~po-S,(so,s)sin~pcos~po~2 nn n~
(4) If the incident light is completely collimated (OS2o =0), light scattered directly backward will be polarized parallel to the incident light polarization. In this case we can orient one of the analyzers parallel to the incident polarization direction ( so ~ s~ ) . If the solid angles of the incident and collected light are sufficiently small and approximately equal, both III and Il will be present. However, the analyzer can still be positioned such that ( eo ~ sq ) . Thus, in this case the collected light will still be highly polarized, and l~l » Il . For this case the expression for the residual intensity, I;. - Il can be simplified:
_ _ 4I a~
III 11 ~ kd2 f Re(S; ~8)SZ (a~~ sin 9d,~ , (5) with ~ o = ~~ .
2 ~c _g_ Consider a system of two layers of scattering media such as epithelial tissue in which a thin layer of large scattered (d»~,) covers a highly turbid layer of underlying tissue. Each of these layers gives rise to a different type of scattering.
This two layer system represents optical properties of many human tissues with the first layer correlated with epithelium and second layer correlated with other tissue layers beneath epithelium. The upper layer is optically thin so that it does not allow multiple scattering. Small portions of incident linearly polarized light is backscattered by the particles in the upper layer. The rest of the signal penetrates to the second layer that is optically thick. Light propagating through the second layer is randomized by means of multiple scattering. This diffusive light, if not absorbed in the second layer, returns to the surface. Thus, emerging light has two contributions: one from light backscattered by the particles of the first layer, Ib, and the other being diffusely reflected from the second layer, Id. Ib has high degree of linear polarization that is parallel to the polarization of the incident light: hb»Ilb.
As a result of multiple scatterings in the second layer, diffusely reflected light is depolarized and Ipd=Ila. Therefore, the residual intensity of the emerging light h -Il~Ipb-I1b 1S dominated by the contribution from the upper layer and is substantially free from both absorption and scattering from the tissue below.
Expressions (3)-(S) relate Id -li to the scattering amplitudes Sl and S2. The amplitudes depend on the wavelength of the light being scattered ~,=~/k, the scatter's size d and the ratio of its refractive index to that of the surrounding medium, relative refractive index h. Therefore, the spectrum of the residual intensity varies with the scatterer's size and relative refractive index. Thus, sizes and refractive indexes of the scatterers can be found by fitting the representation of the Mie theory using equations (3)-(S) to the residual intensity spectrum.
A system 10 that measures excised tissue samples in vitro is illustrated in Figure 1. This system 10 delivers collimated polarized light on tissue 12 and separates two orthogonal polarizations of back-scattered light. The difference of these two components provides information about light scattered in the epithelial layer only. Since linearly polarized light is depolarized faster than circularly polarized light while passing through a random medium, linear polarization was used. The system provides light from a broad-band source 14 (250 W tungsten lamp, Model 66181, Oriel Instruments, Inc., Stratford, CT) is collimated and then refocused with a small solid angle onto the sample using a fiber 16, a lens 18 and an aperture 20. A broadband polarizer 22 linearly polarizes the beam, before it is delivered to the surface of a scattering medium through beamsplitter 24. The light beam strikes the surface of the sample with an angle ~ 1 S ° relative to the normal in order to avoid specular reflectance. The diameter of the beam is 2mm. The reflected light is collected in a narrow cone ( 0.015 radian) with apertures 26 and mirror 28 and two polarizations, parallel Id and orthogonal Ii to the initial polarization, are separated by a broadband polarizing beam sputter cube 28 which also acts as our analyzer (Melles Griot, Inc.). The output from this analyzer is delivered through lenses 30 and ZOO~,m optical fibers 32, 34 (Ocean Optics, Inc., Dunedin, FL) into two channels of a multichannel spectroscope 36 (quadruple spectroscope, Model SQ200, Ocean Optics, Inc., Dunedin, FL). This enables the spectra of both components to be measured simultaneously in the range from 300 nm to 1200 or optionally in the range from 400 nm to 900 nm.
The beams are not perfectly collinear, and when they pass through the polarizer and analyzer cubes this gives rise to a small amount of distortion.
Furthermore, the beamsplitter has different reflectivities for s and p polarizations. A
diffusely reflective white surface was used as standard to correct for wavelength non-uniformity, and to calibrate the signals in the two channels. Il~~,) and I~~ (~,~ were each normalized to the corresponding background spectra, Ii (~,~
and I~~B (~.) were each normalized to the corresponding background spectra, I~~
~~.~ and Il ~~.) taken with the white diffusing surface. This removed spectral non-uniformities in the light source. Thus, the experiments actually measured the normalized residual intensity, DI:
01- III _ 11 I$ IB
II
(5) Measurements on simple single- and two-layer systems were conducted to determine operational parameters. The single layer system included polystyrene beads of various sizes ranging from 0.5~.m to 10~,m (Polyscience, Inc.) embedded in de-ionized water, glycol, or glycerol. The thickness of these layers was varied so that the optical thickness i ranged from 0.1 to 5 a photon propagating through a medium with i=1, undergoes one scattering event on average). The beads of large sizes 4-10 ~m were used to represent cell nuclei. Since the relative refractive index of the polystyrene beads in water is about 1.2 (absolute refractive index is about n=1.59) and is substantially higher than that of the cell nuclei relative to the cytoplasm which is in the range from 1.03 to 1.1, glycol (na 1.45) and glycerol (na 1.48) were used instead of water to decrease the relative refractive index of the beads and, therefore, better approximate biological conditions.
In the single layer measurements the component of the backscattered light with the same state of polarization as the incoming light (denoted by I~ was almost 100 times larger than the component with the polarization orthogonal to the polarization of the incoming light (denoted by li). This establishes that single scattering from large spheroidal particles preserves polarization.
In the measurements with two layer models the first layer consisted of polystyrene beads embedded in water, glycol, or glycerol and was prepared as in the single layer measurements. The second layer included a gel containing solution of BaS04 powder which provided scattering properties of the second layer and human blood. Hemoglobin content of the blood provided absorptive properties to the model. This physical model simulated epithelium and underlying tissues.
Adjusting concentrations of the BaS04 powder and blood, the scattering and absorption properties, can be made similar to those of a biological tissue, since in the optical spectral region hemoglobin is known to be the major absorber.
Figures 2A and 2B shows spectra of the parallel h and orthogonal I1 polarized components of the light reflected from a two layer system. In this measurement, the first layer contained beads embedded in glycol. The beads had an average diameter of 4.56 ~.m. Standard deviation of their sizes was 0.03 p,m.
