WO2001039665A2

WO2001039665A2 - Method and apparatus for noninvasive assessment of skin condition and diagnosis of skin abnormalities

Info

Publication number: WO2001039665A2
Application number: PCT/US2000/032682
Authority: WO
Inventors: Joseph Chaiken; Charles M. Peterson; Karen P. Peterson
Original assignee: Lightouch Medical, Inc.
Priority date: 1999-12-03
Filing date: 2000-11-30
Publication date: 2001-06-07
Also published as: AU1938401A; US6352502B1; WO2001039665A3; US6681133B2; US20020091322A1

Abstract

Disclosed is a method for obtaining feedback to drive a servo system for aligning and maintaining alignment in optical systems that bring light to an in vivo skin sample, for adjusting the focus of the optical system, and for adjusting the net depth of focus of the optical system within the in vivo system under characterization. The invention additionally provides a method for obtaining feedback to drive a servo system for aligning and maintaining alignment in optical systems that collect light from an in vivo skin sample, and for adjusting the focus of the optical system. These methods comprise adjusting the angle of incidence of electromagnetic radiation and/or providing a shielding lens to block scattered incident light, or otherwise limiting the field of view of the Raman scattered radiation collection system to exclude optical surfaces of the excitation delivery portion of the optical system. Also provided is a method for identifying spectroscopic depth markers in tissues. In one embodiment, the method comprises discriminating between Raman signals originating on outer portions of skin from signals originating from substances deeper within the skin or other tissues. In another embodiment, the invention provides a method for detecting skin abnormalities and for assessing the aging of skin and related tissues. The method comprises characterizing the content of the skin using Raman spectroscopy. In one embodiment, the collagen, elastin, and or keratin content of the skin is characterized.

Description

METHOD AND APPARATUS FOR NONINVASIVE ASSESSMENT OF SKIN CONDITION AND DIAGNOSIS OF SKIN ABNORMALITIES

TECHNICAL FIELD OF INVENTION

The invention relates to a method and apparatus for qualitative or quantitative nomnvasive assessment of the metabolic and structural components of skin and nearby tissues using Raman spectroscopy. The invention relates to maintaining depth and position of focus of a Raman excitation source, regardless of whether an imaging light collection system is used. This system also provides first order servo correction for automatic focusing of an imaging system. The invention additionally relates to identifying spectroscopic depth markers in tissues, and to detecting skin abnormalities and assessing the aging of skin and related tissues.

BACKGROUND OF THE INVENTION

There has always been a need for reliable and precise quantitative methods and associated apparatus for diagnosing medical abnormalities and for assessing the general condition of body tissues. While any approach that offers early and reliable warning of medical problems has some utility, nomnvasive methods offer many advantages. Anticipation by a patient of pain and scarring associated with invasive procedures can cause delays in seeking medical attention. There is also a myriad of inconveniences, risks and difficulties associated with direct collection and contact with patient body fluids. For these reasons, there has been intense scientific and engineering research into devising nomnvasive approaches to assessment and diagnosis of medical conditions.

Use of spectroscopic methods, while of considerable use in direct in vitro apphcation to fluids, has not found equal in vivo application. In vivo sampling is substantially more complicated for a variety of reasons, although some of the challenges can be handled by reference to in vitro procedures. First, even in vitro procedures require at least some sample preparation before spectroscopic interrogation. But in vivo samples cannot be handled with nearly the ease of in vitro samples. All chemometnc analyses benefit from the availability of samples having known composition of various analytes. Selectively modulated in vitro samples are much easier to synthesize or otherwise obtain than in vivo samples. Thus, samples for chemometnc interpretation of in mvo samples can be expected to require specialized approaches to sample preparation and specifically designed methods for obtaining modulated samples of known composition Long data collection times are needed to extract small signals from some samples, but in vivo sampling requires the patient to endure the waiting. Prolonged data collection is not always practical. Moreover, applying too much excitation light to m vivo samples can lead to catastrophic results.

Nomnvasive in vivo chemical analysis of human and animal tissues has long been a goal of chemists and the medical community. Blood oximetry is an example of a nomnvasive form of analysis that is now ubiquitous in intensive care and other situations.

Nomnvasive techniques involve contacting the tissue in question with some form of electromagnetic radiation, and detecting the effect of the contact on the radiation. The frequency range of the radiation and the choice of tissue to contact, determines the type of structural, concentration or other physico-chemical information that is available.

The optics of human skin have been extensively reviewed. The interaction with visible light contacting blood in the capillary beds _just beneath the epidermis of human skin can be exploited to estimate the oxygen content of blood, thereby giving a quantitative measure of the condition of the patient's respiratory and cardiovascular systems, ι.e. blood oximetry. The present invention is directed to assessing the condition of the skin at the molecular and supramolecular scale, making vibrational spectroscopy an ideal probe.

SUMMARY OF THE INVENTION

The invention provides a method and apparatus for obtaining feedback to dnve a servo system for aligning and maintaining alignment in optical systems that bring light to an in vivo skin sample, for ad_justing the focus of the optical system, for ad_justing the net depth of focus of the optical system within the in vivo system under characterization, and for dnving a tissue-directed search and mapping algonthm. The invention additionally provides a method and apparatus for obtaining feedback to dnve a servo system for aligning and maintaining alignment in optical systems that collect light from an in vivo skin sample, and for adjusting the focus of the optical system. These methods comprise adjusting the angle of incidence of electromagnetic radiation and/or providing a shielding lens to block scattered incident light, or otherwise limiting the field of view of the Raman scattered radiation collection system to exclude optical surfaces of the excitation delivery portion of the optical system.

Also provided is a method and apparatus for identifying spectroscopic depth markers in tissues. In one embodiment, the method compnses discnminating between Raman signals onginating on outer portions of skin from signals onginating from substances deeper within the skin or other tissues. In some embodiments, these methods compnse selecting optics for Raman detection to maximize one or more Raman features corresponding to lrpids and proteins of the skin.

The invention provides a method and apparatus for obtaining spectroscopic information from living tissue of a subject. In one embodiment, the method compnses irradiating a tissue of interest in a subject with light having an excitation wavelength and that passes from a light source through a first adjustable lens, and passing spectra that are emitted by the tissue through a second adjustable lens. The spectra that are passed through the second adjustable lens are then collected and analyzed to determine a target signal associated with an analyte of interest. The method further compnses denving a correction signal from the target signal, and adjusting the position of the first adjustable lens or the second adjustable lens on the basis of the correction signal so as to enhance the target signal. In a preferred embodiment, the spectra are Raman spectra. The method can optionally further compnse selectively dispersing a target wavelength of the collected spectra pnor to analyzing the collected spectra. Preferably, the dispersing compnses filtering out wavelengths other than the target wavelength, or passing the collected spectra through a spectrograph.

In another aspect, the invention provides a non-invasive method and apparatus for spectroscopically probing and mapping a target layer of skin in a sub_ject. The method comprises irradiating a target layer of skin in a sub_ject with light having an excitation wavelength that passes from a light source through a first ad_justable lens, passing spectra that are emitted by the tissue through a second ad_justable lens, and collecting spectra that are passed through the second adjustable lens. The method further compnses analyzing the collected spectra to determine a target signal associated with the target layer of skin, and ad_justing the position of the first adjustable lens or the second adjustable lens so as to increase the target signal. Optionally, the method further compnses denving a correction signal from the target signal and relaying the correction signal to the first adjustable lens or to the second adjustable lens, wherein the correction signal effects an ad_justment of the first ad_justable lens or the second ad_justable lens. In one embodiment, the method and apparatus include an adjustable aperture, such as one or more inses, as in a confocal microscope, positioned between the skin and the light collection system A correction signal denved from the target signal is then used as feedback to the adjustable aperture to optimize the collection of spectra from the target layer of skin.

