Abstract:
The method is well suited for single molecule observation. A fluorescence or Raman signal from single molecules is detected by photon counting. The sequence of detected photons is divided into counting intervals by defining the end of a counting interval when a predefined number of photons has been counted. For the photons from every counting interval, stochastic variables are determined like fluorescence decay time, anisotropy of the observed signal, etc., which are characteristic for the molecules. A multidimensional histogram is constructed as a function of the stochastic variables, whereby the histogram is built up using values of the variables determined from each counting interval. Regions of the histogram can be used to determine how the molecules are distributed in respect to binding sites, etc. The signal from selected regions of the histograms can then be chosen for further selective analysis to give species specific results.

Description:
CROSS-REFERENCES TO RELATED APPLICATIONS  
       [0001]     This application is a continuation of prior filed copending application Ser. No. 10/451,653, filed Dec. 22, 2003, which is the National Stage of International Application No. PCT/EP01/15108, filed Dec. 20, 2001 and claims the priority of European Patent Applications, Serial Nos. 00128092.4, filed Dec. 21, 2000 and 00128142.7, filed Dec. 21, 2000, pursuant to 35 U.S.C. 119(a)-(d). 
     
    
     BACKGROUND OF THE INVENTION  
       [0002]     The invention relates to a method for characterizing samples of secondary light emitting particles.  
         [0003]     More particularly, the invention relates to the field of fluorescence spectroscopy and light scattering, especially to a qualitative and quantitative method for determining properties of secondary light emitting particles present in a sample.  
         [0004]     The characterization of such samples plays an important role in chemistry, physics, biology, and medicine. Typical applications are drug screening, high throughput drug screening, or chemical analysis in medicine, forensic science, material science, diagnostics, and biotechnology, furthermore, optimization of properties of molecules, identification of particles, particle sorting, optimization of optical properties of a detection system and/or excitation device, or cell and/or matrix characterization. In life science very often ligand-receptor, substrate-enzyme, protein-protein, protein-DNA or protein-cell-membrane interactions are studied. When imaging cells, the information of emitted secondary light can efficiently be used to produce images with a high contrast ratio and a high content of information. Presently, primarily fluorescence intensity is used in imaging. However, fluorescence intensity as an absolute parameter is ambiguous, since fluorescence quenching and the concentration of the fluorophores influence the signal. Thus, relative fluorescence parameters like fluorescence lifetime, anisotropy or intensity ratios are much more suited.  
         [0005]     In the rapidly evolving field of nanobiotechnology manipulation of particles and objects are important issues. Tools for manipulation are atomic force microscope, magnetic tweezers, photonic force microscope (optical tweezers), micro needles, electric fields and field cages and levitated liquid droplets. To control these manipulation tools, secondary light emitted by the particle can be used as an efficient and specific feedback signal.  
         [0006]     Emitted secondary light as a readout-parameter is a sensitive tool for the characterization of particles down to the single particle level. To be detected by emitted secondary light, the particle either has to have the ability to emit light by itself or has to be labeled by a secondary light emitting tag, e. g. a fluorescent dye, a luminescent nanoparticle (e. g. a semiconductor quantum dot), or a metal chelate.  
         [0007]     The scattering or emission of secondary light after excitation by primary light can be an elastic process, like Rayleigh-, Mie-, and Raman-scattering, or an inelastic process, e. g. luminescence such as phosphorescence or fluorescence.  
         [0008]     These processes are typically induced by directing electromagnetic radiation (e. g. appropriate laser light) as primary light onto the sample.  
         [0009]     Whereas elastic emission is a temporally prompt process, inelastic emission is generally delayed with respect to the excitation time. In case of luminescence, the probability of electronic deactivation and hence the inelastic emission of light is temporally exponentially distributed. The lifetime of the electronically excited state is defined as the time where the probability to be in the excited state has dropped to 1/e.  
         [0010]     Many spectroscopic techniques have been developed, some of which are able to detect single molecules. The most advanced of these single-molecule techniques in terms of the collection of data is the so-called BIFL technique (WO 98/23941), i.e. Burst-Integrated-Fluorescence-Lifetime. This technique is derived from TCSPC (time correlated single photon counting). TCSPC directly records the relative time delay between an excitation pulse and the time of detection of a single photon. Besides this time delay, BIFL can detect the absolute time of detection of a photon relative to an arbitrary clock characterizing the actual time axis of a measurement. This is achieved by measuring the time interval between two successively detected photons. BIFL is, thus, able to collect the maximum amount of temporal information for every single photon emitted by every single particle.  
         [0011]     Employing BIFL on a confocal fluorescence microscope, conformational dynamics of dye labeled DNA double strands could be followed and their kinetics and molecular states characterized by monitoring jumps in the fluorescence lifetime as well as intensity and performing correlation analysis on these jumps selectively from the signal of single molecules [Eggeling, C.; Fries, J. R.; Brand, L.; Günther, R.; Seidel, C. A. M.: Monitoring conformational dynamics of a single molecule by selective fluorescence spectroscopy; PNAS 1998, 95, 1556-1561]. Furthermore, this technique was used to qualitatively and quantitatively identify different single molecules in a dye mixture by their different fluorescence properties: fluorescence lifetime [Zander, C.; Sauer, M.; Drexhage, K. H.; Ko, D. S.; Schulz, A.; Wolfrum, J.; Brand, L.; Eggeling, C.; Seidel, C. A. M.: Detection and characterization of single molecules in aqueous solution; Appl. Phys. B 1996, 63 (5), 517-523], fluorescence lifetime and fluorescence intensity [Fries, J. R.; Brand, L.; Eggeling, C.; Köllner, M.; Seidel, C. A. M.: Quantitative identification of different single-molecules by selective time-resolved confocal fluorescence spectroscopy; J. Phys. Chem. A 1998, 102, 6601-6613], and fluorescence anisotropy [Schaffer, J.; Volkmer, A.; Eggeling, C.; Subramaniam, V.; Striker, G.; Seidel, C. A. M.: Identification of single molecules in aqueous solution by time-resolved fluorescence anisotropy; J. Phys. Chem. A 1999, 103 (3), 331-336].  
