WO2017045976A1 - Dispositif et procédé de surveillance de migraine - Google Patents

Dispositif et procédé de surveillance de migraine Download PDF

Info

Publication number
WO2017045976A1
WO2017045976A1 PCT/EP2016/071001 EP2016071001W WO2017045976A1 WO 2017045976 A1 WO2017045976 A1 WO 2017045976A1 EP 2016071001 W EP2016071001 W EP 2016071001W WO 2017045976 A1 WO2017045976 A1 WO 2017045976A1
Authority
WO
WIPO (PCT)
Prior art keywords
region
migraine
indicative
subject
image data
Prior art date
Application number
PCT/EP2016/071001
Other languages
English (en)
Inventor
Maria Estrella Mena Benito
Ihor Olehovych Kirenko
Original Assignee
Koninklijke Philips 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 Koninklijke Philips N.V. filed Critical Koninklijke Philips N.V.
Publication of WO2017045976A1 publication Critical patent/WO2017045976A1/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
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • 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
    • 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
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/024—Detecting, measuring or recording pulse rate or heart rate
    • A61B5/02416—Detecting, measuring or recording 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
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/026—Measuring blood flow
    • A61B5/0261—Measuring blood flow using optical means, e.g. infrared light

Definitions

  • the present disclosure relates to a migraine monitoring device and to a migraine monitoring method. More particularly, the present disclosure relates to refinements in such devices and methods. In a general context, the present disclosure relates to unobtrusive monitoring methods, devices and systems for migraine monitoring, migraine detection, migraine assessment, migraine documentation, and migraine prediction.
  • the present disclosure further relates to a corresponding computer program implementing the above migraine monitoring method.
  • US 5,840,018 A discloses a method and a system for real-time determination of variations in effective diameter of cranial blood vessels, to provide an indication of migraine activity, wherein the method comprises determining the blood flow rate to the brain of a subject; determining the intracranial blood flow rate in selected blood vessels; and comparing said intracranial blood flow rate with said determined blood flow rate to the brain thereby to determine a change in said intracranial blood flow rate relative to said blood flow rate to the brain, indicating a corresponding change in the effective diameter of the preselected blood vessel.
  • BPI blood pulsation imaging
  • Migraine is a medical disorder which usually causes a pounding, throbbing headache on one side of the head. The pain may be very bad and hurt so much that a person may have a hard time doing anything. Most migraines cause a headache and nausea and might make the person dizzy or very sensitive to bright lights or loud noises. Some migraines are preceded or accompanied by sensory warning symptoms (aura), such as flashes of light, blind spots, or tingling in an arm or leg. Other senses can change before or during a migraine attack, and the migraineur may sense strange smells or tastes. Migraines can last a long time. Most migraines only last about four hours. Some can last up to 72 hours.
  • migraine headache is a costly neurological disease in well-developed countries such as in the European Union and the United States.
  • Migraine may be classified, e.g. based on how often attacks happen in a month: If a person suffers from migraine symptoms for less than fifteen days, the migraine is called episodic migraine. If it happens more than fifteen days, it is called chronic migraine. Chronic means it happens over a long amount of time. Some people who start their migraine experiences with getting episodic migraines may start to get chronic migraines later. Even nowadays, exact causes for migraine cannot be fully explained.
  • migraine diagnosis In everyday life of people experiencing migraine (so-called migraineurs), migraine diagnosis, particularly the prediction and/or detection of migraine attacks is a huge and crucial challenge.
  • migraine diaries are commonly used, wherein the migraineur basically has to keep a diary so as to trace the course of migraine attacks and non-migraine periods over a sufficiently long time so as to allow conclusions as to the nature and possible patterns of the recurrent migraine attacks.
  • migraine is characterized by symptoms that include more than just the typically to-be-expected headache. This may particularly apply to younger people, children, etc.
  • mapping of blood pulsations in the face of migraineurs is proposed, using an imaging techniques so as to establish 2D-imaging of blood pulsation parameters.
  • a characteristic phenomenon of transverse waves of facial blood perfusion in migraineurs in contrast to healthy subjects who showed synchronous blood delivery to both sides of the face is described.
  • amplitude of blood pulsations was observed to be symmetrically distributed over the face of healthy subjects, but asymmetrically in migraineurs and subjects with a family history of migraine.
  • migraine patients a remarkable correlation between the side of unilateral headache and the direction of the blood perfusion wave may be detected. Accordingly, it is suggested that migraine is associated with lateralization of blood perfusion and asynchronous blood pulsations in the facial area, which could be due to essential dysfunction of the autonomic vascular control in the face.
  • optical imaging - as a matter of fact - also captures potentially disturbing and distorting artifacts which are somewhat inherent in the detected signals.
  • One approach to this problem is to provide stable conditions which may be also referred to as laboratory conditions. This may involve a well-defined illumination, a defined and fixed position of the monitored subject, etc. However, these laboratory conditions cannot be ensured in everyday life.
  • migraine monitoring and migraine diagnosis which may be implemented in respective methods and devices. More particularly, it is an object of the present disclosure to provide a migraine monitoring device and a corresponding method that enable increased migraine detection reliability and that shows improved performance in everyday life environments. Further, it would be advantageous to provide an enhanced migraine monitoring device and method that enable to utilize standard (off-the-shelf) monitoring equipment, for instance standard illumination sources, common cameras, including webcams, consumer digital cameras, and mobile phone/tablet cameras, etc.
  • standard illumination sources for instance standard illumination sources, common cameras, including webcams, consumer digital cameras, and mobile phone/tablet cameras, etc.
  • a migraine monitoring device comprising:
  • an imaging unit arranged to observe a subject, and to generate image data representing blood perfusion at a skin area of the subject
  • a detector unit arranged to detect a characteristic spatial blood perfusion discrepancy between at least two regions of the skin area
  • a data conditioning unit arranged to condition the image data, taking into account reference image data obtained from at least one reference region of the subject,
  • the data conditioning unit is arranged to process a plurality of regions, wherein the regions comprise a first indicative region, at least one second indicative region, and at least one of a ballistocardiographic motion reference region and a blood perfusion reference region,
  • the detected blood perfusion discrepancy is indicative of a migraine-related symptom
  • reference image data is used as a reference for compensating non- migraine-related influences.
  • This aspect is based on the insight that migraine detection based on blood perfusion monitoring, as described in the above Zaproudina N. et al, is still prone to disturbances and distortions which are inherent to everyday life environments. Therefore, it is proposed in accordance with the above aspect to utilize reference data obtained from at least one reference region may provide a baseline which enables to attenuate or even discard non- migraine related signal components, at least to a great extent. Accordingly, several regions may be defined and monitored, at least over a certain amount of time. At least some of these regions are in a (skin) portion of the subject of interest which is typically affected by migraine.