Optical thickness of the first layer was z ~ 0.8. The second layer was optically thick and its scattering and absorptive properties were comparable to those of a biological tissue. The spectrum of Il is dominated by characteristic hemoglobin absorption bands. At the same time, characteristic spectral features of light scattered by 4.56 ~m beads in the first layer, namely apparent ripple structure, and hemoglobin absorption in the second layer are seen in the spectrum of Ia.
The residual spectrum dI is shown in Figure 3A. No hemoglobin absorption features are seen and the diffusive background coming from the second layer was completely removed. The ripple structure characteristic of scattering from spheres is evident. The comparison with Mie theory representation for scatterers with d =
4.56 ~m , ~d=0.03~Cm and n=1.035 correspond with the ~tm shown in Figure 3B
shows high degree of accuracy. The residual spectra obtained in measurements with other bead sizes (5.7~,m, 8.9~m, and 9.S~,m) embedded in any of the media used (water, glycol, and glycerol) had no measurable diffusive background component and agreed with Mie theory. Figure 3B shows the agreement between the theory and the measurements for 9.5 ~.m beads.
Similarly, the results of the measurements for 5.7 ~m and 8.9 ~m beads in glycerol and glycol are shown in Figures 3(C) and (D) respectively. Mie theory corresponds with the measured values in these cases as well. The high frequency ripple structure decreases as the relative refractive index gets smaller. The law frequency oscillations remain evident. Measurements showed that the instrument was able to detect signal from the bead solution of as low optical thickness as 0.05.
Small disagreements seen in the spectrum can result from imperfect calibration of the instrument for the wavelength dependence of the optical elements used. The beams are not perfectly collinear and so there arises some imperfections in the polarized signals from the two channels when the beam passes through the polarizer and the analyzer elements. Further, the beam sputter used has different reflectivities for the s and the p polarized beams. However, using just a white standard, signals in the two channels were corrected for any wavelength non-uniformity and further used for calibration of signals.
Measurements with cell monolayers were conducted and the results are described in connection with Figures 4-6. A layer of gel containing solution of BaS04 powder and human blood under the monolayers is used to represent underlying tissue. The concentrations of the BaS04 powder and blood, were adjusted to match optical properties of the biological tissue. Three types of cells were measured: normal intestinal cells, T84 cancer colonic cells and the fibroblasts.
The measurements were similar to the measurements with beads. Nuclei of cells, however, had relative refractive indexes smaller then those of beads as well as larger size distributions which substantially eliminate the ripple structure. Fitting of the observed residual spectrum to Mie theory was performed. Three parameters in the f tting procedure were average size of the nuclei, standard deviation in size (a Gaussian size distribution was assumed), and relative refractive index.
For normal intestinal cells, the best fit was obtained using d=S.O~,m,Od=O.S~m, and n=1.045 (Figure 4). For the fibroblast cells, d-7.0 ~,m, ~d=1.0 ~,m and n=1.051 were obtained. For the T84 colon cancer cells the corresponding values were d=9.8 ~,m Od=1.5 Vim, and n=1.04 (Figure 5).
In order to check these results, the distribution of the average size of the cell nuclei was measured using light microscopy. The sizes and their standard deviations were in agreement with the parameters from Mie theory. A histogram showing the size distributions obtained for the normal T84 cells are shown in Figure 6.
The accuracy of the average size is estimated to be 0.1 ~,m, and the accuracy in n as 0.001. Note the larger value of n obtained for cancerous cells, which is in agreement with the hyperchromaticity of cancer cell nuclei observed in conventional histopathology of stained tissue sections.
The backscattered signal can be described by Mie theory if the average size of the nuclei d, standard deviation in sizes Od, and relative refractive index n are varied. Note that in Mie theory, dependence on d and n does not always come as a (n-I)d product. Thus, the residual spectra have enough information to extract d and n simultaneously.
The size distributions for monolayers were compared to light microscopy and were in a good agreement for all three lines of cells. The accuracy of size and standard deviation extraction was approximately 0.1 ~,m which makes the method useful in differentiating nuclei of different cell types, including cancerous and non-cancerous cells of the same organ.
Ability to detect cell nuclear enlargement and changes in refractive index of the nucleus (which can be related to the amount of DNA and protein in the nucleus) has valuable applications in clinical medicine.
The method of tissue diagnosis can be implemented either in a diagnostic device in which light can be delivered to points on the surface of the tissue, and collected and analyzed at each of those points on the surface of the tissue, and collected and analyzed at each of those points. In an in vivo system optical fibers are used to deliver and collect light. The fiber probe can be inserted in the endoscope biopsy channel or any similar device (depending on the type of the procedure and organ under study). Polarizer and analyzer can be placed at the tip of the probe in front of the delivery and collection fibers. Such an instrument can be used during routine endoscopic procedures to detect precancerous changes in-vivo in real time.
Such a probe system 40 is shown generally in Figure 7. This system 40 includes a broadband light source 42 that is optically coupled to a delivery fiber 44 extending through probe 50. As schematically shown in Figure 7, the probe 50 can be inserted through a channel in an endoscope 48, however the probe 50 can be constructed to be used separately. In a preferred embodiment described hereinafter, the light from source is directed through a polarizer at the distal end of probe 50.
However, in another embodiment using polarization preserving optical fibers, a polarizer 26 can be used at the proximal end of probe fiber 44 to direct polarized light 46 through the fiber. Similarly, the proximal ends of collection fibers 65, 66 can employ polarizing elements 65, 66 respectively to transmit selected polarization components into the multichannel fiber spectrometer 54. The data can then be processed by computer 56, stored in computer 56, stored in computer memory and displayed on display 60 as needed.
The probe system can include a fiber optic probe having a distal end incorporating polarizers as seen in Figure 8A and 8B.
Figures 8A and 8B show the distal end of a probe 100 for the use of polarized light for in vivo diagnosis. Figure 8A shows a fiber optic device that is divided into three sections, the inner delivery fiber and two sets of collection fibers 150 and 152 that collect different polarization components. The cross-section of Figure 8B shows fibers 156 delivering light onto the tissue 140. They have to pass through a polarizer 120 which is also seen in the cross-section view of Figure 8B.
The polarizing element is divided into at least two parts or elements 122, 126.
Optical fibers 152 are arranged to collect the back reflected light from the tissue surface.
The backscattered light has two polarization components, corresponding to the parallel and the perpendicular components to the incident light. The two are differentiated by two different birefringent analyzers shown by two sectioned ring elements 122, 126. A first element 122 allows the parallel component to pass through while the second element 126 allows perpendicular component. A portion of element 122 polarizes light exiting fiber 156. As the fibers have low numerical apertures to collect light over very small angles, it is necessary to extend the distance 136 between the fiber ends and the aperture surface 142 opening to the tissue surface 140. It can be as long as Smm. To avoid spurious internal reflections a glass block 130 is shown having refractive index n2 lower than that of the shield 132 with refractive index n~. The shield I32 can be coated with an absorbing element so that light hitting the boundaries is refracted out and then absorbed by the absorbing coating on the outer wall of the shield 132. The glass element 130 is beveled to avoid specular reflections from the tissue surface as it is described to increase the relative signal strength of the back-scattering. The light having the two orthogonal WO 00/42912 PCT/i1S00/01967 polarizations is separated and coupled to two spectrometer channels for detection and analysis.
