"system and method of determining a person's sleep and sleep stages"

专利摘要:
system and method of determining a person's sleep and sleep stages. The present invention relates to a system and method for determining a person's sleep, sleep stage and/or sleep stage transition, which includes heart rate detection means configured to detect a person's heart rate, motion detection means configured to detect a movement of a person's body part where the detected movement is caused by a skeletal muscle of the body, recording means configured to record the detected heart rate and the detected movement of the body part body, heart rate classification means configured to classify the person's recorded heart rate into at least one heart rate class, at least one heart rate class variability, motion classification means configured to classify recorded movement into at least one movement class, and determining means configured to determine sleep, a sleep stage, a sleep stage transition and/or a person's sleep event based at least partially on at least one heart rate class and at least one movement class.
公开号:BR112013029597A2
申请号:R112013029597-0
申请日:2012-05-15
公开日:2020-11-17
发明作者:Alain Gilles Muzet
申请人:V-Watch Sa；
IPC主号:

专利说明:

; 1/70 9 Invention Patent Descriptive Report for "SYSTEM E
METHOD OF DETERMINING SLEEP AND STAGES OF SLEEP . ONE PERSON". The present invention relates to systems and methods for determining sleep and/or sleep stages of a person, and in particular to a system and method for determining sleep stage transitions based on a heart rate class and a movement class derived from the person's heart rate and movement Background of the invention Most people face problems due to sleep abnormalities and sleep disorders. - 4 sleep tologies are many and can be as different as narcolepsy, * sleepwalking, or abnormal sleep duration like insomnia or hypersomnia. In addition, a person's sleep can be interrupted by snoring, which is often associated with sleep syndrome. obstructive sleep apnea, or by environmental factors such as light or noise.These sleep disorders are usually marked by the occurrence of sleep events that combine sudden changes in physiological variables such as changes in sleep. autonomic (respiratory or cardiac) or motor actions. Sleep events can also be caused by symptoms of sleep disorders such as sleep apnea, restless legs, abnormal movement, sleepwalking, erratic heart rate, nightmare, night terrors, etc. Thus, an individual who snores or talks and screams during a nightmare or night terror will usually cause an abnormal sleep event. The consequences of abnormal or interrupted sleep are numerous from a health (care) as well as a socioeconomic point of view.
To detect the reasons of people's sleep abnormalities and disturbances, sleep laboratories can conduct a person's sleep score, that is, the determination of sleep stages and their transitions. In a sleep laboratory, physiological parameters are observed and the corresponding data recorded on a polysomnography. This record | during a polysomnography includes primary data such as electroencephalography
| 2/70 | but (EEG), electro-oculogram (EOG) and electromyogram (EMG), and secondary data such as heart rate, breathing, oximetry and body movements.
EEG is used to detect and name brain waves of wake- | with its frequency and amplitude.
With an EOG, the movement of the globes | oculars is identified and analyzed.
EMG allows the assessment and recording of electrical activity produced by skeletal muscles.
Classically, the sleep score is based on the analysis of EEG, EOG and EMG recordings taken continuously during the sleep period.
These physiological data are represented by fluctuations of electrical potentials recorded by small electrodes attached to different parts of the scalp and face of the tested/registered person. & These electrical potentials are then interpreted by a “sleep specialist according to internationally accepted rules that define the different stages of sleep. Each sleep stage is characterized by the presence and abundance of specific EEG waves during recording.
Furthermore, eye movements detected by the EOG recording are mainly present during the Rapid Eye Movement (REM) stage of sleep, while EMG shows variations in their tonic and phasic levels depending on the stage of sleep and the simultaneous presence of eye movements. bodily.
A polysomnography has several disadvantages. | For example, during an EEG, electrical potentials are recorded using electrodes attached to various sides of the skull, eg electrodes are guided to the face and over the skull.
Also, EOGs and EMGs require the attachment of electrodes and sensors to the face, skull, or other parts of the test subject's body.
To detect eye movement during sleep, an EOG requires electrodes glued or otherwise attached close to the person's eye or eyelid.
All these electrodes also require wires that are fixed to the electrodes and led to a device placed near the head of the bed, limiting the tested person's freedom of movement.
This registration is therefore cumbersome due to wiring, unusual sleep environments and program imposed in bedding conditions.
The results of these tests can therefore be skewed due to the altered environment of the person being tested. Furthermore, polysomnography has limitations due to the complexity of recording techniques. In detail, specific recording sites such as sleep laboratories and special equipment as well as specialized staff are needed. Therefore, polysomnography remains an exceptional and expensive sleep assessment method.
A polysomnography system based on capturing eyelid movement (EOG), head movement and a heartbeat signal (electrocardiogram - ECG) is described in US 5,902,250. The system described, however, is expensive and generates sleep disturbances due to the number of sensors and wires required. Also, the system described in US” 5,902,250 is not very accurate for determining sleep stages and not & determining sleep stage transitions.
In addition, US 7,351,206 relates to a sleep state apparatus that determines a sleep state based on a series of pulse interval data. Body motion data is determined to remove pulse interval data from the pulse interval data series that was measured in parallel with body motion data, if the amount of fluctuation of body motion data is greater than a threshold. predetermined. Lack of data results in inaccurate sleep stage determination whether body movements were heavy or of long duration. Thus, the derived results cannot be sufficient to reliably score sleep stages.
WO 98/43536 A1 describes a method for determining a patient's sleep status. The method includes monitoring the patient's heart rate variability, and determining sleep status based on heart rate variability. The method may also include monitoring the frequency of eyelid movements, and performing sleep state determination also based on the frequency of eyelid movements. One method of determining the breathing pattern includes monitoring the heart rate variability when receiving the heartbeat signals, and determining the breathing pattern from the strength of the signals,
An independent wearable system determines sleep status, breathing pattern, assesses a patient's cardiorespiratory risk based on fre- . frequency of eyelid movements, frequency of head movements, and heart rate variability.
US 2007/0106183 A1 describes a sleep state measurement apparatus with an autonomic nerve index acquisition unit that obtains an autonomic nerve index from the user; and a sleep periodicity index calculation unit that calculates a sleep periodicity index. sleep data based on a temporal change in the au- | refers to a change in a user's sleep cycle, where the rate of | Sleep periodicity indicates whether or not the user is sleeping accordingly, with a user's ideal sleep cycle as an index, or a dominance-index calculation unit that calculates a parasympathetic nerve dominance index that shows the dominance of a parasympathetic nerve index included in the autonomic nerve index versus a sympathetic nerve index included in the autonomic nerve index of a user during Sleep. US 2009/0264715 AÍ describes a sleep system that has sensors capable of gathering a person's sleep data and environmental data during the person's sleep. A processor executes instructions that analyze this data and control the person's sleep and the environment that surrounds the person. Typically, instructions are loaded into a memory where they are executed to generate an objective measure of sleep quality from the person's sleep data and gather environmental data during the person's sleep. Upon execution, instructions receive a subjective measure of the person's sleep quality after sleep, create a sleep quality index from the objective measure of sleep quality and the subjective measure of sleep quality, correlate the index sleep quality index and a current sleep system setting with a historical sleep quality index and historical sleep system settings. The instructions can then modify the current sleep system settings setting depending on the correlation between the quality index and the
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5/70 Sleep Lo ty and Historical Sleep Quality Index. These sleep system settings control and potentially change one or more different elements of an environment associated with the sleep system.
| US 2010/0125215 A1 describes a sleep analysis system and a method of analyzing the same. The sleep analysis system includes an analysis device and a sleep recording apparatus. The sleep recording device includes an ECG signal collector, a multi-axis accelerometer, a wireless transmission unit, and a control unit. The ECG signal collector is used to collect an ECG signal associated with an individual The multiaxial accelerometer is used to detect a multiaxial accelerometer signal associated with the individual. The control unit controls the wireless transmission unit to transmit the ECG signal and the multiaxial accelerometer signal to the analysis device to analyze the individual's sleep. No distinction is made between the stages of Non-REM sleep.