  • At least one additional reference region is provided which may represent a (skin) portion of the subject which is generally not affected by migraine or which may be otherwise used as a reference marker, for instance for motion detection which may involve also the detection of vascular motion attributable to circulatory processes.
  • a main aspect of the present disclosure relates to a beneficial combination of non-obtrusive monitoring and detected characteristics, particularly spatial signal discrepancies in the blood perfusion of migraine patients, and to refinements thereof.
  • non-obtrusive or unobtrusive monitoring relates to non-contact monitoring, particularly to remote unobtrusive monitoring of patients and further subjects of interest. Accordingly, as used herein, unobtrusive non-contact monitoring approaches may dispense with the need of applying contact sensors and similar equipment which may be experienced by the monitored subject as being unpleasant.
  • PPG photoplethysmographic imaging
  • the heart beat rate and respiratory rate can be extracted.
  • the pulsation of arterial blood causes changes in light absorption. Those changes are observed with a photodetector (or an array of photodetectors) form a PPG (photoplethysmography) signal. Pulsation of the blood is caused by the beating heart, i.e. peaks in the PPG signal correspond to the individual beats of the heart.
  • WO 2012/098289 Al disclosing a method for visualization of cardiovascular pulsation waves, in which method the living body is illuminated with light penetrating through the skin of the body for interacting via absorption and/or scattering with a vascular system of the living body, wherein the light reflected from the living body is collected in the form of a focused frame into an image capturing device, and a series of frames is captured by the image capturing unit.
  • the spatial blood perfusion discrepancy may relate to an at least slight discrepancy between the blood pulsation behavior at different skin regions of the subject.
  • blood pulsation is reflected in at least minute fluctuations of the skin color of the subject of interest and may be therefore detected by appropriate imaging units which may, as an example, include CCD-sensors, CMOS-sensors, etc.
  • imaging units may, as an example, include CCD-sensors, CMOS-sensors, etc.
  • an at least partially periodic phenomenon may be detected, namely the blood pulsation waveform.
  • this waveform somewhat varies at different regions, when a migraine attack occurs, or is at least impending.
  • the data conditioning unit is arranged to discard at least one of ballistocardiographic motion artifacts and vasoconstriction- indicative artifacts in the image data, the artifacts being non-indicative of the migraine-related symptom.
  • the conditioning unit may be operated or trained to detect non- indicative patterns by comparing data obtained from at least one reference region and data obtained from at least one indicative (migraine affected) regions.
  • ballistocardiographic motion may be a main reason for a reduced performance of migraine monitoring devices.
  • vasoconstriction may impede the quality and accuracy of migraine detection. Typically, vasoconstriction may be reflected by local drops in an amplitude of the waveform detected signal. It has been observed that vasoconstriction, particularly local differences of
  • vasoconstriction may be indicative of migraine.
  • vasoconstriction may be also caused by other reasons or conditions than migraine-related ones.
  • a reference region for vasoconstriction may be used so as to discriminate non-indicative components.
  • Ballistocardiographic motion is caused by the heartbeat as such and reflected in minute pulsations of tissue portions that are provided with blood vessels.
  • Cardioballistographic motion may cause a non-indicative temporal discrepancy between signals of indicative regions which is, however, not indicative of migraine.
  • a respective reference region may provide a "baseline" or reference signal so as to attenuate or discard the non- indicative ballistocardiography-related signal components.
  • the data conditioning unit is arranged to process a plurality of regions, wherein the regions comprise a first indicative region, at least one second indicative region, and at least one of a motion reference region and a blood perfusion reference region.
  • the regions may be separate from one another. However, at least some of the regions may at least partially overlap one another.
  • at least the two indicative regions are separate and offset from one another, such that a respective comparison reveals the desired signal discrepancy.
  • the device further comprises a region selecting unit arranged to define at least three regions comprising the at least one reference region and the at least two indicative regions in the image data obtained from the imaging unit. Needless to say, the region selecting unit may be also arranged for (overall) motion compensation, i.e.
  • the region selecting unit may be arranged for skin detection, head detection, nose detection, ear detection, eye detection, mouth detection, chin detection, etc.
  • the region selecting unit is arranged to automatically select and track the at least three regions without the need of human intervention, provided that the subject of interest is still in sight and in an appropriate orientation.
  • the region selecting unit may be arranged for manual intervention, for instance for an initial manual selection of the at least three regions.
  • the region selecting unit is arragned to define a first region of interest that is arranged as a first indicative region in a facial portion of the subject, a second region of interest that is arranged as a second indicative region in a facial portion of the subject, wherein the second region of interest is spaced apart from the first indicative region, a third region of interest as a motion reference region that is arranged as a ballistocardiographic motion reference region, and a fourth region of interest that is arranged as a blood perfusion reference region in a non-facial skin portion of the subject.
  • the region selecting unit may be arranged to discriminate a facial (skin) portion and a non-facial skin portion of the subject of interest, and a transitional portion, wherein the transitional portion comprises a skin-to- background transition.
  • the transitional portion may comprise a face-to- background transition or a cheek-to-background transition.
  • a present or impending migraine attack may be reflected in a characteristic blood perfusion/pulsation behavior at the head or face of the subject of interest.
  • the characteristic discrepancy that is highly- indicative of migraine is typically present between distinct portions of the face or head of the subject of interest.
  • a non-facial or non-head skin portion of the subject is therefore generally not afflicted with migraine-related blood perfusion variations.
  • the non- facial skin portion is a proper reference region for detecting non-migraine related artifacts.
  • the transitional portion may be used to detect (overall) macroscopic motion of the subject of interest, but also ballistocardiographic (microscopic) motion at the skin of the subject as such which may involve minute recurring (periodic) extensions and contractions.
  • motion of the skin with respect to the background may be detected in the transitional portion and may be utilized as a further reference for migraine detection.
  • the imaging unit is a remote monitoring imaging minute, particularly a remote photoplethysmographic monitoring imaging unit or a remote laser speckle imaging unit, wherein the detector unit is arranged to detect color fluctuations in the obtained image data that are indicative of blood perfusion.
  • the color fluctuations may be attributed to circulatory processes in the subject of interest.
  • Laser speckle imaging also referred to as Laser Speckle Contrast Imaging (LSCI) is an alternative unobtrusive method for monitoring blood perfusion in a subject of interest.
  • LSCI Laser Speckle Contrast Imaging
  • Lisa M. Richards et al. "Low-cost laser speckle contrast imaging of blood flow using a webcam", Biomed Opt Express, 4(10): 2269-2283 (2013), describing new approaches to laser speckle contrast imaging utilizing standard (off-the-shelf) monitoring equipment.
  • the imaging unit is arranged to detect visible radiation.
  • visible radiation may be referred to as the portion of the electromagnetic spectrum that is visible to a human eye (e.g., a wavelength portion between 380 nm and 780 nm (nanometers)).