Another preferred embodiment of a fiber optic probe 160 is illustrated in Figures 9A-9C. In this embodiment, delivery 156 and collection 162 fibers are housed in flexible tube 164 that is attached to a distal annular housing 166.
Housing 166 includes a fiber retainer 106 and a polarizer 168 which can be a birefringent crystal such as calcite, quartz or sapphire. Delivery fiber 156 delivers light from source 42 to polarizer 168 which delivers ordinary ray 170 through aperture 175 and window 178. Light returning through aperture 175 has ordinary 170 and extraordinary 172 components. The perpendicular component is collected by fibers 162 and the parallel component is collected by fibers 161. The delivery fiber 156 is positioned along the optical axis 176 of the crystal 168. Fibers 161, 156 are aligned along the aperture 175 of absorbing plate 178.
While this invention has been particularly shown and described with references to preferred embodiments thereof, it will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the spirit and scope of the invention as defined by the appended claims.
Claims
-16- What is claimed is:
1. A method of analyzing polarized light comprising:
detecting polarized light having a component that is periodic in wavelength that is returning from a region of interest, and determining a characteristic of the region of interest by analyzing the detected polarized light.
2. The method of Claim 1 further comprising determining a size of tissue cells within the region of interest.
3. The method of Claim 1 further comprising removing a nonpolarized component of the light returning from tissue.
4 The method of Claim 1 further comprising providing a fiber optic probe and collecting polarized light from the tissue with the probe.
5. The method of Claim 1 further comprising detecting the polarized backscattered light and forming a spectrum with the detected light, the spectrum including wavelengths in the range of 300 nm to 1200 nm.
6. The method of Claim 1 further comprising determining a refractive mdex of the region of interest with the detected polarized light 7. The method of Claim 1 further comprising detecting light from a tissue sample.
8. The method of Claim 7 further comprising providing a broadband fight source and a filter wheel and delevering polarized light onto the tissue sample.
9. The method of Claim 1 further comprising separating polarization components of light returning from the region of interest and analyzing the two components to remove non-polarized backscattered light from the detected light.
10. A fiber optic probe for measuring a layer of tissue comprising:
a fiber optic cable optically coupled to a light source, the fiber optic cable delivering polarized light onto the tissue; and a detector system that detects a polarization component of light that is periodic in wavelength which is received from the tissue.
11. The probe of Claim 10 further comprising a polarizer that polarizes light from the light source, the polarizer positioned at a distal end of the fiber optic cable.
12. The probe of Claim 10 further comprising an analyzer that separate polarization components returning from tissue through the fiber optic cable.
13. The probe of Claim 10 further comprising an endoscope having a channel through which the probe is inserted.
14 The probe of Claim 12 wherein the analyzer comprises a polarizing beam splitter.
15. The probe of Claim 12 wherein the analyzer is positioned at a disral end of the fiber optic cable.
16 The probe of Claim 10 further comprising a plurality of polarization filters at the distal end of the probe.
17. The probe of Claim 10 wherein the light source comprises a broadband light source and a filter wheat.
18. The probe of Claim 10 further comprising a spectrometer optically coupled to the fiber optic probe.
19. The probe of Claim 30 further comprising an electronic memory that stores spectra, the spectra including wavelengths in the range of 300nm to 1200nm.
30. The probe of Claim 10 further comprising a computer that analyzes detected spectra to determine whether a surface layer of tissue is normal or epithelial dysplasia.
1. A method of analyzing polarized light comprising:
detecting polarized light having a component that is periodic in wavelength that is returning from a region of interest, and determining a characteristic of the region of interest by analyzing the detected polarized light.
2. The method of Claim 1 further comprising determining a size of tissue cells within the region of interest.
3. The method of Claim 1 further comprising removing a nonpolarized component of the light returning from tissue.
4 The method of Claim 1 further comprising providing a fiber optic probe and collecting polarized light from the tissue with the probe.
5. The method of Claim 1 further comprising detecting the polarized backscattered light and forming a spectrum with the detected light, the spectrum including wavelengths in the range of 300 nm to 1200 nm.
6. The method of Claim 1 further comprising determining a refractive mdex of the region of interest with the detected polarized light 7. The method of Claim 1 further comprising detecting light from a tissue sample.
8. The method of Claim 7 further comprising providing a broadband fight source and a filter wheel and delevering polarized light onto the tissue sample.
9. The method of Claim 1 further comprising separating polarization components of light returning from the region of interest and analyzing the two components to remove non-polarized backscattered light from the detected light.
10. A fiber optic probe for measuring a layer of tissue comprising:
a fiber optic cable optically coupled to a light source, the fiber optic cable delivering polarized light onto the tissue; and a detector system that detects a polarization component of light that is periodic in wavelength which is received from the tissue.
11. The probe of Claim 10 further comprising a polarizer that polarizes light from the light source, the polarizer positioned at a distal end of the fiber optic cable.
12. The probe of Claim 10 further comprising an analyzer that separate polarization components returning from tissue through the fiber optic cable.
13. The probe of Claim 10 further comprising an endoscope having a channel through which the probe is inserted.
14 The probe of Claim 12 wherein the analyzer comprises a polarizing beam splitter.
15. The probe of Claim 12 wherein the analyzer is positioned at a disral end of the fiber optic cable.
16 The probe of Claim 10 further comprising a plurality of polarization filters at the distal end of the probe.
17. The probe of Claim 10 wherein the light source comprises a broadband light source and a filter wheat.
18. The probe of Claim 10 further comprising a spectrometer optically coupled to the fiber optic probe.
19. The probe of Claim 30 further comprising an electronic memory that stores spectra, the spectra including wavelengths in the range of 300nm to 1200nm.
30. The probe of Claim 10 further comprising a computer that analyzes detected spectra to determine whether a surface layer of tissue is normal or epithelial dysplasia.
