Abstract: An analyte detection apparatus, includes a radiation source for irradiating a sample; a receiver, to receive an optical Raman spectrum of radiation transmitted back from the sample in response to the received radiation from the source, wherein the receiver includes a plurality of different types of analysis device each arranged to receive a selected part of the received optical spectrum transmitted back from the sample.

Abstract: An analyte detection apparatus includes a radiation source for irradiating a sample and a receiver to receive an optical Raman spectrum of radiation transmitted back from the sample, the spectrum including one or more parts of significance to an analyte to be detected and one or more parts not of significance to an analyte to be detected. The receiver includes different types of analysis device each arranged to receive a selected part of the spectrum. The different types of analysis device include at least one analysis device having high resolution and/or high signal to noise ratio for detecting a part of the spectrum of significance to the analyte to be detected and at least one second type of analysis device which provides lower resolution and/or lower signal-to-noise ratio, for detecting a part of the spectrum not of significance to the analyte to be detected.

Abstract: An analyte detection apparatus, includes a radiation source for irradiating a sample; a receiver, to receive an optical Raman spectrum of radiation transmitted back from the sample in response to the received radiation from the source, wherein the receiver includes a plurality of different types of analysis device each arranged to receive a selected part of the received optical spectrum transmitted back from the sample.

Abstract: The use of a transdermal Raman spectrum to measure glucose or other substance concentration can give an inaccurate result if the Raman signals originate at a wrong skin depth. To predict whether a spectrum of Raman signals received transdermally in a confocal detector apparatus and having at least one component expected to have an intensity representing the concentration of glucose or another skin component at a point of origin of the Raman signals below the surface of the skin will accurately represent the concentration, peaks in the spectrum at 883/4 cm?1 and 894 cm?1 are measured to determine whether the Raman signals originate primarily within the stratum corneum so that the spectrum will be less likely to represent the concentration accurately or originate primarily below the stratum corneum so that the spectrum will be more likely to represent the concentration accurately.

Abstract: A metabolite concentration is measured in vivo using Raman spectroscopy in such a way as to receive at a detector light scattered from the metabolite in interstitial fluid in skin in a measurement location at a depth of from 200-300 ?m below the skin surface providing improved retention of correct calibration and transferability of calibration between individual subjects.

Abstract: The use of a transdermal Raman spectrum to measure glucose or other substance concentration can give an inaccurate result if the Raman signals originate at a wrong skin depth. To predict whether a spectrum of Raman signals received transdermally in a confocal detector apparatus and having at least one component expected to have an intensity representing the concentration of glucose or another skin component at a point of origin of the Raman signals below the surface of the skin will accurately represent the concentration, peaks in the spectrum at 883/4 cm?1 and 894 cm?1 are measured to determine whether the Raman signals originate primarily within the stratum corneum so that the spectrum will be less likely to represent the concentration accurately or originate primarily below the stratum corneum so that the spectrum will be more likely to represent the concentration accurately.

Abstract: A metabolite concentration is measured in vivo using Raman spectroscopy in such a way as to receive at a detector light scattered from the metabolite in interstitial fluid in skin in a measurement location at a depth of from 200-300 ?m below the skin surface providing improved retention of correct calibration and transferability of calibration between individual subjects.

Abstract: A metabolite concentration is measured in vivo using Raman spectroscopy in such a way as to receive at a detector (229) light scattered from the metabolite in interstitial fluid in skin in a measurement location (217) at a depth (218) of from 200-300 ?m below the skin surface providing improved retention of correct calibration and transferability of calibration between individual subjects.

Abstract: A metabolite concentration is measured in vivo using Raman spectroscopy in such a way as to receive at a detector (229) light scattered from the metabolite in interstitial fluid in skin in a measurement location (217) at a depth (218) of from 200-300 ?m below the skin surface providing improved retention of correct calibration and transferability of calibration between individual subjects.

Abstract: This invention relates to a spectroscopic apparatus for measuring at least two spectrally shifted spectral distributions of a light beam, said apparatus comprises a dispersive element adapted to generate a spatial dispersion of the spectral components in a light beam when said dispersive element is being illuminated by said light beam; and a detector adapted to measure the intensity of at least a part of said dispersed spectral components where said apparatus further comprises an optical shifting means adapted to illuminate said dispersive element in at least two different ways, such that said light beam hits said dispersive element differently, and whereby said dispersive element generates at least two spatially shifted spatial dispersions of the spectral components in said light beam.