However, due to the large uncertainties in determining sleep stages and/or sleep stage transitions compared to the classic visual sleep score, the percentage of agreement between these sleep scoring approaches and the sleep scoring approach sleep | classical visual is considered very low by sleep researchers and | 20 sleep experts. Therefore, these techniques are not yet in use in the medical field.
| An object of the invention is to provide a system and method for determining sleep states and/or sleep stages and/or sleep stage transitions that reduce the sleep disturbance of the tested person and provide reliable results and are sufficiently accurate and cost-effective. waistband.
That object is achieved by the present invention as defined by the independent claims. Preferred embodiments are defined by the dependent claims. Heart rate variability and an LF/HF ratio of a low-frequency (LF) to high-frequency (HF) component of a heart rate variability (HRV) signal can be used to determine sleep status and sleep stages. float-
: non-temporary (stationary) heart rate actions allow a differentiation of sympathetic and parasympathetic activation, these are related to a low frequency (kF) and high frequency (HF) component of a heart rate variability (HRV) signal ). The resulting LF/HF ratio is a quantitative index of the sympathovagal balance and can be computed through spectral analysis.
The more synchronized the sleep, the more the LF/HF ratio decreases, while the LF/HF ratio is significantly increased during REM sleep, indicating a sympathetic predominance during this period.
Thus, HRV spectral analysis provides additional information on the behavior of the ultradian rhythm of autonomic nervous system function in addition to traditional cardiovascular measures (mean heart rate, blood pressure, etc.). - A disadvantage of this spectral analysis approach is that this ratio must be calculated when the heart rate signal is stationary.
When the person is moving, the calculation of this ratio is corrupted by movement-induced changes in heart rate.
In other words, the LF/HF ratio can only be used when the person is standing still.
The sleep score is based not only on determining a particular sleep stage but also on determining transitions from one stage to another.
The determination of a sleep state, a sleep stage and/or a sleep stage transition using the LF/HF ratio, in particular the determination of the exact time of the sleep stage and/or the transition of a sleep stage sleep to another sleep stage is highly problematic and the uncertainty in determining sleep stage and/or stage transition should be a few to several minutes when the heart rate is not sufficiently stationary.
For example, there may be slow transitions in the LF/HF ratio, with the LF/HF ratio fluctuating like a sine wave from high values | 30 for basses and inverts.
However, if there is no information about the value | of the LF/HF ratio indicating a transition between sleep stages, transitions from Non-REM to REM sleep stages must be arbitrarily | o fixed by a horizontal line that cuts this fluctuation curve. However, using this technique, the timing of transition cannot be precise. only determined compared to the classic visual sleep score and therefore the sleep stage determination accuracy is not sufficient. One embodiment of the present invention uses heart rate and body movements to determine a sleep state, a sleep stage, and/or a sleep stage transition. In a preferred modality, the determination of a sleep stage and/or sleep stage transition is based on heart rate and body movement classes. For example, a sleep stage transition can be precisely determined by simultaneously considering the level and the sudden changes in heart rate and possible movements. . concomitant bodies. If no transitional signs are observed, the person remains in the same state (awake or asleep) or in the same sleep stage in the latter case. Thus, the modalities of the present invention are not dependent on any seasonality of the heart rate signals and using their sudden changes, a transition from one stage to another stage can be determined with an uncertainty of a few seconds. .
According to a preferred embodiment, the present invention relates to a system for determining sleep, a sleep stage and/or a sleep stage transition of a person. The system includes heart rate capturing means configured to detect a person's heart rate and motion capturing means configured to detect movement of a person's body part. The detected movement is caused by a skeletal muscle in the body. The system further includes recording means configured to record the detected heart rate and the detected movement of the body part, heart rate classification means configured to classify the person's recorded heart rate into at least one heart rate class, and movement classification means configured to classify the recorded movement and at least one movement class. The system also
also includes determining means configured to determine sleep, a sleep stage and/or a sleep stage transition and/or a sleep event. person's sleep based at least partially on at least one heart rate class and at least one movement class.
In accordance with one aspect of this modality, the system includes a heart rate calculation means configured to calculate an average heart rate, a variability value (including the classically used LF/HF spectral ratio), a rhythm characteristic, and/or or a heart rate event or recorded heart rate change Heart rate classification means are configured to classify the person's heart rate based on the average calculated heart rate, variability value, rhythm characteristic and/or or - heart rate event or change.
In a further aspect of the modality, the means of determination are configured to identify a specific combination of a heart rate class and a class of movement within a specific time period, and the means of determination are configured to determine sleep, a sleep stage, sleep stage transition | and/or a sleep event based on the specific combination identified.
In connection with one aspect of this embodiment, the motion detecting means comprises motion capturing means configured to capture an acceleration of a part of the person's body, where the recording means is further configured to register the acceleration. - | captured feed.
The system includes a movement calculation means configured to calculate, based on the recorded acceleration values, at least the intensity and/or duration of each movement of the person's body part.
As a further aspect of the modality, the movement classification means are configured to classify each movement of the body part into at least a large movement (LM), a 'small movement (SM) or a contraction (TM) , based on the calculated intensity and/or duration of each movement, and/or configured to classify
| 9/70 place each LM, SM and/or TM at least in frequency classes and/or duration classes. | . According to another aspect of this modality, the system includes | further environmental capture means configured to capture at least one environmental factor, where the recording means are additionally configured to record at least one captured environmental factor, and environmental rating means configured to classify at least some values of at least an environmental factor registered in at least one environmental class. The determining means are further configured to determine sleep, a sleep stage, a sleep stage transition and/or a sleep event of the person based at least partially on at least one environmental class. According to one aspect of this modality, the environmental capture means are configured to capture a noise level, an ambient temperature and/or an ambient light.
According to yet another aspect of the modality, the system also includes means of environmental calculation configured to calculate at least an average noise level and/or noise event based on the recorded noise level, and/or calculate at least at least one level and/or change and/or variation in mean ambient temperature based on recorded ambient temperature, and/or calculate at least one level and/or change and/or variation in ambient light based on recorded ambient light.
Regarding another aspect of this modality, the means of determination are additionally configured to determine a transition from wakefulness to sleep and/or a transition from one sleep stage to another and/or a transition from sleep to wakefulness and/or an effect direct causality of at least one environmental factor recorded on a sleep stage transition or a sleep-to-wake transition.
In accordance with one aspect of the modality, the system further includes assessing means configured to assess a person's sleep or wakefulness state based on at least one heart rate class, at least | at least one movement class, at least one environmental class, and/or any combination thereof.
*. | 10/70 : According to an additional modality, a system for determining sleep, a sleep stage and/or the sleep stage transition of . a person comprises a heart rate detection means configured to detect a person's heart rate, and a motion detection means configured to detect a movement of a part of the person's body, wherein the movement is caused by a skeletal muscle of the body.
