Classifications

• • 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 or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
  • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
  • A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/02—Detecting, measuring or recording for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
  • A61B5/024—Measuring pulse rate or heart rate
  • A61B5/02416—Measuring pulse rate or heart rate using photoplethysmograph signals, e.g. generated by infrared radiation
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
  • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
  • A61B5/7207—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise induced by motion artifacts
  • A61B5/7214—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise induced by motion artifacts using signal cancellation, e.g. based on input of two identical physiological sensors spaced apart, or based on two signals derived from the same sensor, for different optical wavelengths
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
  • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
  • A61B5/6802—Sensor mounted on worn items
  • A61B5/681—Wristwatch-type devices

Definitions

• the invention relates to a photoplethysmography apparatus, to a method for operating a photoplethysmography apparatus and to a computer program for operating a photoplethysmography apparatus.
• a photoplethysmography apparatus hereinafter PPG apparatus.
• the apparatus comprises
• tissue-path error signal component which over time is indicative of a variation in optical path length through the tissue
• light- coupling error signal component which over time is indicative of a variation of a coupling between the source light emitted at the tissue and the tissue, from the at least first and second sensor signals of the given time of measuring
• the time-dependent factor c(t) describes the light-coupling error, which is indicative of a variation of source light intensity of the source light.
• the source light intensity measure I 0 describes the intensity of the source light emitted at the tissue. Since the tissue as investigated medium comprises a blood portion and a tissue portion surrounding blood vessels, the absorption parameter of the media is separated into the blood attenuation parameter ⁇ ⁇ ( ⁇ ) and into the effective tissue attenuation parameter ⁇ ⁇ ( ⁇ ) . This leads according to the Beer-Lambert law to the relation
• ln(7Xt, A)) ln(c m (t)) - ( ⁇ ⁇ ( ⁇ ) ⁇ ⁇ (t) + ⁇ ⁇ ( ⁇ ) ⁇ ⁇ (t)) .
• tissue-path error signal component and the light-coupling error signal component do not have to be calculated for providing the corrected sensor signal.
• the present embodiment avoids frequency domain filtering and thus allows the use of particularly simple hardware for providing a corrected sensor signal.
• the absolute values of the effective attenuation parameters need not be known. Only relative values need to be known. Since these values follow from the molecular extinction coefficients, their relative values are fixed. A deviation from the actual absolute values will only result in a scaling error in the computed parameters. This is not a problem since the primary interest for application purposes is in the variation of the blood absorbance z B (t) .
• the corrected sensor signal as a normalized difference of weighted derivatives of the logarithm of the transmission measures of the respective spectral position, weighted by the derivative of the prestored effective tissue attenuation parameter of the respective other spectral position, wherein the respective derivatives are calculated with respect to the spectral position.
• the formula for calculating the corrected sensor signal in this variant can be derived from the Beer-Lambert law by using the derivative of Eq. (1) with respect to ⁇ :
• the at least one source of light is further configured to provide source light of a third spectral position to be directed at the tissue;
• the at least one light detector is further configured to provide at least a third sensor signal indicative of scattered source light of the third spectral position;
• the processing unit is further configured to receive the third sensor signal and to calculate and provide the corrected sensor signal by using the first, second and third sensor signals.
• the first and second part of the corrected sensor signal as a normalized sum of weighted derivatives of the logarithm of the transmission measures of the respective spectral position, weighted by a respective weighting factor depending on a linear combination of respective pairs of the derivatives of the prestored absorption parameters of oxyhemoglobin and of deoxyhemoglobin and the derivatives of the prestored effective tissue attenuation parameters , wherein the respective derivatives are calculated with respect to the spectral position.
• the corrected sensor signal is calculated according to an algebraic formula at subsequent times of measuring.
• the processing unit calculates an algebraic solution of a system of linear equations.
• the linear equations correspond to Eq. (1) but with separated absorption parameters for
• the PPG apparatus further comprises a user interface arranged and configured to receive and provide a user input indicative of blood attenuation parameters or absorption parameters of oxyhemoglobin and deoxyhemoglobm or effective tissue attenuation parameters or a measurement of the PPG apparatus to be displayed.
• the user interface is a keyboard or a touchpad or a notebook.
• the user interface is electrically and functionally coupled to the memory unit.
• the common factor is iteratively determined by the processing unit.
• the common factor can be changed by a user input received by the user interface.
• the invention relates to a method for operating a PPG apparatus, the method comprising
• the calculating of the corrected sensor signal further comprises a numerical solving of a system of at least two linear equations by using the at least two transmission measures.
• the method further comprises the steps of
• Fig. 4 is a schematic illustration of a calculation of a processing unit determining derivatives of respective parameters within an embodiment of the PPG apparatus according to the first aspect of the invention
• the PPG apparatus can comprise as a single source of light a tunable filter to provide source light of the first and second spectral position.
• source light of a third or a forth spectral position is provide by the at least one source of light.
• Fig. 3 illustrates a calculation of the processing unit of an embodiment where source light of a further third spectral position is provided.
• the processing unit 310 calculates the corrected sensor signal 380 as a function of time in dependence on a logarithm of the transmission measure 350 for each spectral position, a prestored blood attenuation parameter 360 for each spectral position, a prestored effective tissue attenuation parameter 370 for each spectral position, the tissue-path error signal component and the light-coupling error signal component, using the Beer-Lambert law.
• the transmission measure 320, the blood attenuation parameter 360 and the effective tissue attenuation parameter 370 are prestored within the processing unit 310.
• the transmission measure 420, the blood attenuation parameter 460 and the effective tissue attenuation parameter 470 are prestored within the processing unit 410.
• the processing unit 410 is further configured to determine a logarithm of the transmission measure 450. Afterwards, the processing unit 410 determines a derivative of the logarithm of the transmission measure 455, of the prestored blood attenuation parameter 465, and of the prestored effective tissue attenuation parameter 475, wherein all derivatives are taken with respect to the spectral position.
• the encasement of this embodiment leads to a simple determination of vital- sign information of the user of the PPG apparatus 500. This also enables an automatized or frequent calculation of the corrected sensor signal. It is particularly advantageous to remove the tissue-path error signal component and the light-coupling error signal component for the PPG apparatus 500, since an intensive motion can lead to a high level of signal error components due to motion, which affects the light-coupling error signal component.
• the method further comprises a calculating of a corrected sensor signal (630), indicative of a variation in blood absorbance within the tissue, by using the at least first and second sensor signal and by removing a tissue-path error signal component, which is indicative of a variation in optical path length through the tissue over time, and a light- coupling error component, which is indicative of a variation of source light intensity of the source light emitted at the tissue, from the at least first and second sensor signals.
• a corrected sensor signal indicative of a variation in blood absorbance within the tissue
• the invention relates to a PPG apparatus, comprising at least one source of light arranged and configured to provide source light of at least a first and a second spectral position to be directed at a tissue; at least one light detector arranged and configured to detect scattered source light, which has been scattered by the tissue, and to provide at least a first sensor signal indicative of the scattered source light of the first spectral position and a second sensor signal indicative of the scattered source light of the second spectral position; and a processing unit.

