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WO2022013592A1 - Système de mesure optique pour surveiller des paramètres physiologiques d'un utilisateur - Google Patents

Système de mesure optique pour surveiller des paramètres physiologiques d'un utilisateur Download PDF

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Publication number
WO2022013592A1
WO2022013592A1 PCT/IB2020/056548 IB2020056548W WO2022013592A1 WO 2022013592 A1 WO2022013592 A1 WO 2022013592A1 IB 2020056548 W IB2020056548 W IB 2020056548W WO 2022013592 A1 WO2022013592 A1 WO 2022013592A1
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WO
WIPO (PCT)
Prior art keywords
measurement system
light
body part
light source
enhancing
Prior art date
Legal status (The legal status 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 status listed.)
Ceased
Application number
PCT/IB2020/056548
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English (en)
Inventor
Christophe Verjus
Patrick Theurillat
Damien Ferrario
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Centre Suisse dElectronique et Microtechnique SA CSEM
Original Assignee
Centre Suisse dElectronique et Microtechnique SA CSEM
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Publication date
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Priority to PCT/IB2020/056548 priority Critical patent/WO2022013592A1/fr
Publication of WO2022013592A1 publication Critical patent/WO2022013592A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • 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
    • A—HUMAN NECESSITIES
    • A01—AGRICULTURE; FORESTRY; ANIMAL HUSBANDRY; HUNTING; TRAPPING; FISHING
    • A01K—ANIMAL HUSBANDRY; AVICULTURE; APICULTURE; PISCICULTURE; FISHING; REARING OR BREEDING ANIMALS, NOT OTHERWISE PROVIDED FOR; NEW BREEDS OF ANIMALS
    • A01K11/00—Marking of animals
    • A01K11/001—Ear-tags
    • 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
    • A61B5/683—Means for maintaining contact with the body
    • A61B5/6838—Clamps or clips
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2503/00—Evaluating a particular growth phase or type of persons or animals
    • A61B2503/40—Animals
    • 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
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/02108—Measuring pressure in heart or blood vessels from analysis of pulse wave characteristics
    • 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
    • A61B5/145—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
    • A61B5/14532—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 for measuring glucose, e.g. by tissue impedance measurement
    • 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
    • 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
    • A61B5/68—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
    • A61B5/6811—External prosthesis
    • 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
    • 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
    • A61B5/6887—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient mounted on external non-worn devices, e.g. non-medical devices
    • A61B5/6898—Portable consumer electronic devices, e.g. music players, telephones, tablet computers

Definitions

  • Optical measurement system for monitoring physiological parameters of a user
  • the present disclosure concerns an optical measuring system for the monitoring of physiological parameters. More particularly, the present disclosure concerns an optical measuring system that can measure a signal having enhanced signal to noise ratio.
  • Measurement devices dedicated to the monitoring of physiological parameters of persons or animals are often based on the detection of optical signals. Typical applications include the measurement of the heart rate, SPO2 (peripheral capillary oxygen saturation), blood pressure, or even the measurement of the concentration of molecules of interest such as glucose by performing in-vivo optical spectroscopy analysis.
  • Such optical measurement devices comprise a light source that emits light into a biological tissue (often the skin of a person or animal), and at least a photodetector which collects light that has been transmitted through the tissue. The physiological parameters are extracted from the measured optical signal, which is modulated by the transmission through the biological tissue.
  • Figs. 1a and 1b illustrate a conventional optical measurement device in contact with a biological tissue 10.
  • the optical measurement device comprises a light source 2 and a light detector 4.
  • the optical measurement device is transmission-based and the light source 2 and the light detector 4 are disposed at opposite sides of a tissue 10 being measured.
  • the light signal 20 emitted from the light source 2 is transmitted through the tissue 10.
  • the detector 4 receives the light signal 20 which has been diffused through the tissue 10.
  • Transmission-based optical measurement devices are typically configured to be clipped to the tissue or body part 10 to be measured, for example, clipped at fingers extremities or at ear lobules. Transmission- based optical measurement devices have good signal quality since the amount of light signal 20 reaching the light detector 4 is important and all the light signal 20 reaching the light detector 4 has passed through the biological tissue or body part 10 and the measured optical signal is strongly modulated by the physiological parameters to be detected.
  • Drawbacks of the transmission-based optical measurement devices include the necessity to clip the device to a body part such as to fix the relative position of the light source 2 and the detector 4.
  • the light source side and the detector side of the device comprise electronic elements and must be wired together for powering and/or for signal read out. These constrains can be particularly annoying for veterinary applications, or for sport activities in humans.
  • the optical measurement device is reflection-based whereby the light source 2 and the light detector 4 are on the same side of the tissue 10 to be measured.