  • standard imaging units may be utilized.
  • the imaging unit may be arranged to detect non- visible radiation, for instance infrared radiation, near- infrared radiation, or ultraviolet radiation.
  • the imaging unit may be combined with appropriate radiation sources.
  • Non-visible radiation may be utilized when the device is at least temporarily used for monitoring resting or sleeping patients, for instance.
  • the remote monitoring imaging unit may be arranged as a non- contact and a non-obtrusive unit. Generally, the remote monitoring imaging unit may be arranged at a distance from the to-be-observed subject. This may on the one hand reduce any discomfort experienced by the user. On the other hand, remote imaging is susceptible to external influences which may cause relatively huge distortions which need to be
  • the detector unit is arranged to detect at least one of a spatial discrepancy between amplitudes of photoplethysmographic signals obtained from the observed region and a spatial discrepancy between phases of photoplethysmographic signals obtained from the observed regions. Both characteristics may be utilized for migraine detection.
  • the detector unit is arranged to detect both amplitude discrepancy and phase discrepancy so as to further improve the reliability and accuracy.
  • the detector unit is arranged to detect a migraine-related vasoconstriction-indicative signal in an observed region, particularly in a nasal region. This may even further improve the validity and reliability of the migraine detection.
  • vasoconstriction may be reflected by local drops in the amplitudes.
  • the detector unit is arranged to detect a characteristic spatial blood perfusion discrepancy between a right facial side of the subject, and a left facial side of the subject.
  • a characteristic spatial blood perfusion discrepancy between a right facial side of the subject typically no migraine-indicative discrepancy between the right facial side and the left facial side of the subject can be detected.
  • typically also no discrepancy can be detected when no migraine attack is present or, at least, impending.
  • a characteristic signal discrepancy between the right facial side and the left facial side may be detected. An evolvement of the discrepancy may be monitored and traced over time which may be used for drawing further conclusions therefrom.
  • the effect of medication against migraine may be observed in this way. Further, it has been found out that even when no (macroscopic) migraine symptoms (headache, etc.) are present, already at least a slight signal discrepancy between the right side and the left side of the subject can be detected which may be used to reliably predict an imminent migraine attack.
  • the first reference region may be arranged in the right or the left facial side of the subject, and the second referenced region may be arranged in the opposite one.
  • the detector unit is further arranged to detect at least one of an amplitude asymmetry and an asynchronicity of facial blood perfusion between different observed facial regions of the subject. This may involve the detection of an amplitude asymmetry (non-symmetry) and an asynchronicity (non- synchronicity) of the PPG waveform (photoplethysmographic waveform) obtained from the different observed regions.
  • an analyzing unit is provided which is arranged to assess an actual migraine status based on at least one of model-based data and empirically obtained data.
  • the device may alert the subject of an imminent or an actual migraine attack.
  • the device may be capable of monitoring, assessing and evaluating the effect of migraine medication.
  • the actual migraine status may be assessed based on a combination of model-based data and empirically obtained data.
  • Empirically obtained data may be obtained from the subject itself.
  • empirically obtained data may be obtained from reference subjects, e.g. representative healthy and/or migraine-suffering subjects.
  • the analyzing unit may be arranged to record or log the migraine status of the subject over a long period.
  • the device may basically automatically keep the subject's migraine diary. This is particularly beneficial for children and further persons which are not capable of handling the diary by themselves.
  • An automatic or semi-automatic (computer-aided or device-aided) assessment of the actual migraine status may have the further advantage that also in cases where no typical migraine symptom is present (e.g., no typical migraine-related headache), an assessment as to whether or not a migraine state is present can be made.
  • a migraine monitoring method comprising the following steps:
  • observing a subject including generating image data representing blood perfusion at a skin area of the subject,
  • conditioning the image data taking into account reference image data obtained from at least one reference region of the subject,
  • the step of conditioning involves processing a plurality of regions, wherein the regions comprise a first indicative region, at least one second indicative region, and at least one of a ballistocardiographic motion reference region and a blood perfusion reference region, and
  • the detected blood perfusion discrepancy is indicative of a migraine-related symptom
  • reference image data is used as a reference for compensating non- migraine-related influences.
  • a migraine monitoring device in accordance with the present disclosure is operated in accordance with the above method.
  • the step of conditioning the image data comprises: detecting at least one of ballistocardiographic motion artifacts and
  • vasoconstriction-indicative artifacts in the image data wherein the detected artifacts are non- indicative of the migraine-related symptom
  • the non-indicative artifacts would have an influence on the detected signal (waveform), but are not attributable to migraine symptoms.
  • the method further comprises:
  • a first region of interest particularly a first indicative region in a facial portion of the subject
  • a second region of interest particularly a second indicative region in a facial portion of the subject, that is spaced apart from the first indicative region
  • a third region of interest as a motion reference region, particularly a ballistocardiographic motion reference region,
  • a fourth region of interest particularly a blood perfusion reference region in a non-facial skin portion of the subject
  • a computer program which comprises program code means for causing a computer to perform the steps of the method as discussed herein when said computer program is carried out on that computer.
  • the computer is coupled with an arrangement in accordance with at least one embodiment of the monitoring device as discussed herein when the program is executed.
  • the program code (or: logic) can be encoded in one or more non-transitory, tangible media for execution by a computing machine, such as a computer.
  • the program code may be downloaded over a network to a persistent memory unit or storage from another device or data processing system through computer readable signal media for use within the system.
  • program code stored in a computer readable memory unit or storage medium in a server data processing system may be downloaded over a network from the server to the system.
  • the data processing device providing program code may be a server computer, a client computer, or some other device capable of storing and transmitting program code.
  • the term "computer” may stand for a large variety of processing devices. In other words, also mobile devices having a considerable computing capacity can be referred to as computing devices, even though they provide less processing power resources than standard "computers". Needless to say, such a “computer” can be part of a medical device and/or system. Furthermore, the term “computer” may also refer to a distributed computing device which may involve or make use of computing capacity provided in a cloud environment. The term “computer” may also relate to medical technology devices, fitness equipment devices, and monitoring devices in general, that are capable of processing data.
  • Fig. 1 shows a schematic block diagram of an exemplary embodiment of a migraine monitoring device in accordance with the present disclosure
  • Fig. 2 shows a simplified schematic representation of an image frame representing an observed subject of interest