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/237,153 US6404497B1 (en) | 1999-01-25 | 1999-01-25 | Polarized light scattering spectroscopy of tissue |
US09/237,153 | 1999-01-25 | ||
PCT/US2000/001967 WO2000042912A1 (en) | 1999-01-25 | 2000-01-25 | Polarized light scattering spectroscopy of tissue |
Publications (1)
Publication Number | Publication Date |
---|---|
CA2359643A1 true CA2359643A1 (en) | 2000-07-27 |
Family
ID=22892544
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002359643A Abandoned CA2359643A1 (en) | 1999-01-25 | 2000-01-25 | Polarized light scattering spectroscopy of tissue |
Country Status (10)
Country | Link |
---|---|
US (2) | US6404497B1 (en) |
EP (1) | EP1148811A1 (en) |
JP (1) | JP4516217B2 (en) |
KR (1) | KR20010101687A (en) |
CN (1) | CN1211046C (en) |
AU (1) | AU3351000A (en) |
CA (1) | CA2359643A1 (en) |
HK (1) | HK1041593A1 (en) |
NZ (1) | NZ513116A (en) |
WO (1) | WO2000042912A1 (en) |
Families Citing this family (111)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7158231B1 (en) * | 1995-09-20 | 2007-01-02 | J.A. Woollam Co., Inc. | Spectroscopic ellipsometer and polarimeter systems |
US7633625B1 (en) | 1995-09-20 | 2009-12-15 | J.A. Woollam Co., Inc. | Spectroscopic ellipsometer and polarimeter systems |
US7616319B1 (en) | 1995-09-20 | 2009-11-10 | James D. Welch | Spectroscopic ellipsometer and polarimeter systems |
US6404497B1 (en) | 1999-01-25 | 2002-06-11 | Massachusetts Institute Of Technology | Polarized light scattering spectroscopy of tissue |
US6717668B2 (en) * | 2000-03-07 | 2004-04-06 | Chemimage Corporation | Simultaneous imaging and spectroscopy apparatus |
US6734962B2 (en) | 2000-10-13 | 2004-05-11 | Chemimage Corporation | Near infrared chemical imaging microscope |
US6766184B2 (en) | 2000-03-28 | 2004-07-20 | Board Of Regents, The University Of Texas System | Methods and apparatus for diagnostic multispectral digital imaging |
US6697652B2 (en) * | 2001-01-19 | 2004-02-24 | Massachusetts Institute Of Technology | Fluorescence, reflectance and light scattering spectroscopy for measuring tissue |
US7202091B2 (en) * | 2001-04-11 | 2007-04-10 | Inlight Solutions, Inc. | Optically similar reference samples |
JP5259033B2 (en) * | 2001-08-03 | 2013-08-07 | オリンパス株式会社 | Endoscope system |
US8308797B2 (en) | 2002-01-04 | 2012-11-13 | Colibri Heart Valve, LLC | Percutaneously implantable replacement heart valve device and method of making same |
WO2003062798A1 (en) * | 2002-01-18 | 2003-07-31 | Newton Laboratories, Inc. | Spectroscopic diagnostic methods and system |
GB0202654D0 (en) * | 2002-02-06 | 2002-03-20 | Univ Nottingham | Examination of superficial regions of a body |
US20040010204A1 (en) * | 2002-03-28 | 2004-01-15 | Pearl Technology Holdings, Llc | Electronic/fiberoptic tissue differentiation instrumentation |
US8131332B2 (en) * | 2002-04-04 | 2012-03-06 | Veralight, Inc. | Determination of a measure of a glycation end-product or disease state using tissue fluorescence of various sites |
WO2003093790A2 (en) * | 2002-04-30 | 2003-11-13 | Moyle William R | Sensors for biomolecular detection and cell classification |
WO2004016155A2 (en) * | 2002-08-16 | 2004-02-26 | The Government Of United States Of America As Represented By The Secretary Of The Department Of Health And Human Services | Apparatus for multifocal deposition and analysis and methods for its use |
US7053783B2 (en) | 2002-12-18 | 2006-05-30 | Biovigilant Systems, Inc. | Pathogen detector system and method |
US9173562B2 (en) * | 2003-01-23 | 2015-11-03 | The Board Of Regents Of The University Of Texas System | Method and apparatus for diagnosing neovascularized tissues |
US7623908B2 (en) | 2003-01-24 | 2009-11-24 | The Board Of Trustees Of The University Of Illinois | Nonlinear interferometric vibrational imaging |
US7102758B2 (en) | 2003-05-06 | 2006-09-05 | Duke University | Fourier domain low-coherence interferometry for light scattering spectroscopy apparatus and method |
WO2004110264A1 (en) * | 2003-06-11 | 2004-12-23 | Kose Corporation | Skin evaluation method and image simulation method |
ES2625486T3 (en) * | 2003-08-25 | 2017-07-19 | Monsanto Technology Llc | Tubulin regulatory elements for use in plants |
US7289205B2 (en) * | 2003-09-19 | 2007-10-30 | The General Hospital Corporation | Fluorescence polarization imaging devices and methods |
US7532325B2 (en) * | 2003-09-23 | 2009-05-12 | Research Foundation Of The City University Of New York | Method and apparatus for the separation of fluoroscence and elastic scattering produced by broadband illumination using polarization discrimination techniques |
JP4823064B2 (en) * | 2003-09-23 | 2011-11-24 | スティヒテング フォール デ テフニシェ ウェテンシャッペン | Method and apparatus for backscattering spectroscopy |
US8064976B2 (en) | 2003-10-03 | 2011-11-22 | Can Ince | Systems and methods for sidesstream dark field imaging |
SE0400145D0 (en) * | 2004-01-27 | 2004-01-27 | Anders Johansson | An arrangement and method for assessing joints |
US20060155178A1 (en) * | 2004-03-26 | 2006-07-13 | Vadim Backman | Multi-dimensional elastic light scattering |
US8060172B2 (en) * | 2004-03-29 | 2011-11-15 | Olympus Corporation | In-vivo information measurement apparatus |
US7724374B2 (en) * | 2004-06-17 | 2010-05-25 | Bayer Healthcare Llc | Coaxial diffuse reflectance read head |
KR101170859B1 (en) | 2004-07-30 | 2012-08-02 | 바이오비질런트 시스템즈 인코포레이티드 | Pathogen and particle detector system and method |
US7417740B2 (en) * | 2004-11-12 | 2008-08-26 | Medeikon Corporation | Single trace multi-channel low coherence interferometric sensor |
US9131861B2 (en) | 2004-11-30 | 2015-09-15 | Academisch Medisch Centrum | Pulsed lighting imaging systems and methods |
US7428048B1 (en) * | 2004-12-30 | 2008-09-23 | Spectral Molecular Imaging Inc. | Imaging elastic scattering spectroscopy |
JP2006208681A (en) * | 2005-01-27 | 2006-08-10 | Olympus Corp | Connection unit and optical scanning type fluorescent observation device |