  • a reflection-based measurement device can be of simpler construction since it does not require clipping or cumbersome wiring across two different sides of the tissue 10.
  • a reflection-based measurement device is often used for temporary measurements. Reflection-based measurement devices can be easily implemented on wearable devices, such as a wristwatch, chest belt or swimming goggles, integrated in clothing, or implemented using the light source and camera of a smartphone. However, reflection-based measurement devices have lower signal quality than transmission-based measurement devices. One reason is that the amount of light signal reaching the detector 4 is significantly smaller than in transmission-based measurement devices.
  • the emitted light signal 20 is scattered inside the tissue 10 and reaches the light detector 4 only through the diffuse reflections 21 occurring in biological structures such as dermal layers, blood cells, vessels or bones.
  • Another technical problem of the reflection-based measurement device is the possible light shorting, i.e. direct transmission of light 22 from the light source 2 to the detector 4 without passing through the biological tissue 10. This may be particularly problematic in wearables, where the device can be temporarily separated from the skin due to motion or shocks.
  • Another technical problem of the reflection-based measurement device is that most of the collected light is often reflected at external layers of the dermis 11.
  • venous blood contained in the tissue under the sensor is another source of problem since it can corrupt the PPG signal or reduce its quality. Pulsating venous blood (due to cardiac activity or motion) can corrupt the signal and hinder the detection of the physiological signal. Venous blood contained in the tissues attenuates the light, limiting the penetration depth, and therefore provide a measurement that is more superficial and containing less physiological information.
  • EP3427657A1 discloses an optical measurement device where the light source and light detector are mounted on protrusions of a transparent surface which is pushed against the skin. The skin folds filling the gap between the protrusions and the light source and detector are oriented roughly facing each other, allowing to enhance the amount of light that is scattered through the skin into the detector.
  • an optical measurement device comprises an actuator configured to lift a surface of skin tissue in order to create an optical path through the skin from the light source to the light sensor.
  • the light transmission and collection in a reflection-based optical measurement device is achieved by light-guiding structures between the light source and the skin, respectively between the skin and the detector, to direct the light beam into a desired direction in the tissue and to increase the collection efficiency.
  • the present disclosure concerns an optical measurement system for detecting physiological parameters of a user.
  • the measurement system comprises a sensor part comprising a light source configured to emit a light signal destined to illuminate a body part of the user, and a light detector configured to receive the light signal that has illuminated the body part.
  • the optical measurement system further comprises an enhancing part comprising a reflective element, the sensor part and enhancing part being configured to cooperate with the body part such that the light signal illuminating the body part is reflected by the reflective element, towards the light detector.
  • the sensor part and the enhancing part are configured to be arranged at two opposed surfaces of the body part such that the light signal emitted by the light source passes through the body part and is reflected back on the reflective element.
  • the measurement system combines the advantages of simplicity of a reflection-based optical measurement system to the signal quality of a transmission-based optical measurement system.
  • the optical measurement system disclosed herein has an improved path for the light signal between the light source and the light detector.
  • the improved light path through the tissue results in an enhanced signal to noise ratio and enables better extraction of the physiological parameter of interest.
  • the measurement system can be of simple construction.
  • FIGs. 1a and 1b schematically illustrate a conventional transmission-based (Fig. 1a) and reflection-based (Fig. 1b) optical measurement system;
  • Fig. 2 shows an optical measurement system comprising a sensor part and an enhancing part, according to an embodiment
  • Fig. 3 shows the measurement system comprising an ear tag assembly, according to an embodiment
  • Fig. 4 shows the measurement system comprising an attachment system, according to an embodiment
  • Fig. 5 represents the measurement de system vice comprising an attachment system, according to another embodiment
  • Fig. 6 represents the measurement system wherein the enhancing part is implantable within a body part, according to an embodiment
  • Fig. 7 illustrates the measurement system with the implantable enhancing part, according to another embodiment
  • Fig. 8a shows a side view
  • Fig. 8b shows a top view of the sensor part, according to an embodiment.
  • Fig. 2 shows an optical measurement system 100 for monitoring physiological parameters of a user, according to an embodiment.
  • the measurement system 100 comprises a sensor part 1 comprising a light source 2 configured to emit a light signal 20 destined to illuminate a body part 10 of the user.
  • the sensor part 1 further comprises a light detector 4 configured to receive the light signal 20 that has illuminated the body part 10.
  • the optical measurement system 100 further comprises an enhancing part 5 comprising a reflective element 6.
  • the sensor part 1 and enhancing part 5 are configured to cooperate with the body part 10 such that the light signal 20 illuminating the body part 10 is reflected by the reflective element 6, towards the light detector 4.
