WO2001040776A1 - Procede permettant de mesurer la saturation du tissu en hemoglobine au moyen d'une decomposition gaussienne - Google Patents

Procede permettant de mesurer la saturation du tissu en hemoglobine au moyen d'une decomposition gaussienne Download PDF

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Publication number
WO2001040776A1
WO2001040776A1 PCT/US2000/032830 US0032830W WO0140776A1 WO 2001040776 A1 WO2001040776 A1 WO 2001040776A1 US 0032830 W US0032830 W US 0032830W WO 0140776 A1 WO0140776 A1 WO 0140776A1
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WIPO (PCT)
Prior art keywords
tissue
recited
deoxyhemoglobin
tissue oxygenation
feature
Prior art date
Application number
PCT/US2000/032830
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English (en)
Inventor
David A. Wilson
Original Assignee
Johns Hopkins University
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Johns Hopkins University filed Critical Johns Hopkins University
Priority to AU18140/01A priority Critical patent/AU1814001A/en
Publication of WO2001040776A1 publication Critical patent/WO2001040776A1/fr

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/47—Scattering, i.e. diffuse reflection
    • G01N21/49—Scattering, i.e. diffuse reflection within a body or fluid
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
    • A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases
    • A61B5/14553—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases specially adapted for cerebral tissue
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
    • G01N21/31—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry
    • G01N21/35—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry using infrared light
    • G01N21/359—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry using infrared light using near infrared light