US9597024B2 (en) * | 2005-02-09 | 2017-03-21 | Medici Instruments Llc | Methods and apparatuses for noninvasive determinations of analytes |
WO2006086579A2 (en) * | 2005-02-09 | 2006-08-17 | Inlight Solutions, Inc. | Methods and apparatus for noninvasive determinations of analytes |
US7586618B2 (en) | 2005-02-28 | 2009-09-08 | The Board Of Trustees Of The University Of Illinois | Distinguishing non-resonant four-wave-mixing noise in coherent stokes and anti-stokes Raman scattering |
US7515265B2 (en) * | 2005-04-28 | 2009-04-07 | Research Foundation Of The City University Of New York | Imaging systems and methods to improve backscattering imaging using circular polarization memory |
CN101223560B (en) | 2005-07-15 | 2012-12-12 | 百维吉伦特系统有限公司 | Pathogen and particle detector system and method |
US20120302892A1 (en) * | 2005-07-25 | 2012-11-29 | Niyom Lue | Portable optical fiber probe-based spectroscopic scanner for rapid cancer diagnosis |
US20070173736A1 (en) * | 2005-10-07 | 2007-07-26 | Femspec Llc | Apparatus and methods for endometrial biopsies |
US8537366B2 (en) | 2005-10-11 | 2013-09-17 | Duke University | Systems and methods for endoscopic angle-resolved low coherence interferometry |
EP2950065A1 (en) | 2005-10-11 | 2015-12-02 | Duke University | Method for fiber-based endoscopic angle-resolved low coherence interferometry |
US9314164B2 (en) | 2005-10-27 | 2016-04-19 | Northwestern University | Method of using the detection of early increase in microvascular blood content to distinguish between adenomatous and hyperplastic polyps |
US20090203977A1 (en) * | 2005-10-27 | 2009-08-13 | Vadim Backman | Method of screening for cancer using parameters obtained by the detection of early increase in microvascular blood content |
US20070129615A1 (en) * | 2005-10-27 | 2007-06-07 | Northwestern University | Apparatus for recognizing abnormal tissue using the detection of early increase in microvascular blood content |
US20070179368A1 (en) * | 2005-10-27 | 2007-08-02 | Northwestern University | Method of recognizing abnormal tissue using the detection of early increase in microvascular blood content |
US8131112B1 (en) | 2006-01-23 | 2012-03-06 | Sandia Corporation | Method for detecting cancer in a single cell using mitochondrial correlation microscopy |
AU2007211061B2 (en) * | 2006-01-31 | 2013-04-18 | The Board Of Trustees Of The University Of Illinois | Method and apparatus for measurement of optical properties in tissue |
CN101489471B (en) * | 2006-05-19 | 2014-08-27 | 北岸大学健康系统公司 | Apparatus for recognizing abnormal tissue using the detection of early increase in microvascular blood content |
CN101453942B (en) * | 2006-05-30 | 2012-01-11 | 皇家飞利浦电子股份有限公司 | Apparatus for depth-resolved measurements of properties of tissue |
CA2658481A1 (en) * | 2006-07-21 | 2008-01-24 | Oncoscope, Inc. | Protective probe tip, particularly for use on a fiber-optic probe used in an endoscopic application |
WO2008066911A2 (en) * | 2006-11-30 | 2008-06-05 | Newton Laboratories, Inc. | Spectroscopically enhanced imaging |
DE602008006170D1 (en) * | 2007-02-20 | 2011-05-26 | Koninkl Philips Electronics Nv | OPTICAL DEVICE FOR EVALUATING THE OPTICAL DEPTH OF A SAMPLE |
WO2008110968A1 (en) * | 2007-03-12 | 2008-09-18 | Koninklijke Philips Electronics N.V. | A system, computer-readable medium, method, and use for combined epithelial early cancer diagnosis and staging |
US20090062662A1 (en) * | 2007-08-27 | 2009-03-05 | Remicalm, Llc | Optical spectroscopic device for the identification of cervical cancer |
WO2009036418A1 (en) * | 2007-09-13 | 2009-03-19 | Duke University | Apparatuses, systems, and methods for low-coherence interferometry (lci) |
US20090099460A1 (en) | 2007-10-16 | 2009-04-16 | Remicalm Llc | Method and device for the optical spectroscopic identification of cervical cancer |
US8628976B2 (en) | 2007-12-03 | 2014-01-14 | Azbil BioVigilant, Inc. | Method for the detection of biologic particle contamination |
CA2711643A1 (en) * | 2008-01-08 | 2009-07-16 | Oncoscope, Inc. | Systems and methods for tissue examination, diagnostic, treatment, and/or monitoring |
US8983580B2 (en) | 2008-01-18 | 2015-03-17 | The Board Of Trustees Of The University Of Illinois | Low-coherence interferometry and optical coherence tomography for image-guided surgical treatment of solid tumors |
WO2009105537A2 (en) * | 2008-02-19 | 2009-08-27 | Trustees Of Tufts College | Non-invasive optical characterization of biomaterial mineralization |
JP5100457B2 (en) | 2008-03-10 | 2012-12-19 | オリンパスメディカルシステムズ株式会社 | Endoscope observation system |
JP5380725B2 (en) * | 2008-03-31 | 2014-01-08 | 富士フイルム株式会社 | Optical system, method, and program |
JP2009283871A (en) * | 2008-05-26 | 2009-12-03 | Fujitsu Ltd | Rework soldering method and its apparatus |
US20100249607A1 (en) * | 2008-09-26 | 2010-09-30 | Massachusetts Institute Of Technology | Quantitative spectroscopic imaging |
EP2385786A4 (en) * | 2009-01-08 | 2013-07-03 | American Biooptics Llc | Probe apparatus for recognizing abnormal tissue |
US9885834B2 (en) | 2009-01-08 | 2018-02-06 | Northwestern University | Probe apparatus for measuring depth-limited properties with low-coherence enhanced backscattering |
WO2010085348A1 (en) * | 2009-01-23 | 2010-07-29 | Perelman Lev T | Endoscopic polarized multispectral light scattering scanning method |
US9254123B2 (en) | 2009-04-29 | 2016-02-09 | Hansen Medical, Inc. | Flexible and steerable elongate instruments with shape control and support elements |
EP2468173A4 (en) | 2009-08-20 | 2013-08-28 | Olympus Medical Systems Corp | Living organism measuring device and living organism measuring method |
WO2011043077A1 (en) * | 2009-10-09 | 2011-04-14 | 川崎重工業株式会社 | Method and apparatus for discrimination of undifferentiated plyripotent stem cell, and automatic culture method and apparatus |
US9220412B2 (en) * | 2009-11-19 | 2015-12-29 | Modulated Imaging Inc. | Method and apparatus for analysis of turbid media via single-element detection using structured illumination |