  • the sensor part 1 and the enhancing part 5 are in physical contact with the body part 10.
  • the sensor part 1 and the enhancing part 5 are in physical contact with two opposed surfaces 15 of the body part 10 such that the light signal 20 emitted by the light source 2 pass through the body part 10 and is reflected on the reflective element 6.
  • the reflected light signal 23 is detected by the light detector 4.
  • the configuration of the measurement system 100 allows the light signal 20 to travel twice the thickness of the body part 10 before reaching the light detector 4.
  • the light detector 4 can further collect a portion 21 of the emitted light signal 20 scattered by the body part 10.
  • the sensor part 1 and the enhancing part 5 need not be in physical contact with the body part 10.
  • the sensor part 1 and the enhancing part 5 can be configured to be arranged at two opposed surfaces 15 of the body part 10 such that the light signal 20 emitted by the light source 2 pass through the body part 10 and is reflected back on the reflective element 6.
  • the body part 10 can include a biological tissue of a human or animal, such as the skin, or body parts such as a finger or an ear.
  • the light source 2 may comprise any one of the following (non- exhaustive list): single or multiple light emitting diodes (LED), single or multiple laser diodes (LD), micro-plasma emitters, thermal sources, organic LEDs or tunable lasers.
  • LED light emitting diodes
  • LD laser diodes
  • micro-plasma emitters thermal sources, organic LEDs or tunable lasers.
  • the light source 2 may be monochromatic or comprise several wavelengths. Different wavelengths can be emitted at the same time or alternating periodically, or be scanned across a continuous range, for example with a tunable laser.
  • the light source 2 may further include a single emitter or several emitters distributed sparsely across a surface or tightly packed in an array.
  • the light source 2 may further comprise light-guiding structures or lenses to collimate or direct the emitted light beam or beams.
  • the light detector 4 can comprise any one of the following (non- exhaustive list): photodiodes, phototransistors or any other light sensitive element or a digital camera.
  • the light detector 4 can comprise optical filters adapted to select specific wavelengths emitted by the light source (spectral filters) or polarization filters.
  • the light detector 4 may further include a single element or several elements, distributed sparsely across a surface or tightly packed in an array.
  • the light detector 4 may further comprise light-guiding structures or lenses to select the direction or adjust the solid angle of light collection.
  • the light detector 4 may also comprise imaging optics to produce a spatially resolved image.
  • the reflective element 6 can comprise any one of the following (non-exhaustive list): a metallic or dielectric coating of any solid or polymeric material, a metallic part or metal foil, high-reflective paint, e.g. white paint or silver paint, different types of cat's eyes and reflex reflectors, any surface with a particular finish (polishing, diffractive structures, etc.) that enhances the reflection of light, in particular of the wavelengths emitted by the light source 2.
  • a metallic or dielectric coating of any solid or polymeric material e.g. white paint or silver paint, different types of cat's eyes and reflex reflectors, any surface with a particular finish (polishing, diffractive structures, etc.) that enhances the reflection of light, in particular of the wavelengths emitted by the light source 2.
  • the reflector 6 may be directional, like a polished mirror, or scattering, like a rough painted surface.
  • the reflector 6 may be flat, or curved, e.g. have a concave curvature to enhance the reflection of light towards the detector.
  • the enhancing part 5 can be, as such, the reflector 6.
  • the enhancing part 5 can consist of a reflective part, such as a metallic part.
  • the sensor part 1 can comprise an optical barrier element 7 arranged between the light source 2 and the light detector 4.
  • the optical barrier element 7 is configured to avoid, or at least minimize, the light signal 20 to pass directly between the light source 2 and the light detector 4 (optical shorting of the light signal 20).
  • the optical barrier element 7 may be opaque or reflective to the wavelengths emitted by the light source 2.
  • Fig. 3 shows the measurement system 100 configured as an ear tag assembly destined to be attached to an outer ear of an animal, according to an embodiment.
  • the ear tag configuration can be useful in veterinary applications for monitoring the health of mammals such as pigs, cows, goats or lambs.
  • the measurement system 100 comprises an attachment device configured to hold the sensor part 1 and the enhancing part 5 in physical contact with two opposed surfaces of the outer ear (not shown).
  • the attachment device comprises a shaft assembly 31 provided on the sensor part 1 and a retainer member 34 provided on the enhancing part 5.
  • the shaft assembly 31 is provided with a tip 32 configured to pierce through the outer ear.
  • the shaft assembly 31 is configured to be received and mechanically locked to the retainer member 34, such that the sensor part 1 and the enhancing part 5 are attached and fixed to the outer ear (not shown).
  • the sensor part 1 has a first body 30 that can be made of plastic or any other suitable material.