  • Fig. 3 shows an illustrative signal chart representing an exemplary photoplethysmographic signal (PPG signal);
  • Fig. 4 shows an illustrative signal chart representing a first and a second photoplethysmographic signal, wherein an amplitude discrepancy between the first and the second signal is present;
  • Fig. 5 shows an illustrative signal chart representing a first and a second photoplethysmographic signal, wherein a phase discrepancy between the first and the second signal is present;
  • Fig. 6 shows an illustrative block diagram representing several steps of an exemplary embodiment of a migraine monitoring method in accordance with the present disclosure
  • Fig. 7 shows another illustrative block diagram representing several steps of another exemplary embodiment of a migraine monitoring method in accordance with the present disclosure.
  • a migraine monitoring or migraine detecting device 10 in accordance with at least some embodiments of the present disclosure is shown in Fig. 1.
  • the device 10 shall be understood as a migraine monitoring device.
  • the device 10 may be also arranged as a migraine tracking, migraine detecting, migraine predicting device, or a combination thereof.
  • the device 10 may comprise a distributed structure, i.e. at least some components thereof are arranged remote or separate from other components.
  • the device 10 may comprise an integral or integrated arrangement.
  • mobile devices such as mobile phones, tablet computers, mobile computers, etc. are referred to.
  • the device 10 comprises an observing module 12 and a processing module 14.
  • the observing module 12 comprises at least one imaging unit 16 which may be arranged as a camera unit comprising at least one imaging sensor, such as a CCD-sensor or a CMOS-sensor.
  • imaging sensor such as a CCD-sensor or a CMOS-sensor.
  • on-board cameras provided in mobile computing devices, mobile phones, etc. may be utilized.
  • separate imaging units 16 may be utilized, for instance separate cameras such as so-called webcams, action cams, etc.
  • the imaging unit 16 may be arranged as a visible light imaging unit, a non- visible light imaging unit, or a combination thereof.
  • visible light shall refer to the range of electromagnetic radiation that is visible to the human eye.
  • non- visible radiation or light shall refer to portions or ranges of the electromagnetic spectrum that are not visible to the human eye (i.e. infrared radiation, ultraviolet radiation, etc.).
  • the observing module 12 may be provided with or coupled to appropriate radiation sources, such as visible light sources and/or non-visible light sources. Needless to say, also already present ambient light sources may be utilized, since the device 10 is generally arranged as a non-obtrusive, non-contact remote detection device.
  • the processing modules 14 may arranged as an integrated processing module or a distributed processing module. I.e., at least some of the components thereof may be embodied in separate hardware. However, also at least some of the components of the processing module 14 may be embodied by or may share the same common hardware units. Further, one or more components of the processing module 14 may be implemented in discrete hardware. However, also off-the-shelf computing and processing devices may be utilized, such as standard computing environments (including desktop computers, mobile computers, mobile phones, server-client environments, distributed computing environments, cloud computing environments, etc.). Hence, components of the processing module 14 may be arranged as virtual components defined by appropriate software code.
  • the processing module 14 in accordance with the embodiment shown in Fig. 1 comprises a region selecting unit 18, a data conditioning unit 20, a detector unit 22, and an analyzing unit 24. Further, an input interface 26 and an output interface 28 may be provided. Via the input 26, image data obtained by the observing module 12 may be transmitted to the processing module 14. Typically, the image data comprises an image stream representing at least part of a subject of interest.
  • the processing module 14 may be provided with or coupled to a memory unit 30.
  • the memory unit 30 is arranged as a separate memory unit which is coupled to at least the analyzing unit 24.
  • the region selecting unit 18, the data conditioning unit 20, and the detector unit 22 may be provided with or coupled to the same or a separate memory unit 30.
  • Fig. 2. showing an exemplary image frame 32 provided in the image data captured by the observing module 12, particularly the at least one imaging unit 16 thereof.
  • the image frame 32 represents a forehead portion of an observed subject 34.
  • the image frame 32 may contain a head portion 36 including a facial portion 38 of the subject 34.
  • at least one non- facial portion 40 may be provided in the image frame 32.
  • a so-called transition portion 42 is provided.
  • the transition portion 42 includes a skin-to-background or face-to- background transition, and is preferably a high-contrast portion (i.e., a relatively sharp edge between the subject 34 and the background portion may be detected).
  • regions of interest that may be processed by the processing module 14 are indicated in Fig. 2 by dashed blocks.
  • the regions of interest may cover a basically rectangular portion, but may also cover non-rectangular or even freeform portions, depending on the actually utilized region selecting algorithm or procedure.
  • a first region of interest is indicated by reference numeral 44.
  • a second region of interest is indicated by reference numeral 46.
  • a third region of interest is indicated by reference numeral 48.
  • a fourth region of interest is indicated by reference numeral 50.
  • a nasal region of interest is indicated by reference numeral 52.
  • the first region 44 may be also referred to as first indicative region.
  • the second region 46 may be also referred to as second indicative region.
  • the first region 44 and the second region 46 are arranged on respective sides of the face of the subject 44. In other words, one of the first and second region 44, 46 is arranged the right side (with respect to the vertical axis of symmetry of the face), whereas the other one is arranged in the left side.
  • the first region 44 and the second region 46 are selected since in migraine-experiencing patients a characteristic discrepancy between blood-perfusion signals of the respective regions 44, 46 may be detected.
  • the first region 44 may be referred to as right side region, and the second region 46 may be referred to as left side region (as seen from the perspective of the subject 34).
  • the supplemental or auxiliary regions 48, 50, 42 may be also referred to as reference regions. Region 48 covers at least part of the transition portion 42.
  • motion reference data may be obtained since macroscopic and/or microscopic motion of the subject 34 with respect to a steady motion reference (background, camera-based reference, etc.) can be detected.
  • so-called ballistocardiographic motion which is attributable to blood pulsation in blood tissues may be detected in this way and, so-to-say, removed from the signals obtained from the indicative regions 44, 46 so as to attenuate or level off these non- migraine-related influences.
  • the fourth region 50 basically comprises a non-facial skin portion of the subject 34, for instance a neck portion.
  • a signal reference particularly a photoplethysmographic reference signal
  • the respective blood-perfusion or blood-pulsation indicative signals obtained from the fourth region 50 are not affected by migraine.
  • a proper signal reference is provided which enables to detect and attenuate or level off non-migraine related signal patterns in blood- pulsation indicative data.
  • the nasal region 52 may be defined and utilized which covers at least a portion of the nose of the subject 34. It has been observed that at the nose or adjacent to the nose, so-called vasoconstriction-related signal patterns may be detected which may be caused by non-migraine -related reasons and which may therefore distort the obtained signals and mitigate the detection accuracy. Hence, proper correction may further improve the reliability of migraine detection.
  • the region selecting unit 18 of the processing module 14 may be arranged for automatically defining and selecting appropriate regions 44, 46, 48, 50, 52.
  • the region selecting unit 18 may utilize and implement skin-detection algorithms, face-detection algorithms, edge-detection algorithms, and further pattern-detection algorithms.
