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WO2006067690A2 - Dispositif de mesure du rythme cardiaque - Google Patents

Dispositif de mesure du rythme cardiaque Download PDF

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Publication number
WO2006067690A2
WO2006067690A2 PCT/IB2005/054246 IB2005054246W WO2006067690A2 WO 2006067690 A2 WO2006067690 A2 WO 2006067690A2 IB 2005054246 W IB2005054246 W IB 2005054246W WO 2006067690 A2 WO2006067690 A2 WO 2006067690A2
Authority
WO
WIPO (PCT)
Prior art keywords
heart rate
user
motion
sensor
measuring
Prior art date
Application number
PCT/IB2005/054246
Other languages
English (en)
Other versions
WO2006067690A3 (fr
Inventor
Olaf Such
Jens Muehlsteff
Josef Lauter
Robert Pinter
Original Assignee
Philips Intellectual Property & Standards Gmbh
Koninklijke Philips Electronics N. V.
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 Philips Intellectual Property & Standards Gmbh, Koninklijke Philips Electronics N. V. filed Critical Philips Intellectual Property & Standards Gmbh
Publication of WO2006067690A2 publication Critical patent/WO2006067690A2/fr
Publication of WO2006067690A3 publication Critical patent/WO2006067690A3/fr

Links

Classifications

    • 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
    • A61B5/721—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise induced by motion artifacts using a separate sensor to detect motion or using motion information derived from signals other than the physiological signal to be measured
    • 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
    • A61B5/02444—Details of sensor
    • 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
    • A61B5/6813—Specially adapted to be attached to a specific body part
    • A61B5/6814—Head
    • A61B5/6815—Ear
    • A61B5/6816—Ear lobe
    • 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
    • A61B5/6843—Monitoring or controlling sensor contact pressure