  • the light source 2 and light detector 4 are mounted on a sensing side 37 of the first body 30 destined to physically contact the outer ear.
  • the light source 2 comprises two LEDs 2a, 2b and the light detector 4 comprises two photodetectors 4a, 4b.
  • the LEDs 2a, 2b may emit different wavelengths, e.g. 660 nm and 940 nm, as typically used for SpC>2 measurements. Alternatively, they may both emit the same wavelength, e.g. 940 nm for a simple detection of heart rate. Even for monochromatic detection, (i.e.
  • LEDs 2a, 2b when both LEDs 2a, 2b emit the same wavelength), there is an advantage to provide several light sources (LEDs) and light detectors (photodetectors) distributed on the sensing side 37 of the first body 30.
  • LEDs light sources
  • photodetectors photodetectors
  • the LEDs 2a, 2b and the photodetectors 4a, 4b are conveniently distributed around the shaft assembly 31.
  • the shaft assembly 31 also play the role of an optical barrier element 7, avoiding, or at least minimizing, direct transmission of the light signal 20 emitted from the LED 2a to the diagonally opposed photodiode 4a, and from the LED 2b to the diagonally opposed photodiode 4b.
  • the enhancing part 5 can comprise a second body 33, that can also be made of plastic or any other suitable material.
  • the reflector 6 can be included on a side of the second body 33 facing the sensing side 37 of the first body 30, when the sensor part 1 and the enhancing part 5 are attached.
  • the reflector 6 can comprise a metallic reflecting foil or any suitable reflecting coating or material.
  • the sensor part 1 can further comprise a control module (within casing 40, see below) configured to operate the light source 2 and the light detector 4.
  • the control module can be battery powered or can be configured to be remotely powered.
  • the control module can further comprise a remote communication element, such as an optical or radio wave communication device, notably using RFID and near field communication, the Bluetooth® transmission protocol, a near field communication protocol (NFC), a WiFi connection, or any other suitable remote communication element.
  • the control module is housed in a casing 40 provided on a side of the first body 30 opposed to the sensing side 37.
  • the control module can comprise a current source to operate the light source 2 and read-out electronics for the light detector 4.
  • the control module can further comprise a microprocessor and possibly a storage medium.
  • the control module can further comprise a remote communication element, such as listed above.
  • the control module can be powered by a battery or can be remotely powered, for example, by inductive coupling to a power emitter. Remotely powering the control module allows for avoiding replacing the battery which can be difficult on an animal. Remotely powering the control module also allows for reducing the weight of the measurement system 100 (ear tag) being worn at the animal's ear.
  • a power emitter may be conveniently installed in the animal's cage or, for animals living in an open field, at a location where the animal is regularly fed or go for water or salt.
  • the measurement system 100 may only function at specific moments, when the animal gets close to the power source.
  • the remote powering (wireless powering) may be stocked in a small rechargeable battery for continuous operation.
  • the remote powering (or remote charging or activating) of the measurement system 100 for veterinary applications can be applied to wearable devices other than the measurement system 100 presented herein.
  • the LEDs 2a and 2b can be alternatively turned ON and OFF, such as to only have one LED emit at a time.
  • the On-Off cycle for each LED 2a, 2b can comprise for example 100 ps of operation (ON), followed by 9.9 ms OFF. This cycle can be repeated continuously in a periodic way, in this example featuring one acquisition every 10 ms.
  • the detection of the light signal 20 emitted by each LED 2a, 2b can be performed with the photodiode 4a, 4b that is diagonally opposed to the operating LED 2a, 2b.
  • the photodiode 4a detects the light signal 20 emitted by the LED 2a and the photodiode 4b detects the light signal 20 emitted by the LED 2b.
  • This sequence allows the shaft assembly 31 to effectively block direct transmission of light signal 20 from the emitting LED 2a, 2b to the detecting photodiode 4a, 4b.
  • the measurement system 100 in the configuration of figure 3 can be used for heart rate detection.
  • the light signal 20 emitted during the LED ON and OFF phases are recorded (possibly stored in the storage medium).
  • Ambient light, measured when both diodes are OFF, can be subtracted from the recorded light signal 20 in order to remove the ambient component of the signal and obtain a background- free signal.
  • the background-free signal is then filtered, and a pulsatile part is extracted from the filtered background-free signal.
  • the pulsatile part result is then processed to extract physiological parameters including heart rate and inter-beat variability.
  • the heart rate and inter-beat variability can then be used in post-processing to determine others physiological parameters including stress level, respiration rate and/or animal illness or parturition.
  • the measurement system 100 can be used for the indirect measurement of hyperthermia or fever caused by health issues (infection or others).
