broadband dos is a technique that combines frequency domain ( fd ) measurements with a broadband steady - state ( ss ) measurement and determines the absolute absorption and scattering of the tissue within the near - infrared ( 600 - 1050 nm ). from the measured tissue absorption the absolute tissue chromophores can be determined . broadband dos using combined frequency domain ( fd ) measurements with a broadband steady - state ( ss ) measurement has recently been developed by researchers at the beckman laser institute at the university of california at irvine , and has been published in bevilacqua et . al ., applied optics , vol 39 , no . 34 , pp 6498 - 6507 ( december 2000 ). see also tromberg et al , “ broadband absorption spectroscopy in turbid media by combined frequency - domain and steady state methodologies ” u . s . patent application 20030023172 ( jan . 30 , 2003 ) incorporated herein by reference . as described in the published literature most of the wavelength coverage is provided by a white - light ss measurement , whereas the fd data are acquired at a few selected wavelengths . coefficients of absorption μ a and reduced scattering μ &# 39 ; s derived from the fd data are used to calibrate the intensity of the ss measurements and to estimate μ &# 39 ; s at all wavelengths in the spectral window of interest . after these steps are performed , one can determine μ a by comparing the ss reflectance values with the predictions of diffusion theory , wavelength by wavelength . absorption spectra of a turbid phantom and of human breast tissue in vivo , derived with the combined ssfd technique , agree well with expected reference values . all measurements can be performed at a single source - detector separation distance , reducing the variations in sampling volume that exist in multidistance methods . the technique uses relatively inexpensive light sources and detectors and is easily implemented on an existing multiwavelength fd system . by way of background fig1 is a diagrammatic block diagram which shows the experimental arrangement for broadband dos ssfd measurements as is conventionally know in the published literature . in all cases , light is delivered via optical fiber 16 a shown on the probe head 14 in fig1 to the surface of the sample 22 and collected at some distance away . in the fd mode , the light arrives sequentially from one of six amplitude - modulated diode lasers at 661 , 681 , 783 , 803 , 823 and 850 nm all with output powers of up to 20 mw at the sample 22 . the light is detected by an avalanche photodiode unit 24 ( hamamatsu c556p - 56045 - 03 ) coupled to optic fiber 16 b that amplifies the ac component of the signal . a network analyzer 26 ( hewlett - packard 8753c ) coupled to photodiode unit 24 delivers 251 modulation frequencies from 50 to 500 mhz and measures phase and modulation amplitudes of the photon intensity signal as described in the publication cited above . in the ss mode light comes from a 150 - w halogen lamp 30 ( fiber - lite ) and is analyzed by a fiber - coupled spectrograph 28 ( ocean optics s2000 ) with a linear ccd detector from 525 to 1155 nm , with the useful range for our experiments being 650 - 1000 nm . the spectrograph 28 records a total of 2048 points ( 0 . 35 nm / pixel ), and the spectral resolution is 5 nm full width at half - maximum . we measure the spectrum of the light source separately by inserting the source and detector fibers 16 b and 16 d into different ports of an integrating sphere ( labsphere , is - 040 - sf ). relative reflectance is calculated to be the sample spectrum divided by the source spectrum . total acquisition time per sample for ssfd measurements is of the order of 40 s , namely 30 s for fd and 10 s for ss . we calculate pa according to the above published methods with an in - house matlab ( the mathworks , inc .) code , making use of the optimization toolbox . computer 32 is coupled to spectrometer 28 and network analyzer 26 for data processor and to an ac controlled rf switch 34 and dc diode controller 36 for control of broadband frequency sweeping of diode lasers 10 by means of bias t &# 39 ; s 38 coupled to rf switch 34 and diode controller 36 . for the fd measurements six diode lasers 10 at wavelengths of 661 , 681 , 783 , 803 , 823 and 850 nm were used and intensity modulated from 50 to 500 mhz . the delivery and collection fd and ss optical fibers 16 a - 16 d were secured in a delrin ® acetal resin probe 14 diagrammatically depicted in fig1 . the probe head 18 was a one - inch ( 2 . 