         [0012]     Other powerful spectroscopic techniques on the single-molecule level are signal fluctuation methods. Since its early invention fluorescence correlation spectroscopy (FCS) has developed to a frequently used method in life science to characterize samples via their translational diffusion properties or time constants of kinetics, in particular photophysical kinetics. FCS extracts the information by correlating changes in the raw photon count signal originating from number fluctuations of secondary light emitting particles in the detection volume.  
         [0013]     A very recently developed fluctuation method is fluorescence intensity distribution analysis (FIDA) [Kask, P.; Palo, K.; Ullman, D.; Gall, K.: Fluorescence-intensity distribution analysis and its application in biomolecular detection technology; PNAS 1999, 96 (24), 13756-13761], [Chen, Y.; Muller, J. D.; So, P. T. C.; Grafton, E.: The Photon Counting Histogram in Fluorescence Fluctuation Spectroscopy; Biophys. J. 1999, 77, 553-567.], [Fries, J. R.; Brand, L.; Eggeling, C.; Köllner, M.; Seidel, C. A. M.: Quantitative identification of different single-molecules by selective time-resolved confocal fluorescence spectroscopy; J. Phys. Chem. A 1998, 102, 6601-6613]. FIDA builds up a frequency histogram over the photon counts detected within fixed time intervals of the raw data stream. Applying a theoretical description of this histogram, FIDA is able to distinguish molecular components within a particle mixture via their different signal brightness properties and to yield their absolute concentrations.  
         [0014]     Further recently developed theories in the field of molecular brightness analysis are:  
         [0015]     (1) Two-dimensional FIDA (2D-FIDA) which collects the two-dimensional joint photon count number distribution within fixed time intervals of two detectors monitoring different wavelength ranges or different polarization directions of the emitted secondary light [Kask, P.; Palo, K.; Fay, N.; Brand, L.; Mets, Ü.; Ullman, D.; Jungmann, J.; Pschorr, J.; Gall, K.: Two-Dimensional Fluorescence Intensity Distribution Analysis: Theory and Applications; Biophys. J. 2000, 78, 1703-1713]. 2D-FIDA yields absolute molecular concentrations of a sample mixture comprising particles which exhibit different polarization, brightness, or spectral properties of the emitted secondary light.  
         [0016]     (2) Fluorescence intensity multiple distribution analysis (FIMDA) builds up several signal intensity distributions of different fixed time intervals to characterize molecular components of a particle mixture via their different translational diffusion and brightness properties [Palo, K.; Mets, Ü.; Jäger, S.; Kask, P.; Gall, K.: Fluorescence Intensity Multiple Distribution Analysis: Concurrent Determination of Diffusion Times and Molecular Brightness; Biophys. J. 2000, 79 (6)].  
         [0017]     Due to their high statistical accuracy the FIDA(-based) methods are increasingly applied in high-throughput-screening [Schaertl, S.; Meyer-Almes, F. J.; Lopez-Calle, E.; Siemers, A.; Kramer, J.: A novel and robust homogeneous fluorescence-based assay using nanoparticles for pharmaceutical screening and diagnostics; J. Biomolecular Screening 2000, 5 (4), 227-237], [Ullman, D.; Busch, M.; Mander, T.: Fluorescence correlation spectroscopy-based screening technology; Inn. Pharm. Tech. 1999, 30-40].  
         [0018]     Up to date, the potential of these powerful techniques has not yet fully been exploited.  
       SUMMARY OF THE INVENTION  
       [0019]     The object of the invention is to improve known spectroscopic techniques.  
         [0020]     This object is solved by the invention according to the independent claim. Advantageous embodiments of the invention are characterized in the dependent claims.  
         [0021]     According to the invention, emitted secondary radiation is induced for particles in a measurement volume. Excitation of the particles can e. g. take place as single-photon excitation, two-photon excitation or multi-photon excitation or by chemical reactions. The mechanism of secondary radiation emission can e. g. be Rayleigh scattering, Raman- or Mie-scattering, Surface-Enhanced-Raman-Scattering (SERS), Surface-Enhanced-Resonance-Raman-Scattering (SERRS) or luminescence such as fluorescence or phosphorescence or chemiluminescence. In the following, the word “light” will sometimes be used instead of “radiation”. The word “light” is used as abbreviation for electromagnetic radiation, visible or invisible.  
         [0022]     The light used for inducing the secondary light emission may be continuous or sinusoidally modulated, e. g. for phase modulation measurements, or it may be a series of light pulses.  
         [0023]     The emitted secondary light, e. g. the intensity of Raman-scattering or of fluorescence light emitted from said particles, is monitored by detecting a sequence or sequences of photon counts emitted by said particles. This can be done with the help of one or more than one photon detector which monitor different polarization components and/or wavelengths of the emitted secondary light. By using different detectors and/or different polarization filters in front of the detectors, one can observe the whole range of orientation, polarization and rotational diffusion of the secondary light emitting particles.  
         [0024]     Fluorescence is generally but not exclusively characterized by four variables: (1) spectral properties characterized by the excitation and emission wavelengths of radiation; (2) fluorescence quantum yield resulting in a certain fluorescence brightness at a given excitation intensity and wavelength; (3) polarization of the fluorescence with respect to the polarization of the excitation light; and (4) fluorescence lifetime characterizing the mentioned electronic deactivation.  
         [0025]     In this invention, the sequence or sequences of detected photon counts are divided into counting intervals. From the detected photons in every counting interval at least two stochastic variables are derived. In general, these variables can be of those mentioned above.  
         [0026]     One of the stochastic variables can be the number of photons counted by one of the detectors or a function of the numbers of photons counted by different detectors within each counting interval. The term function generally includes the identical function or identity, i.e. a function whose result is identical to the variable it takes as argument.  
         [0027]     In an advantageous embodiment of the invention, at least two detectors observe different polarizations of the emitted light and one of the stochastic variables is the anisotropy of the emitted secondary light. The anisotropy r of scattered light is generally defined as
 