Definitions

  • the present invention relates to determining hemoglobin saturation
  • hemoglobin The principal function of hemoglobin is to transport oxygen from
  • tissue hypoxia oxygen in tissues
  • the device has
  • saturation is a parameter that conveys to the physician how well the heart
  • blood may be adequately oxygenated, but unavailable to tissues because
  • a surgeon may choose to apply a
  • surgeon relies upon indirect measures of stress to determine when and if
  • the brain is relatively near the surface of the skin and is separated from
  • hemoglobin individually, and in such a manner, as to allow the
  • hemoglobin various forms had to be characterized as well, because
  • the INVOS 3100 instrument has
  • baseline absorbency i.e., that light scattering is not strongly wavelength dependent
  • baseline influences can be nulled by derivatizing spectra.
  • PRM Pseudo-random modulated code spectroscopy
  • PRM spectroscopy evolved as a means of quantifying the much shorter
  • sequences can be identified using autocorrelation analysis.
  • time-of-travel for photons through tissue can be characterized.
  • oxygenation can be measured by performing the calculations at two
  • a coded light signal typically is a coded light signal
  • the signal information is
  • FRS relies upon a mathematical
  • the NIM instrument (PMD 4002, MM Inco ⁇ orated, Philadelphia, PA)
  • the amplitude of the acoustic signal is proportional to
  • the useable signal originates close to the surface of the tissue, and was,
  • TRS, FRS, and PRM technologies are at the
  • NIR near infrared
  • An object of the present invention is to provide a method of
  • the present invention is a method for decomposing compound
  • diffuse reflectance spectra collected from tissue, such as brain tissue
  • tissue hemoglobin discrete constituents that can then be used to compute tissue hemoglobin
  • the present invention requires a spectrometer capable of
  • tissue cytochrome oxidase tissue cytochrome oxidase
  • cerebral tissue lipid content tissue lipid content
  • the secondary constituent characterizations are qualitative, but the values can be used for trending pu ⁇ oses, or for
  • the method of the present invention can be further developed to
  • absorbency i.e., oxyhemoglobin, deoxyhemoglobin, water, lipid,
  • hemoglobin saturation Because it is a ratio, it does not require a
  • FIGURE 1 is a graph showing the abso ⁇ tion spectra of
  • FIGURE 2 is a block diagram of the instrumentation used to carry
  • FIGURE 3 is a graph showing NIR prediction versus measured
  • FIGURE 4 is a graph showing that the oxyhemoglobin feature
  • FIGURE 5 is a graph showing that adding linkage between the 760
  • FIGURE 6 is a graph showing the ratio of oxyhemoglobin
  • FIGURE 7 is a graph showing that the ratio of oxyhemoglobin
  • abso ⁇ tion to abso ⁇ tion attributable to total hemoglobin can be adjusted using two coefficients to provide a numerical predictor of brain tissue
  • FIGURE 8 is a graph showing the best and worst case fits to
  • FIGURE 9 is a graph showing that feature absorbency is optrode
  • FIGURE 10 is a graph showing tissue hemoglobin saturation
  • FIGURE 11 is a graph showing water corrected spectra from bacon
  • FIGURE 12 is a graph showing the result of fitting the HbSat bt
  • FIGURES 13 A and B are graphs showing the effect linking two
  • deoxyhemoglobin features has on the total hemoglobin attenuation.
  • FIGURE 14 is a graph showing an abso ⁇ tion spectrum from cat
  • FIGURE 15 is a graph showing an abso ⁇ tion spectrum from
  • An abso ⁇ tion spectrum is a plot of how light within a range of
  • wavelength, ⁇ is proportional to the concentration of a constituent, c, and the pathlength, L, through which the light travels during measurement, so
  • ⁇ ( ⁇ ) is the molar abso ⁇ tion coefficient and is wavelength
  • ⁇ ( ⁇ ) has the characteristics of a gaussian
  • ⁇ max is the maximum value of the abso ⁇ tion
  • FWHM is the width of the spectrum at
  • ⁇ c is the wavelength around which the spectral range is
  • Equation 1 It follows that c may be determined from [A] ⁇ m i n.. ⁇ max , if ⁇ max ,
  • This information may be used to determine the location of optical monitoring.
  • the deoxyhemoglobin molecule has two absorbencies in the
  • oxyhemoglobin will be a constant fraction of the non-overlapping feature.
  • the knowledge base must also include
  • lipid cytochrome oxidase and includes a component to characterize light
  • oxyhemoglobin and deoxyhemoglobin are "recovered" and used to
  • One hemoglobin molecule consists of two alpha and two beta heme
  • polypeptide chains containing polypeptide chains (globins). Together, the chains form a
  • hemoglobin depend on the relative proportion of the number of
  • hemoglobin molecules that contain bound oxygen.
  • features of high absorbency are located at 415, 542,
  • brain tissue hemoglobin saturation has focused on identifying the
  • NIR near-infrared window
  • absorbers water, hemoglobin, cytochrome oxidase, and lipid, water is the
  • hemoglobin (-0.4%), and cytochrome oxidase ( ⁇ 0.1%).
  • FIGURE 1 shows the abso ⁇ tion spectra 11 and 12 of oxygenated
  • hemoglobin For instrument tilt and water abso ⁇ tion.
  • the absorbing properties of hemoglobin have been extensively
  • oxyhemoglobin absorbs light in a broad
  • Table 1 itemizes the major NIR band absorbing constituents of
  • the knowledge base consists of a series of equations that characterize each of the
  • [OOJ ⁇ mm ⁇ ma ⁇ is a range of optical density, or absorbence, and is
  • ⁇ is wavelength, in nanometers
  • FWHM is the full width
  • Equation 3 is replicated n times, for the n absorbency peaks
  • Baseline OD is
  • Model A for descriptive pu ⁇ oses
  • ABL Radiometer Co ⁇ oration
  • Hvpoxic-hypoxia All animals were challenged with multiple
  • administering the hypoxic gas mixtures was usually from normoxic levels
  • Anemic-hypoxia In another two of the animals, anemic-hypoxia
  • hypothermia In one animal, body temperature was cooled to 18
  • FIG. 2 is a schematic illustration of the instrumentation 10 used
  • Light is generated via a high intensity halogen lamp 13
  • exiting light 26 was collected by a short, 3 -foot length of shielded fiber
  • optic bundle 34 also an optode, and passed to a peltier-cooled avalanche
  • APD Advanced Photonix, Inc., Camarillo, CA.
  • APD 36 is powered by a high voltage power supply 38.
  • APD 36 was then passed to the control of a computer 40 after being
  • Model A was applied to resolve h c for each of the ten
  • tissue hemoglobin saturation is a construct that
  • tissue hemoglobin saturation stems from a literature citing that suggests
  • Standard HbSat bt refers to a computed value that
  • HbSatcven where HbSatgr t and HbSat cve n are the percentage saturation of
  • HbSat bt was used to verify the NIR HbSat bt method. The features were
  • Figure 3 is a graph showing NIR prediction versus measured tissue hemoglobin
  • tissue hemoglobin saturation estimated as a weighted fraction of
  • deoxyhemoglobin 47 were inversely proportional to tissue hemoglobin
  • the measured extraction fraction indicates such a change
  • the model system was revised to include two rules. First, it was
  • Model B The revised model system, Model B, was reapplied to the
  • Attenuation 60 is such that a reduction in this parameter value is observed as tissue hemoglobin saturation is reduced.
  • deoxyhemoglobin
  • Figure 6 shows the ratio 64 formed as attenuation due to
  • deoxyhemoglobin is a linear function 66 of standard tissue hemoglobin
  • Figure 7 shows the Model B prediction of HbSat bt - Tissue
  • hemoglobin saturation 70 can be predicted from recovered optical
  • Prediction error is least at tissue saturations greater than 30%.
  • tissue hemoglobin saturation 58 when tissue hemoglobin saturation 58 is high, tissue oxyhemoglobin
  • tissue deoxyhemoglobin 62 is low, and when tissue
  • hemoglobin saturation 58 is low, tissue oxyhemoglobin 60 is low and
  • tissue deoxyhemoglobin 62 is high.
  • hypoxia induced vasodilation and hypercarbia induced vasodilation hypoxia induced vasodilation and hypercarbia induced vasodilation
  • Figures 8A and B illustrate the best and worst fit cases. The left
  • Figure 8 A illustrates a correlation between Model B predicted
  • tissue hemoglobin saturation 74 and the standard of comparison 72 for an
  • the absolute concentration of the recovered constituent can be any value
  • tissue hemoglobin saturation is computed as a ratio, pathlength effects contained by in the numerator and denominator of the
  • the method provides a measure that is
  • tissue hemoglobin saturation measured
  • Model B the absorbency at 920 nm is attributed to
  • the FWHM used to resolve the 937 nm absorbency depends on the animal species from which the spectra were collected. For cat
  • cytochrome oxidase a secondary peak of cytochrome oxidase, or a peak of
  • NIRHbSatbt 100 x OD 937nm / (OD 760nm + OD 937 nm). (Eq 4)
  • HbSat bt to become greater. This can be offset in part by increasing the
  • Model C correlates the ratio of oxyhemoglobin 94 to total hemoglobin 96
  • hemoglobin components 98 showed an increased absorbency in the
  • hemoglobin 102 either remains unchanged, or decreases. ( Figure 13B).
  • hemoglobin parameter as an index of blood volume. Hypercapnia
  • the method of the present invention has application to other types
  • Figures 14 and 15 illustrate the general
  • Figure 14 shows an abso ⁇ tion spectrum 104
  • Brain spectra contain two notable features: a peak
  • Figure 15 shows an abso ⁇ tion spectrum 108 collected from human
  • Model C was able to decompose spectra from skeletal muscle
  • abso ⁇ tion spectra contains a prominent triglyceride
  • Model C is also able to recover constituent information