  • the region selecting unit 18 may be operated or controlled by manual/human intervention, wherein for instance an operator of the device may initially define at least some of the respective regions, 44, 46, 48, 50, 52.
  • the operator may be the subject 34 itself, or may be an auxiliary person, medical staff, etc.
  • the region selecting unit 18 may be arranged for (overall) macroscopic motion detection and compensation.
  • macroscopic movements of the subject 34 with respect to the background may be tracked and compensated in the obtained signals.
  • microscopic movements, particularly ballistocardiographic movements may pass a respective motion-compensation algorithm and procedure for being further processed by the processing module 14.
  • the data conditioning unit 20 is arranged to condition the signals, particularly photoplethysmographic signals obtained from the indicative regions 44, 46.
  • the reference regions 48, 50, 52 may be utilized as a source for reference signals.
  • a distortion-compensated signal baseline may be obtained based on which the signals obtained from the indicative regions may be conditioned or rectified.
  • particularly migraine- indicative characteristic signal patterns remain in the signals obtained from the indicative regions 44, 46.
  • Corrected and conditioned data may be transmitted to the detector unit 22 which is arranged to detect characteristic signal discrepancies at or between the indicative regions 44, 46.
  • characteristic signal discrepancies As already explained above, migraine attacks and even impending or imminent migraine attacks may be reflected in a so-to-say asymmetric blood pulsation or blood perfusion between the right side and the left side of the face of the subject 34. Hence, the presence and level of the detected discrepancy is indicative of migraine or migraine- related symptoms.
  • the device 10 is arranged as a mobile device, and comprises a camera integrally arranged observing module 12, for measuring PPG signals, wherein the camera is arranged to observe a facial portion 38 and neck portion 40 of the subject of interest 34.
  • the device 10 is arranged to measure PPG signals at various wavelengths (e.g. RGB channels, R and IR channels, or even a combination thereof).
  • a computing or processing module 14 is provided which may form an integral part of the mobile device 10.
  • the device 10 may therefore also utilize screens, touchscreens, and wireless and wire communications for interaction with users and further devices (e.g. fitness trackers, computing networks, Sp02 sensors, etc.). Hence, the device 10 may provide feedback to the migraine sufferers and to further people.
  • PPG detection may involve defining a pattern of sub-regions (covering one or more pixels) of the skin of the subject 34 which may be processed accordingly.
  • a PPG imaging map of the spatial distribution of the PPG waveform (including shape, amplitude, and phase) may be provided and further processed.
  • a so-called blood perfusion imaging baseline may be obtained.
  • an initial version of the blood perfusion imaging baseline is generated in a basically migraine-free period wherein no symptoms are present in the subject 34.
  • a corresponding record may be referred to as blood perfusion imaging baseline.
  • the blood perfusion imaging baseline may be used as reference value for calculation of a migraine probability.
  • the device 10 is operated to monitors changes in the PPG pulsatility map over a defined period of time, by way of a spot-check monitoring or in a basically continuous fashion. Accordingly, the obtained PPG imaging maps at various wavelengths may be compared against blood perfusion imaging baselines acquired at the same wavelengths during the first, initial monitoring procedure. Then, differences in pulsatility of the PPG signals at the defined wavelengths may be calculated, dependent on the respective spatial location of the sub-regions of the skin portion. Consequently, a two-dimensional map of changes in the blood perfusion may be detected and registered.
  • the two-dimensional map may be further processed and analyzed, involving a comparison with the previously obtained blood perfusion imaging baseline, so as to estimate a pre-disposition or probability of having or becoming a migraine attack. Further on, mid-term and long-term measurement may be used to record the temporal and dynamic course of the migraine.
  • Figs. 3 to 5 represent so-called photoplethysmographic charts which may be obtained by remote
  • FIGs. 3, 4 and 5 an axis of abscissas indicates time.
  • An ordinate axis indicates a photoplethysmographic (PPG) signal which may be aggregated over a respective region of interest (which typically covers a plurality of image pixels).
  • PPG photoplethysmographic
  • Fig. 3 illustrates a reference chart 58 representing a reference PPG signal.
  • the reference PPG signal may be obtained from the PPG reference region 50, and may be therefore not affected by migraine.
  • FIG. 4 and Fig. 5 exemplarily illustrate PPG charts 60, 62 and 68
  • a characteristic signal discrepancy between the regions of interest 44, 46 may be present in the PPG-signals when a migraine attack is present or at least impending.
  • Fig. 4 illustrates a first PPG signal 60 having a first amplitude 64. Further, a second PPG signal 62 having a second amplitude 66 is illustrated. As with the embodiment of Fig. 4, the signals 60, 62 are basically synchronized (phase- synchronized) but exhibit different amplitudes. As both signals 60, 62 are obtained from the same subject, and from basically similar and comparable portions thereof, the discrepancy between the amplitudes 64, 66 is a measure for migraine-related symptoms, or migraine as such.
  • Fig. 5 illustrates a first PPG signal curve 68 and a second PPG signal curve 70.
  • the PPG signals 68, 70 have similar or basically equal amplitudes, but are phase-shifted, refer to the phase shift indicated by reference numeral 72 in Fig. 5. Since similar and comparable regions of the subject 34 are utilized for obtaining the PPG signals 68, 70, basically no or only a small phase shift may be expected in healthy subject that do not suffer from migraine. Basically the same applies to migraine patients which are in a basically migraine-free state. Therefore, the presence of a significant phase shift 72 is highly indicative of an impending, imminent or an actual migraine attack.
  • a combination of the discrepancies illustrated in Figs. 4 and 5 may be present. Therefore, both an amplitude difference and a phase shift may be present between PPG signals obtained from the first indicative region 44 and the second indicative region 46.
  • a spatial signal shape discrepancy between the indicative regions 44, 46 may be detected, particularly a characteristic spatial PPG signal discrepancy.
  • the detector unit 22 is basically arranged to detect migraine indicative signal discrepancies. Since the PPG data is conditioned by the conditioning unit 20, migraine detecting and migraine predicting reliability can be further improved.
  • the analyzing unit 24 is present in the processing module 14.
  • the analyzing unit may be arranged to assess an actual migraine status based on the detected signal discrepancy.
  • the analyzing unit 24 may utilize model-based approaches and approaches based on empirically obtained data. Respective algorithms and reference data may be provided by the storage unit or memory 30.
  • the analyzing unit 24 may be arranged to trace and track the course of migraine attacks and non-migraine periods and may therefore generate (or assist in generating) a migraine record or keep (or assist in keeping) a migraine diary. A long-term migraine record may be created in this way which may be used for improved and enhanced migraine treatment, and for assessing medication and therapeutic effects.
  • the processing module 14 may communicate with, or may be coupled with, appropriate output units, such as screens, speakers, control lights, etc. or with external data processing/exchanging/storing facilities.
  • a subject of interest is observed, wherein image data is generated.
  • image data representing blood pulsation or blood perfusion at a skin area of the subject of interest is generated.
  • non-contact monitoring or remote monitoring is utilized.
  • the step S10 preferably implements remote photoplethysmographic monitoring.
  • the image data obtained in the step S10 is conditioned.
  • Conditioning the image data may include deriving photoplethysmographic (PPG) signals from more than one region in the image data.