Definitions

  • the present invention relates to a device for measuring a user' s heart rate.
  • the present invention also relates to a portable sound reproducing device comprising such a measuring device.
  • the invention relates to a method of measuring a user' s heart rate and to a computer program for measuring a user' s heart rate.
  • PPG photoplethysmography
  • this technique is not very suitable for use by persons exercising an activity, for example a sports activity, because of the high level of motion artifacts. In other words the motion of the user causes corruption of the PPG signal.
  • These artifacts lead to erroneous interpretation of the PPG signals and degrade the accuracy and reliability of PPG-based algorithms for the estimation of the heart rate.
  • US 2003/0233051 Al it is suggested to remove motion artifacts by using a correction signal generated by an accelerometer device. The use of an accelerometer is expensive and power consuming.
  • a device for measuring a user's heart rate comprising a user- wearable heart rate sensor for measuring a heart rate signal, a motion sensor for sensing a motion signal, the motion signal representing a relative movement between the heart rate sensor and the user, and a processing unit for removing at least partially artifacts caused by motion in the heart rate signal by using the motion signal.
  • the motion signal representing the relative movement is used as a correction signal.
  • the object of the present invention is also achieved by a portable sound reproducing device, which comprises such a measuring device.
  • the object of the present invention is also achieved by a method of measuring a user's heart rate, comprising the steps of measuring a heart rate signal, sensing a motion signal, the motion signal representing a relative movement between the heart rate sensor and the user, and removing at least partially artifacts due to motion in the heart rate signal by using the motion signal.
  • the object of the present invention is finally achieved by a computer program for measuring a user' s heart rate, the computer program comprising computer instructions to remove at least partially artifacts due to motion in a heart rate signal by using a motion signal representing a relative movement between the heart rate sensor and the user, when the computer instructions are carried out in a computer.
  • a computer program can be stored on a carrier or it can be available over the internet or another computer network. Prior to executing the computer program, it is loaded into a computer by reading the computer program from a carrier, for example by means of a CD-ROM player, or from the internet or another network, and storing it in the memory of the computer.
  • the computer includes inter alia a central processor unit (CPU), a bus system, memory means, e.g. RAM or ROM etc. and input/output units.
  • the instructions of the computer program can also be implemented as embedded software.
  • an embedded system is used, which is housed for example on a single microprocessor board with the computer program stored in a ROM.
  • the invention is based on the idea of utilizing the relative movement between the heart rate sensor and the user to generate a correction signal.
  • the present invention uses a more accurate method for carrying out the correction. Because the user himself is used as a reference, the correction signal represents the real relative sensor-to-body motion in a very realistic way.
  • the heart rate sensor and/or the motion sensor is adapted to be in contact with the user.
  • the heart rate sensor and/or the motion sensor is adapted to be fixed to an ear of a user.
  • the heart rate sensor and/or the motion sensor is preferably implemented in a device for reproducing sound, e.g. an earphone, stereo headset or mobile phone headset etc. If all parts of the device for measuring the heart rate are implemented in an earphone or headset etc. a very high usability is provided. Alternatively, another part of the user's body can be used, e.g. the tip of a finger etc.
  • a contact with the user makes a motion detection possible based on measuring the contact pressure corresponding to the pressure between the heart rate sensor and the user.
  • the mechanical coupling between heart rate sensor and user is determined.
  • the mechanical coupling corresponds to the optical coupling between heart rate sensor and user.
  • information can be given about the optical coupling. Movements of the sensor relative to the user lead to changes in optical coupling. Motion artifacts in the heart rate signal will occur. If changes in the mechanical coupling can be detected, motion artifacts can be predicted and a artifact correction can be carried out in the processing unit to achieve an accurate heart rate signal, which is at least partially free of motion artifacts.
  • the contact pressure between the heart rate sensor and the user is measured either directly or indirectly. In the latter case the contact pressure the heart rate sensor and the user is detected by measuring the contact pressure between a separate contact device and the user and predicting the real contact pressure using that measuring signal. If the device for measuring the heart rate is used in a headphone etc. the sensors for measuring heart rate and motion can easily be used in the design of the headphone.
  • the relative movement between the heart rate sensor and the user can not only be detected by measuring the contact pressure.
  • Other measuring techniques can be implemented as well, for example distance measurements with optical, acoustic, mechanical or other means.
  • the contact pressure between the heart rate sensor and the user can be detected using several methods, as described below. All described methods can be realized in a very power-saving way, e.g. employing low-current devices.
  • the motion sensor is adapted to measure the contact pressure based on a piezoelectric effect.
  • the motion sensor comprises a piezoelectric contact device, e.g. a piezoelectric polymer foil or another pressure-sensitive material.
  • a piezoelectric contact device e.g. a piezoelectric polymer foil or another pressure-sensitive material.