 r= ( F   p   −F   s )/( F   p +2 F   s )  (1)
 
 where F p  and F s  are the temporally integrated values of the detected intensities with parallel (F p ) and perpendicular (F s ) polarization relative to the polarization of the exciting light. In the case of counting intervals, r can be determined from F p  and F s , which then represent the number of photons detected with parallel and perpendicular polarization within each counting interval. 
 
         [0028]     Equally well, one of the stochastic variables can be the detection delay times of the detected photons or photon counts relative to a reference time within the period of the modulated light, e. g. relative to the corresponding excitation pulse. This can be done using techniques well known from TCSPC. In general, one will also measure the absolute time of detection of a photon relative to some clock, as it is common for BIFL. The stochastic variables can also be a function of the detection delay times, e. g. the mean delay time observed for each counting interval, which, for fluorescence, is generally close to the fluorescence lifetime. For promptly scattered light, the delay time will be close to zero. The function can also be the sum of the detection delay times within each counting interval or a resulting parameter of a fit to the histogram of detection delay times within each counting interval.  
         [0029]     The detection delay times allow the determination of the signal decay time. In general, the signal decay time reflects the characteristic time delay between the excitation of a particle and its secondary photon emission. The signal decay time is a specific property of the secondary light emitting particle and differs for the various secondary light emission processes. In the case of fluorescence it can be the fluorescence lifetime.  
         [0030]     One can also use the rotational correlation time of the emitted secondary light as one stochastic variable. The rotational correlation time ρ is the time in which an orientation of the secondary light emitting particle relaxes to 1/e of its initial value. It can be determined either by analyzing the histograms of the delay times from one or all detectors or from the fluorescence lifetime τ and the anisotropy r using the Perrin-equation, r=r 0 (1+τ/ρ). r 0  is a particle specific constant.  
         [0031]     Orientation (or anisotropy) and deexcitation (or fluorescence lifetime) can be correlated, indicating binding and local neighborhood of the scattering particle.  
         [0032]     When using two detectors monitoring the emitted secondary light in different wavelength ranges, one has the possibility to observe e. g. the intensity in the different wavelength ranges and, thus, fluorescence resonance energy transfer (FRET) from one particle to some other particle. This allows the determination of the FRET-efficiency and of distances between particles, and, furthermore, the observation of conformational changes, binding equilibria, and spatially resolved reactions.  
         [0033]     Also, the stochastic variables can be two signal decay times or at least one signal decay time and an efficiency of energy transfer from one scattering particle to some other scattering particle. The embodiment allows e. g. the observation and correlation of signals in different wavelength ranges and their respective decay constants. It also allows the characterization of biexponential signal decays. One can determine whether both decay constants occur at the same time (correlated) or whether they are uncorrelated, because they are e. g. caused by different binding sites or different molecular states.  
         [0034]     Besides the already mentioned variables, further examples of variables are: intersystem crossing rate, transport properties characterized by the translational and rotational diffusion coefficient, absorption cross-section, etc.  
         [0035]     When choosing the number of photon counts within the counting intervals or the time duration of the counting intervals as one stochastic variable, one can measure the brightness of the secondary light emitting particles, e. g. the brightness of a fluorescence signal. The brightness is defined as the efficiency of turning excitation light into detected light. It mainly is a product of the scattering or absorption cross-section, the emission or fluorescence quantum yield and the detection efficiency. The determination of the brightness can e. g. be performed via FIDA and allows e. g. the determination of concentrations, stoichiometry, and multimerization instead of just dimerization, i.e. the absolute number of scattering particles can be observed [see e. g. Peet Kask, Kaupo Palo, Dirk Ullmann, and Karsten Gall: “Fluorescence-intensity distribution analysis and its application in biomolecular detection technology”; PNAS 1999, vol. 96, 13756-13761.].  
         [0036]     The time duration of counting intervals by itself can be used as one stochastic variable, providing e. g. a measure of the intensity of the radiation detected in the counting interval. Furthermore, in order to use the intensity of the counting interval as a direct stochastic variable, one can directly calculate it e. g. by dividing the number of photon counts within the counting interval by its time duration. In case one observes the secondary light emission from single particles, the intensity equals the above mentioned brightness of the single secondary light emitting particle.  
         [0037]     When choosing a function of the temporal interval between the detection times of successively detected photons (interphoton times) of one detector or a group of different detectors within the same counting interval as one stochastic variable, as it is common in BIFL experiments, one can e. g. calculate the absolute arrival time of every photon. This is a way of determining the absolute time axis and intensity of the detected signal, which allows auto- or cross-correlation analysis like in FCS or intensity distribution analysis like in FIDA. As one example of application, one can determine triplet state properties within a counting interval from this analysis , e. g. by comparing the triplet decay time or triplet population of a counting interval as determined from FCS with the signal decay time. Kinetic constants, transport properties like translational diffusion constants, and brightness values can also be deduced from interphoton times.  
         [0038]     Arbitrary combinations of two or more of the above mentioned stochastic variables are possible to determine correlations between these parameters. In particular, any one or more of the above mentioned stochastic variables can be combined or correlated with the signal decay time or the signal decay times observed by different detectors.  
         [0039]     To determine correlations of the stochastic variables a multidimensional distribution function is deduced from the data, in particular a histogram. In the following, the word “histogram” will sometimes be used instead of “distribution function”.  