  • Body temperature is an independent determinant of heart rate.
  • 10 beats per minute per degree (https://www.ncbj.nlm.nih.qov/pybmed/19700579) ⁇
  • 15 beats per minute per degree (https://www.ncbi.nlm.nih.gov/pmc/articles/PMC4774660/).
  • a wearable system such as the measurement system 100, can be used on farm animals to continuously monitor the heart rate of each animal at rest or sleeping.
  • basal heart rate This is called the "basal” or “resting” heart rate. It can be defined as the heart rate when a person is awake, in a neutrally temperate environment, and has not been subject to any recent exertion or stimulation, such as stress or surprise.
  • the basal heart rate is typical of each animal.
  • the history of basal heart rates can be stored (locally in the system or in a database) for each animal.
  • a change in basal heart rate can be an indicator of hyperthermia or fever.
  • indirect measurement of hyperthermia or fever using the measurement system 100 can be used to detect and track epizooties, for example by following hyperthermia or fever events in a group of animals (measured by measurement system 100) within a given geographic region. It is then possible to combine the measurement of hyperthermia or fever with localization information to follow geographic spread of epizooties.
  • the measurement of hyperthermia or fever using the measurement system 100 can thus be applied to public health issues whereby, for example, national veterinary service could follow hyperthermia or fever of livestock and perform an early detection and tracking of epizooty.
  • the measurement system 100 can also be used for human health monitoring.
  • the measurement system 100 can have the ear tag configuration shown in Fig. 3.
  • the measurement system 100 can also be implemented in other configurations such as to be worn as a piercing, in the ear, nose, eyebrows, belly button, tongue, lips, or on any other part of the body.
  • the piercing configuration can additionally fulfil an aesthetic function.
  • Fig. 4 shows the measurement system 100 according to an embodiment, wherein the attachment device comprises magnets 35 provided on the sensor part 1 and magnets 36 provided on the enhancing part 5.
  • the attachment device comprises magnets 35 provided on the sensor part 1 and magnets 36 provided on the enhancing part 5.
  • at least one magnet 35, 36 can be provided only in one of the sensor part 1 or the enhancing part 5.
  • the sensor part 1 or enhancing part 5 not comprising the magnet 35, 36 can include a counter element comprising a ferromagnetic material (not shown).
  • the measurement system 100 comprising the attachment device including a magnet 35, 36 can be advantageously used for long term monitoring applications.
  • the measurement system 100 can be worn on ears that should not be pierced, for instance horse's ears.
  • the measurement system 100 with the magnet attachment device can further be worn across a fold of a tissue 10 (such as skin) as schematically illustrated in Fig. 4.
  • Such arrangement of the measurement system 100 can be better adapted to a rapid, single-time determination of a physiological parameter.
  • the pressure applied on the body part 10 by the magnetic attraction between the sensor part 1 or the enhancing part 5 can advantageously contribute to blocking the flow of venous blood through the body part 10.
  • the pressure can be adapted to selectively allow arterial flow into the body part 10 and thus, procure an optical signal preferentially corresponding to arterial blood parameters without the disturbance of a large venous blood background.
  • the attachment device can be configured to apply a controlled pressure higher than the pressure of the venous blood between the sensor part 1 or the enhancing part 5 and the body part 10.
  • a controlled pressure higher than the pressure of the venous blood between the sensor part 1 or the enhancing part 5 and the body part 10.
  • Such applied pressure can remove influence of venous blood in the PPG signal and provide a signal corresponding to deeper structures under the skin 12, necessary for a more accurate measurement of SpC>2 or blood pressure.
  • the applied pressure can be between 0.5 kPA and 10 kPa (between about 5 and 80 mmHg).
  • the applied pressure can be between 1.5 kPA and 5 kPa (between about 10 and 40 mmHg).
  • the attachment device comprises a spring-loaded mechanism 50.
  • the spring-loaded mechanism 50 is configured to hold the sensor part 1 and the enhancing part 5 in physical contact with two opposed surfaces of the body part 10.
  • the spring-loaded mechanism 50 can be further configured to apply a predetermined pressure between the sensor part 1 and the body part 10, for example by adjusting the force of a spring 51.
  • the spring-loaded mechanism 50 can control the relative flow of venous and arterial blood into the tissue or body part 10 by varying the pressure applied between the sensor part 1 and the enhancing part 5.
  • the measurement system 100 is adapted for the detection of physiological parameters during a surgical operation, such as on a body part 10 comprising an internal body tissue.
  • a surgical operation such as on a body part 10 comprising an internal body tissue.
  • a possible example is the monitoring of blood oxygenation of an organ during an operation or for the identification of necrosed parts in an organ or tissue, e.g. the intestines, based on the optical detection of oxygenation.