54 cm ) diameter cylinder with holes drilled through lengthwise for placement of the four fibers 16 a - 16 d . two detection fibers 16 b and 16 d for the fd and ss measurement respectively were each fixed in the probe 14 at an equal distance from their corresponding source fibers 16 a and 16 c . the source - to - detector separation on the probe head 18 was 6 mm for liquid phantom measurement and 10 mm for the animal measurements . it must be understood that many different types and configurations of probe geometry may be employed and that the present embodiment is provided only for purposes of example . in addition , not only probe geometry can be varied but the number optical elements or fibers can be varied . for the fd measurements , the amplitude and phase of light were calibrated either using a liquid phantom consisting of two parts lyposyn 10 % iv ( lot 05 - 372 - de ) with one part water or a silicon phantom . the optical properties of the liquid calibration phantom were determined prior to the sample measurements through a set of multi - frequency , multi - distance , infinite geometry measurements . the chromophore concentration fit was performed to the absolute μ a spectrum using the extinction coefficients of the main absorbers within the tissue or sample . in this study the samples are liquid phantoms and rabbit muscle , therefore the chromophore fit extracts concentrations of water , lipid , and nigrosin for the phantom model and hb , hbo 2 , water and lipid for the animal model . the liquid phantom measured was composed of 250 ml water , 250 ml lyposyn 10 % iv ( lot 08 - 412 - de ) and 1 . 27 mg nigrosin . the lyposyn 10 % iv emulsion was added for scattering and the nigrosin was added to mimic tissue absorption . the liquid phantom was placed in a pyrex beaker on a heating and stirring plate . the broadband dos probe 14 was placed directly on the surface of the liquid phantom and the distance between the optical source fibers 16 a and 16 c and detector fibers 16 d and 16 d was 6 mm . a thermistor probe ( not shown ) was placed adjacent to the optical fibers at a depth of ˜ 1 - 2 mm into the phantom , which was approximately the mean probing depth of the light . a magnetic stir bar ( not shown ) was placed in the phantom and used before each measurement to stir the phantom and ensure a homogeneous composition of both optical properties and temperature . baseline measurements were acquired at room temperature before heating the phantom and the thermistor resistance was recorded at the beginning and end of each optical measurement ; an average resistance was calculated from the two values and converted to temperature . the phantom was then heated with the hot plate from room temperature up to 47 ° c . and then allowed to cool down . broadband dos measurements were acquired throughout the heating and cooling process . a pathogen - free white new zealand rabbit ( myrtle rabbitry inc ., thompson station , tenn .) was used . the animal was housed in a pathogen - free animal facility and given a commercial basal diet and water ad libitum . all procedures followed a protocol approved by the institutional laboratory animal care and use committee , university of california , irvine ( arc protocol no . 2000 - 2218 ). details of the experimental procedure involving sedation and drug injection in the animal were conventional . a plastic probe 14 incorporating the source and detector fibers was placed on the medial surface of the right hind thigh for the broadband dos measurements . a source and detector separation of 10 mm was used for both fd and ss acquisitions . prior to euthanizing the animal by standard procedures at the end of studies ( eutha , intravenous injection ), two thermistors were imbedded in the leg of the animal adjacent to the broadband dos probe . one thermistor was imbedded ˜ 3 mm deep into the muscle tissue and the other was more superficial and placed directly under the skin . baseline measurements were taken with the broadband dos system prior to sacrifice and then after sacrifice , plastic bags filled with ice were placed around the dos probe on the surface of the animal &# 39 ; s tissue and underneath the animal &# 39 ; s leg . broadband dos measurements as well as thermistor resistance values were then acquired continuously as the tissue cooled . thermistor readings were acquired at the beginning and end of each broadband dos measurement and averaged . the algorithm used to fit the broadband dos data for temperature was the following . starting with the broadband absorption measured using the dos instrument the bound water shift ( bws ), was calculated for the baseline measurements prior to cooling as described in the doctoral thesis by sean merritt on file at the library or the university of california , irvine . for the bws fit the tissue temperature was assumed equal to the baseline temperatures measured using the thermistors . in the case of these experiments the true temperature was known from the thermistors , but in a clinical system it would be necessary to assume the temperature based on previous knowledge . with the bws , we could then correct the water chromophore used in the algorithm for effects due to macromolecule binding described the doctoral thesis of sean merritt . a temperature dependent pure water spectra were measured in a spectrophotometer . measurement of purely absorbing samples within a spectrophotometer allow for a direct measurement of the extinction coefficients . the water spectrum we have used in the past was measured at 22 ° c ., much lower than tissue temperatures of interest ( 33 - 35 ° c .). we focus on the measurement of water absorption over a range of temperatures ( 17 - 60 ° c .) that are used for the temperature fitting in this disclosure . the spectrophotometer used was a beckman du650 which has a piezo temperature controller system . in order to get an accurate measure of the water temperature , two cuvettes 20 were filled and placed size by side in the cuvette cell holder 22 . one water sample was within the light path of the spectrophotometer and used for absorption measurements while the other sample had a thermistor ( newport , ± 0 . 