         [0040]     The multidimensional histogram is constructed as a function of at least two stochastic variables, whereby the histogram is built up using values of the variables determined for each counting interval; e. g. the frequency of a pair of values of two variables jointly determined from each counting interval is obtained for a whole measurement. Similar histograms are known from [Herten, D. P.; Tinnefeld, P.; Sauer, M.: Identification of single fluorescently labeled mononucleotide molecules in solution by spectrally resolved time-correlated single-photon counting; Appl. Phys. B 2000, 71, 765-771] or from [Kask, P.; Palo, K.; Fay, N.; Brand, L.; Mets, Ü.; Ullman, D.; Jungmann, J.; Pschorr, J.; Gall, K.: Two-Dimensional Fluorescence Intensity Distribution Analysis: Theory and Applications; Biophys. J. 2000, 78, 1703-1713].  
         [0041]     The construction of a multidimensional histogram in general allows the rendering of correlations between the variables. If for example the examined sample comprises two separate molecular components, these may be identified by two well-separated distributions within the histogram, since in general the components give rise to different sets of stochastic variables. It also helps to reduce the calculation effort needed to analyze the data by reducing the number of data from hundreds of thousands of photon counts with their temporal information to merely one histogram. The generated multidimensional histograms can also be used to recognize or classify certain parameter patterns, which can easily be analyzed by pattern recognition or image analysis algorithms like smoothing, contrast enhancement, filtering, statistical analyses like maximum likelihood analysis, parameter fitting, clustering with a fuzzy covariance matrix, Bayesian analysis, K-means clustering, application of the Fuzzy Kohonen Clustering Network, etc. [D. Driankov, D.; Hellendoorn, H.; Reinfrank, M.: An Introduction to Fuzzy Control; Springer-Verlag, 1993], [Roeder, K.; Wasserman, L.: Practical Bayesian density estimation using mixtures of normals; Journal of the American Statistical Association, 1997, 92, 894-902], [Anderberg, M. R.: Cluster analysis for applications; Academic Press, New York, 1973, xiii+35p. Nauck, D.; Klawonn, F.; Kruse, R.: ‘Neuronale Netze und Fuzzy-Systeme’; Vieweg, 1994]. In this way, also dynamic sequences of e. g. two-dimensional histograms can be viewed like a film or analyzed with pattern recognition algorithms.  
         [0042]     Thus, the histogram is analyzed to determine combinations of the at least two stochastic variables belonging selectively to at least one species of light emitting particles. These species can e. g. simply be bound or unbound states of a given molecule or they can be chemically different molecules.  
         [0043]     According to the invention, at least one species of light emitting particles is selected from the multidimensional histogram for further analysis. This can be achieved by further processing only those counting intervals having a combination of the at least two stochastic variables which belong to the at least one selected species of light emitting particles. As mentioned before, a single species can generally be recognized by a well-separated distribution within the histogram.  
         [0044]     The detected photons from the selected counting intervals are further analyzed by spectroscopic analysis techniques to characterize the secondary light emitting particles of the selected species. Any spectroscopic analysis techniques can be utilized for further analysis. Further analysis can e. g. result in more detailed values of the above mentioned stochastic variables. Often, correlation analysis (e. g. FCS), FIDA or lifetime analyses will be used. Resulting from this further analysis different particles of a sample can be further characterized, which e. g. reveals details of heterogeneities within the different particles.  
         [0045]     Thus, a very powerful tool for selecting parts of the data for further analysis can be derived from the multidimensional histogram.  
         [0046]     Most of the stochastic variables listed above are very sensitive to the local environment of the secondary light emitting particle and can be measured e. g. via fluorescence detection. Thus, in the case of changes in the local environment of the secondary light emitting particle, e. g. during an aggregation, changes of the variables are generally induced. Therefore, the information about a reaction between two particles can be detected by relating the change of one of the variables to the reaction.  
         [0047]     A polarization measurement allows e. g. the selective determination of rotational diffusion constants, i.e. mobilities of particles, for states with e. g. different signal decay times or signal brightness, like particles in different binding states or binding sites.  
         [0048]     The described method is generally well suited for single molecule spectroscopy. The observation of single molecule events is especially well suited for observing the correlation of stochastic variables, since the correlation between these variables can be observed for a single particle at a time and is not blurred by a statistical average over several particle signals.  
         [0049]     For example, the invention allows observing binding reactions that are of uttermost importance for high throughput screening in pharmacology. The binding reactions can be studied using the invention in great detail. In general, one can observe the dynamics of a reaction, the conformation of complexed molecules, conformational changes, distances between molecules, e. g. with the help of FRET (fluorescence resonance energy transfer). Also, one can observe the orientation of particles or their local mobility using polarization measurements.  
         [0050]     In an advantageous embodiment of the invention, the sequence of photon counts is divided into counting intervals by defining the end of a counting interval when a predefined number of photons has been counted either by a given single detector or jointly by a given set of detectors, wherein said predefined number of photons is greater than one. The counting intervals can be chosen more or less arbitrarily, e. g. based on the average intensity value of a certain number of photons or based on the time delay between successively detected photons averaged over a certain number of photons, etc. These intervals can be overlapping, they can be immediate neighbors, or they may be well spaced from one another. The latter will be the case if single molecules are observed and the counting intervals roughly correspond to the fluorescence bursts caused by a single molecule traversing the measurement volume. The number of photons can be on the order of e. g. 100-200. The definition of counting intervals with a predetermined number of detected photons leads to well-defined statistical properties of the detected signal. Thus, by choosing a certain number, N, of photons for the counting interval, the accuracy of the measured parameters can directly be chosen. This is due to the dependence of the standard deviations, στ, σ r , and σ E , of the parameters fluorescence lifetime, τ, anisotropy, r, and efficiency of fluorescence resonance energy transfer (FRET), E, on the number, N, of photon counts used for parameter determination. The formulas are: 
 