  • the measurement system 100 comprising the spring-loaded mechanism 50 can be easily mounted on body extremities such as fingers, toes or ear lobes.
  • the measurement system 100 disclosed herein has the light source 2 and the light detector 4 on the same side of the body part 10, such that the light signal 20 traverse the body part 10 two times before reaching the light detector 4, as discussed above.
  • the attachment device can comprise an adhesive device configured to adhere the sensor part 1 and/or the enhancing part 5 to a surface of the body part 10.
  • the sensor part 1 and/or the enhancing part 5 can be attached to the body part 10 by using an adhesive film.
  • the measurement system 100 can be included in a hearing aid destined to be worn on a human (or animal) ear.
  • the hearing aid can comprise a behind the ear (BTE) or in the ear (ITE) type, both comprising a case which hangs behind the pinna and an ear mold or dome tip that inserts into the external auditory canal.
  • BTE and ITE hearing aids extend from the front side to the rear side of the ear.
  • the front side or the rear side of the hearing aid can be provided with the enhancing part 5 and the other side can be provided with the sensor part 1.
  • the enhancing part 5 can be placed behind the ear (behind the pinna), for example by using an adhesive device, and the sensor part 1 can be provided in the in-canal hearing aid.
  • the measurement system 100 included in a hearing aid can be advantageously used for measuring a parameter such as SpC ⁇ .
  • This parameter is typically measured from the comparison of two optical signals at different wavelengths, emitted by two distinct LEDs.
  • a correct determination of the SpC>2 requires that the optical paths of the two optical signals are equivalent. Since the position of the two LEDs is not the same, the path-equivalence condition is hard to guarantee in a thin, sparsely vascularized body part such as the outer ear.
  • a configuration as proposed by the present invention increases the length of the optical path from the emitter to the detector and also enhances the random diffusion of the light through the tissue on its path from the emitter to the detector, thus contributing to a homogenization of the effective path, with less sensitivity to the exact position of the light emitter.
  • the sensor part 1 may be a hand-held device, including, for instance a smartphone, provided with a light source 2 and light detector 4.
  • the light-emitting diode flashes (LEDs) of the smartphone can be used for the light source 2.
  • the light detector 4 can be the smartphone camera.
  • the light source 2 and light detector 4 can be dedicated devices added to the smartphone.
  • the enhancing part 5 can be attached to a surface of the body part 10 by using an adhesive device as described above.
  • the enhancing part 5 can be held temporarily with the hand.
  • the enhancing part can be a sub-cutaneous implanted element (see below). In that case, the hand-held device, for instance a smart phone, can be pressed against the surface of the body part 10 covering the enhancing part 5.
  • the enhancing part 5 is configured to be implanted within the body part 10.
  • the enhancing part 5 can be implanted under the skin, for example, in a region of the belly, arm, leg, etc.
  • the enhancing part 5 comprising the reflective element 6 is preferably made of a biocompatible material, such as a biocompatible soft polymeric material.
  • the enhancing part 5 can consist of a reflective material being reflective at the wavelengths used by the light source 20.
  • the enhancing part 5 can comprise a polished or roughed disc made of a biocompatible metal or clear-colored ceramic.
  • the form and size of the enhancing part 5 can be chosen according to comfort and biocompatibility criteria for the intended application and region of the body to be monitored.
  • the enhancing part 5 can further comprise magnets or ferromagnetic material to facilitate the relative positioning of the sensor part 1 on the body part 10, as well as regulating the pressure exerted by the sensor part 1 on the body part 10.
  • the sensor part 1 of the exemplary embodiment of Fig. 6 can comprise a hand-held device, for example a smart phone.
  • the measurement system 100 in the configuration of Fig. 6 is advantageous for monitoring involving complex optical analysis, such as recognizing spectral signatures from deep tissues across a continuous range of the spectrum, especially when the analysis must be performed frequently.
  • the measurement system 100 comprising the implanted enhancing part 5 can be used to reliably detect in-vivo glucose concentration.
  • the value of detected glucose concentration can further be used to control an implanted insulin pump in order to dose the amount of insulin to be injected.
  • One current problem with the measurement of glucose concentration through the skin 12 when using a conventional reflection-based optical measurement system is the little amount of light that is back-scattered towards the detector, and the fact that most of the detected light is reflected at the external layers 11 of the epidermis, characterized by a low degree of vascularization.
  • the enhancing part 5 By implanting the enhancing part 5 at a convenient depth under the skin, e.g. in the subcutaneous tissue 13, the amount of light signal 20 reflected towards the light detector 4 can be increased by at least one order of magnitude.