2 ° c .) immersed in the water sample at the same level as the light path on the measured sample . resistance was recorded from the thermistor during the spectrophotometer measurements and converted to temperature which was used as the true temperature of the measurement sample . ideally , calibration of the measurement would be performed using different cell path lengths , which would allow for the absorption of the plastic cuvette to be removed . because the cuvette cell 22 on the spectrophotometer available was a fixed distance a blank was acquired using an empty cuvette 20 in order to account for the absorption of the cuvette 20 itself as well as the source intensity . fig1 illustrates the water filled cuvette 20 with the index of refractions for air , plastic and water given as n air , n p and n w . the source intensity is given by i 0 and enters the cuvette 20 at the left side of fig1 . the output intensity on the right side is given by i where : i = t 1 × t 2 × t 3 × t 4 × t w × t p × i 0 , ( 0 & lt ; t i & lt ; 1 ) where t 1 through t 4 are transmission factors determined from the perpendicular fresnel reflections occurring at the boundaries and are given by : t ⊥ = 4 ⁢ n 1 2 ( n 1 + n 2 ) 2 with n 1 and n 2 being the index of refraction of the medium the light is exiting and entering respectively . t w and t p account for the transmitted light through the water and the plastic due to the absorption of these materials . as stated above the calibration measurement was performed on an empty cuvette . the only difference between the measurement sample and the blank is then that the water index of refraction is replaced with that of air . the transmitted intensities for a pure water sample and an empty cuvette are given by i s and i b respectively : i s = 256 ⁢ n p 4 ⁢ n w 2 ( n p + 1 ) 4 ⁢ ( n p + n w ) 4 × t w × t p × i 0 i b = 256 ⁢ n p 4 ( n p + 1 ) 8 × t p × i 0 the measured parameter reported by the spectrophotometer is the absorbance ( a spec ) which is given by taking the ratio of the measured sample intensity with the intensity measured on the blank cuvette : i s i b = n w 2 ⁡ ( n p + 1 ) 4 ( n p + n w ) 4 × t w = 10 - a spec a spec = - log ( n w 2 ⁡ ( n p + 1 ) 4 ( n p + n w ) 4 ) - log ⁡ ( t w ) if the sample and the blank measurement had the same index of refraction , as is normally the case , the first log term would be equal to zero and the absorbance would be equal to − log ( t w ), which is the desired parameter being measured . therefore , the true absorbance of pure water can be determined given knowledge of the index of refraction of water and the material of the cuvette , which is polymethyl methacrylate ( pmma ) using the following : a water = - log ⁡ ( t w ) = - log ( n w 2 ⁡ ( n p + 1 ) 4 ( n p + n w ) 4 ) - a spec the indexes of refraction of water and pmma have been well characterized within the wavelength region of interest . plugging n w and n p from the above plots into the equation above results in a water = - log ⁡ ( t w ) = - log ( n w 2 ⁡ ( n p + 1 ) 4 ( n p + n w ) 4 ) - a spec which provides an absolute pure water spectrum . the corrected water spectra that were measured in the spectrophotometer are presented in fig8 . the direction of the arrows in the figure indicate the direction of the changing absorption as the temperature is increased . as the temperature is increased from 17 to 60 ° c . there is a blue shift and narrowing of the absorption peak as well as an increase in intensity . there is also an isosbestic point at about 1000 nm , which is consistent with references and suggests the majority of the water hydrogen is in one of two states : unbound or bound . in order to test the accuracy of the above correction , the 22 ° c . water spectrum measured in the spectrophotometer can be interpolated from the temperature dependent data in fig8 and compared with the water spectrum measured by known published standards . the primary wavelength range of interest is between 935 - 1000 nm given that this is the spectral window used for the temperature fitting . over this wavelength range , the percentage difference is within ± 5 % of the water absorption measured by published standards . the largest percentage difference between the two curves is around 600 nm where the absorption is very small and the differences can be as large as 40 %. the measured water spectra