  • the contact device produces an electrical output signal from a mechanical input signal.
  • the output signal is amplified and used as a measure for the contact pressure.
  • the relative movement is determined on the basis of this information.
  • the motion sensor is adapted to measure the contact pressure based on a piezoresistive or resistive effect.
  • the motion sensor comprises a piezoresistive contact device, e.g. a metal or semiconductor material.
  • the motion sensor comprises a resistive contact device, e.g. a soft conductive material, for example the form of an earphone.
  • a mechanical pressure is applied to said contact devices the electrical resistivity of the contact devices changes.
  • the changes in resistivity are determined using measurement of current or voltage.
  • the changes in resistivity are a measure for the contact pressure and the relative movement is determined based upon this information.
  • the motion sensor is adapted to measure the contact pressure based on a bioimpedance measuring technique. For this purpose, alternating current of effective value passes through the living tissue, e.g.
  • bioimpedance can be measured indirectly by means of the voltage. Alternatively, a direct current can be applied.
  • the motion sensor comprises at least one bioimpedance contact device, preferably in the foam of an electrode to be fixed t the user's skin.
  • the level of bioimpedance depends on the electrical contact between the contact device and the user' s skin. Since, on the other hand, the electrical contact depends on the mechanical contact between contact device and skin, the bioimpedance gives a measure for the level of contact pressure between contact device and user.
  • All described methods can be used for carrying out a heart rate measuring at a single location on the user, e.g. on one side of the user's ear, i.e. on the side of an earphone.
  • the number of motion sensors can be increased.
  • motion sensors are positioned on both sides of a user's ear.
  • motion sensors are positioned near both ears. The motion signals obtained from the two locations can be correlated to reduce errors and to improve heart rate detection. If the motion sensors are positioned near both ears e.g. the bioimpedance is measured between the ears of the user, providing a current through the user' s head. All these different techniques can be employed alternatively as well as in addition to each other. In cases where two or more different measuring techniques are used at the same time, a high quality correction of the heart rate signal can be carried out because of the large number of motion signals at hand.
  • the contact pressure between the heart rate sensor and the user can also be measured employing other known measuring techniques.
  • the portable device comprises a sensor unit using conductive electrodes for measuring a galvanic skin response and/or a sensor unit for measuring a temperature of the user's skin. These additional measurements can be used to obtain an index for stress. The signals obtained are correlated with the motion signals to provide a better correction of the heart rate signals. If the motion signals are detected based upon the bioimpedance measuring technique, the same electrodes can be used for both bioimpedance measuring and measuring of the galvanic skin response.
  • the heart rate sensor is an optical sensor.
  • the heart rate sensor is a photoplethysmographic sensor.
  • transmission technique employing parts of the heart rate sensor on both sides of a user's body part
  • other techniques can be used as well, such as a so called reflection technique (based upon diffusion within the tissue), where e.g. both transmitter and receiver are positioned on the same side of the ear.
  • reflection techniques can be employed in a combined approach.
  • Fig. 1 shows a schematic block diagram of a portable device for measuring a user's heart rate
  • Figs. 2-5 show sectional views of different embodiments of the invention in a working position near a user's ear.
  • a device 1 for measuring a user' s heart rate is illustrated in Fig. 1.
  • the device 1 comprises a heart rate sensor 2 for measuring a heart rate signal, a motion sensor 3 for measuring a motion signal, the motion signal representing a relative movement between the heart rate sensor 2 and the user (not shown), and a processing unit 4 for removing at least partially artifacts due to motion in the heart rate signal by the use of the motion signal.
  • Heart rate sensor 2, motion sensor 3 and processing unit 4 are integrated in an earphone 5, e.g. an earphone of a portable radio, CD-player or MP3-player or the like.
  • the earphone design allows the heart rate sensor 2 and the motion sensor 3 to be in contact wih the user's ear.
  • the heart rate sensor (optical PPG sensor) 2 is adapted to measure the user' s heart rate based on photoplethysmography (PPG) utilizing a transmission technique. A measurement of the subcutaneous blood flow in the ear is carried out.
  • the heart rate sensor 2 comprises a light emitting diode (LED) 6 as a light source and a photodetector 7 as a receiver.
  • the optical signal is corrected in the processing unit 4 by combining the optical signals and the motion signals. In other words a data fusion is carried out.
  • a computer program for signal correction is provided in the processing unit 4.
  • the processing unit 4 is connectable to a display device 8 for displaying the user's heart rate.
  • the communication link 9 is preferably established using a radio communication technique.
  • the display device 8 is a monitor implemented in a wrist-worn device.
  • FIG. 2 an embodiment according to the invention is shown.
  • An LED 6 is positioned in mechanical contact with the surface of a user's ear 10.
  • a photodetector 7 is positioned in mechanical contact with the surface of the ear 10. The light is scattered through the earlobe or cartilage of the ear 10, where it is submitted to modifications due to reflection, refraction and absorption, depending on the blood content. After propagation of the light through the tissue the light is picked up by the photodetector 7.