The system further comprises a recording means configured to record the detected heart rate and the detected movement of the body part, a heart rate classification means configured to classify the person's recorded heart rate into at least one class of heart rate and at least one heart rate variability class, and a movement classification means configured to classify recorded movement into at least one movement class.
The system further comprises determination means configured to determine sleep, a sleep stage, a sleep stage transition, and/or a person's sleep event based at least partially on at least one heart rate class. , at least one heart rate variability class, and at least one movement class, where the determination means is configured to identify a combination of a heart rate class, a rate variability class heart rate, and a movement class within a time interval, and to determine sleep, a sleep stage and/or a sleep stage transition based on the identified combination.
According to a preferred embodiment, at least one heart rate class comprises an average heart rate class.
In a preferred embodiment, the average heart rate rating is based on an average heart rate, with the -30 average heart rate being calculated over a predetermined time interval.
Preferably, the predetermined time interval "for averaging heart rate varies depending on a
. body movement detected in the person. For example, in a preferred mode, the average heart rate is calculated by averaging the . heart rate over a first time interval if there is any body movement, and is calculated by averaging heart rate over a second time interval if no or little body movement occurs with the second time interval being greater than the first time interval. According to an additional embodiment, a system for determining a person's sleep, a sleep stage and/or a sleep stage transition includes a wearable device configured to detect and record the person's heart rate and configured to detect and record a movement of a person's body part, where the movement is - caused by a skeletal muscle of the body, and an analysis device configured to classify the person's recorded heart rate into at least one heart rate class , configured to classify the recorded movement into at least one movement class, and confi- | used to determine the person's sleep, a sleep stage, a sleep stage transition, and/or a sleep event based at least partially on at least one heart rate class and at least one movement class . The system also includes a data link configured to communicate data representing recorded heart rate and recorded movement from the wearable recording device to the analysis device.
In yet another embodiment, a method for determining a person's sleep, a sleep stage and/or a sleep stage transition and/or a sleep event comprises the steps of detecting the person's heart rate, recording the detected heart rate, detect a movement of a person's body part where the movement is caused by a skeletal muscle of the body, record the detected movement, classify the person's recorded heart rate into at least one heart rate class , classify the recorded movement into at least one movement class, determine the person's sleep, a sleep stage and/or a sleep stage transition, and/or a sleep event based at least partially on at least one class of . heart rate and at least one movement class. According to one aspect of this modality, the method comprises identifying a specific combination of a heart rate class and a movement class within a specific period of time, where the determination comprises determining the sleep stage based on the specific combination identified.
Regarding another aspect of the modality, the method comprises capturing at least one environmental factor, recording at least one environmental factor! captured, classify at least some values of at least one recorded environmental factor in at least one environmental class, and determine a person's sleep event based at least partially on at least one environmental class.
According to one aspect of the embodiment, the method includes assessing a person's sleep or wakefulness state based on at least one heart rate class, at least one movement class, at least one environmental class, and/or any combination. the same.
In yet another embodiment, the method comprises determining a direct causal effect of at least one environmental factor! recorded over a sleep stage transition or a sleep event or a sleep-to-wake transition based at least partially on at least one environmental class.
With reference to an additional modality, a system for determining a person's sleep, a sleep stage and/or sleep stage transition includes heart rate detection means configured to detect the person's heart rate, motion detection means, devices configured to detect movement of a person's body part, where the movement is caused by a skeletal muscle of the body, heart rate classification means configured to classify the person's detected heart rate into at least one rate class heart rate, motion classification means configured to
: classify the detected movement into at least one movement class, and determine configured means to determine sleep, sleep stage . eluted a person's sleep stage transition based at least partially on at least one heart rate class and at least one movement class.
Regarding one aspect of this modality, the system includes | heart rate calculation means configured to calculate the average | heart rate, a variability value (including the LF/HF spectral ratio), a rhythm characteristic, and/or a heart rate event or change from the detected heart rate, where the heart rate classification means are configured to classify the person's heart rate based on the average heart rate, value of | - variability, rhythm characteristic and/or event or calculated heart rate change.
In accordance with another aspect of the modality, the means of determination is further configured to identify a specific combination of a class of heart rate and a class of movement within a specific period of time, where the means of determination - termination are configured to determine sleep, sleep stage and/or sleep stage transition and/or a sleep event based on the specific combination identified.
In accordance with yet another aspect of the embodiment, the determining means is configured to identify a successive order of 'heart rate class and movement class of the combination | specific.
With reference to another aspect of the modality, the means of determination are configured to identify, as a specific combination, a heart rate accelerating event together with a body part movement, a heart rate accelerating event. acaque precedes a body part movement, a heart rate acceleration event without a body part movement within the specified time period, and/or a heart rate acceleration event |
: diac after a movement of the body part.
According to another aspect of the modality, the means of de-. heart rate detection comprises pulse wave capturing means configured to capture a pulse wave from the person's heart According to a further aspect of the embodiment, the motion detection means comprises motion capturing means configured to capture an acceleration part of the person's body, wherein the system includes a movement calculation means configured to calculate, based on the values of the captured acceleration, at least an intensity and/or duration of each movement of the person's body part.
According to another aspect of the modality, the movement classification means are configured to classify each movement - of the body part into at least one large movement, a small movement or a contraction, based on intensity and/or calculated duration of each movement. In accordance with yet another aspect of the modality, the movement classification means are configured to classify each movement of the body part into at least a large movement (LM), a small movement (SM) or a contraction (TM), based on in the calculated intensity and/or duration of each movement, and/or configured to classify each LM, SM and/or TM at least into frequency classes and/or duration classes.
According to another aspect of the modality, the system also includes environmental capture means configured to capture at least one environmental factor, and environmental classification means configured to classify at least some values of at least one environmental factor captured in at least one environmental class. .
In accordance with yet another aspect of the embodiment, the determining means is further configured to determine a person's sleep event based at least partially on at least one environmental class.
With reference to an additional aspect of the modality, the environmental capture means are configured to capture a noise level, a
' ambient temperature and/or ambient light.
With respect to an additional aspect of the modality, the system further includes environmental calculation means “configured to calculate at least one average noise level and/or noise event based on the noise level captured, and/or calculate at least an average ambient temperature level and/or a change and/or change in ambient temperature captured, and/or calculate at least one ambient light level and/or change in ambient light based on the ambient light captured.
In accordance with another aspect of the embodiment, the determining means are further configured to determine a transition from one sleep stage to another and/or from a sleep stage to wakefulness and/or a sleep event.
In accordance with yet another aspect of the modality, the means of N determination are configured to determine that the transition is a descending transition or an ascending transition, where a descending transition starts from wakefulness or from a stage of sleep. lighter sleep and results in a deeper sleep stage, and where an upward transition starts from a deeper sleep stage and results in a lighter sleep stage or awakening.
According to one aspect of the modality, the system further includes identifying a missing value and/or an abnormal value within the detected heart rate, the detected movement, and/or the values of at least one captured environmental factor. to another aspect of the modality, the system includes | further evaluating means configured to assess a person's sleep or wake state | based on at least one heart rate class, | at least one movement class, at least one environmental class ' and/or any combination thereof.