in fig1 were first corrected for the bound water shift of the tissue and then used as the temperature dependent water chromophore . water spectra at specific temperatures were interpolated from this library of temperature dependent water spectra to provide water absorption spectra at all temperatures between 17 and 60 ° c . the broadband dos data was weighted such that only the absorption values around the water absorption peak were used because weighting the full spectra equally converged on temperatures which correlated with the true temperatures , but were underestimated . for both the liquid phantom and animal model a spectral window defined from 935 - 1000 nm was used in the fitting . with the spectral window defined , a matlab least squares fitting routine (‘ isqcurvefit ’) determines the temperature of the sample by finding the best fit between the measured water absorption spectrum and the addition of a flat baseline chromophore and a water absorption spectrum at a specific temperature from the temperature dependent water chromophore set . the details behind defining the spectral weighting window are described in more detail below . the fitting algorithm continues by performing a chromophore fit in which the water absorption spectrum used is at the temperature determined by the previous temperature fit . after new chromophore values are determined , the temperature fit is repeated with the new chromophore values fixed and the algorithm is set in a loop that fits for chromophore values and follows with a temperature fit . the final temperature is determined when the difference between two consecutive fit temperatures is less than a fixed value which was set at 0 . 1 ° c . for the measurements presented in embodiment . this temperature fitting algorithm was insensitive to the initial guess of the chromophores and temperature and in all the measurements presented , the temperature fitting algorithm converged to a temperature within five iterations in the loop described . in order to determine the optimal spectral window for the weighting of the liquid phantom data , the data was processed by fixing the upper or lower bound of the spectral window at 1000 nm or 945 nm respectively . the opposite window position was then incrementally increased or decreased from a starting wavelength of 975 nm . for each spectral window , temperatures were recovered using broadband dos as described above . these recovered temperatures were then correlated and compared with the thermistor temperatures . fig1 a is a plot of the correlation coefficient ( r ) from the broadband dos vs . thermistor temperatures where the spectral window upper bound is fixed at 1000 nm and the lower bound of the window is varied from 975 to 935 nm . fig1 b is a plot of the mean temperature difference ( thermistor — dos ) between the two measurements and the standard deviation of the temperature differences over the same spectral window range . as the lower bound of the spectral window is increased the correlation of the temperatures increases and plateaus and the mean differences between the temperatures decrease and levels off . figs . a and 2 b are the same type of plots as shown in fig1 a and 1 b respectively except the lower bound of the spectral window is fixed at 945 nm and the upper bound is increased from 975 nm to 1015 nm . increasing the upper bound of the spectral window has similar effects to those in fig1 a and 1 b , namely the correlation increases and the mean error decreases . the above analysis of the weighted data led to the use of a spectral window between 935 and 1000 nm to be used for all the data presented in this chapter . fig1 a and 1 b illustrate that the lower bound wavelength of the spectral window should be below 950 nm and fig2 a and 2 b show that the upper bound wavelength of the spectral window should be above 985 nm . expanding the window to 935 and 1000 nm provided an overlap of the spectral region in which the bound water correction describe in merritt et al was implemented . fig3 is a plot of the temperature (° c .) vs . time of measurement ( minutes ) from data acquired on a liquid phantom . the black squares are the temperatures determined from the thermistor resistance and the error bars on the measurements are within the squares . the circles are the temperatures derived using broadband dos . the bws determined from the first measurement and applied in the fitting for all following measurements was 0 . 5 nm . for the case of the liquid phantom the molecular water binding is due to the water interacting with the emulsifying agent within the 10 % lyposin solution . taking the difference between the recovered broadband dos temperature and the measured thermistor temperature at all the points results in an average absolute difference of 2 . 0 ± 1 . 4 ° c . although the correlation is high ( r = 0 . 