  • the amount of light signal 20 reflected can be further increased when the light source 2 comprises a laser source, emitting a collimated beam that can be reflected towards the light detector 4 with good directionality.
  • the light source 2 can comprise at least a tunable laser or a plurality of light sources, the tunable light source or a plurality of light sources emitting a plurality of light signals 20 at different wavelengths.
  • the measurement system 100 is thus adapted for performing spectroscopic detection of biomolecules in blood and/or for the measurement of biomolecule concentration in blood.
  • the implantable enhancing part 5 can also be used in a configuration where the sensor part 1 is remote from the body part 10.
  • Fig. 7 shows the measurement system 100 according to yet another embodiment, where the enhancing part 5 is configured to be implanted within the body part 10.
  • the sensor part 1 is remote from the monitored subject 80 and thus from the body part 10.
  • the light source 2 may comprise a lamp configured to project a light signal beam 20 destined to illuminate an illuminated area. More generally, the light source need not be projected towards the illuminated area having a given directionality.
  • the light source may comprise diffuse light from standard lighting sources or even natural day light.
  • a monitored subject 80 a pig in the example of Fig. 7, is located within the illuminated area, the light signal beam 20 is reflected by the enhancing part 5 implanted in the body part 10, toward the light detector 4.
  • the light detector 4 can comprise a camera provided with imaging optics configured to generate a local image 81 of the monitored subject 80 from the reflected light signal 23.
  • the image at the high contrast region 61 has a strong component of light reflected at the enhancing part 5 under the skin and not at the external surface of the skin.
  • the lamp 2 can be configured such as to illuminate the whole area comprising the monitored subject 80.
  • the lamp 2 can have a wide illumination cone.
  • the lamp 2 can be configured to scan a larger area (large cage or farmyard) comprising the monitored subject 80.
  • the light source 2 can comprise a LED lamp emitting infrared light, e.g. at 940 nm, for good epidermal penetration and capture of blood irrigation signatures.
  • the light source 2 can comprise a halogen lamp and include filters to select a convenient range of wavelengths.
  • the light source 2 may further comprise collimating optics to direct the light signal 20 beam towards the illuminated area.
  • the light source may be diffuse light from standard illumination lamps or direct or diffuse natural sun light.
  • the light source 2 is ambient day light.
  • the light detector 4 can comprise a digital camera provided with imaging optics to produce the global image 81 of the illuminated area.
  • the camera may additionally comprise optical filters to select a convenient wavelength or range of wavelengths emitted by the light source 2.
  • the reflecting element 6 of the enhancing part 5 can be advantageously designed as a cat's eye or reflex reflector, which provides strong reflectivity directed back towards the light source 2 for a large range of incidence angles. In that way, there is no need to adjust the angle of the projected beam 20 to be perpendicular to the reflective plane of the enhancing part 5. Instead, it is enough to place the detector 4 close to the light source 2, to ensure an efficient collection of the light signal reflected back by the enhancing part 5.
  • the light source 2 and the detector 4 can be integrated in a single mechanical support 70 or can be configured as physically separate devices.
  • the configuration of the light source 2 with respect to the light detector 4 is not limitative.
  • the implantable enhancing part 5 in combination with the remote sensor part 1 provides following advantages: higher reflectance of light coming from a defined depth under the body part 10 and comporting stronger physiological signatures than light just reflected from the outer layers of the body part 10. High contrast for easy identification and tracking of the high-contrast region image 61 of the enhancing part 5, enabling time-varying data collection from a well-defined unique spot.
  • Fig. 8a shows a side view and Fig.
  • the optical barrier element 7 can be arranged concentric between the light source 2 and the light detector 4. The axial symmetry of this sensor part 1 configuration allows for efficient reflected light collection.
  • optical barrier element 10 body part 11 external skin layers 12 deeper skin layers 13 subcutaneous tissue 15 surfaces of the body part 20 light signal 21 scattered portion of the light signal, diffuse reflection 22 direct transmission of light not interacting with the monitored tissue 23 reflected light signal

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Abstract

L'invention concerne un système de mesure optique (100) pour détecter des paramètres physiologiques d'un utilisateur, lequel dispositif comprend une partie capteur (1) comprenant une source de lumière (2) configurée pour émettre un signal lumineux (20) destiné à éclairer une partie corporelle (10) de l'utilisateur, et un détecteur de lumière (4) configuré pour recevoir le signal lumineux (20) qui a éclairé la partie corporelle (10). Le système de mesure optique (100) comprend en outre une partie amélioration (5) comprenant un élément réfléchissant (6), la partie capteur (1) et la partie amélioration (5) étant configurées pour coopérer avec la partie corporelle (10) de telle sorte que le signal de lumière (20) éclairant la partie corporelle (10) est réfléchi par l'élément réfléchissant (6), vers le détecteur de lumière (4). La partie capteur (1) et la partie amélioration (5) sont conçues pour être disposées au niveau de deux surfaces opposées (15) de la partie corporelle (10) de telle sorte que le signal de lumière (20) émis par la source de lumière (2) passe à travers la partie corporelle (10) et est réfléchi en arrière sur l'élément réfléchissant (6).