  • LED 6 and photodetector 7 are each placed in a support ring 11, 12 made of a soft material for a better mechanical contact to the ear 10.
  • the support member can also take another form, e.g. the form of a sheet or the like.
  • the photodetector 7 and its support ring 12 is fixed directly to a carrier 13, made e.g. from a plastic material.
  • the carrier 13 is preferably part of the earphone 5.
  • the LED 6 and its support ring 11 are fixed to another part of the carrier 13 situated on the opposite side of the ear 10 by means of an intermediate pressure layer 14. In other words the LED 6 and its support ring 11 are in direct mechanical contact with the pressure layer 14.
  • the pressure layer 14 consists of a piezoelectric polymer foil.
  • a mechanical pressure is applied to the pressure layer 14 and a voltage is produced, approximately proportional to the pressure resting on the layer 14 and representing the user's movement.
  • This pressure also directly influences the optical coupling of the device and the underlying motion additionally causes blood volume changes in the tissue.
  • the resulting voltage signal is detected by an adequate measuring device (not shown) preferably used in the carrier 13 and transmitted to the processing unit 4, amplified and used for correction of the heart rate signal.
  • the processing unit 4 comprises processing means for processing input data from the photodetector 7 as well as from the pressure layer 14.
  • Fig. 3 another embodiment according to the invention is shown.
  • an intermediate pressure layer 14 is provided on both sides of the ear 10.
  • both the LED 6 and its support ring 11 and the photodetector 7 and its support ring 12 are fixed to the carrier 13 by means of the pressure layer 14.
  • the components 6, 7 of the heart rate sensor 2 are located on both sides of the ear 10, it is advantageous to detect changes of the contact pressure between these components 6, 7 and the ear 10 in the same way, i.e. on both sides of the ear 10. In this case there are two motion signals to be fed into the processing unit 4 for correlation with the heart rate signal.
  • a further embodiment according to the invention is shown.
  • support rings 15 surrounding the LED 6 and the photodetector 7 are adapted to take over the function of the pressure layer.
  • the support rings 15 are made of a resistive material, e.g. the foam of the earphones.
  • a movement of the user results in a mechanical pressure applied to the support ring 15, leading to a change in electrical resistivity of the support ring 15.
  • This resistivity change is determined using a measurement of voltage by an adequate measuring device (not shown) preferably implemented in the carrier 13, transmitted to the processing unit 4, amplified and used for correction of the heart rate signal.
  • the support ring 16 of the LED 6 comprises at least two electrodes 17 to be in contact with the user's ear 10.
  • the electrodes 17 are preferably made of conductive plastics or rubber. They can also be formed of metal or conductive foam, to integrate well with the design of the earphone 5.
  • the electrodes 17 are supplied with an alternating current in a way that the current passes through the ear 10.
  • the bioimpedance is measured indirectly by voltage.
  • adequate devices (not shown) are provided, preferably used in the carrier 13.
  • the resulting signal is transmitted to the processing unit 4, amplified and used for correction of the heart rate signal.
  • the support ring 12 of the photodetector 7 serves as a support member only.
  • Fig. 6 still another embodiment according to the invention is shown.
  • the support ring 16 of the LED 6 but also the support ring 18 of the photodetector 7 comprises bioimpedance electrodes 17.
  • bioimpedance measurements can be carried out between electrodes 17 on the same side of the ear 10 and furthermore between electrodes 17 on different sides of the ear 10, i.e.leading a current flow from one side of the ear 10 to the other side.
  • both LED 6 and photodetector 7 and the support rings 16, 18 are provided with a pressure layer 14 for carrying out a piezoelectric measurement as described above.
  • pressure layers for a piezoresistive or a resistive measurement can be used.
  • both the bioimpedance signals and the voltage signals derived from the other motion sensors are transmitted to the processing unit 4, amplified and used for correction of the heart rate signal.
  • the carrier 13 comprises an earclip 19 which serves as a fixation to hold the earphone parts in place.
  • the earclip is adapted to be in contact both with the ear 10 and the skull of the user.
  • additional impedance electrodes are positioned on the distant side of the earclip 19 to enable measurement of the impedance between ear 10 and skull. This additional bioimpedance signal is used as a further parameter for correction of the heart rate signal.
  • the heart rate sensor 2 can of course also be used to determine a further parameter, e.g. heart rate variability (HRV), a stress factor or breathing rate.
  • HRV heart rate variability
  • the removing of artifacts according to the present invention can be applied in those cases as well.
  • the present invention is not limited to heart rate sensors.
  • the invention can be applied to other sensors for measuring vital parameters, e.g. to a sensor for direct determining of the breathing rate.
  • the invention can be applied to any sensor for measuring any kind of parameter, if there are artifacts in the sensor signal thatare due to motion of the sensor relative to the user.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Medical Informatics (AREA)
  • Surgery (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Veterinary Medicine (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Public Health (AREA)
  • Molecular Biology (AREA)
  • Physics & Mathematics (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Cardiology (AREA)
  • Physiology (AREA)
  • Signal Processing (AREA)
  • Otolaryngology (AREA)
  • Artificial Intelligence (AREA)
  • Computer Vision & Pattern Recognition (AREA)
  • Psychiatry (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)