  • PPG photoplethysmographic
  • Indicative regions may be selected in the facial skin portion of the subject of interest.
  • Reference regions may be selected in a non-facial skin portion of the subject of interest.
  • Further reference regions may involve transitional regions including a skin-to-background transition for motion detection, and further reference regions, for instance a nasal region.
  • a signal baseline may be obtained which may be utilized to condition the signals obtained from the indicative regions so as to attenuate or discard non-migraine-related signal patterns.
  • a characteristic spatial blood perfusion discrepancy between at least two regions of the skin area is detected.
  • the characteristic discrepancy is preferably detected by comparing at least two indicative regions at different face portions of the subject of interest.
  • a significant discrepancy between the right face side and the left face side may be highly indicative of an imminent or an actual migraine attack.
  • the signal discrepancy may be reflected in PPG signals obtained from the indicative regions, and may for instance involve an amplitude discrepancy, a phase discrepancy, or, more generally, a signal shape discrepancy.
  • the detected blood perfusion discrepancy is indicative of at least one migraine-related symptom or, more generally, of an imminent or an actual migraine attack.
  • a further step S16 may follow which includes the assessment of an actual migraine status based on at least one model-based data and empirically obtained data.
  • Assessing the migraine status may also involve keeping a migraine diary or, more generally, generating a migraine record over a long period. Further, assessing the actual migraine status may also involve predicting an impending or imminent migraine attack since the
  • characteristic signal discrepancy at least in some cases, may be already detected when no clearly perceivable migraine symptom (headache, etc.) is present yet.
  • a further embodiment of the present disclosure relates to a processing module which is arranged to carry out additional steps so as to further enhance the migraine detection.
  • virtual (software) or discrete (hardware) processing blocks may be provided which, as a result, allow more reliable diagnosis of migraine in an uncontrolled (non- laboratory) environment.
  • the processing module is arranged to process image data captured by off-the-shelf (remotely-detecting) camera systems.
  • the processing module particularly the data conditioning unit and the detector unit thereof, comprise(s) the following blocks:
  • a spatial PPG reference extraction block arranged to measure a shape, amplitude and time of a PPG signal from non-face skin area (invariant to migraine impacts), wherein the data is used as a reference to estimate the amplitude discrepancy (e.g.
  • a temporal PPG reference extraction block arranged to measure PPG signals from at least two distinct regions of a face, affected by migraine
  • a motion analysis block arranged to differentiate an impact of ballistocardiography from the PPG phase discrepancy.
  • Fig. 7 shows a corresponding flowchart of an exemplary embodiment of the disclosure.
  • an image stream (video stream) of a subject of interest is provided.
  • the step S50 may involve an automatic or manual selection of several regions of interest in the image of a face and torso of the subject of interest (refer also to Fig. 2).
  • a PPG reference region contains a skin area outside a face (e.g. on a neck), where the shape and amplitude of a PPG signal is not affected by migraine.
  • a step S52 indicates corresponding signal processing action.
  • the respective region may be referred to as blood perfusion reference region.
  • a first indicative region and a second indicative region are selected on opposite sides of a face and contain skin areas with PPG signals affected by migraine.
  • first indicative region and second indicative region are selected on opposite cheeks of a person, since those may be regarded as sources of a strong PPG signal.
  • a step S54 indicates corresponding signal processing action for the first indicative region.
  • a step S56 indicates corresponding signal processing action for the second indicative region.
  • a motion reference region is selected, e.g. on the edge of the head (or another portion including a basically high-contrast edge), and may be used for detection and estimation of ballistocardiography motion, which might affect the analysis of phase difference between PPG signals of the first indicative region and the second indicative region.
  • a step S58 indicates corresponding signal processing action.
  • the respective region may be referred to as ballistocardiographic motion reference region.
  • a further step S60 relates to ballistocardiographic motion compensation based on motion reference data obtained from the motion reference region. Further, in case the amplitude of ballistocardiographic motion is within the range of amplitudes detected during previous measurements, the phase difference between PPG signals extracted from first indicative region and second indicative region may be calculated. If the phase difference between PPG signals from first indicative region and second indicative region is higher than the difference measured in previous sessions (preferably during periods of time without migraine pain), then quite probably an actual symptom (headache, for instance) is caused by migraine.
  • the amplitude and shape of PPG signals extracted from first indicative region and second indicative region are compared with a PPG signal extracted from the PPG reference region, step S62.
  • the step S62 may further include a comparison of the differences in shape and amplitude between the first indicative region/PPG reference region and the second indicative region/PPG reference region with corresponding differences calculated in previous periods of time, which may be referred to as baseline (preferably detected during periods of time without migraine symptoms). Large differences in shape and amplitude may basically point to a high probability of a migraine attack.
  • the results of the shape, amplitude, and phase asymmetry analysis are estimated to define an (overall) likelihood of an actual or imminent migraine attack, as a source of an actual symptom (headache, for instance).
  • an actual symptom headache, for instance.
  • migraine prediction based on the processed signals may be envisaged.
  • both the steps S60 and S62 are executed for monitoring migraine.
  • one of the steps, i.e. S60 or S62, may be executed to monitor migraine.
  • a device in accordance with the current disclosure may be suited for being used for diagnosis of migraine and management of migraine episodes over longer time periods.
  • the device may also process additional information, e.g. estimated hormonal changes (e.g. fluctuations of estrogen hormone in women) as an increasing factor of having a migraine attack.
  • the device may also automatically keep a migraine diary.
  • migraine management can be greatly facilitated, which may involve detecting and tracking of particular patterns of the (recurrent) migraine attacks.
  • These insights may be linked with potential triggers that might cause migraine attacks.
  • the device may also generate and provide data for enhancing post-processing analysis which may include the determination of further derived information and signals.
  • a computer program may be stored/distributed on a suitable medium, such as an optical storage medium or a solid-state medium supplied together with or as part of other hardware, but may also be distributed in other forms, such as via the Internet or other wired or wireless telecommunication systems.
  • a suitable medium such as an optical storage medium or a solid-state medium supplied together with or as part of other hardware, but may also be distributed in other forms, such as via the Internet or other wired or wireless telecommunication systems.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Signal Processing (AREA)
  • Surgery (AREA)
  • Medical Informatics (AREA)
  • Veterinary Medicine (AREA)
  • Physics & Mathematics (AREA)
  • Public Health (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • General Health & Medical Sciences (AREA)
  • Molecular Biology (AREA)
  • Animal Behavior & Ethology (AREA)
  • Artificial Intelligence (AREA)
  • Physiology (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)
  • Measuring And Recording Apparatus For Diagnosis (AREA)