996 ) between the thermistor temperature and the broadband dos temperature , there is a relatively large difference between the values , nearly 5 ° c . at the peak temperature . the differences between the thermistor (▪) and the broadband dos (∘) temperatures in the liquid phantom measured in fig are linearly increasing with temperature . in order to investigate this effect further two additional liquid phantoms were measured on separate days over different temperature ranges . the temperature difference between the thermistor and broadband dos values are plotted for all three liquid phantoms in fig2 . for all phantoms , as the temperature of the phantom increases the difference between the thermistor temperature and the broadband dos temperatures increase at the same rate . the temperature at which the difference is minimized is around 30 ° c . for these phantoms . all phantoms had a 0 . 5 nm bound water shift correction implemented , but if this shift is increased to 1 . 5 nm the entire temperature difference curve is displaced downward , such that the temperature at which the difference is minimized becomes ˜ 50 ° c . therefore , the bound water shift correction only moves the curve in fig2 in the vertical direction , but does not change the slope . the liquid phantom data above provides an ideal case where the sample is homogeneous in composition and temperature as well as being mostly water , which is the source of the contrast in temperature . in order to provide a proof of principle for this technique to be used in vivo we now present data acquired on the animal model described above . as with the liquid phantom the spectral window used in the temperature fitting portion of the algorithm was examined . fig5 a and 5 b are the same type of plots as fig1 a and 1 b with data from the rabbit model substituted for the liquid phantom data . similar to the liquid phantom data there is a plateau that is reached for the correlation between the dos temperatures and the thermistor temperatures . also , the mean difference between the temperatures levels off and the standard deviation of the differences is relatively flat . the graphs in which the upper bound wavelength of the spectral window is increased are also similar to the data acquired on the liquid phantom . therefore , the same spectral window from 935 - 1000 nm was used for the analysis on the animal model data . fig6 is a plot of the temperature (° c .) vs . time of measurement for the data acquired on the animal model described above . here there are three values plotted : the broadband dos measurement (∘), thermistor # 1 (▪) placed ˜ 3 mm deep into the tissue and thermistor # 2 (▴) superficially placed directly under the skin . four baseline measurements were taken prior to sacrifice , which occurred at the point of the vertical dashed line on the plot . after the fifth measurement was taken ice packs were applied to the tissue surface and underneath the animal leg to cool down the tissue . broadband dos measurements tracked well with thermistor # 2 measurements prior to the application of the ice packs and then track better with thermistor # 1 temperatures . following the placement of the ice packs , the registered temperature begins to drop in both of the thermistor readings and the broadband dos measurement . thermistor # 2 , which was placed directly under the skin drops 10 ° c . directly after the ice packs were applied to the tissue . thermistor # 1 and the broadband dos readings both begin to drop in temperature at similar rates with a final temperature of 25 ° c . being reached after the ice packs had been applied for 40 minutes . the mean bws determined from the first four measurements and applied in the fitting for all following measurements was 1 . 5 ± 0 . 1 nm . taking the difference between the recovered broadband dos temperature and the measured thermistor # 1 temperature at all the points results in an average absolute difference of 0 . 7 ± 0 . 7 ° c . and the correlation between the temperatures was r = 0 . 989 . the thermistor reading in this case can only act as a guide for comparison with the broadband dos measurements , but is not actually the true tissue temperature over the entire broadband dos light field since the temperature in the animal model is more heterogeneously distributed . a second rabbit was measured for further validation ( see fig7 ). in this case the average bws measured for the five baseline measurements was 2 . 7 ± 0 . 1 nm . the same spectral window from 935 - 1000 nm was used for this rabbit for consistency . the difference between the recovered broadband dos temperature and the thermistor temperature of the 32 time points measured gave an average absolute difference of 0 . 4 ± 0 . 3 ° c . as seen in fig5 there is gap of data points missing directly following the sacrifice of the animal . during this time the thermistor , which was imbedded in the muscle came loose and a repositioning of the dos probe and thermistor was necessary . therefore , the measurements following death are probing a slightly different tissue volume , although the measurements were taken at approximately the same location . the correlation of the thermistor temperature and the broadband dos temperature for the second rabbit measurement was r = 0 . 