In yet another embodiment, a system for determining a person's sleep, a sleep stage, and/or a sleep stage transition includes a wearable device configured to detect a person's heart rate and configured to detect a person's heart rate. a movement of a person's body part, where the movement is caused by a muscle | | the skeletal loop of the body, an analysis device configured to classify a person's detected heart rate into at least one heart rate class, configured to classify detected movement into at least one movement class, and configured to determine the sleep, a sleep stage and/or a sleep stage transition and/or a person's sleep event based at least partially on at least one heart rate class and at least one movement class, and a data connection configured to communicate data representing detected heart rate and detected motion from the wearable recording device to the analysis device.
According to one aspect of this embodiment, the identification means are additionally configured to recover missing data and/or abnormal data.
According to another aspect of the modality, the 15th dose connection is a wireless data connection.
In accordance with yet another aspect of the embodiment, the wearable device is worn by the subject on a limb, torso and/or head of the subject.
With respect to another aspect of the modality, the wearable is additionally configured to record data representing at least successive heart rate intervals, and is configured to record data representing detected motion, where the ! data is configured to communicate recorded data representing at least successive heart rate intervals and/or data representing detected movement from the wearable device to the analysis device.
With reference to another aspect of the modality, the analysis device is further configured to assess a person's sleep or wake state based on at least one heart rate class, at least one movement class, and/or any combination. the same.
According to an additional embodiment, a method for de- |
, MM 17/70 : ending sleep, sleep stage and/or a person's sleep stage transition comprises the steps of detecting a person's heart rate, detecting a movement of a person's body part, where the movement is caused by a skeletal muscle in the body, classify the person's detected heart rate into at least one frequency class | heart rate, classify the detected movement into at least one movement class, and determine the person's sleep, a sleep stage and/or a sleep stage transition, and/or a sleep event based at least partially on at least a heart rate class and at least one movement class.
According to one aspect of this modality, the method comprises the step of identifying a specific combination of a heart rate class and a movement class within a specific time period, where the determination comprises determining sleep, stage and/or a sleep stage transition and/or a sleep event based on the specific combination identified.
According to another aspect of the modality, the method comprises calculating the average heart rate, a variability value, a rhythm characteristic and/or an event or change in heart rate | 20 diaeach heart rate detected, where the rate classification | person's heart rate comprises classifying heart rate based on average heart rate, variability value, rhythm characteristic and/or event or calculated heart rate change.
According to another aspect of the modality, the method comprises the steps of capturing at least one environmental factor and classifying at least some values of at least one environmental factor captured in at least one environmental class.
With reference to a further aspect of the modality, the determination comprises determining a person's sleep event based at least partially on at least one environmental class.
Still according to another aspect of the modality, capturing at least one environmental factor comprises capturing a noise level, a
. ambient temperature and/or ambient light. : According to one aspect of the embodiment, the method includes ava- . assess a person's sleep or wake state based on at least one heart rate class, at least one movement class, at least one environmental class, and/or any combination thereof.
According to a further embodiment, the present invention: relates to a system for determining sleep, a sleep stage and/or a person's sleep stage transition.
The system includes a heart rate detector configured to detect a person's heart rate and a motion detector configured to detect a movement of a part of the person's body, where the detected movement is caused by a skeletal muscle of the body.
The system also includes a | - recording unit configured to record detected heart rate | measured and detected body part movement, a heart rate classification unit configured to classify the person's recorded heart rate into at least one heart rate class, and a motion classification unit configured to classify the recorded movement in at least one movement class.
The system also includes a determination unit configured to determine sleep, a sleep stage and/or a sleep stage transition and/or a person's sleep event based at least partially on at least one frequency class. heart rate and at least one movement class.
In accordance with one aspect of this modality, the system includes a heart rate calculation unit configured to calculate an average heart rate, a variability value, a rhythm characteristic, and/or a heart rate event or change from the recorded heart rate. .
The heart rate rating unit is configured to rate the person's heart rate based on average heart rate, variability value, rhythm characteristic and/or event, or calculated heart rate change.
In an additional aspect of the modality, the unit of determination |
| 19/70 the nation is configured to identify a specific combination of a heart rate class and a movement class within a specific time period and the determination unit is configured to determine sleep, sleep stage and /or sleep stage transition and/or a sleep event based on the specific combination identified. In relation to one aspect of this embodiment, the motion detection unit comprises a motion sensor configured to sense an acceleration of the subject's body part, where the unit | is additionally configured to record the captured acceleration The system includes a means of calculating motion configured for cal- | : cular, based on recorded acceleration values, at least one in- | tension and/or duration of each movement of the person's body part | - sounds. | According to an additional aspect of the modality, the means of | movement classification is configured to classify each body part movement into at least a large movement (LM), a small movement (SM) or a contraction (TM), based on intensity and/or du- ! calculated ration of each movement, and/or configured to classify each LM, SM and/or TM at least into frequency classes and/or duration classes. According to another aspect of this modality, the system also includes an environmental sensor configured to capture at least one environmental factor, where the recording unit is additionally configured to record at least one captured environmental factor, and an environmental classification unit configured to classify at least some values of at least one environmental factor recorded in at least one environmental class. The determination unit is further configured to determine a person's sleep event based at least partially on at least one environmental class. In one aspect of this embodiment, the environmental sensor is configured to pick up a noise level, ambient temperature, and/or ambient light. K
Lo According to another aspect of the modality, the system also includes an environmental calculation unit configured to calculate by . least one noise level and/or average noise event based on the recorded noise level, and/or calculate at least one level and/or average ambient temperature change and/or variation based on the recorded ambient temperature, and /or calculate at least one ambient light level and/or ambient light level change based on recorded ambient light In another aspect of this modality, the de- | termination is additionally configured to determine an as- | . 10 transition from one sleep stage to another and/or a sleep transition to | wakefulness and/or a direct causal effect of at least one environmental factor or one | sleep event recorded in an ascending sleep stage transition - and/or a sleep-to-wake transition. ' According to one aspect of the modality, the system includes even- | 15 gives an assessment unit configured to assess a person's sleep or wake state based on at least one heart rate class, at least one movement class, at least one environmental class, or any combination thereof.
In accordance with a further embodiment, the present invention provides a method for determining a person's sleep, a sleep stage, and/or a sleep stage transition.
The method comprises detecting a person's heart rate, recording the detected heart rate, detecting a movement of a person's body part, where the movement is caused by a skeletal muscle of the body, recording the detected movement, classifying the recorded heart rate of the person in at least one heart rate class and at least one heart rate class variability, classify the registered movement in at least one movement class; and determining the person's sleep, a sleep stage, a sleep stage transition, and/or a sleep event based at least partially on at least one heart rate class, at least one heart rate class variability , and at least one movement class.
jo NSrUEE-EAA A aa aaafP“áÁÂd -uaçaF“"-x)P 122 2—2"52= —aa Aa mi um nun NNE uwwwP<â ÃO, , ii A2,2tó“ 2“ “2 ““““ “““.““.“., “ .+. ÔS oAQ2“ OO OO “SOON and emo EESC 21/70 o | o According to a preferred embodiment of the method, at least one heart rate class comprises an average class. heart rate and an average heart rate rating.
In a preferred embodiment, the average heart rate rating is based on an average heart rate, with the heart rate being calculated over a predetermined time interval.
Preferably, the time interval for calculating the average heart rate varies depending on a person's detected body movement.
For example, in a preferred mode, the average heart rate is calculated by averaging the heart rate during a first time interval if there is any body movement, and it is calculated by averaging the heart rate during a second time interval if there is little or no body movement, such as second time interval being longer than the first time interval.
Aspects of different embodiments of the present invention may be combined unless otherwise stated.