In another aspect, the invention provides a method and apparatus for spatial mapping and detecting abnormalities in living tissue of a subject. The method compnses irradiating a tissue of interest in a subject with light having an excitation wavelength and that passes from a light source through a first adjustable lens, passing spectra that are emitted by the tissue through a second adjustable lens, and collecting spectra that are passed through the second adjustable lens. The method further compnses analyzing the collected spectra to determine a target signal associated with a tissue feature indicative of an abnormality, denving a correction signal from the target signal, and adjusting the position of the first adjustable lens or the second adjustable lens on the basis of the correction signal so as to enhance the target signal. In one embodiment, the tissue of interest compnses skin. Other examples of tissues of interest include, but are not limited to, stratum corneum, epidermis, intradermal capillary beds, and dermis.

The invention further provides a method and apparatus for stabilizing a wavelength and/ or amplitude of light emitted by a diode laser The method compnses irradiating a specimen with excitation light from the diode laser, and collecting Raman spectra at a target wavelength emitted by the irradiated specimen, wherein the target wavelength is associated with a strong feature in the specimen. In one embodiment, the target wavelength is associated with silica, as present in the optical path, such that an optical element within the system serves as the irradiated specimen. The target wavelength associated with silica is a wavenumber shift of about 1003 cm ¹ from the excitation wavelength. The method further compnses determining a quantity of spectra emitted at the target wavelength, relaying to the diode laser a signal proportional to the determined quantity, and regulating the temperature of the diode laser so as to maintain a maximal spectra emitted at the target wavelength.

In another embodiment, Raman spectra are collected at two or more wavelengths: at least one positive target wavelength associated with a strong feature in the specimen, and at least one a negative target wavelength associated with a weak feature in the specimen. The method further compnses determining a quantitative difference between the spectra emitted at the positive target wavelength and the spectra emitted at the negative target wavelength, relaying to the diode laser a signal proportional to the determined difference, and regulating the temperature of the diode laser so as to maintain a maximal difference between the spectra emitted at the positive target wavelength and the spectra emitted at the negative target wavelength. In a prefened embodiment, the specimen is skin, the positive target wavelength is a wavenumber shift of about 2940 or 1665 cm^-1 from the excitation wavelength and the negative target wavelength is a wavenumber shift of about 2800 or 1775 cm^-1, respectively, from the excitation wavelength.

The method can be performed non-invasively on living tissue. Optionally, the method further compnses adjusting the position of a first ad_justable lens located in the optical path of the excitation light so as to increase the determined quantity of the spectra emitted at the target wavelength, or the difference between the spectra emitted at the positive target wavelength and the spectra emitted at the negative target wavelength, and/or likewise adjusting the position of a second ad_justable lens located in the optical path of the emitted spectra so as to increase the determined quantity of spectra or difference between the spectra emitted at the positive target wavelength and the spectra emitted at the negative target wavelength.

In another embodiment, the invention provides a method and apparatus for assessing the aging of skin and related tissues. The method compnses characterizing the content of the skin using Raman spectroscopy as descnbed above. The aging of skin is related to morphological changes in the tissues on a spatial scale of 10-10,000 microns which can be mapped at very early stages of their development using the method of this invention These morphological changes, ι.e. wrinkles, may or may not be associated with chemical vanations. These changes are purely physical and may be precisely mapped using the method of the invention. In one embodiment, the collagen, elastin, and/or keratin content of the skin is characterized. In another embodiment, the size and location of fat deposits is characterized.

In another aspect, the invention provides an apparatus for enhancing spectroscopic information obtained from living tissue of a subject. The apparatus compnses a signal analyzer adapted to receive input from a detector and a processor connected to the signal analyzer, wherein the processor is capable of producing an output signal that is proportional to a quantity of Raman spectra received by the signal analyzer from the detector. The output signal can be directed to a diode laser for regulating the temperature of the diode laser, thereby stabilizing the wavelength and/or amplitude of hght emitted by the diode laser and focused onto the living tissue to be spectroscopicaUy probed. The output signal can also be directed to an adjustable lens, either a first adjustable lens used to focus the hght onto the living tissue, or a second adjustable lens used to collect Raman spectra scattered by the living tissue.

Alternatively, the output signal can be directed to an adjustable aperture, such as an ins in a confocal microscope. The adjustable aperture can be coupled to an electronically controlled translation stage that is connected to the processor and optically aligned with an input path to the detector, wherein the output signal regulates movement or diameter of the adjustable aperture along or perpendicular to an optical axis aligned with the input path of the detector. The apparatus provides a feedback system for optimizing the quahty and the focusing of the spectroscopic system, and provides connections between data processors and translation stages that control the positions of optical elements in a device.

BRIEF DESCRIPTION OF THE DRAWINGS

Figure 1 is a schematic illustration of an apparatus 100 for use in accordance with one embodiment of the invention for spectroscopic probing of skin 102.

Figure 2 is a schematic representation of a simple confocal, four-lens system for combining depth discrimination with spectroscopy. Figure 3 is a plot of background-corrected spectral counts at wavenumber shifts of 600- 1800 for 3 different samples: an in vitro blood sample; an in vivo blood sample; and a NaCl pellet.

Figure 4 is a flow chart representing a scanning method according to the invention.

Figure 5 is a flow chart representing a depth profiling method according to the invention

DETAILED DESCRIPTION

The method and apparatus descnbed herein allow detection of molecular "fingerprints" associated with vanous structural and metabolic components of the skin and nearby tissues via non-invasive spectroscopy. In some cases such "fingerpnnts" reveal abnormahties of the skin. Such fingerprints will often be useful in revealing the general condition of skin. The method provides for quantitation of moisture content, total callus content as well as protein, hpid and carbohydrate content In one embodiment, collagen, α-keratui, β-keratin, elastin, mucopolysacchandes, neutral hpids, polar hpids, ceramides, and/or cholesterol sulfate are assessed. The degree of skin oxidation and protein cross- linking via disulfide, linkages can also be assessed.

The method of the invention also provides for using the detected spectra to feedback and regulate the output of the hght source as well as to regulate the positioning of focusing and collecting lenses, and the positioning of an ins in a confocal microscope This feedback system allows the method to be performed with simpler, less expensive lasers, and without requiring the use of fiber optics. Not only does the invention avoid the need for lasers having elaborate and expensive temperature regulating systems, it also avoids the need for more complicated and expensive feedback systems for adjusting the focus of the apparatus. The apparatus of the invention removes unwanted incident hght and sets the focal plane via filtering and simple electronics. Because the feedback system of the invention relies on chemical information rather than image data, it does not require use of a CCD camera, for example, in the feedback loop.

The method also allows for ad_justments to accommodate movement by the subject. In addition, the method and apparatus of the invention can be used in combination with other techniques, such as magnetic resonance imaging (MRI), confocal optics, and the use of chemical markers or labels (e.g., deutenum). Moreover, combination of the method with MRI can be done without introducing metal.