Abstract

L'invention se rapporte à une caractérisation additionnelle des composants des tissus cérébraux qui contribuent à l'absorption de la lumière, soit l'oxyhémoglobine, la désoxyhémoglobine, l'eau, les lipides, l'oxydase cytochrome et ainsi que d'un composant permettant de caractériser la perte de flux lumineux résultant de la diffusion, et l'utilisation de ceux-ci pour construire un système modèle qui reproduit les spectres de réflectance du tissu cérébral dans différentes conditions. Utilisé selon un mode inversé, ce système modèle permet de décomposer les spectres composites collectée à partir du tissu cérébral en caractéristiques spectrales individuelles. On utilise ensuite les valeurs des caractéristiques pouvant être attribuées à l'oxyhémoglobine et à la désoxyhémoglobine pour dériver un indice permettant de chiffrer le pourcentage total d'hémoglobine contenant de l'oxygène. Etant donné que la majeure partie de la lumière collectée par l'élément détecteur de l'équipement a transité par le tissu cérébral, cet indice représente une mesure quantitative de la saturation du tissu cérébral en hémoglobine. Outre le tissu cérébral, ce procédé d'analyse par décomposition peut être appliqué de manière générale à divers autres tissus.
PCT/US2000/032830 1999-12-02 2000-12-04 Procede permettant de mesurer la saturation du tissu en hemoglobine au moyen d'une decomposition gaussienne WO2001040776A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU18140/01A AU1814001A (en) 1999-12-02 2000-12-04 Method of measuring tissue hemoglobin saturation using gaussian decomposition