Abstract

L'invention concerne un dispositif de mesure du rythme cardiaque et un procédé de mesure correspondant. Pour présenter une technique de mesure fiable et peu onéreuse du rythme cardiaque, on décrit un dispositif (1) et un procédé correspondants : le mouvement relatif entre un capteur cardiaque (2) et la personne est décelé, ce qui donne un signal de correction permettant d'éliminer les artefacts de mouvement induits par le mouvement de la personne.
PCT/IB2005/054246 2004-12-22 2005-12-14 Dispositif de mesure du rythme cardiaque WO2006067690A2 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
EP04106846.1 2004-12-22
EP04106846 2004-12-22

Publications (2)

Publication Number Publication Date
WO2006067690A2 true WO2006067690A2 (fr) 2006-06-29
WO2006067690A3 WO2006067690A3 (fr) 2006-10-05

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Cited By (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2008020376A2 (fr) 2006-08-17 2008-02-21 Koninklijke Philips Electronics N.V. Dispositif d'affichage d'état de corps dynamique
EP2116183A1 (fr) * 2008-05-07 2009-11-11 CSEM Centre Suisse d'Electronique et de Microtechnique SA Dispositif de surveillance cardiovasculaire opto-électrique robuste localisé sur l'oreille
GB2500651A (en) * 2012-03-28 2013-10-02 Biorics Nv Replacing low quality heart rate measurements with a simulated signal generated form a relationship between measured activity level and heart rate
US9289135B2 (en) 2009-02-25 2016-03-22 Valencell, Inc. Physiological monitoring methods and apparatus
US9289175B2 (en) 2009-02-25 2016-03-22 Valencell, Inc. Light-guiding devices and monitoring devices incorporating same
US9427191B2 (en) 2011-07-25 2016-08-30 Valencell, Inc. Apparatus and methods for estimating time-state physiological parameters
EP3064128A1 (fr) * 2015-03-03 2016-09-07 Nokia Technologies OY Appareil portable par un utilisateur avec capteur optique
US9538921B2 (en) 2014-07-30 2017-01-10 Valencell, Inc. Physiological monitoring devices with adjustable signal analysis and interrogation power and monitoring methods using same
US9717424B2 (en) 2015-10-19 2017-08-01 Garmin Switzerland Gmbh System and method for generating a PPG signal
US9750462B2 (en) 2009-02-25 2017-09-05 Valencell, Inc. Monitoring apparatus and methods for measuring physiological and/or environmental conditions
US9794653B2 (en) 2014-09-27 2017-10-17 Valencell, Inc. Methods and apparatus for improving signal quality in wearable biometric monitoring devices
US9801552B2 (en) 2011-08-02 2017-10-31 Valencell, Inc. Systems and methods for variable filter adjustment by heart rate metric feedback
US9808204B2 (en) 2007-10-25 2017-11-07 Valencell, Inc. Noninvasive physiological analysis using excitation-sensor modules and related devices and methods
US10015582B2 (en) 2014-08-06 2018-07-03 Valencell, Inc. Earbud monitoring devices
US10076253B2 (en) 2013-01-28 2018-09-18 Valencell, Inc. Physiological monitoring devices having sensing elements decoupled from body motion
US10258243B2 (en) 2006-12-19 2019-04-16 Valencell, Inc. Apparatus, systems, and methods for measuring environmental exposure and physiological response thereto
US10413197B2 (en) 2006-12-19 2019-09-17 Valencell, Inc. Apparatus, systems and methods for obtaining cleaner physiological information signals
US10610158B2 (en) 2015-10-23 2020-04-07 Valencell, Inc. Physiological monitoring devices and methods that identify subject activity type
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US10945618B2 (en) 2015-10-23 2021-03-16 Valencell, Inc. Physiological monitoring devices and methods for noise reduction in physiological signals based on subject activity type
US10966662B2 (en) 2016-07-08 2021-04-06 Valencell, Inc. Motion-dependent averaging for physiological metric estimating systems and methods
US11512889B2 (en) 2019-02-25 2022-11-29 Lg Electronics Inc. Entrance refrigerator
US12336797B2 (en) 2023-09-01 2025-06-24 Garmin International, Inc. Wrist-worn electronic device with optical cardiac monitor