Definitions

All scientific and technical terms used in this apphcation have meanings commonly used in the art unless otherwise specified. As used in this apphcation, the following words or phrases have the meanings specified.

As used herein, "Raman spectra associated with" a given component refers to those emitted Raman spectra that one skilled in the art would attnbute to that component. One can determine which Raman spectra are attnbutable to a given component by irradiating that component in a relatively pure form, and collecting and analyzing the Raman spectra emitted by the component in the relative absence of other components. Those skilled in the art are aware of available hbranes that catalog known Raman spectra.

As used herein, to "enhance a target signal" means to increase the quantity or quahty of a target signal having a wavelength associated with an analyte of interest relative to the quantity or quahty of a non-target signal having a wavelength not associated with the analyte of interest.

As used herein, a "strong" feature is a Raman feature that results in one scattered wavelength-shifted photon per 10⁴-10⁶ incident excitation photons. Where the Raman features have been resonance enhanced or surface enhanced, strong features can result in one scattered wavelength-shifted photon per 10 -10⁶ incident excitation photons.

As used herein, a "weak" feature is a Raman feature that results in one scattered wavelength-shifted photon per 10⁸-10⁹ incident excitation photons.

As used herein, "wavelength dispersion" means spatially separating signals of individual wavelengths within a group of wavelengths. Such dispersion can be achieved with, for example, a spectrograph or use of one or more filters.

As used herein, "tissue" means any portion of an organ or system of the body, including, but not limited to, skin, capillary beds, blood, muscle, breast and brain. As used herem, unless context clearly indicates otherwise, "a" or "an" means at least one, and can include a plurality.

The invention descnbed herein is based on the discovery that Raman scattering can be used noninvasively to obtain quantitative information concerning skin and nearby tissues As disclosed herem, the methods and apparatus used to obtain Raman spectroscopic data can be adapted for apphcation to skin and other in vivo samples. This intradermal excitation provides an objective approach to skin characterization.

Raman Spectroscopy of Skin

To perform absorption based vibrational spectroscopy, the use of infrared radiation to obtain quantitative information is limited by the transmission properties of the tissue. There is considerable Mie scattering, spatial inhomogeneity, and tortuous interfaces permeating tissues and organs, making quantitation of path length problematic and complicating, if not invalidating, the applicability of Beer's Law. Moreover, absorption limits the amount of hght that can be employed. The availability of adequate infrared lasers or adequate incoherent hght sources is limited. Optical contact with the skin or other tissue can be made using either waveguide, i.e. evanescent wave, or direct contact.

In large part, moisture content of a naturally hydrated biomembrane, such as stratum corneum, makes direct infrared absorption/reflectance spectroscopy problematic, l e. difficult to execute reproducibly, regardless of how the hght contacts the skin. For example, stratum corneum is typically about 10 μm thick, but can swell to several times that thickness when wet. This vanation in density affects hght propagation in a way that poses non neanty problems. Raman spectroscopy, on the other hand, is much less affected by water, and so is often the method of choice for wet samples.

On the other hand, Raman scattering is a comparatively weak process and, given the peculiar optical properties of human tissue, a novel approach is required to actually obtain meaningful in vivo spectra. There must be control of blood flow, or some type of compensation in the data analysis for whatever form of tissue modulation is employed Local pressure and temperature can have a dramatic effect on the blood volume of the intersection between the irradiation zone and the collection zone. Described herein is a system to maintain focus of the combined excitation and collection systems at the desired position on or within the skin or surrounding tissues. To this end, an approach has been devised to allow a nonimaging optical system to establish a feedback loop and thereby a servo system for maintaining the position and the depth of focus of the Raman excitation source as the sample is moved. The same approach can work equally well to maintain the optimal configuration of the hght collection system as well.

The method disclosed herein allows such spectroscopic data to be collected with greater efficiency, greater selectivity, and ultimately, higher signal to noise. Contrary to the teachings of other processes, real lasers lack the spectral punty required to forego the need for extensive blocking of the Rayleigh scattered hght from the Raman detector. Raman scattering is actually quite weak when not resonance enhanced, and adequately shielding the detector from the blinding effects of the incident hght is required to observe quantitative results from in vivo Raman scattering and utilize the full dynamic range of any detector.

Part of the necessary blocking can be achieved by contacting the skin with the laser hght at an appropnate angle and by properly onenting the observation system The remaining reduction can be achieved by specifying that there can be no optical surface of the excitation delivery part of the optical system that is within the direct field of view of the Raman scattered radiation collection system. The field of view is designated such that it does not include objects visible because of hght reflected from the skin surface.

The methods and apparatus disclosed herein overcome the challenges presented by spectroscopic probing of in vivo tissues by providing for regulation of lens and aperture positions and excitation wavelength output. Target spectra for obtaining information about skin and tissue contents have been identified m the literature. Edwards et al., 1995, J. Molecular Structure 347:379-388; and Carter et al, 1998, SPIE 3257:72-77, descnbe Raman features of interest to dermatological diagnostics. Lawson et al., 1997, J Raman Spectroscopy 28:111-117 describes Raman spectra associated with cancers, tumors, DNA, stratum corneum, hair and nails Tu, 1982, Raman Spectroscopy in Biology: Principles and Applications, Chap. 5:134-149, describes Raman features associated with nucleic acids and inorganic phosphate. Spectroscopic Depth Markers

Beyond the considerations noted above, there is a need for spatial stability in the excitation and hght collection systems. The structure of the stratum corneum, epidermis, and dermis layers has a chemical and physical complexity on a spatial scale of tens to hundreds of microns. Wrinkles represent physical complexities on a larger scale. Failure to fully consider this compositional and physical heterogeneity leads to an inability to distinguish between the sources of the vibrational spectroscopic signals. It is therefore desirable to identify and utilize inherent spectroscopic depth markers. This overcomes difficulties in obtaining adequate contrast, which is a limiting factor in the use of standard in vivo scanning confocal microscopy of human skin (Ra_jadhyaksha et al., 1995, J. Invest. Derm. 104(6):946-952).

It is known that there is a strong Raman feature centered near 3000 cm^-1 corresponding to the -C-H stretching motions of the hpids and proteins in the skin. This feature is sufficiently removed from the Rayleigh line that it can be utilized for the depth-marking purpose mentioned above. Other features known to be associated with epidermis, dermis, subdermal fat or capillary beds can be used as depth markers. For example, more information associated with a particular analyte found m the epidermis than in deeper layers suggests that the subject acquired the analyte via touch. In contrast, higher levels of analyte associated with subdermal fat than with epidermis would be indicative of acquiring the analyte by lngestion.

Using a simple filter to isolate the signal from other Raman/fluorescence/source contamination (e g unwanted amplified spontaneous emιssιon(ASE)), the excitation system focusing optics can provide this signal to a microprocessor to provide feedback for servo control. In one embodiment, a graph of total Raman (inelastic) hght scattered shows that this observable measure is sensitive to the position of the excitation focusing and so filtering can be used for signal isolation. In another embodiment, the optics can be adjusted to maximize the entire 3000 cm Raman feature. This provides a first order method for optimizing the parameters of the hght collection and excitation systems

The shape of this same Raman feature vanes with depth below the stratum corneum The composition of the 3000 cm^-1 Raman feature vanes with composition, and so can be used to lock onto a particular depth of focus for the excitation and/or for the collection optics The greater the depth, the more the Raman feature is composed of longer Raman shifts There are also other Raman features between 1000-1800 cm^-1 that can be equally useful for obtaining depth information.