 (a) fluorescence lifetime, τ:  
                 σ   τ     ⁡     (     τ   ,   N     )       =       k     T   /   τ       ⁢     (     1   -     ⅇ       -   T     /   τ         )     ⁢       (           ⅇ     T   /     (     τ   ⁢           ⁢   k     )         ⁡     (     1   -     ⅇ       -   T     /   τ         )           (       ⅇ     T   /     (     τ   ⁢           ⁢   k     )         -   1     )     2       -       k   2       (       ⅇ       -   T     /   τ       -   1     )         )       1   2       *     τ     N                 (   2   )             
 
         [0051]     (T: time window of TCSPC used for lifetime determination, k: number of channels within this time window) [Hall, P.; Selinger, B.: Better Estimates of Exponential Decay Parameters; 1981, 85, 2941-2946], [Zander, C.; Sauer, M.; Drexhage, K. H.; Ko, D. S.; Schulz, A.; Wolfrum, J.; Brand, L.; Eggeling, C.; Seidel, C. A. M.: Detection and characterization of single molecules in aqueous solution; Appl. Phys. B 1996, 63 (5), 517-523]
 
 (b) anisotropy, r:  
               σ   r     =       1   3     ⁢         (     2   +   r     )     ⁢         (     1   -   r     )     ⁢     (     1   +     2   ⁢   r       )             N                 (   3   )             
 
 (This equation is derived from error propagation assuming Poissonian noise of the detected signal.) 
 
 (c) efficiency of FRET, E:  
               σ   E     =       1     N       ⁢   E   *     [       E   *     (     1   -   X     )       +   X     ]     *         1   -   E     E                 (   4   )             
 