Applications Claiming Priority (2)

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US16852999P 1999-12-02 1999-12-02
US60/168,529 1999-12-02

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Cited By (26)

* Cited by examiner, † Cited by third party
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US7684842B2 (en) 2006-09-29 2010-03-23 Nellcor Puritan Bennett Llc System and method for preventing sensor misuse
US8219170B2 (en) 2006-09-20 2012-07-10 Nellcor Puritan Bennett Llc System and method for practicing spectrophotometry using light emitting nanostructure devices
US8265724B2 (en) 2007-03-09 2012-09-11 Nellcor Puritan Bennett Llc Cancellation of light shunting
US8280469B2 (en) 2007-03-09 2012-10-02 Nellcor Puritan Bennett Llc Method for detection of aberrant tissue spectra
US8315685B2 (en) 2006-09-27 2012-11-20 Nellcor Puritan Bennett Llc Flexible medical sensor enclosure
US8610769B2 (en) 2011-02-28 2013-12-17 Covidien Lp Medical monitor data collection system and method
US8622916B2 (en) 2008-10-31 2014-01-07 Covidien Lp System and method for facilitating observation of monitored physiologic data
US8862196B2 (en) 2001-05-17 2014-10-14 Lawrence A. Lynn System and method for automatic detection of a plurality of SP02 time series pattern types
US8870783B2 (en) 2011-11-30 2014-10-28 Covidien Lp Pulse rate determination using Gaussian kernel smoothing of multiple inter-fiducial pulse periods
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US8930145B2 (en) 2010-07-28 2015-01-06 Covidien Lp Light focusing continuous wave photoacoustic spectroscopy and its applications to patient monitoring
US8965473B2 (en) 2005-09-29 2015-02-24 Covidien Lp Medical sensor for reducing motion artifacts and technique for using the same
US8968193B2 (en) 2008-09-30 2015-03-03 Covidien Lp System and method for enabling a research mode on physiological monitors
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US9042952B2 (en) 1997-01-27 2015-05-26 Lawrence A. Lynn System and method for automatic detection of a plurality of SPO2 time series pattern types
US9053222B2 (en) 2002-05-17 2015-06-09 Lawrence A. Lynn Patient safety processor
CN105158169A (zh) * 2015-06-03 2015-12-16 遵义师范学院 一种油茶籽成分含量软件检测系统及其方法
WO2016086071A1 (fr) * 2014-11-24 2016-06-02 Nueou, Inc. Appareil et procédés de spectromètre consommable à codage spectral
US9468378B2 (en) 1997-01-27 2016-10-18 Lawrence A. Lynn Airway instability detection system and method
US9521971B2 (en) 1997-07-14 2016-12-20 Lawrence A. Lynn System and method for automatic detection of a plurality of SPO2 time series pattern types
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US10076276B2 (en) 2008-02-19 2018-09-18 Covidien Lp Methods and systems for alerting practitioners to physiological conditions
US10354753B2 (en) 2001-05-17 2019-07-16 Lawrence A. Lynn Medical failure pattern search engine