Apparatus

Figure 1 is a schematic illustration of an apparatus 100 for use in accordance with one embodiment of the invention for spectroscopic probing of skin 102. The apparatus 100 can be directed at the stratum corneum 104 at the skin 102 surface, or at progressively deeper layers, including epidermis 106, capillary beds 108 and dermis 110. A laser 112 emits excitation hght along an optical path 114 that is focused onto the skin 102 via a first adjustable lens 116 Scattered hght emitted by the skin 100 travels along an optical path 118 through a second adjustable lens 120 to a wavelength dispersion element 122. Wavelengths of hght passing through the dispersion element 122 are converted to electronic signals by a detector 124, the output of which goes to a signal analyzer 126 and then to a processor 128 that denves a correction signal 130 that returns to the laser 112, the first adjustable lens 116, the second adjustable lens 120 and/or an ad_justable aperture 240, as shown in Figure 2. The correction signal 130 can relate to, for example, wavelength, spatial onentation, alignment of optical elements and/or depth selection. Motorized translation stages and controllers, such as the Newport 860-C2 controller and the 860A dnve (Newport Inc., Irvine, CA), can be easily integrated into closed loop applications for adjusting position of lenses 16, 120 and apertures 240

The laser 112 can be a 785 n , amplitude and wavelength stabilized, external cavity, CW laser 500, (SDL XC-30; SDL Inc., San Jose, CA) or similar laser such as a PI-ECL-785- 1000-FHP (Process Instruments, Inc., Salt Lake City, UT), producing a maximum total power of 300-700 mW. In the case of the SDL laser, more than half of this power is associated with a large, spectrally wide and unsymmetncal base of amplified spontaneous emissions (ASE) This is adequate to obtain Raman spectra of simple, less challenging samples, l e virtually any in vitro sample To obtain acceptable in vivo spectra, however, a substantial amount of the ASE should be removed. This is done using a holographic bandpass filter (Kaiser Optical Systems, Ann Arbor, MI). While this does not remove all of the disturbing background radiation, it is adequate to allow in vivo spectra to be obtained. Alternatively, ASE can be removed by using a dielectnc filter (Omega Optical, Brattleboro, VT; CVI, Tucson, AZ). The Process Instruments laser contains much less ASE, and so a dielectnc filter is adequate to allow in vivo Raman signals to be observed

Optics for correcting the spatial arrangement of the fast and slow axes of the laser divergence, as well as for obtaining the optimum polarization for diffraction efficiency and background reduction in the fl.4 holographic spectrograph 122 eventually allow us to bnng only about 50-300 mW of laser power to the sample 102. The spectrograph 122 can be a Holospec (Kaiser Optical Systems, Ann Arbor, MI) or other available spectrograph (e.g., from Process Instruments, Salt Lake City, UT). All optics are antireflection coated for 785 nm and a 13 cm focal length lens 116 is used to finally bring the hght to the tissue 102 in question. An angle of mcidence of approximately 53° gives acceptable results.

The hght collection system uses two 50 mm fl.4 Nikon camera lenses, a holographic notch filter (Kaiser Optical Systems, Ann Arbor, Ml) and a Polacor™ (Corning) polarizer to bnng the scattered hght from the sample 102 to the entrance of the spectrograph 122. Alternatively, properly anti-reflection-coated (performed by CVI, Tucson, AZ) high punty fused sihca single element lenses (Corning HPFS 7940 or 7980, Corning, NY) can be used in place of camera lenses, with the benefit of increasing total throughput and reducing a large amount of unwanted fluorescence from optical elements.

The detection system 124 is an IR enhanced, liquid nitrogen cooled CCD array (LN/CCD-1024-EHRB/l, Princeton Instruments, Inc., Trenton, NJ). The resolution of the spectrograph system is 6 cm^-1 with wavenumber accuracy of 6 cm using a calibration based on known lines in atomic emission spectra. Standard computer equipment can be used for the signal analyzer 126 and processor 128 (e.g., parallel, senal, interface cards, A/D and D/A converters).

The invention provides an apparatus for enhancing spectroscopic information obtained from living tissue of a subject, and for searching for and mapping specific types of tissue The apparatus compnses a signal analyzer adapted to receive input from a detector and a processor connected to the signal analyzer, wherein the processor is capable of producing an output signal that is proportional to a quantity of Raman spectra received by the signal analyzer from the detector. The output signal can be directed to a diode laser for regulating the temperature of the diode laser, thereby stabilizing the wavelength and/ or amplitude of hght emitted by the diode laser and focused onto the living tissue to be spectroscopicaUy probed The output signal can also be directed to an adjustable lens aperture, either a first adjustable lens used to focus the hght onto the living tissue, or a second adjustable lens or an adjustable aperture used to coUect Raman spectra scattered by the living tissue. The apparatus provides a feedback system for optimizing the quahty and the focusing of the spectroscopic system.

Figure 2 shows a schematic representation of a confocal, four-lens system adapted for depth discrrrnination Such a system can be used to determine the depth of a signal emitted by tissue that is spectroscopicaUy probed. Determination of the depth of a source of emitted hght permits identification of the type of tissue, e.g., skin, blood, and of the type of hpid, e g., hpid, phosphohpid, sphingohpid. In particular, the system mcludes an adjustable aperture, or confocal ins 240, that can be adjusted along the x, y and z axes as weU as the diameter to vary the field of view and depth information The adjustment of the aperture 240 can be electronicaUy controUed by a translation stage receiving a correction signal that is sent out by a processor on the basis of wavelength information coUected by the detector.

With reference to Figure 2, hght is directed from a laser source (SDL-XC30) 200 to a penscope 202, then through a 4 meter lens 204, a half-wave plate 206, in ins 208, a metal/dielectnc filter 210, a holographic bandpass filter 212, a second periscope 214, a second half-wave plate 216, a second ins 218, a series of three mirrors 220, 222, 224, and a focusing lens 226, before arnvmg at the tissue, which is positioned in the sample holder 228 (tissue modulation device). Light emitted by the tissue passes through a camera lens 230 and on to a pellicle 232, which directs some of the hght to a CCD imaging camera 236 after passing through a lens 234. The remaining hght from the tissue is directed through a second camera lens 238, a confocal ins 240, a third camera lens 242, a polarizer 244, a holographic notch filter 246, and a fourth camera lens 248, before the hght enters the holographic spectrograph 250 having a hght coUection efficiency of f=1.4, to which is coupled a CCD detector 252. Wavelength Stabilization

In recent years, near infrared lasers have become increasingly attractive as excitation sources for Raman spectrometers. Because of their high continuous wave (CW) powers, smaU size, relatively low cost, mass manufacturabihty and abihty to produce Raman spectra across the region of maximum sensitivity of silicon based detectors, such lasers have many ideal properties as Raman excitation sources. Near infrared lasers are particularly weU-suited to biomedical apphcations because of their overlap with the spectral region of minimum absorbance and maximum transmission through human tissues.