Abstract

La présente invention concerne un dispositif de surveillance de migraine (10) et un procédé de surveillance de migraine. Le dispositif (10) comprend une unité d'imagerie (16) disposée pour observer un sujet (34) et pour produire des données d'image représentant une perfusion sanguine au niveau d'une zone de peau du sujet (34), une unité détecteur (22) disposée pour détecter un écart de perfusion sanguine spatial caractéristique entre au moins deux régions (44, 46) de la zone de peau, une unité de conditionnement de données (20) disposée pour conditionner les données d'image, en tenant compte de données d'image de référence obtenues depuis au moins une région de référence (48, 50) du sujet (34), l'écart de perfusion sanguine détecté étant indicatif d'un symptôme associé à la migraine et les données d'image de référence étant utilisées comme une référence pour compenser des influences non associées à la migraine. La présente invention concerne en outre un programme d'ordinateur correspondant.
PCT/EP2016/071001 2015-09-18 2016-09-07 Dispositif et procédé de surveillance de migraine WO2017045976A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
EP15185904 2015-09-18
EP15185904.8 2015-09-18

Publications (1)

Publication Number Publication Date
WO2017045976A1 true WO2017045976A1 (fr) 2017-03-23

Family

ID=54151163

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/EP2016/071001 WO2017045976A1 (fr) 2015-09-18 2016-09-07 Dispositif et procédé de surveillance de migraine

Country Status (1)

Country Link
WO (1) WO2017045976A1 (fr)