PCT/IB2020/056548 2020-07-13 2020-07-13 Système de mesure optique pour surveiller des paramètres physiologiques d'un utilisateur Ceased WO2022013592A1 (fr)

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Citations (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB2316171A (en) * 1996-07-29 1998-02-18 Thames Medical Ltd Pulse Oximeter
US6343223B1 (en) * 1997-07-30 2002-01-29 Mallinckrodt Inc. Oximeter sensor with offset emitters and detector and heating device
WO2002028274A1 (fr) * 2000-10-05 2002-04-11 Cybro Medical Ltd. Sphygmo-oxymetre et procede d'utilisation
US6654622B1 (en) * 1999-11-19 2003-11-25 Linde Medical Sensors Ag Device for the combined measurement of the arterial oxygen saturation and the transcutaneous CO2 partial pressure on an ear lobe
US20080269575A1 (en) * 2005-02-17 2008-10-30 Iddan Gavriel J Method and Apparatus for Monitoring Bodily Analytes
US20130085346A1 (en) * 2011-10-04 2013-04-04 National Taiwan University Of Science And Technology Real-time physiological signal measurement and feedback system
WO2016022295A1 (fr) 2014-08-06 2016-02-11 Valencell, Inc. Modules à capteurs physiologiques optiques avec réduction du bruit de signal
US20170065178A1 (en) * 2014-03-12 2017-03-09 Sony Corporation Measurement device and measurement method
US10078052B2 (en) 2014-08-28 2018-09-18 Apple Inc. Reflective surface treatments for optical sensors
EP3427657A1 (fr) 2017-07-14 2019-01-16 Koninklijke Philips N.V. Détecteur pour photopléthysmographe et procédé de fabrication d'un capteur pour photopléthysmographe
WO2019071222A1 (fr) * 2017-10-06 2019-04-11 Animal Health Analytics, Inc. Dispositif et système de surveillance de la santé d'un animal
US20190216400A1 (en) 2016-10-11 2019-07-18 Nokia Technologies Oy Skin Lifting for Photoplethysmography
WO2020060911A1 (fr) * 2018-09-19 2020-03-26 Valencell, Inc. Dispositif d'aide auditive avec capteur biométrique

Patent Citations (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB2316171A (en) * 1996-07-29 1998-02-18 Thames Medical Ltd Pulse Oximeter
US6343223B1 (en) * 1997-07-30 2002-01-29 Mallinckrodt Inc. Oximeter sensor with offset emitters and detector and heating device
US6654622B1 (en) * 1999-11-19 2003-11-25 Linde Medical Sensors Ag Device for the combined measurement of the arterial oxygen saturation and the transcutaneous CO2 partial pressure on an ear lobe
WO2002028274A1 (fr) * 2000-10-05 2002-04-11 Cybro Medical Ltd. Sphygmo-oxymetre et procede d'utilisation
US20080269575A1 (en) * 2005-02-17 2008-10-30 Iddan Gavriel J Method and Apparatus for Monitoring Bodily Analytes
US20130085346A1 (en) * 2011-10-04 2013-04-04 National Taiwan University Of Science And Technology Real-time physiological signal measurement and feedback system
US20170065178A1 (en) * 2014-03-12 2017-03-09 Sony Corporation Measurement device and measurement method
WO2016022295A1 (fr) 2014-08-06 2016-02-11 Valencell, Inc. Modules à capteurs physiologiques optiques avec réduction du bruit de signal
US10078052B2 (en) 2014-08-28 2018-09-18 Apple Inc. Reflective surface treatments for optical sensors
US20190216400A1 (en) 2016-10-11 2019-07-18 Nokia Technologies Oy Skin Lifting for Photoplethysmography
EP3427657A1 (fr) 2017-07-14 2019-01-16 Koninklijke Philips N.V. Détecteur pour photopléthysmographe et procédé de fabrication d'un capteur pour photopléthysmographe
WO2019071222A1 (fr) * 2017-10-06 2019-04-11 Animal Health Analytics, Inc. Dispositif et système de surveillance de la santé d'un animal
WO2020060911A1 (fr) * 2018-09-19 2020-03-26 Valencell, Inc. Dispositif d'aide auditive avec capteur biométrique

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