Vanous schemes are utilized to minimize laser bandwidth and maximize power. Incorporation of the laser diode into an external resonant cavity produces, in many respects, a nearly ideal excitation source at the expense of increasing size, cost and optomechamcal complexity. It would be advantageous for many apphcations to be able to reduce the cost, physical complexity, and size of the excitation source.

No matter what scheme is employed, diode lasers require some form of external temperature stabilization. ThermaUy induced cavity length vanation causes a corresponding vanation of the output wavelength. Thermistor and thermocouple sensors are typicaUy employed in combination with thermoelectnc transducers to momtor and actively stabilize the temperature of diodes. The abihty to regulate the temperature limits the abi ty to stabilize the wavelength and amplitude.

Averaging Raman spectra coUected over penods of time exceeding the time required for the laser output wavelength to dnft a typical amount results in an effective loss of spectral resolution. That is, wavelength stabilization based on independent temperature stabilization is barely adequate for certam Raman based apphcations because some of the spectral bandwidth and the residual wavelength fluctuations can exceed the difference in s aU Raman shifts. The independent temperature based approach requires recahbration as the diode and transducers age and their charactenstics change, e.g. the relation between output wavelength and temperature dnfts. Having a method and apparatus for maintaining wavelength stability in the excitation source that drifts with the laser as it ages would increase the useful lifetime of the laser.

One could simply insert some type of internal standard into the optical system that generated a Raman signal that could be used for feedback to stabilize the excitation wavelength or amphtude. However, for many biomedical apphcations requiring a smaU, inexpensive, portable Raman based, near infrared monitoring device, as weU as those using larger, nonportable devices, one cannot easily incorporate extra detectors or wavelength coUection and analysis hardware due to the increase in system overhead. Even if a separate detector must be used, a simple, inexpensive detector with an optical system of minimal complexity is desirable. The invention provides a stabilization method in which a Raman signal is denved from a matenal that must be in the optical tram for other reasons. For example, certam glass optical elements generate both fluorescence and Raman signals that can be used for stabilization.

Monitoring the strong, spectraUy sharp Raman signal of sihca at about 1003 cm^-1 produces an exceUent feedback signal for wavelength and amphtude stabilization. The strength and appearance of this signal is correlated with the laser wavelength and the laser amphtude. A window or lens can be used in the optical tram that produces a strong silica Raman band, but low fluorescence, such as Corning HPFS 7940 or 7980. For example, from the excitation focusmg lens, wavelength stabilization and amplitude stabilization information can be extracted usmg either the same multichannel detector as is used to coUect the sample Raman signals, m the context of a multichannel device, or, in the context of a smaU portable instrument, by including one more single channel detectors and one or more appropnate filters.

Another solution is to utilize the Raman signal from the samples themselves. Consideration must be given to what types of signals are sought. In the case of nomnvasive spectroscopic probing of in vivo human tissue, there will always be signals from the tissues themselves that can be used. In particular, the stratum corneum is the source of a strong Raman feature at 1650-1670 cm ¹ due to the proteins keratin, elastin and coUagen. This signal is typicaUy about as broad spectraUy as a multimode diode laser output, 50 cm^-1, and is sufficiently strong to aUow easy coUection of sufficient signal to provide the necessary feedback. Perhaps the best Raman feature for this purpose is the 2900-3000 cm ¹ feature attnbutable to C-H stretching vibrations.

A method for usmg this Raman signal as feedback for wavelength stabilization comprises illuminating the tissue with a focussed beam of diode laser radiation at wavelength λ. This produces scattered radiation that is gathered by a coUection lens and directed to an entrance of a detection system. The detection system counts the number of Raman shifted photons for a penod of time, caUed the "counting penod". In the context of a multichannel apparatus, the scattered radiation is passed through a spectrograph, which disperses the radiation across the detector face (e.g., CCD) producing a set of scattered wavelength shifted photon counts as a function of wavelength shift. In the context of a single channel detector, the coUected photons are passed through a filter that transmits only photons in the appropriate wavelength shifted spectral region, and these are detected by a detector like an avalanche photodiode, a photomultipher or possibly in some cases even a PIN diode. Before an automated feedback cycle begins, the entire system (laser wavelength, detection charactenstics, positions of excitation focusmg lens and scattered radiation coUection lens) is viewed as manuaUy configured to produce an optimal signal.

The multichannel detector controUer (computer) is programmed to automaticaUy compare the number of shifted photons, e.g., at a Raman shift of 2950 cm ¹, with the number obtamed (at the same shift) dunng the previous counting penod. If the number is the same, within a present tolerance range, then the controUer sends a signal to the thermoelectnc cooler to maintain the same temperature. If the number has decreased, then the controUer sends a different electronic signal to the thermoelectnc cooler associated with the diode excitation laser. This electronic signal causes the cooler to mcrease or decrease its coohng. If, at the end of the next penod, the number of shifted photons at a Raman shift of 2950 cm ^J is less than the number before, then the diode temperature was not adjusted m the correct direction (ι.e. made too cold or too hot) and a signal is sent out to decrease or mcrease the coohng, as appropnate. At the end of the next counting penod, the photon numbers are compared again, and if the number is increasing, then the direction of coohng or heating is maintained until a subsequent counting penod produces the same or a decreased signal. The cycle delineated above can be continued for as long and as often as one cares to make measurements. The amount of the cooling/heating signal sent to the thermoelectnc device can be either a direct companson of Raman counts from counting during successive penods, i.e. the "denvative" signal itself, or it can be proportional to both the difference between the counts obtamed m successive counting periods and the difference between the two succeeding differences (i.e. the second denvative). In this way, it is possible to maintain the wavelength and amphtude stability of a less expensive and bulky laser system usmg the Raman signals themselves for feedback.

Focusmg and CoUection Lenses

Similarly, it is possible to maintain the onentation and ahgnment of the coUection and excitation lenses 120, 116 m the optical system 100 as the subject moves, or as other factors in the measurement system change. In this case, the feedback is again derived directly from the Raman signals as above (denvatives or second denvatives), but now the positions of the two lenses 116, 120 are adjusted to obtain a stable signal. The feedback signal can be fed to translation stages that control the position of each lens independently. Assuming an actively wavelength and amphtude stabilized laser system, e.g., utilizing the method descnbed above, one momtors a Raman feature that can be easily observed and can be identified with a specific layer of the tissue in question, such as stratum corneum, epidermis, or dermis. These features occur in the C-H stretching region, ι.e. 2920-3100 cm ¹ or m the protein regions, ι.e. 1645 cm , associated with keratin, elastin, coUagen, or in the 1445 cm ¹ region, associated with fats, i.e. adipose tissue.

Wavelength adjustments and lens position adjustments can occur in any order, but not simultaneously. That is, s ce the wavelength stability is mdependent of the spatial adjustments, it is necessary to optimize the diode properties for the positions of the two lenses being constant. After diode wavelength and amphtude stabilization is complete (for at least one cycle, aU other factors being constant), then the processor can perform the lens and aperture adjustments.

Two exemplary situations m which the methods and apparatus of the invention are apphcable clude a biopsy situation and a scanning situation. In the first situation, the sample of mterest is being biopsied for a particular type of tissue. In this case, an optimal position for the lens system is sought as the sample is moved in the directions perpendicular to the excitation optical axis (x,y) to sample the Raman activity The task is to search for or "lock onto" a particular type of activity indicative of a diseased tissue or a particular depth or layer of tissue that is held constant as the sample is moved in the directions perpendicular to the optical axis of the excitation hght. For example, this approach can be useful for differentiating between basal ceU carcinoma (deeper ceUs or layers) and malignant melanoma (surface ceUs).