995 . the temperature differences between the thermistor and broadband dos measurements for the animal model data are similar to the trends in the liquid phantom data . fig6 is a plot of the temperature differences in the liquid phantom presented in fig (▪) and rabbit hind - leg muscle data presented in fig4 (∘) and fig5 ( δ ). the data from the animal models is distributed along the curve that was initially observed for the phantom data . given that the temperature difference between all the samples changes in a systematic way following the bound water correction , a linear fit can be performed between the thermistor temperatures and the broadband dos temperatures to determine a linear correction for the broadband dos data . fig7 is a plot of the thermistor temperature vs . the broadband dos temperatures for all the measurements presented . the best linear fit to the data is given by the black line which is defined by the following equation : the correlation coefficient from the fit is r = 0 . 996 . applying this correction to the broadband dos temperatures gave an absolute difference between the measured temperature and corrected temperature of 0 . 68 ± 0 . 58 ° c . and 0 . 66 ± 0 . 56 ° c . for the liquid phantom and animal model temperatures respectively . the above disclosure describes a method for determining bulk deep tissue temperatures . from the motivation presented in the introduction and the preliminary in vivo results presented , this method is clearly useful for application to skin remodeling which could benefit from the measurement of skin as well as subcutaneous tissue temperatures . with the current algorithm an accuracy of 0 . 7 ± 0 . 6 ° c . for rabbit skin / muscle was achieved . through a better understanding of a water molecules interactions in a particular tissue type as well as larger numbers of measurements that could possibly be used as a calibration of the instrument , the accuracy in predicted temperature would be even better . the method is also applicable to any tissue including particularly to human breast tissue . compared to the phantoms and tissue investigated in this disclosure , a normal breast would be more challenging because of its lack of water . breast tissue has water content as low as 10 % by volume and therefore , the contrast of tissue temperature will be significantly reduced . the larger tissue volumes will also require tomographic capabilities in order to map out normal and tumor tissue temperatures . this will require a tomography system with broad spectral capabilities , which is entirely within the spirit and scope of the present invention . many alterations and modifications may be made by those having ordinary skill in the art without departing from the spirit and scope of the invention . therefore , it must be understood that the illustrated embodiment has been set forth only for the purposes of example and that it should not be taken as limiting the invention as defined by the following invention and its various embodiments . for example , vulnerable plaques are typically small lesions comprised of a lipid - rich core , surrounded by a thin , collagenous cap with varying degrees of smooth muscle cells . the vulnerable plaques form within the walls of cardiovascular vessels . the plaques may be characterized by a thickened arterial wall , partial stenosis , and generally elliptical distortion of the cardiovascular lumen with blockages ranging from zero up to about 70 %. stenoses are generally less severe with vulnerable plaques than stable plaques . however , mild stenoses are far more common and are responsible for more occlusions than tighter stenoses . vulnerable plaques may be differentiated by their size , shape and composition of their lipid cores and fibrous caps . acute lesions are larger with crescent - shaped cross - sections rich in extracellular lipid accumulation . the fibrous cap may be infiltrated with macrophages throughout , a precursor to initiating the disruption of the vulnerable plaque with mechanical strain or degradation of the wall thickness . the fibrous cap may fatigue and rupture from mechanical stresses , releasing macrophages and tissue factor leading to thrombosis . the cap may be compromised by the presence of inflammation and swelling . as a result , activated inflammatory cells release heat that , when detected , indicates the presence and progression of vulnerable plaque . the illustrated embodiment of the invention thus provides a method to measure intravascular temperature noninvasively . broadband diffuse optical spectroscopy ( dos ) is a non - invasive method used for quantifying absorption and scattering parameters of tissue over a broad wavelength range ( 600 - 2500 nm ). using broadband dos , endovascularly delivered via a catheter to a region of interest , to give an absolute measure of the tissues absorption , it is possible to determine the concentrations of the