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN111833314A (zh) * 2020-06-22 2020-10-27 中国科学院西安光学精密机械研究所 一种运动状态下皮肤血流灌注非接触监测方法及监测系统
US10994135B2 (en) 2015-01-13 2021-05-04 Theranica Bio-Electronics Ltd. Treatment of headaches by electrical stimulation
CN117649403A (zh) * 2024-01-29 2024-03-05 吉林大学第一医院 视频衍生面部血流脉动定量评测方法、装置及设备

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5840018A (en) 1996-11-15 1998-11-24 Inta Medics Ltd. Non-invasive real time diagnosis of migraine
WO2012098289A1 (fr) 2011-01-19 2012-07-26 Delfin Technologies Oy Procédé et système de visualisation d'ondes de pulsation cardiovasculaire

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5840018A (en) 1996-11-15 1998-11-24 Inta Medics Ltd. Non-invasive real time diagnosis of migraine
WO2012098289A1 (fr) 2011-01-19 2012-07-26 Delfin Technologies Oy Procédé et système de visualisation d'ondes de pulsation cardiovasculaire

Non-Patent Citations (6)

* Cited by examiner, † Cited by third party
Title
LISA M. RICHARDS ET AL.: "Low-cost laser speckle contrast imaging of blood flow using a webcam", BIOMED OPT EXPRESS, vol. 4, no. 10, 2013, pages 2269 - 2283
NINA ZAPROUDINA ET AL: "Asynchronicity of Facial Blood Perfusion in Migraine", PLOS ONE, vol. 8, no. 12, 4 December 2013 (2013-12-04), pages e80189, XP055253614, DOI: 10.1371/journal.pone.0080189 *
TEPLOV V. ET AL.: "Ambiguity of mapping the relative phase of blood pulsations", BIOMEDICAL OPTICS EXPRESS, vol. 5, no. 9, 22 August 2014 (2014-08-22), pages 3123, XP055257931, DOI: doi:10.1364/BOE.5.003123
VICTOR TEPLOV ET AL: "Ambiguity of mapping the relative phase of blood pulsations", BIOMEDICAL OPTICS EXPRESS, vol. 5, no. 9, 22 August 2014 (2014-08-22), United States, pages 3123, XP055257931, ISSN: 2156-7085, DOI: 10.1364/BOE.5.003123 *
WIM VERKRUYSSE ET AL.: "Remote plethysmographic imaging using ambient light", OPTICS EXPRESS, vol. 16, no. 26, December 2008 (2008-12-01), XP055065281, DOI: doi:10.1364/OE.16.021434
ZAPROUDINA N. ET AL.: "Asynchronicity of Facial Blood Perfusion in Migraine", PLOS ONE, vol. 8, no. 12, 2013, pages E80189

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10994135B2 (en) 2015-01-13 2021-05-04 Theranica Bio-Electronics Ltd. Treatment of headaches by electrical stimulation
CN111833314A (zh) * 2020-06-22 2020-10-27 中国科学院西安光学精密机械研究所 一种运动状态下皮肤血流灌注非接触监测方法及监测系统
CN111833314B (zh) * 2020-06-22 2023-09-01 中国科学院西安光学精密机械研究所 一种运动状态下皮肤血流灌注非接触监测方法及监测系统
CN117649403A (zh) * 2024-01-29 2024-03-05 吉林大学第一医院 视频衍生面部血流脉动定量评测方法、装置及设备
CN117649403B (zh) * 2024-01-29 2024-04-12 吉林大学第一医院 用于偏头痛的视频衍生面部血流脉动定量评测方法、装置及设备

Similar Documents

Publication Publication Date Title
Tasli et al. Remote PPG based vital sign measurement using adaptive facial regions
KR101777738B1 (ko) 동영상을 이용하여 혈압을 추정하는 방법
EP3057487B1 (fr) Dispositif et procédé pour l'obtention d'un signe vital chez un sujet
US10070796B2 (en) Systems and methods for quantitative microcirculation state monitoring
CN106413533B (zh) 用于检测对象的呼吸暂停的设备、系统和方法
Gupta et al. Real-time physiological measurement and visualization using a synchronized multi-camera system
US20140276104A1 (en) System and method for non-contact monitoring of physiological parameters
JP2020510487A (ja) 対象の生理学的信号を測定及び処理するデバイス、システム並びに方法
KR102285999B1 (ko) 얼굴 색상과 떨림을 이용한 카메라 기반 심박 측정 방법 및 시스템
US20150297142A1 (en) Device and method for extracting physiological information
WO2019140155A1 (fr) Systèmes, dispositifs et méthodes de suivi et/ou d'analyse d'images et/ou de vidéos d'un sujet
Feng et al. Motion artifacts suppression for remote imaging photoplethysmography
JP2016193021A (ja) 脈波検出装置、及び脈波検出プログラム
JP6620999B2 (ja) 生体情報計測装置、生体情報計測プログラム、及び生体情報計測方法
KR101752873B1 (ko) 동공 크기 변화율을 이용한 심장 시간 영역의 정보 추출 방법 및 그 장치
JP2019097757A5 (fr)
Kumar et al. PulseCam: High-resolution blood perfusion imaging using a camera and a pulse oximeter
WO2017045976A1 (fr) Dispositif et procédé de surveillance de migraine
Qiao et al. Revise: Remote vital signs measurement using smartphone camera
KR101996027B1 (ko) 동공 크기 변화를 이용한 심장 주파수 영역의 정보 추출 방법 및 그 장치
JP6455761B2 (ja) 脈波検出装置、及び脈波検出プログラム
WO2017103616A1 (fr) Procédé, appareil de traitement d'informations et serveur pour déterminer un paramètre physiologique d'un individu
EP4260801A2 (fr) Imagerie de perfusion sanguine à haute résolution à l'aide d'une caméra et d'un oxymètre de pouls
Mateu-Mateus et al. Comparison of video-based methods for respiration rhythm measurement
Chan et al. Improving heart rate and heart rate variability estimation from video through a hr-rr-tuned filter

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 16760741

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 16760741

Country of ref document: EP

Kind code of ref document: A1