In the other situation, the positions of the tissue perpendicular to the optical axis of the excitation hght are held constant while scannmg in the direction along the optical axis (z) of the excitation hght. That is, the position of the excitation laser focusing lens is moved lncrementaUy, and the coUection lens is then adjusted after each incremental movement of the focusing lens. This generates a "depth profile" with regard to a particular type of tissue. The lens adjustments made in this process are not mdependent. Regardless of the position of the coUection optics, Raman signal can only come from the region sufficiendy lUummated by the excitation laser. It therefore makes sense to initiate any search/mapping/locking algonthm with some incremental movement of the excitation lens.

In each case, the optimization wiU find the relative position of the two lenses that maximizes the Raman feature of mterest (or in a multichannel environment, maximizes some feature(s) while minimizmg others, as in the differentiation of dermis from epidermis and stratum corneum based on the C-H stretching region). In a single channel environment, a filter/detector can be used for obtain information related to each feature of mterest. In a multichannel environment, the different features can be observed usmg a spectrograph, within the limits of dispersion. The optimal position of the coUection lens relates not only to the propagation of the excitation laser into the inhomogeneous tissues but also to the propagation of the Raman scattered radiation out of the lUuminated region. These issues relate to vanous aspects of the tissue including types and degree of spatial and optical inhomogeneity m and near the region of interest.

For samphng (x,y axes) over relatively smaU regions, having a charactenstic size of about a few millimeters to a few centimeters or depths (z axis) of microns up to a millimeter or so, and relatively flat tissues, (back, neck, even finger tips over smaU enough regions, such as a millimeter or two in the x-y direction), one can model the radiation propagation through the tissue and thereby relate the variation of the strength of the Raman features with either the vanation of tissue charactenstics with depth or the relative vanation of tissue type as the "Raman biopsy" is scanned paraUel across the surface of the skin. This latter characterization can either be at a constant depth with regard to the surface or simply a measure of maximum amount of tissue type vanation across the dιrection(s) paraUel to the skin surface (line scan or surface map). Characterization at a constant depth that shows fluctuations is indicative of wrinkles.

In either case, one lens ad_justment (excitation is vaned first either in response to motion of the sample or in response to the desire to illuminate a different depth of tissue in question) must be foUowed by the system finding the optimal position of the other lens, ι.e. the coUection lens. This wiU tend to find the best overlap between the coUection and excitation cones with regard to the tissues producing the Raman signal of interest. Thus the system aUows a search of the tissues with optimal overlap of the excitation and coUection systems.

Methods

The invention provides a method for obtaining spectroscopic information from living tissue of a subject. In one embodiment, the method compnses irradiating a tissue of mterest in a subject with hght passing from a hght source through a first adjustable lens, and passing spectra that are emitted by the tissue through a second adjustable lens. The spectra that are passed through the second ad_justable lens are then coUected and analyzed to determine a target signal associated with an analyte of mterest. The method further compnses denving a correction signal from the target signal based on comparing the new target signal with a target signal associated with a previous counting penod, and adjusting the position of the first adjustable lens or the second adjustable lens and/or an adjustable aperture on the basis of the correction signal so as to enhance the target signal.

In a preferred embodiment for obtaining feedback based on static tissues, the spectra are Raman spectra. However, in an embodiment based on prob g mobde tissues (e.g., blood), use of visible fluorescence is preferred. In this case, a preferred excitation wavelength is m the range of about 580-680 nm. The method can optionaUy further compnse selectively dispersing a target wavelength of the coUected spectra pnor to analyzing the coUected spectra. Preferably, the dispersing compnses filtering out wavelengths other than the target wavelength, or passmg the coUected spectra through a spectrograph.

Examples of excitation wavelengths mclude, but are not limited to, about 785, 805, 808, 830, and 850 nm. Examples of target wavelengths include, but are not limited to, Raman shifts of about 529-556, 811-830, 938, 1087-1101, 1245, 1269, 1297, 1445, 1650-1670, 2100-2200, 2852, 2883, 2933, 2935, 2944, 2987, and 2850-3000 cm"¹. Examples of analytes mclude, but are not hmited to, phosphorous-containing bonds, carbon-hydrogen bonds, carbon-deutenum bonds, amide linkages, moisture, nucleic acid (DNA, RNA), protem, hpid, carbohydrate, coUagen, elastin and keratin

In another aspect, the invention provides a non-invasive method for spectroscopicaUy probing a target layer of skm in a subject. The method compnses irradiating a target layer of skin m a sub_ject with hght having an excitation wavelength that passes from a hght source through a first adjustable lens, passmg spectra that are emitted by the tissue through a second adjustable lens and/or an adjustable aperture, and coUectmg spectra that are passed through the second adjustable lens and/or aperture The method further comprises analyzing the coUected spectra to determine a target signal associated with the target layer of skm, and adjusting the position of the first ad_justable lens, the second adjustable lens, and/or the adjustable aperture so as to mcrease the target signal. OptionaUy, the method further compnses denvmg a correction signal from the target signal and relaying the correction signal to the first ad_justable lens, the second ad_justable lens and/or the ad_justable aperture, wherein the correction signal effects an adjustment of the first adjustable lens or the second adjustable lens.

In another aspect, the invention provides a method for detecting abnormahties in hvmg tissue of a subject. The method compnses irradiating a tissue of interest m a subject with hght passing from a hght source through a first adjustable lens, passmg spectra that are emitted by the tissue through a second adjustable lens and/or an adjustable aperture, and coUectmg spectra that are passed through the second ad_justable lens and/or aperture

The method further compnses analyzing the coUected spectra to determine a target signal associated with a tissue feature indicative of an abnormality, deriving a correction signal from the target signal, and adjusting the position of the first ad_justable lens, the second adjustable lens and/or the adjustable aperture on the basis of the correction signal so as to enhance the target signal. In one embodiment, the tissue of mterest compnses skin. Other examples of tissues of mterest mclude, but are not limited to, stratum corneum, epidermis, lntradermal capiUary beds, and dermis.

Abnormahties that can be detected mclude, but are not limited to, vanous cancers, genetic disorders such as so-caUed "elephant skm", psonasis, and other conditions related to imbalances of hpid, protein, carbohydrate and water content. Cancers can be detected, for example, by detecting mcreases in phosphorous-contaimng bonds, as are abundant in nucleic acids such as DNA and RNA, and by detecting changes in morphology and tissue density. Because metabolites are excreted to a significant extent via the sweat glands, the process can be used to detect substances that an individual has ingested. In addition, one can discriminate between substances that find their way onto the skm from exogenous sources as opposed to from endogenous sources. It is therefore possible to use the method to serve as a forensic or security tool. Such a tool would also reveal individuals who have handled guns or bomb making materials, drugs or drug making chemicals or who have ingested certam foods or substances.