Brief Description of the Drawings To describe the manner in which the aforementioned and other advantages and features can be obtained, a more detailed description of the subject briefly described above will be presented with reference to the specific embodiments which are illustrated in the accompanying drawings.
With the understanding that these drawings only show typical modalities and therefore are not considered limiting in scope, the modalities will be described and explained with specificity and additional detail through the use of the attached drawings, in which: 1 illustrates a hypnogram of a young adult; Figure 2 shows the components of a recording device and a data extraction unit according to an embodiment of the present invention; Figure 3 shows the components of a classification unit.
. . cation according to an embodiment of the present invention; Figure 4 shows the components of a detection device. mining in accordance with an embodiment of the present invention; Figure 5 illustrates sleep determination method steps, a sleep stage and/or sleep stage transition in accordance with an embodiment of the present invention; Figure 6 illustrates method steps of verifying a heart rate record according to another embodiment of the present invention; | Figure 7 illustrates heart rate events or changes. over time; Figure 8 shows relationships between wakefulness states and sleep stages and illustrates the transitions between these states and stages; Figure 9 illustrates method steps for adapting a time interval to average a heart rate; Figure 10 illustrates a sleep stage transition from light sleep to REM sleep; Figure 11 illustrates a sleep stage transition from deep sleep to light sleep; Figure 12 illustrates a short transition from light sleep to awake followed by a return to light sleep; Figure 13 illustrates a short transition from REM to awake sleep followed by a return to REM sleep.
Detailed description of the invention ' | 25 The present invention provides a system and method for scoring an individual's waking and sleeping periods, based on the ambulatory recording of heart rate and body motility, and for describing the characteristics and variations of the physical environment in which that person is living.
During the sleep period, the method will automatically score the different stages of sleep in a similar way and with the same precision as that classically used through polysomnographic recording and visual scoring.
Therefore, the present invention can achieve a | '
23/70 | .the creation and detailed sleep assessment fully comparable with the method | that uses a simpler and easier methodology.
These recordings, taken, for example, from a person's wrist, will be less subject to the limitations of electrical artifacts or wiring than ordinary polysomnography.
Furthermore, the present invention is fully autonomous and capable of recording not only the sleep period but also all the person's activities.
As mentioned above, as used in this document, a person's wakefulness state can be basically defined as wakefulness or sleep.
These states alternate and are dependent on each other.
During sleep, various sleep stages can be determined.
These sleep stages can be categorized as rapid eye movement (REM) sleep stages and non-REM sleep stages.
The - REM stage of sleep is the one where vivid dreams occur.
This can be identified by the occurrence of rapid eye movements under closed eyelids, motor atony, and low-voltage EEG patterns.
The stage of REM sleep, also referred to as REM sleep, is also associated with bursts of muscle contraction, irregular breathing, irregular heart rate, and increased autonomic activity.
Periods of REM sleep are also referred to as paradoxical sleep.
In addition, a person's sleep can also be scored in non-REM (NREM) stages, which are numbered from 1ad4. Figure 1 shows an example hypnogram of a young adult showing the different stages of sleep from an eight-hour sleep record.
It should be noted that transitions from one stage to another are conventionally regarded as abrupt steps.
As illustrated, within the first hour of sleep, a person who starts from an awake state and falls asleep can transition into NREM sleep stage 1 and further into stages 2, 3, and 4. NREM sleep consists of a low-voltage EEG followed by well-defined alpha activity and theta frequencies in the range of 3 to 7 Hz, occasional spikes, and slow eye movements (SEMs). This stage includes the absence of sleep spindles, Ko complexes, and REMs. Stage 1 typically represents 4 to 5% of the total sleep time period. ' Stage 2 sleep of NREM sleep is characterized by the occurrence of sleep spindles and K complexes against a relatively low voltage, mixed frequency EEG history. High voltage delta waves can comprise up to 20% of stage 2 sleep periods. Stage 2 sleep generally accounts for 45 to 55% of total sleep time. | Stage 3 sleep of NREM sleep is defined by at least 20% and no more than 50% of the period consisting of EEG waves of 2 cps or more, with amplitudes greater than 75 pV (high-amplitude delta waves). This is often combined with stage 4 NREM sleep in slow wave sleep (SWS) due to the absence of physiological differences - documented between the two stages. This stage 3 normally appears only in the first third of the healthy adult's sleep period and usually comprises 4 to 6% of total sleep time.
All of the above statements regarding N-REM stage 3 sleep can also apply to stage 4 sleep except that high voltage slow delta EEG waves cover 50% or more of the recording. NREM stage 4 sleep usually represents 12 to 15% of total sleep time. For example, sleepwalking, night terrors, and sleep-related enuresis episodes usually begin at stage 4 or during stage 4 arousal.
A non-REM light sleep stage is a common term for stages 1 and 2 sleep, while non-REM deep sleep is a term for the combination of stages 3 and 4 sleep.
Returning to Figure 1, after a period of stage 4 sleep, the test person's sleep changes to stage 2 sleep and REM sleep. In addition, a phase of non-REM light sleep stages is followed to then return to another stage of non-REM deep sleep.
The rest of sleep as shown in Figure | comprises transitions from periods of REM sleep to stages of lighter Non-REM sleep, such as stages 1 and 2 o To determine a test subject's wakefulness state and to determine sleep stages, sleep stage transitions and/or or: sleep events of the tested person, the present invention provides a system and method for continuously detecting and recording for several days or weeks basic physiological variables such as heart rate and body motility along with some characteristics of the physical environment. This methodology will be able to punctuate the basic states such as periods of wakefulness and sleep of the tested person. During wakefulness, the present invention will make it possible to distinguish between active and rest periods. During the sleep state, sleep stages will be scored each period of | : 30 seconds. Furthermore, the simultaneous recording of physical variables of the environment together with biological ones will allow the assessment of the possible - impact from the former to the latter. Figure 2 illustrates the components of an exemplary capture/recording system in accordance with an embodiment of the present invention. The present invention is not limited to the arrangement of devices and components shown. As will be described in more detail below, variations of the arrangement shown are possible and are also included within the scope of the present invention. The exemplary system comprises a recording device 100 which may include sensing means such as sensors and sensor-related units. Additionally, the recording device 100 includes a memory 170.
Recording device 100 may include heart rate detection means that can detect the heart rate of a person being tested and emit signals representing the heart rate. The heart rate detection means may be an entity or unit of recording device 100. This entity or unit may be a set of circuitry, such as an integrated circuit (IC), constructed to perform heart rate detection and recording. emission of heart rate signals as well as other functions described below. Alternatively, the entity or unit is a circuit capable of executing specific software or firmware that performs the functions of the heart rate detection means as will be described in more detail below. Preferably and alternatively
; Again, the entity or unit is a processor, such as a microprocessor, that executes a conceptual component of software or firmware, - where the execution of the conceptual component performs the functions below the heart rate detection means.