US9823127B2 (en) | 2010-01-22 | 2017-11-21 | Duke University | Systems and methods for deep spectroscopic imaging of biological samples with use of an interferometer and spectrometer |
AU2011207444A1 (en) | 2010-01-22 | 2012-08-09 | Duke University | Multiple window processing schemes for spectroscopic optical coherence tomography (OCT) and fourier domain low coherence interferometry |
WO2011109450A2 (en) | 2010-03-01 | 2011-09-09 | Colibri Heart Valve Llc | Percutaneously deliverable heart valve and methods associated therewith |
JP5696144B2 (en) | 2010-06-25 | 2015-04-08 | 川崎重工業株式会社 | Method and apparatus for identifying pluripotent stem cell colonies and method and apparatus for automatically culturing pluripotent stem cells |
CA2806544C (en) | 2010-06-28 | 2016-08-23 | Colibri Heart Valve Llc | Method and apparatus for the endoluminal delivery of intravascular devices |
US20120071894A1 (en) | 2010-09-17 | 2012-03-22 | Tanner Neal A | Robotic medical systems and methods |
SG10201601962WA (en) | 2010-12-14 | 2016-04-28 | Colibri Heart Valve Llc | Percutaneously deliverable heart valve including folded membrane cusps with integral leaflets |
WO2013011778A1 (en) | 2011-07-15 | 2013-01-24 | オリンパスメディカルシステムズ株式会社 | Probe |
US20130030363A1 (en) * | 2011-07-29 | 2013-01-31 | Hansen Medical, Inc. | Systems and methods utilizing shape sensing fibers |
JP5623470B2 (en) * | 2012-07-06 | 2014-11-12 | 富士フイルム株式会社 | ENDOSCOPE SYSTEM, ENDOSCOPE SYSTEM PROCESSOR DEVICE, AND ENDOSCOPE CONTROL PROGRAM |
KR102028199B1 (en) * | 2012-08-28 | 2019-10-04 | 한국전자통신연구원 | Medical diagnosis device and method for controlling the device |
EP2898326B1 (en) | 2012-11-07 | 2018-03-14 | Modulated Imaging Inc. | Efficient modulated imaging |
US10149720B2 (en) | 2013-03-08 | 2018-12-11 | Auris Health, Inc. | Method, apparatus, and a system for facilitating bending of an instrument in a surgical or medical robotic environment |
US10376672B2 (en) | 2013-03-15 | 2019-08-13 | Auris Health, Inc. | Catheter insertion system and method of fabrication |
CN111166274A (en) | 2013-10-24 | 2020-05-19 | 奥瑞斯健康公司 | Robotically-assisted endoluminal surgical systems and related methods |
CN103781253B (en) * | 2014-01-23 | 2015-08-26 | 安徽理工大学 | A kind of method and apparatus controlling wideband light source stabilized intensity |
US9744335B2 (en) | 2014-07-01 | 2017-08-29 | Auris Surgical Robotics, Inc. | Apparatuses and methods for monitoring tendons of steerable catheters |
US9561083B2 (en) | 2014-07-01 | 2017-02-07 | Auris Surgical Robotics, Inc. | Articulating flexible endoscopic tool with roll capabilities |
US10792464B2 (en) | 2014-07-01 | 2020-10-06 | Auris Health, Inc. | Tool and method for using surgical endoscope with spiral lumens |
CN104523241B (en) * | 2015-01-21 | 2016-08-24 | 浙江大学 | The detection device of a kind of biological organism optical characteristic and detection method |
US11819636B2 (en) | 2015-03-30 | 2023-11-21 | Auris Health, Inc. | Endoscope pull wire electrical circuit |
CN106092905B (en) * | 2016-06-21 | 2021-06-22 | 北京化工大学 | Polarized infrared spectrometer |
US10463439B2 (en) | 2016-08-26 | 2019-11-05 | Auris Health, Inc. | Steerable catheter with shaft load distributions |
AU2018270785B2 (en) | 2017-05-17 | 2023-11-23 | Auris Health, Inc. | Exchangeable working channel |
CN107202773B (en) * | 2017-06-01 | 2019-07-05 | 重庆大学 | A kind of cell cycle scattered light intensity method for establishing model using polystyrene spheres |
WO2018231724A1 (en) * | 2017-06-12 | 2018-12-20 | Trustees Of Boston University | Systems and methods for oblique laser scanning |
WO2019051476A1 (en) | 2017-09-11 | 2019-03-14 | Incubar, LLC | Conduit vascular implant sealing device for reducing endoleak |
CN110831480B (en) | 2018-03-28 | 2023-08-29 | 奥瑞斯健康公司 | Medical device with variable bending stiffness profile |
WO2020033318A1 (en) | 2018-08-07 | 2020-02-13 | Auris Health, Inc. | Combining strain-based shape sensing with catheter control |
CN112584748A (en) * | 2018-08-13 | 2021-03-30 | 索尼公司 | Medical system, medical light source device and method in medical light source device |
US11179212B2 (en) | 2018-09-26 | 2021-11-23 | Auris Health, Inc. | Articulating medical instruments |
US20220125280A1 (en) * | 2019-03-01 | 2022-04-28 | Sri International | Apparatuses and methods involving multi-modal imaging of a sample |
US11617627B2 (en) | 2019-03-29 | 2023-04-04 | Auris Health, Inc. | Systems and methods for optical strain sensing in medical instruments |
KR20220050151A (en) | 2019-08-15 | 2022-04-22 | 아우리스 헬스, 인코포레이티드 | Medical device having multiple bend sections |
CN110672527A (en) * | 2019-08-30 | 2020-01-10 | 南京航空航天大学 | Cervical cancer precancerous lesion screening system and screening method thereof |
EP4084717A4 (en) | 2019-12-31 | 2024-02-14 | Auris Health Inc | Dynamic pulley system |
Family Cites Families (63)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3675768A (en) | 1969-03-17 | 1972-07-11 | Gildardo Legorreta Sanchez | Method and apparatus for classifying and segregating particles with electrical and optical means |
US4281931A (en) | 1977-12-21 | 1981-08-04 | Machida Endoscope Co., Ltd. | Measuring apparatus comprising light optics utilizing cylindrical focusing glass fiber |
US4515165A (en) | 1980-02-04 | 1985-05-07 | Energy Conversion Devices, Inc. | Apparatus and method for detecting tumors |
US4336809A (en) | 1980-03-17 | 1982-06-29 | Burleigh Instruments, Inc. | Human and animal tissue photoradiation system and method |
US4625167A (en) | 1983-07-05 | 1986-11-25 | Sigma Research, Inc. | Flaw imaging in ferrous and nonferrous materials using magneto-optic visualization |
US4829184A (en) | 1984-06-25 | 1989-05-09 | Nelson Robert S | Reflective, transmissive high resolution imaging apparatus |
US4948974A (en) | 1984-06-25 | 1990-08-14 | Nelson Robert S | High resolution imaging apparatus and method for approximating scattering effects |