         [0052]     (X=(Ψ D /Ψ A )*(Φ D /Φ A ), Ψ D/A : detection efficiency of the signal emitted by the donor/acceptor molecule of the FRET-pair, Φ D/A: fluorescence quantum yield of the donor/acceptor molecule of the FRET-pair alone. This equation is derived from error propagation assuming Poissonian noise of the detected signal.)    
         [0053]     When comparing the width of the separated distributions to the theoretical prediction of the according parameters or stochastic variable (e. g., eqs. (2) to (4)), heterogeneities of the different particles can be discovered. An important feature of this approach is the possibility to vary the size of the photon window in order to vary statistical accuracy to a desired level. This allows one to answer the above question in a most efficient manner. In this way, it is also possible to plot the photon number vs. the parameter to directly resolve heterogeneities.  
         [0054]     The described method goes beyond known spectroscopic techniques in particular in the following aspects:  
         [0055]     (1) The signal of photon counts can be detected in distinct intervals of a fixed photon count number as well as in a fixed time interval.  
         [0056]     (2) In the case, a fixed photon count number is chosen for the counting intervals, this determination of the counting intervals leads to well-defined statistical properties of the stochastic variables. Therefore, the width of the whole or of parts of the multidimensional histogram directly reveals heterogeneities of the sample or of molecular components of the sample. Also a plot of the photon number within a photon window against theoretical and observed standard deviations can reveal heterogeneities.  
         [0057]     (3) The signal properties of the photon counts are used to determine stochastic variables within each counting interval to build up a multi-dimensional joint histogram of these variables or properties. In contrast, 2D-FIDA directly plots the two-dimensional joint photon count number distribution.  
         [0058]     (4) The most important new feature of this invention is that it enables to select only those photon counts from counting time intervals assigned to at least one species and to further analyze these selected photons. This species-selective analysis enables new possibilities like revealing heterogeneities within a single species.  
         [0059]     Other objects, advantages and novel features of the invention will become apparent from the following detailed description of the invention when taken in conjunction with the accompanying drawings. 
     
    
     BRIEF DESCRIPTION OF THE DRAWING  
       [0060]      FIG. 1  is a schematic diagram of the optical setup;  
         [0061]      FIG. 2  is a graph showing time-gated signal traces;  
         [0062]      FIG. 3  is a multidimensional histogram; and  
         [0063]      FIG. 4  is a graph showing a selective fluorescence intensity distribution analysis for data selected from  FIG. 3 . 
     
    
     DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS  
       [0064]     In the presently preferred embodiment, silver particles were investigated. These were nearly spherical, essentially mono-disperse particles (Ag54) with 54±6 nm diameter at a concentration of app. 10 13  particles/liter and a characteristic diffusion time τ D =20 ms across the measurement volume. The silver hydrosols were activated by Cl-ions at a concentration of 2 mM and incubated with a dilute solution of Rhodamine 6G at a concentration of app. 10 −12  M. This procedure led to less than one dye molecule per silver particle.  
         [0065]      FIG. 1  shows a schematic diagram of the optical setup. Single-molecule SERRS was performed with a confocal epi-illuminated microscope  10  with two detectors  12 ,  14  for separate detection of parallel or perpendicular polarized signal components, separated by a polarization beam splitter cube  16 . The confocal microscope has a pinhole  18  with a diameter of 100 μm. Additionally, spectral band-pass filters  20  for the relative wavenumbers of 550-2300 cm −1  were used in front of each detector. The size of the measurement volume was app. 3 fl, resulting in a characteristic diffusion time for Rhodamine 6G molecules in water of τ D =0.3 ms. A linearly polarized, mode-locked argon ion laser  22  was applied for pulsed excitation at 496 nm. The repetition rate of the laser was 73 MHz, the pulse width 190 ps, and the focal excitation irradiance 190 kW cm −2 . The scattered photons were detected with the help of avalanche photodiodes as detectors  12 ,  14 . The detected photon counts were registered by a PC-BIFL-card (SPC 432, Becker&amp;Hickl GmbH, Berlin, Germany). The stored data were subjected to selective analysis as described below.  
         [0066]     Using pulsed laser excitation and a highly diluted aqueous solution of silver colloids Ag54 (app. 10 13  particles/liter) with less than one Rhodamine 6G molecule per particle, signal bursts with count rates higher than 100 kHz indicate transits of individual particles or molecules, respectively.  
         [0067]      FIG. 2  shows time-gated signal traces (see below for more details) that allow distinguishing between temporally prompt, p, Raman scattering signal (upper trace) and delayed, d, fluorescence signal (lower trace).  
         [0068]     Using excitation by a pulsed, linearly polarized laser and a confocal microscope with two detectors, one can calculate three spectroscopic parameters from the raw data: 
    intensity, I s , measured by the interphoton times, Δt, between successively detected photons with a time resolution of 50 ns;     signal decay properties characterized by the 1/e-decay time, τ s , which is obtained from detection delay times measured by time-correlated single-photon counting (TCSPC); and     time-integrated anisotropy, r.    
 