For example, heart rate detection means comprise sensors and sensor-related units. These sensor-related units of the heart rate detection means may include a pulse sensor 110 that captures a pulse wave from the person being tested. Pulse waves can be measured in a peripheral artery. For example, pulse waves can be measured in a | radial artery located in the wrist, if the recording device 100 is located in the wrist of the person being tested. The present invention is not limited to an artery in the wrist, however the test subject may also wear the recording device in an ankle or other position with access to an artery. The pulse sensor 110 captures arterial pulse waves produced by momentary increases in arterial vessel volume due to blood ejected by heart contractions, ie, systoles. Therefore, these pulse waves correspond exactly to the heartbeats. A sensor-related unit of the heart rate detection means may be an instantaneous heart rate unit 112 which determines a heart rate (HR) of the tested person based on the pulse wave captured. The instantaneous HR unit 112 counts pulse waves captured during a specified minimum period of time and determines a heart rate, ie, heartbeats per minute. In addition, the heart rate detection means may also comprise an interpulse interval unit 114 which measures the elapsed time between two successive pulse waves and outputs the elapsed time, for example, expressed in milliseconds. This elapsed time is also referred to as pulse wave intervals (PWis) or heartbeat intervals. Both the 112 instant heart rate unit and the u-
| 27/70 | * , | The interpulse interval unit 114 outputs data for storage in a memory 170 of the recording device 100 and/or for additional calculations. nais. These data represent the heart rate at certain time points, stored, for example, every second or every 5 seconds. In addition, the data can also represent the elapsed time of at least one PWI as emitted by the interpulse interval unit.
114. Depending on the memory capacity, the raw sensor data from the sensor 110 can also be recorded and stored in the memory 170. According to another embodiment, the functions of the instantaneous heart rate unit 112 and the interpulse interval unit 114 | À are combined into one unit. This combined unit simultaneously outputs an HR value and values representing PWils for storage in memory 170 or further processing. Furthermore, in accordance with the embodiment shown, the apparatus 100 also includes motion detection means that can detect a movement of the subject's body, also referred to as a body movement (BM). The motion detection means may also be an entity or unit of recording device 100. As noted above, this entity or unit may be a set of circuits, co-ordinate integrated circuit (IC), constructed to perform the functions of the motion detection means described further below. Alternatively, the entity or unit is a set of circuitry capable of running specific software or firmware that performs these functions. Preferably, and also alternatively, the entity or unit is a processor, such as a microprocessor, which executes a conceptual component of software or firmware, where the execution of the conceptual component performs the functions below the motion detection means. To score sleep stages or sleep stage transitions or detect the sleep events of the test person, skeletal muscle movement is of primary interest. Although eyeball movement and/or movement caused by the person's heart and/or lungs can also allow conclusions to be drawn about sleep stages,
Ma TT O TO OO RAS Oiii he 28/70 | . The present invention relies on movement caused by the left muscles | lectic. . The motion detection means may be a sim- | ples 120 that allows you to determine if a sensor movement has occurred. Beyond | In addition, the motion detection means can also be one or more | 120 acceleration sensors, which are able to capture a body movement more precisely. Such sensing means 120 may be acceleration sensors 120 for sensing acceleration along one or more axes. This also allows a determination of a direction, duration and intensity of a BM. | : In a preferred embodiment, the test subject's body movement will be measured by a miniaturized three-axis accelerometer | - rized 120, placed in recording device 100. Accelerometer 120 measures an acceleration value, for example, 20 times per second and all absolute values are summed during each second. The measurement frequency and summation time period can be sent to adjust the sensitivity of the device 100 to the movement habits of the tested person.
As mentioned above, the registration device can be | worn, for example, on the wrist of the tested/registered person. This is convenient for the person as it does not disturb sleep like instruments | polysomnography and conventional sensors do. In addition, any | movement caused by skeletal muscles occurs in one part of the body, such as a limb, torso, and/or head. These movements will in most cases be accompanied by a slight flick of the wrist. Therefore, the sensitivity of the system is selected to detect these movements. The sensitivity of sensor 120 can be adjusted to customize system 100 to user movements. | Returning to Figure 2, the motion detection means of the recording device 100 may also comprise a com- | 122 which receives the output signals from sensor 120. The com- | paradora 122 compares these output signals with a predefined threshold. Only if the acceleration on one or more axes exceeds the predefined threshold, is |
| | 29/70 : o the particular movement represented by the output signal of the sensor 120 recorded, ie in memory 170. Thus, the sensitivity of the acceleration sensing system can be adjusted by selecting the preset threshold.
Furthermore, the system of the present invention allows the adjustment of a threshold for each geometry axis or for each acceleration sensor 120 of the device. register 100. The system can then be adjusted to emphasize that | the particular movements of the wrist, such as a movement towards the | along the arm should be less intense than in a direction orthogonal to the arm.
In another aspect, the comparator unit 122 has more than one threshold with which the captured acceleration is compared.
This allows a pre-classification of motions based on the magnitude of the captured acceleration. | The output of sensor 120 is stored in memory 170 for further processing.
As mentioned above, the storage may depend on the output signals from the comparator unit 122. In addition to the above sensors and units, the recording device 100 may also include environmental capturing means for capturing an environmental factor.
As noted above, the environmental capture means can also be an entity or unit of the recording device 100. Uma | entity or unit may be a set of circuits, such as an integrated circuit (IC), constructed to perform the functions of the environmental capture means described below.
Alternatively, the entity or unit is a circuit capable of executing specific software or firmware that performs these functions.
Preferably and also alternatively, the entity or unit is a processor, such as a microprocessor, which executes a conceptual component of a software or firmware, where the execution of the conceptual component performs the functions below the environmental capture means.
Environmental capture means may comprise several u- | such as a noise sensor 130, a light sensor 140 and/or a temperature sensor 150. | The
| | : For example, the physical characteristics of the tested person's environment can be captured. Noise can be recorded as a value. integrated every second and ambient noise level is measured every second (Leglsec) within a range of 20 to 100dB with an accuracy of 1dB. Ambient light is measured every second in a range of 10 to 1000lux with an accuracy of 1lux. Ambient temperature is measured every second with a dedicated temperature sensor 150 within a range of -20 to +50°C with an accuracy of 0.5°C. All physical environment values are recorded in internal memory 170 of device 100. | 10 Returning again to Figure 2, the recording device 100 | may also include additional pickup means 180. As already described above, additional pickup means 180 may be an entity or unit of recording device 100. An entity or unit may be a set of circuitry, such as an integrated circuit (IC ), built to perform the functions of additional capture media described below. Alternatively, the entity or unit is a circuit capable of executing specific software or firmware that performs these functions. Preferably and also alternatively, the entity or unit is a processor, such as a microprocessor, that executes a conceptual component of a software or firmware, where the execution of the conceptual component performs the functions below the environmental capture means.
Additional capture means 180 may, for example, include physiological sensors specifically made to measure blood oxygen saturation, also referred to as "pulse oximetry". This sensor measures the oxygen saturation in the bloodstream. Your value is | normally close to 100% in a healthy individual. Desaturation | with values below 90% can be observed in apnea syndrome | sleep. | Additional sensors 180 can be sensors to measure a pulse transit time or sensors that measure skin temperature or sensors that detect possible skin variations. Pulse transit time is directly related to arterial blood pressure.
The wall of an artery is elastic and contains small muscles that can change the diameter of the vessel.
For each contraction of the heart, a certain amount of blood is ejected into the arterial vessels with a certain force.
This blood pressure depends on the arterial wall tension.
If that tension is high, blood pressure is elevated, and if that tension is reduced, blood pressure is reduced.
The pulse velocity corresponding to a beat | heart rate depends on the stiffness of the artery wall.
Therefore, the pulse is ace- | read when wall voltage is high and reduced when voltage is low.
The transit time is then calculated between two locations placed on the . same artery and separated by a few centimeters.
An equal passing pulse is measurable at these two separate locations and the elapsed time is directly related to artery wall tension or blood pressure.