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WO2008020376A2 (fr) 2006-08-17 2008-02-21 Koninklijke Philips Electronics N.V. Dispositif d'affichage d'état de corps dynamique
US11272849B2 (en) 2006-12-19 2022-03-15 Valencell, Inc. Wearable apparatus
US11083378B2 (en) 2006-12-19 2021-08-10 Valencell, Inc. Wearable apparatus having integrated physiological and/or environmental sensors
US11399724B2 (en) 2006-12-19 2022-08-02 Valencell, Inc. Earpiece monitor
US11395595B2 (en) 2006-12-19 2022-07-26 Valencell, Inc. Apparatus, systems and methods for monitoring and evaluating cardiopulmonary functioning
US11350831B2 (en) 2006-12-19 2022-06-07 Valencell, Inc. Physiological monitoring apparatus
US11324407B2 (en) 2006-12-19 2022-05-10 Valencell, Inc. Methods and apparatus for physiological and environmental monitoring with optical and footstep sensors
US11295856B2 (en) 2006-12-19 2022-04-05 Valencell, Inc. Apparatus, systems, and methods for measuring environmental exposure and physiological response thereto
US10258243B2 (en) 2006-12-19 2019-04-16 Valencell, Inc. Apparatus, systems, and methods for measuring environmental exposure and physiological response thereto
US11412938B2 (en) 2006-12-19 2022-08-16 Valencell, Inc. Physiological monitoring apparatus and networks
US11272848B2 (en) 2006-12-19 2022-03-15 Valencell, Inc. Wearable apparatus for multiple types of physiological and/or environmental monitoring
US11109767B2 (en) 2006-12-19 2021-09-07 Valencell, Inc. Apparatus, systems and methods for obtaining cleaner physiological information signals
US11000190B2 (en) 2006-12-19 2021-05-11 Valencell, Inc. Apparatus, systems and methods for obtaining cleaner physiological information signals
US10987005B2 (en) 2006-12-19 2021-04-27 Valencell, Inc. Systems and methods for presenting personal health information
US10413197B2 (en) 2006-12-19 2019-09-17 Valencell, Inc. Apparatus, systems and methods for obtaining cleaner physiological information signals
US10716481B2 (en) 2006-12-19 2020-07-21 Valencell, Inc. Apparatus, systems and methods for monitoring and evaluating cardiopulmonary functioning
US10595730B2 (en) 2006-12-19 2020-03-24 Valencell, Inc. Physiological monitoring methods
US9808204B2 (en) 2007-10-25 2017-11-07 Valencell, Inc. Noninvasive physiological analysis using excitation-sensor modules and related devices and methods
EP2116183A1 (fr) * 2008-05-07 2009-11-11 CSEM Centre Suisse d'Electronique et de Microtechnique SA Dispositif de surveillance cardiovasculaire opto-électrique robuste localisé sur l'oreille
US10842387B2 (en) 2009-02-25 2020-11-24 Valencell, Inc. Apparatus for assessing physiological conditions
US11026588B2 (en) 2009-02-25 2021-06-08 Valencell, Inc. Methods and apparatus for detecting motion noise and for removing motion noise from physiological signals
US10076282B2 (en) 2009-02-25 2018-09-18 Valencell, Inc. Wearable monitoring devices having sensors and light guides
US11660006B2 (en) 2009-02-25 2023-05-30 Valencell, Inc. Wearable monitoring devices with passive and active filtering
US10092245B2 (en) 2009-02-25 2018-10-09 Valencell, Inc. Methods and apparatus for detecting motion noise and for removing motion noise from physiological signals
US9955919B2 (en) 2009-02-25 2018-05-01 Valencell, Inc. Light-guiding devices and monitoring devices incorporating same
US11589812B2 (en) 2009-02-25 2023-02-28 Valencell, Inc. Wearable devices for physiological monitoring
US11471103B2 (en) 2009-02-25 2022-10-18 Valencell, Inc. Ear-worn devices for physiological monitoring
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