The invention further provides a method for stabilizing a wavelength of hght emitted by a diode laser. This stabilization of the wavelength will also stabilize amphtude. The method comprises irradiating a specimen with excitation hght from the diode laser, and coUect g Raman spectra at a target wavelength emitted by the irradiated specimen, wherem the target wavelength is associated with a strong feature in the specimen. In one embodiment, the target wavelength is associated with sihca, as present in the optical path, such that an optical element within the system serves as the irradiated specimen. The target wavelength associated with sihca is a wavenumber shift of about 1003 cm ^x from the excitation wavelength. The method further comprises determining a quantity of spectra emitted at the target wavelength, relaying to the diode laser a signal proportional to the determined quantity, and regulating the temperature of the diode laser so as to maintain a maximal spectra emitted at the target wavelength Figure 3 shows spectral counts obtamed at Raman shifts of about 600-1800 wavenumbers and revealing a peak associated with sihca at 1003 cm ^J. The lower trace was obtamed from a peUet of NaCl, and the middle trace from an in vivo non-invasive probing of blood in a human subject using equipment and methods as described herem The upper trace is from Koo et al., 1999, Diabetes Tech. Ther 1:153-157, and was taken from an in vitro sample of whole blood using fiber optics. The sihca peak at 1003 cm appears consistently m aU three conditions, including the NaCl peUet, confirming that this peak is indeed attnbutable to sihca m the optical path.

In another embodiment, Raman spectra are coUected at two wavelengths: a positive target wavelength associated with a strong feature the specimen, and at a negative target wavelength associated with a weak feature m the specimen. The method further comprises determining a quantitative difference between the spectra emitted at the positive target wavelength and the spectra emitted at the negative target wavelength, relaying to the diode laser a signal proportional to the determined difference, and regulating the temperature of the diode laser so as to maintain a maximal difference between the spectra emitted at the positive target wavelength and the spectra emitted at the negative target wavelength.

In a preferred embodiment, the specimen is skm, the positive target wavelength is a wavenumber shift of about 2940 or 1665 cm ' from the excitation wavelength and the negative target wavelength is a wavenumber shift of about 2800 or 1775 cm , respectively, from the excitation wavelength. The method can be used to differentiate between dermis, epidermis and stratum corneum. In this approach, the positive target wavelength is associated with the layer of interest and the negative target wavelength is associated with a layer to be distinguished from the layer of mterest. For dermis, a positive target wavelength is a wavenumber shift of about 856, 938, 1245, 1269 or 2987 cm from the excitation wavelength, and a negative target wavelength is a wavenumber shift of about 1130, 1297 or 2852 cm from the excitation wavelength For epidermis, a positive target wavelength is a wavenumber shift of about 2933 cm ^λ from the excitation wavelength, and a negative target wavelength is a wavenumber shift of about 856, 938, 2987 or 2990 cm ¹ from the excitation wavelength. For stratum corneum, a positive target wavelength is a wavenumber shift of about 1297, 2852 or 2883 cm⁴ from the excitation wavelength, and a negative target wavelength is a wavenumber shift of about 2987 cm^-1 from the excitation wavelength.

The method can be performed non-invasively on living tissue. OptionaUy, the method further compnses adjusting the position of a first adjustable lens located m the optical path of the excitation hght so as to mcrease the determined difference between the spectra emitted at the positive target wavelength and the spectra emitted at the negative target wavelength, and/or adjusting the position of a second ad_justable lens and/or an adjustable aperture located m the optical path of the emitted spectra so as to mcrease the determined difference between the spectra emitted at the positive target wavelength and the spectra emitted at the negative target wavelength.

In another embodiment, the invention provides a method for assessing the aging of skin and related tissues. The method comprises characterizing the content of the skm usmg Raman spectroscopy as descnbed above. In one embodiment, the coUagen, elastin, and or keratin content of the skm is characterized, as is the spatial mapping of wrinkles.

Flow Charts

Figure 4 is a flow chart showing the logic mvolved m performing a scan of tissue in the x-y dimensions. At box 400, start x,y and stop x,y positions for the sample are chosen and mput to a computer. At box 402, the sample is manuaUy positioned to the start x,y position and the excitation and coUection lens positions are manuaUy optimized. At box 404, a Raman spectrumo is obtamed. At box 406, the excitation lens is moved m or out, in a direction along the z axis. Then the coUection lens position is optimized usmg Raman feedback at 408, and a new Raman spectrurm is obtained at 410. At box 412, spectrumo is compared to spectrurm. Box 414 is a decision box. If the new spectrum is better, control moves to box 422, with movement of the excitation lens m the same direction as previously, and then returns to box 408. If the new spectrum is worse, control moves to box 424, with movement of the excitation lens m the opposite direction as previously, and then returns to box 406 If no change, within a preset tolerance, is detected at decision box 414, control moves to box 416, where Raman spectrurm data and the x,y position are stored. At box 418, the sample is automaticaUy moved to a new x,y position. Box 420 is a decision box. If the new x,y is not equal to the stop x,y, then control returns to box 404. If the new x,y is equal to the stop x,y, then the process stops. It is understood that vanation of the size of incremental spatial adjustments of lenses and apertures are made m accordance with preset tolerances so as to yield optimized conditions m a reasonable number of iterations and with a minimal number of oscillations.

Figure 5 is a flow chart showing the logic involved m obtaining a depth profile. At box 500, the start and stop excitation lens positions are chosen. At box 502, the selected Raman signal is manuaUy optimized. At box 504, a Raman signal is obtained. Then, the position of the excitation lens is moved m an increment toward the stop position at 506. At box 508, the coUection lens position is optimized. The Raman spectrum is recorded at box 510. Box 512 is a decision box. If the final position of the excitation lens has not been met, control returns to box 506. If the final position has been met, the process stops.

Those skilled m the art wiU appreciate other vanations and modifications that can be adapted for the methods and apparams disclosed herem without departing from the spint and scope of the invention.

Claims

What is claimed is:

1. A method for obtaining spectroscopic information from living tissue of a subject compnsing:

(a) irradiating a tissue of mterest in a subject with hght having an excitation wavelength and that passes from a hght source through a first adjustable lens along a first optical axis;

(b) passmg spectra that are emitted by the tissue through a second adjustable lens along a second optical axis;

(c) coUectmg spectra that are passed through the second adjustable lens;

(d) analyzing the coUected spectra to determine a target signal associated with an analyte of mterest;

(e) denvmg a correction signal from the target signal; and

(f) adjusting the position of the first adjustable lens or the second adjustable lens along the optical axis of the lens on the basis of the correction signal so as to enhance the target signal.

2. The method of claim 1, wherem the spectra are Raman spectra or visible fluorescence.

3. The method of claim 1, further compnsing repeating steps (a)-(d) after the adjusting of step (f), and wherem the denvmg of the correction signal compnses determining the difference between the target signal obtained before and after the adjusting of step (f).

4. The method of claim 1 , wherem the analyzmg compnses filtering out wavelengths other than the target wavelength.

5. The method of claim 1 , wherem the analyzmg compnses passmg the coUected spectra through a spectrograph.

6. The method of claim 1, wherem the tissue is skin.

7. The method of claim 1, wherem the excitation wavelength is selected from the group consisting of about 580-680, 785, 805, 808, 830, and 850 nm.

8. The method of claim 1, wherem the target wavelength is selected from the group consisting of Raman shifts of about 529-556, 811-830, 938, 1087-1101, 1245,

1269, 1297, 1445, 1650-1670, 2100-2200, 2852, 2883, 2933, 2935, 2944, 2987, and 2850-3000 cm

9. The method of claim 1, wherem the analyte is selected from the group consisting of phosphorous-contaimng bonds, carbon-hydrogen bonds, carbon-deutenum bonds, and amide linkages.