A reduction in this time corresponds to an increase in pressure | blood pressure while an increase in this elapsed time corresponds to a decrease in blood pressure.
The value of this elapsed time is dependent on the distance between the two sites, and the variation of this time provides a value of the blood pressure variation, which can be calibrated.
Skin temperature can be measured by a small sensor attached to the surface of the skin.
This provides a satisfactory indication of caloric exchange between the skin and the environment.
Its variations may be indicative of adaptation to changes in ambient temperature and changes in the surveillance state.
It is also possible to measure variations in potentials | of the skin using the appropriate sensors.
This measurement is a direct indicator of sympathetic nervous system activity.
This may be indicative of a particular reactivity with the environment or a particular emotional state, including possible stress on the part of the person.
According to an embodiment of the present invention, the recording device is separated into at least two modules.
One of these mill- | —dulos includes only the physiological sensors described above 110 and 120 and/or related sensor units 112, 114 and 122. This device is : compact and cannot exceed the dimensions of, for example, a watch.
The | :
« * ,” second module can include environmental sensors 130, 140 and/or 150. A | The third module may comprise the additional sensor 180. The additional sensor 180 may also be included in one of the first and second modules, if possible. | 5 This separation has the advantage that during the night, while the person is in bed, the module dedicated to physiological variables will still be fixed on the person, while the module dedicated to environmental factors could be separated and placed on the side as in the headboard. from the bed. This allows for more stable ambient values and will avoid noise artifacts caused by motion or changes in light level due to a . covered or uncovered light sensor depending on the individual's posture. Each of these separate modules can include its own memory or just a first module includes a memory while the second and/or third module transmits data from its sensors and sensor related units to the first module for storage. Data transmission can be performed over a wireless connection as explained in more detail below. At least two separate modules can also be constructed in this way to connect them to form a single device. In this case, the modules include fastening means and electrical connectors to function as a single device. For example, if only one module has memory, electrical connectors can be used to transmit data from one module to the memory of the other module. In any event, a recording device 100 in accordance with each of the embodiments described above may also include a clock
160. The clock output signal 160 is transmitted to each of the | res or units described above 110 to 150 and 180. Sensors 110, 120, | 130, 140, 150 and/or 180 and units 112, 114 and/or 122 can use the | 30 clock emitted to determine the time-dependent values. Just as an example, the instantaneous heart rate unit 112 and/or the interpulse interval unit 114 may use the clock signal to
| | 33/70 o determine the heart rate of the person being tested and measure the time elapsed between two successive pulse waves, respectively. ' As mentioned above, recording device 100 may include recording means for recording heart rate, body movement and/or detected environmental factor.
The recording means may be an entity or unit of the recording device 100. An entity or unit may be a set of circuits, such as an integrated circuit (IC), constructed to perform the functions of the recording means described below. .
Alter- | natively, the entity or unit is a CI capable of running specific software or firmware that performs these functions.
Preferably and also | . alternatively, the entity or unit is a processor, such as a microprocessor, which executes a conceptual component of software or firmware, where the execution of the conceptual component performs the functions of | | record below. | The recording means may comprise a memory 170 | which is connected to the sensors and units described above of the recording device 100. The memory 170 can be connected to the sensors and units through a bus and is capable of storing the signals emitted from the sensors 110, 120, 130, 140, 150 and/or or 180 received over the bus.
To correctly store the captured values, the recording means may further comprise a memory controller 172 which is connected to the bus as well as to the clock 160. Thus, the memory controller 172 can control the storage of the captured values and can add a time stamp or other signal that can be stored in combination with each captured value.
This allows for additional evaluations and/or calculations of the captured values at a later time.
Memory controller 172 may also be responsible for storing the output values of units 112, 114 and/or 122. Memory controller 172 stores in memory 170 the output values of these units and an optional time stamp or indication of a time period associated with each output value.
According to another modality
| | 34/70.. ity, device 100 does not include memory 170 and memory controller
172. In this case, only sensors 110, 120, 130, 140, 150 and/or 180 and | ' Associated units 112, 114 and/or 122 could be present on device 100. Output signals from the sensors and units described above could then be transmitted to an additional device for storage and/or further calculations. For example, this pickup device | could continuously transmit the captured values to a device that can receive the data and store the received sensor values and/or emitted values from the units described above. Data transmission can, for example, be implemented as a wireless connection (wireless LAN, Bluetooth, infrared data communication) or a wired connection (universal serial bus (USB), Firewire, LAN or other | - network). In accordance with a further aspect of the present invention, the registration device 100 may include a button or other actuator (not shown). If the tested/registered person acts the same, for example by pressing the button, the recording device stores the current time together with an indication of the actuation of the button. This allows you to tag private |:events with a simple press of a button by the person. As an example, only the person could press the button when he or she decides to voluntarily interrupt the recording system, for example, to take a shower, or before going to sleep and again immediately after waking up in the morning. These flagged events can then be used at a later stage in the system to more easily identify particular events as will be more apparent from the description below. | The recording device 100 can also have more than one actuator to identify various predefined events. According to another aspect, the actuator can be used in a certain way to identify different events, such as holding it for 1, 2 or 3 seconds or pressing it once, twice, etc. For all modes, the recorded data stored in memory 170 can be used for calculations and determinations.
o additional nations by a data extraction unit 200. Therefore, data is communicated from memory 170 with data extraction unit 200. A data connection for this data communication can also be implemented as a wireless connection. wired or wired.
By | 5 For example, a wireless connection may be based on wireless LAN, Bluetooth, infrared data communication, or other wireless communication technique.
Wired data communication can be implemented with a universal serial bus (USB), Firewire, LAN, or other network connection.
According to a further aspect, the data extraction unit 200, which includes at least some of its sub-units described below, and the recording device 100 can be integrated in one device, - in this case, the data extraction unit 200 can have direct access to memory 170, for example over a bus.
This device can be constructed, for example, as a wearable device to detect and record the heart rate and/or body movement of a person wearing the device.
To reduce the test subject's distraction during sleep, the wearable device can be formed similar to a wristwatch that is worn on the subject's wrist.
Since people are used to wearing a watch, they will be less distracted by this device during sleep than by the electrodes and wiring of a polysomnography.
Returning to the embodiment shown in Figure 2 and in the data extraction unit 200, a heart rate calculating means 210 may be part of the data extraction unit 200. As already shown for the recording device means 100, the recording means heart rate calculation 210 can also be an entity or unit.
An entity or unit may be a set of circuits, such as an integrated circuit (IC), constructed to perform the functions of the heart rate calculator.
Alternatively, the entity or unit is a circuit capable of executing specific software or firmware that performs these functions.
Preferably and also alternatively, the entity or unit is a processor, such as a microprocessor, which executes a conceptual component.
"” of a software or firmware, where the execution of the conceptual component performs the below heart rate calculation functions. /or interpulse interval unit 114. For example, heart rate calculation means 210 extracts heart rate data constructed from raw values of successive pulse wave intervals (PWI) described above.
The data calculated and output by the heart rate calculator 210 may comprise HR averages, HR variability values, rhythm characteristics and/or HR events or changes as will be explained in more detail now.
In detail, HR averages can be of two types: global HR average (GHRA) and resting HR average (RHRA). The GHRA will be calculated over long periods of time, such as 5 to 10 minutes depending on the time of day or night.
Furthermore, the standard deviation of this mean will be used to quantify the HR variability (HRV) over the period considered.