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US9468378B2 (en) 1997-01-27 2016-10-18 Lawrence A. Lynn Airway instability detection system and method
US9042952B2 (en) 1997-01-27 2015-05-26 Lawrence A. Lynn System and method for automatic detection of a plurality of SPO2 time series pattern types
US9521971B2 (en) 1997-07-14 2016-12-20 Lawrence A. Lynn System and method for automatic detection of a plurality of SPO2 time series pattern types
US8932227B2 (en) 2000-07-28 2015-01-13 Lawrence A. Lynn System and method for CO2 and oximetry integration
US10058269B2 (en) 2000-07-28 2018-08-28 Lawrence A. Lynn Monitoring system for identifying an end-exhalation carbon dioxide value of enhanced clinical utility
US9031793B2 (en) 2001-05-17 2015-05-12 Lawrence A. Lynn Centralized hospital monitoring system for automatically detecting upper airway instability and for preventing and aborting adverse drug reactions
US8862196B2 (en) 2001-05-17 2014-10-14 Lawrence A. Lynn System and method for automatic detection of a plurality of SP02 time series pattern types
US10297348B2 (en) 2001-05-17 2019-05-21 Lawrence A. Lynn Patient safety processor
US11439321B2 (en) 2001-05-17 2022-09-13 Lawrence A. Lynn Monitoring system for identifying an end-exhalation carbon dioxide value of enhanced clinical utility
US10366790B2 (en) 2001-05-17 2019-07-30 Lawrence A. Lynn Patient safety processor
US10032526B2 (en) 2001-05-17 2018-07-24 Lawrence A. Lynn Patient safety processor
US10354753B2 (en) 2001-05-17 2019-07-16 Lawrence A. Lynn Medical failure pattern search engine
US9053222B2 (en) 2002-05-17 2015-06-09 Lawrence A. Lynn Patient safety processor
US8965473B2 (en) 2005-09-29 2015-02-24 Covidien Lp Medical sensor for reducing motion artifacts and technique for using the same
US8219170B2 (en) 2006-09-20 2012-07-10 Nellcor Puritan Bennett Llc System and method for practicing spectrophotometry using light emitting nanostructure devices
US8315685B2 (en) 2006-09-27 2012-11-20 Nellcor Puritan Bennett Llc Flexible medical sensor enclosure
US7684842B2 (en) 2006-09-29 2010-03-23 Nellcor Puritan Bennett Llc System and method for preventing sensor misuse
US8280469B2 (en) 2007-03-09 2012-10-02 Nellcor Puritan Bennett Llc Method for detection of aberrant tissue spectra
US8265724B2 (en) 2007-03-09 2012-09-11 Nellcor Puritan Bennett Llc Cancellation of light shunting
US11298076B2 (en) 2008-02-19 2022-04-12 Covidien Lp Methods and systems for alerting practitioners to physiological conditions
US10076276B2 (en) 2008-02-19 2018-09-18 Covidien Lp Methods and systems for alerting practitioners to physiological conditions
US9895068B2 (en) 2008-06-30 2018-02-20 Covidien Lp Pulse oximeter with wait-time indication
US8968193B2 (en) 2008-09-30 2015-03-03 Covidien Lp System and method for enabling a research mode on physiological monitors
US8622916B2 (en) 2008-10-31 2014-01-07 Covidien Lp System and method for facilitating observation of monitored physiologic data
US9993208B2 (en) 2008-10-31 2018-06-12 Covidien Lp System and method for facilitating observation of monitored physiologic data
US8930145B2 (en) 2010-07-28 2015-01-06 Covidien Lp Light focusing continuous wave photoacoustic spectroscopy and its applications to patient monitoring
US8610769B2 (en) 2011-02-28 2013-12-17 Covidien Lp Medical monitor data collection system and method
US9668681B2 (en) 2011-05-05 2017-06-06 Nemodevices Ag Measuring device for measuring cerebral parameters
US8870783B2 (en) 2011-11-30 2014-10-28 Covidien Lp Pulse rate determination using Gaussian kernel smoothing of multiple inter-fiducial pulse periods
US9833146B2 (en) 2012-04-17 2017-12-05 Covidien Lp Surgical system and method of use of the same
US10022089B2 (en) 2012-11-06 2018-07-17 Luciole Medical AG Measuring device for determining cerebral parameters
WO2014187849A1 (fr) * 2013-05-22 2014-11-27 Nemodevices Ag Système et procédé de mesure de paramètres dans un tissu corporel
JP2019048055A (ja) * 2013-05-22 2019-03-28 ルシオール メディカル アクチェンゲゼルシャフトＬｕｃｉｏｌｅ Ｍｅｄｉｃａｌ ＡＧ 人体組織内のパラメータを測定するための測定システムおよび方法
US10682100B2 (en) 2013-05-22 2020-06-16 Luciole Medical AG Measurement system and method for measuring parameters in a body tissue
WO2016086071A1 (fr) * 2014-11-24 2016-06-02 Nueou, Inc. Appareil et procédés de spectromètre consommable à codage spectral
CN105158169A (zh) * 2015-06-03 2015-12-16 遵义师范学院 一种油茶籽成分含量软件检测系统及其方法

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Klaessens et al. In vivo measurements of the influence of the skin on cerebral oxygenation changes measured with near-infrared spectrophotometry (NIRS)

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