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• Health & Medical Sciences (AREA)
• Life Sciences & Earth Sciences (AREA)
• Physics & Mathematics (AREA)
• Engineering & Computer Science (AREA)
• Surgery (AREA)
• Public Health (AREA)
• Pathology (AREA)
• Veterinary Medicine (AREA)
• Biomedical Technology (AREA)
• Heart & Thoracic Surgery (AREA)
• Medical Informatics (AREA)
• Molecular Biology (AREA)
• Biophysics (AREA)
• Animal Behavior & Ethology (AREA)
• General Health & Medical Sciences (AREA)
• Cardiology (AREA)
• Physiology (AREA)
• Signal Processing (AREA)
• Spectroscopy & Molecular Physics (AREA)
• Optics & Photonics (AREA)
• Artificial Intelligence (AREA)
• Computer Vision & Pattern Recognition (AREA)
• Psychiatry (AREA)
• Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
• Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)

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• 2016
  • 2016-05-24 CN CN201680032053.9A patent/CN107666860B/zh not_active Expired - Fee Related
  • 2016-05-24 JP JP2017562012A patent/JP6878312B2/ja not_active Expired - Fee Related
  • 2016-05-24 WO PCT/EP2016/061624 patent/WO2016193048A1/en not_active Ceased
  • 2016-05-24 EP EP16725491.1A patent/EP3302253A1/en not_active Withdrawn
  • 2016-05-24 US US15/579,065 patent/US10966642B2/en not_active Expired - Fee Related
  • 2016-05-24 BR BR112017025708A patent/BR112017025708A2/pt not_active Application Discontinuation

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