chromophores in the tissue such as oxy - and doxy - hemoglobin , water , fat in addition to reduced scattering coefficient which is related to the tissue matrix . the absorption profiles of these chromophores are temperature dependent and can therefore be used as temperature meters . fundamentally , what we are measuring is the vibrational energies of bonds within these chromophores and as tissue temperature changes these energies will change due to complex interactions of the chromophores as bonds are created and broken with other molecules . by characterizing how these tissue chromophores change with temperature we can then use broadband dos to measure tissue temperature . the invention can also be extended to encompass tomographic methods whereby two or three dimensional images of tissue may be generated using an array of scanning elements , each element measuring the absolute absorption of light at each pixel in the image according to conventional tomographic processing . therefore , it must be understood that the illustrated embodiment has been set forth only for the purposes of example and that it should not be taken as limiting the invention as defined by the following claims . for example , notwithstanding the fact that the elements of a claim are set forth below in a certain combination , it must be expressly understood that the invention includes other combinations of fewer , more or different elements , which are disclosed in above even when not initially claimed in such combinations . a teaching that two elements are combined in a claimed combination is further to be understood as also allowing for a claimed combination in which the two elements are not combined with each other , but may be used alone or combined in other combinations . the excision of any disclosed element of the invention is explicitly contemplated as within the scope of the invention . the words used in this specification to describe the invention and its various embodiments are to be understood not only in the sense of their commonly defined meanings , but to include by special definition in this specification structure , material or acts beyond the scope of the commonly defined meanings . thus if an element can be understood in the context of this specification as including more than one meaning , then its use in a claim must be understood as being generic to all possible meanings supported by the specification and by the word itself . the definitions of the words or elements of the following claims are , therefore , defined in this specification to include not only the combination of elements which are literally set forth , but all equivalent structure , material or acts for performing substantially the same function in substantially the same way to obtain substantially the same result . in this sense it is therefore contemplated that an equivalent substitution of two or more elements may be made for any one of the elements in the claims below or that a single element may be substituted for two or more elements in a claim . although elements may be described above as acting in certain combinations and even initially claimed as such , it is to be expressly understood that one or more elements from a claimed combination can in some cases be excised from the combination and that the claimed combination may be directed to a subcombination or variation of a subcombination . insubstantial changes from the claimed subject matter as viewed by a person with ordinary skill in the art , now known or later devised , are expressly contemplated as being equivalently within the scope of the claims . therefore , obvious substitutions now or later known to one with ordinary skill in the art are defined to be within the scope of the defined elements . the claims are thus to be understood to include what is specifically illustrated and described above , what is conceptionally equivalent , what can be obviously substituted and also what essentially incorporates the essential idea of the invention .
a method for noninvasively determining deep tissue temperature comprises measuring data relating to spectral shifts of chromophore absorption in tissue using broadband diffuse optical spectroscopy and generating a temperature reading corresponding to the spectral shift of an absorption peak of the chromophore . a bound water correction is made to the spectral shift . a frequency domain measurement at multiple wavelengths is made to determine the absolute absorption and scattering values between 600 and 1050 nm . the measurement of an absolute absorption comprises measuring an absolute absorption coefficient of selected tissue and further comprising deducing concentrations of tissue composition including lipids , deducing information related to heterogeneity and integrity of tissue matrix , and deducing temperature heterogeneity related to vulnerable plaque in vascular tissue . the measurement comprises making a measurement in the range of 600 - 1100 nm to interrogate a vessel wall in the presence of blood .