         [0072]     An important step in analyzing a single molecule experiment is to distinguish between signal and background.  
         [0073]     Burst selection can nicely be realized using the time-information obtained by the interphoton time, Δt. A signal is classified as signal burst, if Δt for 150 consecutive photons is below the threshold value of 0.049 ms after Lee filtering [Enderlein, J.; Robbins, D. L.; Ambrose, W. P.; Goodwin, P. M.; Keller, R. A. “The statistics of single molecule detection: an overview”; Bioimaging 1997, 5, 88-98]. Thus, data analysis is restricted to only those registered events which are within the signal burst of a single molecule/particle transit selected from the signal trace.  
         [0074]     TCSPC allows to construct histograms of photon arrival times relative to the incident laser pulse for each selected region in the signal trace (see histograms {circumflex over (1)} {circumflex over (2)}, {circumflex over (3)}, and {circumflex over (4)} in the lower part of  FIG. 2 ). Due to the pronounced difference in the decay times of Raman and fluorescence signals, time-gating is an efficient criterion to distinguish between prompt Raman (p: channels  20 - 50 ) and delayed fluorescence signal (d: channels  60 - 250 ) in computed multi-channel scaler traces (upper/lower trace in  FIG. 2 ). Shaded bars p, d in signal arrival time histogram {circumflex over (1)} indicate the time gating intervals.  
         [0075]     Four typical situations {circumflex over (1)}, {circumflex over (2)}, {circumflex over (3)}, and {circumflex over (1)} are marked in the signal traces and the corresponding arrival time histograms {circumflex over (1)}, {circumflex over (2)}, {circumflex over (3)}, and {circumflex over (4)} illustrate different signal decay properties: 
    {circumflex over (1)} background signal due to the Raman signal of water and dark counts of the detector (count rate: 12 kHz, 65% of the total signal appear in the p-channel);     {circumflex over (2)} SERRS bursts with count rates of more than 100 kHz (87% of the signal in the p-channels);     {circumflex over (3)} fluorescence signal within a SERRS-burst for the two polarization components x and y;     {circumflex over (4)} fluorescence burst of a freely diffusing Rhodamine 6G for the two polarization components x and y.    
 
         [0080]     An established maximum-likelihood estimator [Hall, P.; Selinger, B.: “Better Estimates of Exponential Decay Parameters”; J. Phys. Chem. 1981, 85, 2941-2946] was applied to calculate the 1/e-signal-decay time, τ s , for a total number of channels, m=200, starting from the maximum (Channel:  30 ) to  230 , whereby the channel width T is equal to 49 ps. τ s  is determined by the weighted sum of the events, N l , registered in channel i, divided by the total number of number of events N. Following this estimator, τ s  is the solution of equation (5):  
               1   +       (       Exp   ⁡     (       -   T     /     τ   S       )       -   1     )       -   1       -       m   ⁡     (       Exp   ⁡     (       -   mT     /     τ   S       )       -   1     )         -   1         =       N     -   1       ⁢       ∑     i   =   1     m     ⁢     iN   i                 (   5   )             
 