JPS6125030A (en) | 1984-07-13 | 1986-02-03 | Hitachi Ltd | Fluorescence-polarization measuring apparatus |
US4884886A (en) | 1985-02-08 | 1989-12-05 | The United States Of America As Represented By The Department Of Energy | Biological particle identification apparatus |
US5106387A (en) | 1985-03-22 | 1992-04-21 | Massachusetts Institute Of Technology | Method for spectroscopic diagnosis of tissue |
US4718417A (en) | 1985-03-22 | 1988-01-12 | Massachusetts Institute Of Technology | Visible fluorescence spectral diagnostic for laser angiosurgery |
ATE167792T1 (en) | 1985-03-22 | 1998-07-15 | Massachusetts Inst Technology | FIBER OPTICAL PROBE SYSTEM FOR THE SPECTRAL DIAGNOSTICS OF TISSUE |
US4655225A (en) | 1985-04-18 | 1987-04-07 | Kurabo Industries Ltd. | Spectrophotometric method and apparatus for the non-invasive |
JPS62116263A (en) | 1985-11-15 | 1987-05-27 | Olympus Optical Co Ltd | Method and apparatus for measuring immunoreaction using multiple scattering of linearly polarized light |
JPS62247232A (en) | 1986-04-21 | 1987-10-28 | Agency Of Ind Science & Technol | Fluorescence measuring apparatus |
JPH0797081B2 (en) | 1987-03-25 | 1995-10-18 | 日本分光工業株式会社 | Crystal orientation analyzer utilizing polarization characteristics of Raman scattered light |
DE58903504D1 (en) | 1988-07-19 | 1993-03-25 | Siemens Ag | METHOD FOR MEASURING THE CONCENTRATION OF OPTICALLY ACTIVE SUBSTANCES AND ARRANGEMENT FOR IMPLEMENTING THE METHOD. |
US5284137A (en) | 1988-07-26 | 1994-02-08 | Manfred Kessler | Process and device for the determination of local dye concentrations and of scattering parameters in animal and human tissues |
US5402778A (en) | 1993-01-19 | 1995-04-04 | Nim Incorporated | Spectrophotometric examination of tissue of small dimension |
US5596987A (en) | 1988-11-02 | 1997-01-28 | Noninvasive Technology, Inc. | Optical coupler for in vivo examination of biological tissue |
SE462408B (en) | 1988-11-10 | 1990-06-18 | Pharmacia Ab | OPTICAL BIOSENSOR SYSTEM USING SURFACE MONITORING RESONSE FOR THE DETECTION OF A SPECIFIC BIOMOLIC CYCLE, TO CALIBRATE THE SENSOR DEVICE AND TO CORRECT FOUND BASELINE OPERATION IN THE SYSTEM |
US5386827A (en) | 1993-03-30 | 1995-02-07 | Nim Incorporated | Quantitative and qualitative in vivo tissue examination using time resolved spectroscopy |
US4953978A (en) | 1989-03-03 | 1990-09-04 | Coulter Electronics Of New England, Inc. | Particle size analysis utilizing polarization intensity differential scattering |
US5014709A (en) | 1989-06-13 | 1991-05-14 | Biologic Systems Corp. | Method and apparatus for high resolution holographic imaging of biological tissue |
US5061075A (en) | 1989-08-07 | 1991-10-29 | Alfano Robert R | Optical method and apparatus for diagnosing human spermatozoa |
US5369496A (en) | 1989-11-13 | 1994-11-29 | Research Foundation Of City College Of New York | Noninvasive method and apparatus for characterizing biological materials |
US5419321A (en) | 1990-05-17 | 1995-05-30 | Johnson & Johnson Professional Products Limited | Non-invasive medical sensor |
EP0458601B1 (en) | 1990-05-22 | 1996-08-28 | Research Development Corporation Of Japan | Method of and apparatus for measuring spectral absorption in opaque specimens and method of and apparatus for measuring microscopic absorption distribution |
US5434669A (en) * | 1990-10-23 | 1995-07-18 | Olympus Optical Co., Ltd. | Measuring interferometric endoscope having a laser radiation source |
IL96483A (en) | 1990-11-27 | 1995-07-31 | Orbotech Ltd | Optical inspection method and apparatus |
US5168162A (en) | 1991-02-04 | 1992-12-01 | Cornell Research Foundation, Inc. | Method of detecting the presence of anomalies in exfoliated cells using infrared spectroscopy |
US5784162A (en) | 1993-08-18 | 1998-07-21 | Applied Spectral Imaging Ltd. | Spectral bio-imaging methods for biological research, medical diagnostics and therapy |
US5303026A (en) | 1991-02-26 | 1994-04-12 | The Regents Of The University Of California Los Alamos National Laboratory | Apparatus and method for spectroscopic analysis of scattering media |
US5280788A (en) | 1991-02-26 | 1994-01-25 | Massachusetts Institute Of Technology | Devices and methods for optical diagnosis of tissue |
US5203328A (en) | 1991-07-17 | 1993-04-20 | Georgia Tech Research Corporation | Apparatus and methods for quantitatively measuring molecular changes in the ocular lens |
DE4129438A1 (en) | 1991-09-04 | 1993-03-18 | Siemens Ag | MEASURING ARRANGEMENT FOR THE EXAMINATION OF AN OBJECT WITH VISIBLE, NIR OR IR LIGHT |
US5418136A (en) | 1991-10-01 | 1995-05-23 | Biostar, Inc. | Devices for detection of an analyte based upon light interference |
US5398685A (en) | 1992-01-10 | 1995-03-21 | Wilk; Peter J. | Endoscopic diagnostic system and associated method |
US5317156A (en) | 1992-01-29 | 1994-05-31 | Sri International | Diagnostic tests using near-infrared laser absorption spectroscopy |
JP3181655B2 (en) | 1992-01-29 | 2001-07-03 | オリンパス光学工業株式会社 | Optical system and sample support in ellipsometer |
US5452723A (en) | 1992-07-24 | 1995-09-26 | Massachusetts Institute Of Technology | Calibrated spectrographic imaging |
US5494829A (en) | 1992-07-31 | 1996-02-27 | Biostar, Inc. | Devices and methods for detection of an analyte based upon light interference |
US5460177A (en) | 1993-05-07 | 1995-10-24 | Diasense, Inc. | Method for non-invasive measurement of concentration of analytes in blood using continuous spectrum radiation |
JP3310390B2 (en) | 1993-06-10 | 2002-08-05 | 浜松ホトニクス株式会社 | Method and apparatus for measuring concentration of light absorbing substance in scattering medium |
US5596992A (en) | 1993-06-30 | 1997-01-28 | Sandia Corporation | Multivariate classification of infrared spectra of cell and tissue samples |
US5440388A (en) | 1993-08-02 | 1995-08-08 | Erickson; Jon W. | Chemical analysis and imaging by discrete fourier transform spectroscopy |