10 The method of claim 1, wherem the analyte is selected from the group consisting of moisture, prote , hpid, carbohydrate, coUagen, elastin and keratin.

11. A non-mvasive method for spectroscopicaUy prob g a target layer of skm in a subject compnsmg:

(a) irradiating a target layer of skm in a sub_ject with hght havmg an excitation wavelength that passes from a hght source through a first adjustable lens;

(b) passmg spectra that are emitted by the tissue through a second adjustable lens;

(c) coUectmg spectra that are passed through the second adjustable lens;

(d) analyzmg the coUected spectra to determine a target signal associated with the target layer of skin; and

(e) adjusting the position of the first adjustable lens or the second adjustable lens so as to mcrease the target signal.

12 The method of claim 11, further compnsing denvmg a correction signal from the target signal and relaymg the correction signal to the first ad_justable lens or to the second adjustable lens, wherem the correction signal effects an adjustment of the first adjustable lens or the second adjustable lens.

13 The method of claim 12, further compnsmg repeating steps (a)-(d) after the ad_justing of step (e), and wherem the denving of the correction signal compnses determining the difference between the target signal obtamed before and after the adjusting of step (e).

14. The method of claim 11, wherem the excitation wavelength is selected from the group consisting of about 580,680, 785, 805, 808, 830, and 850 nm.

15. The method of claim 11, wherem the target layer of skin compnses stratum corneum, intradermal capillary beds, or dermis.

16. The method of claim 11, wherem the target signal is a signal associated with Raman shifts of about 938, 1245, 1269, 1297, 2852, 2883, 2933, 2944, 2955, or 2987 cm-¹.

17. A method for detecting abnormahties m living tissue of a sub_ject compnsmg:

(a) irradiating a tissue of mterest m a sub_ject with hght having an excitation wavelength and that passes from a hght source through a first adjustable lens along a first optical axis;

(c) coUectmg spectra that are passed through the second adjustable lens along a second optical axis;

(d) analyzmg the coUected spectra to determine a target signal associated with a tissue feature indicative of an abnormality,

(e) denvmg a correction signal from the target signal; and (f) adjusting the position of the first adjustable lens or the second adjustable lens along the optical axis of the lens on the basis of the correction signal so as to enhance the target signal.

8. The method of claim 17, wherein the excitation wavelength is selected from the group consisting of about 580-680, 785, 805, 808, 830, and 850 nm.

19. The method of claim 7, wherein the tissue feature is carbon-hydrogen stretching.

20. The method of claim 19, wherein the target signal is associated with a Raman shift of about 2850-3000 cm-¹.

21. The method of claim 17, wherein the tissue feature is carbon-deuterium stretching.

22. The method of claim 21, wherein the target signal is associated with a Raman shift of about 2000-2200 cm"¹.

23. The method of claim 17, wherein the tissue feature is tissue density.

24. The method of claim 23, wherein the target signal is total integrated area of coUected spectra.

25. The method of claim 17, wherein the tissue feature is phosphorous-containing bonds.

26. The method of claim 25, wherein the target signal is associated with a Raman shift of about 529-556, 811-830 or 1087-1101 cm"¹.

27. The method of claim 17, wherein the tissue feature is hpid content.

28. The method of claim 27, wherein the target signal is associated with a Raman shift of about 1445 cm"¹.

29. The method of claim 17, wherein the tissue feature is protein content.

30. The method of claim 29, wherein the protein is coUagen, elastin or keratin.

31. The method of claim 29, wherem the target signal is associated with a Raman shift of about 1650-1670 cm"¹.

32 The method of claim 17, wherein the spectra compnse Raman spectra.

33. The method of claim 17, wherem the tissue of mterest compnses skin.

34. The method of claim 33, wherem the tissue of mterest compnses stratum corneum.

35. The method of claim 33, wherem the tissue of mterest compnses epidermis.

36 The method of claim 33, wherem the tissue of mterest compnses an intradermal capillary bed.

37. The method of claim 33, wherem the tissue of mterest compnses dermis.

38. A method for stabilizing a wavelength of hght emitted by a diode laser compnsmg:

(a) irradiating a specimen with excitation hght from the diode laser;

(b) coUectmg Raman spectra at a positive target wavelength and at a negative target wavelength emitted by the irradiated specimen, wherem the positive target wavelength is associated with an abundant feature m the specimen and wherem the negative target wavelength is associated with a scant feature m the specimen;

(c) determining a quantitative difference between the spectra emitted at the positive target wavelength and the spectra emitted at the negative target wavelength;

(d) relaymg to the diode laser a signal proportional to the determined difference; and (e) regulating the temperature of the diode laser so as to maintain a maximal difference between the spectra emitted at the positive target wavelength and the spectra emitted at the negative target wavelength.

The method of claim 38, wherem the specimen is skm.

The method of claim 38, wherem the positive target wavelength is a Raman shift of about 1640 cm ^l and the negative target wavelength is Raman shift of about 1720 cm relative to the excitation hght.

The method of claim 38, wherem the specimen is living tissue and the method is performed noninvasively.

The method of claim 38, further compnsmg adjusting the position of a first adjustable lens located m an optical path of the excitation hght so as to mcrease the determined difference between the spectra emitted at the positive target wavelength and the spectra emitted at the negative target wavelength.

The method of claim 38, further compnsmg adjusting the position of a second adjustable lens located m an optical path of the emitted spectra so as to mcrease the determined difference between the spectra emitted at the positive target wavelength and the spectra emitted at the negative target wavelength.

An apparatus for enhancmg spectroscopic information obtained from hvmg tissue of a subject compnsmg:

(a) a signal analyzer adapted to receive input from a detector; and

(b) a processor connected to the signal analyzer, wherem the processor is capable of producmg an output signal that is proportional to a quantity of Raman spectra received by the signal analyzer from the detector.

The apparatus of claim 44, further compnsmg a diode laser connected to the processor, wherem the output signal regulates the temperature of the diode laser, thereby stabilizing the wavelength or amplitude of hght emitted by the diode laser.

46. The apparatus of claim 44, further compnsmg an ad_justable lens connected to the processor and opticaUy ahgned with an output path from a laser, wherem the output signal regulates movement of the ad_justable lens along an optical axis ahgned with the output path of the laser.

47. The apparatus of claim 46, further compnsmg an electromcaUy controUed translation stage coupled to the ad_justable lens for receiving an output signal from the processor.

48. The apparatus of claim 44, further compnsmg an adjustable lens connected to the processor and opticaUy ahgned with an mput path to the detector, wherem the output signal regulates movement of the adjustable lens along an optical axis ahgned with the mput path of the detector.

49. The apparatus of claim 48, further compnsmg an electromcaUy controUed translation stage coupled to the ad_justable lens for receiving an output signal from the processor.

50. The apparatus of claim 44, further compnsmg an ad_justable aperture coupled to an electromcaUy controUed translation stage that is connected to the processor and opticaUy ahgned with an mput path to the detector, wherem the output signal regulates movement or diameter of the ad_justable aperture along or perpendicular to an optical axis ahgned with the mput path of the detector.