         [0081]     The statistical relevance of single-molecule observations is judged by analysis of 300 bursts. Within each burst, the signal is binned into sub-histograms with a constant number of 150 counts. Sliding this event-window or counting interval stepwise along the registered counts, sliding signal-parameter analysis can be performed to generate parameter-time trajectories [Eggeling, C.; Fries, J. R.; Brand, L.; Günther, R.; Seidel, C. A. M.: Monitoring conformational dynamics of a single molecule by selective fluorescence spectroscopy; PNAS 1998, 95, 1556-1561].  
         [0082]     Three parameter-traces for signal intensity, I s , 1/e signal decay time, τ s , and anisotropy, r, are calculated. The macroscopic time information of these signal parameter traces is obtained by the mean of the interphoton times, Δt, for every counting interval. In this way, the time evolution of characteristic parameters of a single molecule/particle can be monitored simultaneously in real time.  
         [0083]     For each counting interval or point of time, respectively, the values of the pairs (r,τ s ) and (I s τ s ) are counted to generate a two-dimensional normalized frequency histogram as shown in  FIG. 3  for the Ag54 sample.  
         [0084]     Two different species, adsorbed and free dye, marked as regions A and B, respectively, are clearly evident in the normalized histogram of r vs. τ s  and I s  vs. τ s  ( FIG. 3 ). Within the error limits of ±17% determined for the sliding analysis window of 150 events, the adsorbed dye (A) is characterized by a prompt, strongly polarized Raman signal. The decay time τ s  is small and equal to the instrument response function with background events included. The average anisotropy r av  is 0.24. The free dye (B) is characterized by a well-known, unquenched, mainly depolarized fluorescence (τ s =3.8 ns, r av =0.02).  
         [0085]     This clear identification of the two different species would have posed difficulties without the two-dimensional histogram representation. The one-dimensional projections of the data of  FIG. 3  onto the r-axis or I s -axis, respectively, do not allow a distinction between the two different species. They only show one broad distribution.  
         [0086]     The lower plot of I s  vs. τ s  ( FIG. 3 ) shows that under the conditions described, where the selected spectral range favors SERRS detection, the Raman scattering signal is higher than the fluorescence signal. If, however, the set-up is optimized for the detection of Rhodamine 6G fluorescence, I s  values&gt;300 kHz (data not shown) can be obtained; i.e. SERRS and fluorescence can approximately achieve the same signal strengths.  
         [0087]     The clear identification of the two different species (A: bound to silver particle, B: free dye) allows a selection of the data from one of the species for selective further analysis, e. g. to answer the question how many Rhodamine 6G molecules are bound to the silver particles.  
         [0088]     Such quantitative questions can be answered by fluorescence-intensity distribution analysis (FIDA). FIDA has been developed for confocal microscopy studies in which the fluorescence intensity has a spatially heterogeneous brightness profile.  
         [0089]     FIDA allows determining specific brightness values, C 0 , in a heterogeneous sample. Besides experimental parameters (laser intensity, I(r), r now denoting a spatial coordinate, or detection efficiency, g) the brightness C 0 =g I(r) t depends on the fluorescence quantum yield, dark state properties, and on the number of bound fluorophores on a single nanoparticle. The specific brightness C 0  corresponds to the number of counts in a time interval, t, where the molecule is in the center of the detection volume element, i.e. I(r=0).  
         [0090]     For the selective FIDA-analysis, the intensity data only of region A in  FIG. 3  are converted into a probability density, P 1 (C t ,t), of fluorescence count rates, C t , in a certain time interval t (here t=100 μs) to obtain information on the brightness, C 0 (X), of each contributing species X.  
         [0091]     The results are shown in  FIG. 4 , showing the distribution of the fluorescence count rate C t . The decrease of the observed relative frequencies (open circles) in the first three channels is due to the selection of signal bursts of particles passing through the measurement volume. These bursts have a certain minimum intensity and thus a certain minimum count rate. This decrease is neglected in the simulation.  
         [0092]     The signal intensity distribution of the bursts in region A of  FIG. 3  is compared with four simulations assuming different numbers of species with fixed brightness values. Thereby P 1 (C t ,t) is computed as a normalized sum of a background signal with a Poissonian distributed and a fluorescence signal with species-specific brightnesses, C 0 (X) (Eq. 9 of [Fries, J. R.; Brand, L.; Eggeling, C.; Köllner, M.; Seidel, C. A. M.: Quantitative identification of different single-molecules by selective time-resolved confocal fluorescence spectroscopy; J. Phys. Chem. A 1998, 102, 6601-6613]). The four simulations for the photon count density, P 1 (C t ,t=100 μs), are based on models with a background signal of 12 kHz (14%) and a varying number of fixed brightnesses: one brightness (black dots), C 0 =12 (86%); two brightnesses (dashed line), C 0 (1)=12 (56%) and C 0 (2)=28 (30%); three brightnesses (dotted line), C 0 (1)=12 (56%), C 0 (2)=28 (28%), and C 0 (3)=56 (2%) and four brightnesses (solid line), C 0 (1)=12 (56%), C 0 (2)=28 (26%), C 0 (3)=40 (3%) and C 0 (4)=56 (1%).  
         [0093]     The comparison shows that at least three (small dotted line) or four brightnesses (solid line), C 0 (1)=12 (56%), C 0 (2)=28 (26%), C 0 (3)=40 (3%) and C 0 (4)=56 (1%), and a background of 12 kHz (14%) are necessary to achieve a satisfactory agreement between theory and experiment. In principle, this heterogeneity of the signal can have several reasons such as particle aggregation, more than one SERRS-active molecule adsorbed on the nanoparticle and different binding sites with specific SERRS enhancement factors. Due to the rotational and translational diffusion characteristics resulting from photon correlation experiments (data not shown) and due to the spectral properties of the colloid (data not shown), particle aggregation as the main reason for the heterogeneity can be excluded. In view of the applied stoichiometry, binding of multiple dyes on the nanoparticles is not very likely. Accordingly, the low fraction of the large brightnesses, C 0 (3)=40 (3%) and C 0 (4)=56 (1%), might be attributed to binding of multiple dyes on the nanoparticles. Therefore, it can be deduced from  FIG. 4  that the main fraction of signal, characterized by the two brightnesses C 0 (1)=12 (56%) and C 0 (2)=28 (26%), is predominantly generated by single SERRS active dye molecules in heterogeneous binding sites of the nanoparticles.  
         [0094]     These results cannot be achieved by simple FIDA analysis without preselection in a multidimensional histogram since for FIDA the freely diffusing particles would blur the signal. Only the preselection with the help of the multidimensional histogram leads to the correct results.  
         [0095]     Many other methods for further data analysis can equally be applied, e. g. fluorescence correlation spectroscopy.  
         [0096]     Many modifications and variations of the present invention are possible without departing from the scope of the invention.  
         [0097]     For example, the excitation can be accomplished by more than one light source. Besides the epi-illuminated microscope, many other optical arrangements are suitable for the excitation, including evanescent excitation, Raman microscopes, confocal laser scanning microscopes and scanning near-field microscopes.  
         [0098]     Also the detector does not necessarily have to be an avalanche photodiode. Any sensitive detector will do, like photomultipliers or CCD cameras. The latter have the additional advantage to allow the simultaneous observation of many samples, e. g. in a microtiter plate.  
         [0099]     In case some of the properties of the particles are known, it is possible to perform more complex analyses to generate histograms. In a heterogeneous sample, e. g., fluorescence decay histograms can be analyzed with more than one exponential for the lifetime and/or rotational correlation time. Usually some parameters, e. g. the lifetimes, are known from previous experiments and can be used as constants in a fit. Thus, e. g. the amplitudes of the individual lifetime components remain to be determined by the fit, which improves the accuracy substantially. The obtained amplitudes can be used as stochastic variables for a multidimensional histogram. This is also well suited for the analysis of samples of higher concentrations than used for single molecule detection.  
         [0100]     Finally, further analysis after preselection in a multidimensional histogram does not necessarily have to rely on counting interval with a predefined number of photons. The counting intervals can be defined by any manner, e. g. by a fix temporal interval, as it is usually the case.  
         [0101]     It is, therefore, to be understood that within the scope of the appended claims the invention may be practiced otherwise than as specifically described.