JP3433508B2 (en) | 1993-12-01 | 2003-08-04 | 浜松ホトニクス株式会社 | Scattering absorber measurement method and scattering absorber measuring device |
US5491344A (en) | 1993-12-01 | 1996-02-13 | Tufts University | Method and system for examining the composition of a fluid or solid sample using fluorescence and/or absorption spectroscopy |
US5560356A (en) | 1994-02-23 | 1996-10-01 | Vitrophage, Inc. | Diagnostic system and method using an implanted reflective device |
DE69400022T2 (en) | 1994-02-24 | 1996-03-07 | Becton Dickinson Co | Double dark field staining process; Samples obtained by the method and use of enzyme markers in double dark field stains. |
US5599717A (en) * | 1994-09-02 | 1997-02-04 | Martin Marietta Energy Systems, Inc. | Advanced synchronous luminescence system |
US5625458A (en) | 1994-11-10 | 1997-04-29 | Research Foundation Of City College Of New York | Method and system for imaging objects in turbid media using diffusive fermat photons |
US5697373A (en) | 1995-03-14 | 1997-12-16 | Board Of Regents, The University Of Texas System | Optical method and apparatus for the diagnosis of cervical precancers using raman and fluorescence spectroscopies |
US5699795A (en) | 1995-03-31 | 1997-12-23 | Board Of Regents, The University Of Texas System | Optical probe for the detection of cervical neoplasia using fluorescence spectroscopy and apparatus incorporating same |
US5813987A (en) * | 1995-08-01 | 1998-09-29 | Medispectra, Inc. | Spectral volume microprobe for analysis of materials |
US5636633A (en) | 1995-08-09 | 1997-06-10 | Rio Grande Medical Technologies, Inc. | Diffuse reflectance monitoring apparatus |
US5630423A (en) | 1996-01-31 | 1997-05-20 | Wang; Lihong | Method of measuring tissue optical properties using an optical beam of oblique incidence and uses thereof |
JP2001515382A (en) | 1997-03-06 | 2001-09-18 | マサチューセッツ インスティチュート オブ テクノロジー | Equipment for optical scanning of living tissue |
US6011626A (en) * | 1997-03-20 | 2000-01-04 | The Regents Of The University Of California | Characterization of highly scattering media by measurement of diffusely backscattered polarized light |
US6002480A (en) | 1997-06-02 | 1999-12-14 | Izatt; Joseph A. | Depth-resolved spectroscopic optical coherence tomography |
US6091984A (en) | 1997-10-10 | 2000-07-18 | Massachusetts Institute Of Technology | Measuring tissue morphology |
US6177984B1 (en) * | 1998-01-23 | 2001-01-23 | Providence Health System | Video imaging of superficial biological tissue layers using polarized light |
US6404497B1 (en) | 1999-01-25 | 2002-06-11 | Massachusetts Institute Of Technology | Polarized light scattering spectroscopy of tissue |
-
1999
- 1999-01-25 US US09/237,153 patent/US6404497B1/en not_active Expired - Lifetime
-
2000
- 2000-01-25 EP EP00911646A patent/EP1148811A1/en not_active Withdrawn
- 2000-01-25 KR KR1020017009359A patent/KR20010101687A/en not_active Application Discontinuation
- 2000-01-25 AU AU33510/00A patent/AU3351000A/en not_active Abandoned
- 2000-01-25 NZ NZ513116A patent/NZ513116A/en unknown
- 2000-01-25 CA CA002359643A patent/CA2359643A1/en not_active Abandoned
- 2000-01-25 JP JP2000594380A patent/JP4516217B2/en not_active Expired - Fee Related
- 2000-01-25 CN CNB008042586A patent/CN1211046C/en not_active Expired - Fee Related
- 2000-01-25 WO PCT/US2000/001967 patent/WO2000042912A1/en not_active Application Discontinuation
-
2002
- 2002-04-30 HK HK02103267.8A patent/HK1041593A1/en unknown
- 2002-05-24 US US10/155,194 patent/US6624890B2/en not_active Expired - Fee Related
Also Published As
Publication number | Publication date |
---|---|
JP2002535027A (en) | 2002-10-22 |
WO2000042912A9 (en) | 2002-03-28 |
CN1341004A (en) | 2002-03-20 |
KR20010101687A (en) | 2001-11-14 |
EP1148811A1 (en) | 2001-10-31 |
JP4516217B2 (en) | 2010-08-04 |
US6404497B1 (en) | 2002-06-11 |
NZ513116A (en) | 2003-10-31 |
AU3351000A (en) | 2000-08-07 |
US20020171831A1 (en) | 2002-11-21 |
US6624890B2 (en) | 2003-09-23 |
WO2000042912A1 (en) | 2000-07-27 |
CN1211046C (en) | 2005-07-20 |
HK1041593A1 (en) | 2002-07-12 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US6404497B1 (en) | Polarized light scattering spectroscopy of tissue | |
CA2371782A1 (en) | Imaging of tissue using polarized light | |
US6091984A (en) | Measuring tissue morphology | |
Backman et al. | Polarized light scattering spectroscopy for quantitative measurement of epithelial cellular structures in situ | |
US7706862B2 (en) | Detecting human cancer through spectral optical imaging using key water absorption wavelengths | |
RU2288636C2 (en) | Method and systems for detecting parameters and mapping of tissue lesions | |
US6975899B2 (en) | Multi-modal optical tissue diagnostic system | |
US4930516A (en) | Method for detecting cancerous tissue using visible native luminescence | |
US20090204009A1 (en) | Medical device system and related methods for diagnosing abnormal medical conditions based on in-vivo optical properties of tissue | |
US20060173355A1 (en) | Detecting human cancer through spectral optical imaging using key water absorption wavelengths | |
Hohmann et al. | Preliminary results for hyperspectral videoendoscopy diagnostics on the phantoms of normal and abnormal tissues: towards gastrointestinal diagnostics | |
US20090076396A1 (en) | Optical wavelength range for high contrast imaging of cancer | |
AU2004205093A1 (en) | Polarized light scattering spectroscopy of tissue | |
AU2004222851A1 (en) | Imaging of tissue using polarized light | |
AU781659B2 (en) | Method for measuring tissue morphology | |
Wu | Quantitative optical imaging for the detection of early cancer | |
Nathel | Diagnostic Scattering Properties of Particles and Tissues | |
Motz et al. | Irene Georgakoudi | |
Belkov et al. | Studies of optical probe for breast cancer diagnostics performed in Regional Oncology Center of Nizhny Novgorod |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
EEER | Examination request | ||
FZDE | Dead |