Therefore, the GHRA calculation will include periods with no body movement (BM) as well as periods with body movement.
This will also provide an average total RH that reflects the influence of environmental factors such as noise, temperature or light variations.
The RHRA will be calculated over much shorter periods, eg 10 to 60 seconds depending on the surveillance state, and during periods when no BM is present or was present during the previous 10 seconds.
The standard deviation of this mean will be calculated to qualify the HR rhythm, that is, whether it is regular or irregular.
Therefore, the RHRA is independent of | motor activity of the tested person although it may still be influenced by environmental factors.
Calculating an average heart rate, such as the GHRA average or the RHRA average, can be performed by averaging the heart rate over a predetermined time interval (period of time). The time interval for calculating an average heart rate, eg the GHRA average or the RHRA average, can be fixed.
By e- | For example, GHRA (which includes periods with and without body movement) can be calculated by averaging heart rate over, for example, 5 minutes, 10 minutes, etc., and RHRA can be calculated by cal - calculate the average heart rate over, for example, 5 seconds, 10 seconds, 30 seconds, 60 seconds, etc.
An average heart rate can also be calculated by averaging heart rate over different predetermined time intervals. Specifically, an average heart rate can be calculated by averaging heart rate over a first time interval in a first situation, and by averaging heart rate over a second time interval in a second situation. For example, in a situation with simultaneous-occurring body movements, the average heart rate could be calculated by averaging the heart rate over a shorter time interval (e.g., 5 heartbeats), while in a situation without or with just a few (negligible) body movements, heart rate could be averaged by averaging heart rate over a longer time interval (eg 30 heartbeats). The range averaging could vary two or more steps (e.g. 2, 3, 4, 5, etc.) or it could vary continuously (e.g. the inverse of an amount and/or intensity of movements bodily). If the time interval varies gradually, the body movement threshold values could be used to select the appropriate time interval to calculate the average heart rate. For example, if the amount and/or intensity of body movements is below a threshold, a longer time interval can be used to calculate the average heart rate. Body movement limits for selecting different time intervals could be defined similarly to the body movement classes further described below. The time interval for calculating the average heart rate could also be changed according to a detected body movement class further described below. | o Variation of the time interval to calculate the average heart rate allows to provide improved accuracy and temporal resolution when greater accuracy is required, for example in situations where there are body movements. In the latter case, the average calculated over a short time interval will still show the variation of the heart rate curve while an average calculated over a longer time interval could smooth it out. In situations with relatively few or relatively few (insignificant) body movements, the time interval for calculating an average can be increased, to increase the quality of classification, for example, by reducing the number of stage transitions. of sleep erroneously detected.
Interval averaging can be determined in terms of heartbeats, or it can also be determined in terms of seconds and/or minutes. In addition, the time interval to calculate the average heart rate could also depend on the current heart rate and/or average heart rate. | Figure 9 illustrates an example set of method steps for adapting a time interval for averaging a heart rate. At step 910, an amount and/or intensity of body movement is detected over a certain period of time. Detection could be performed, for example, in real time, or it could be performed after data has been recorded for several minutes, hours, or days. In step 920, the detected amount/intensity of body movement is compared to a predetermined threshold. The threshold may, for example, be related to thresholds that indicate a sleep stage, a sleep stage transition, etc.
If the detected amount/intensity of body movement is greater than the threshold, the method proceeds with step 930. If the detected amount/intensity of body movement is less than or equals the threshold, the method proceeds with step 940. At step 930 , the time interval for averaging heart rate is set to a first time interval t1, and in step 940, the time interval for averaging r
| : | 39/70 o of heart rate is adjusted for a second time interval t2. Preferably, the time interval t2 is longer than the first time interval t1. The method then proceeds with step 950 and averages the heart rate using the adjusted time interval as determined by step 930 or 940. The method can then be repeated for an additional time frame. For this purpose, the evaluation time could be, for example, shifted by a fixed time, or by a variable time, such as the time interval selected in step 930 or 940. Preferably, the method is repeated until all samples of data to be evaluated.
: Also, returning to Figure 2, an HR 212 event unit can extract data from memory 170. The HR 212 event unit - determines the variation in the interval between two successive pulses which provides a direct value of the variation in heart rate . A reduction in this time interval corresponds to an acceleration of heart rate while an increase in this interval corresponds to a lower heart rate. Thus, two types of HR changes can be extracted from the data stored in memory 170: HR acceleration (HRA) and HR deceleration (HRD). These changes will last from a few seconds to tens of seconds depending on the surveillance state and time of day. These will be detected by calculating a sliding window average and conducting corresponding analyzes performed over a few seconds. Exemplary heart rate gradients over time for an HRA and an HRD are shown in Figure 7.
In particular, an HRA will be observed when the person being tested is moving or when an activation or arousal is taking place. This is a biphasic variation with an initial heart rate acceleration accompanied by a heart rate deceleration. This deceleration can be accentuated and the lowest HR value can be less than the initial average level. During surveillance, any BM or reaction to an external stimulus from the physical environment will be accompanied by an HRA. During sleep, HRA will be produced by either BM or an excitation Ega.
" dog.
This excitation can be internal or due to an external cause, for example noise.
The HRA will be defined by its amplitude, i.e., the difference between the highest instantaneous HR value and the next lowest instantaneous HR value, and its duration, i.e., from the start of acceleration to the return of the initial HR value. (see also Figure 7). In addition, an HRD will be observed in the absence of either BM or excitation. This is a monophasic change with a progressive decrease in mean heart rate from one level to a lower one.
This is usually observed when the individual is relaxing or when there is a transition from wakefulness to light sleep or from light sleep: to deep sleep.
In these latter cases, HRD can last several minutes
In addition, the heart rate calculation means 210 - can also determine whether some items of pulse wave interval (PWI) data are abnormal or missing.
To improve the classification of HR data, the present invention also provides for the recovery of missing or abnormal pulse wave interval data.
Therefore, the | heart rate calculation unit 210 can perform PWis recovery as described in more detail with reference to Figure 6. l Returning to Figure 2, the data extraction unit 200 may further include a body movement calculation means 220. As previously noted, the body motion calculation means 220 can also be an entity or unit.
An entity or unit can be a set of circuits, such as an integrated circuit (IC), built to perform the functions of the body movement calculation medium.
Alternatively, an entity or unit is a circuit capable of executing specific software or firmware that performs these functions.
Preferably and also alternatively, the entity or unit is a processor, such as a micropro | terminator, which executes a conceptual component of a software or firm- | ware, where the execution of the conceptual component performs the calculation functions
culoofbody movement below.
This body movement calculation means 220 calculates, based on the recorded acceleration values, the intensity and/or duration of:
| 41/70 o every bodily movement of the person.
For example, the means of calculating mo- | Body Sensor 220 Accesses and Evaluates Logged Data from the Body Sensor | ' acceleration 120 and comparator unit 122. As described above, recorded raw data of body movements can be obtained over a certain period of time, for example, depending on processing power and memory capacity, this time period can be adjusted from less than one second to more than five or even ten seconds.
Preferably, raw recorded body movement data is obtained every second.
A counter 222 may be part of the motion calculation means. body movement 220 or may be a separate unit within data extraction unit 200. Counter 222 determines the intensity of movement by counting the number of BMs per second.
Another unit comprised of or connected to the body movement calculating means 220 may be a duration determining unit 224. The unit 224 calculates the duration of the body movement, i.e. the | number of successive seconds where the move counts were | determined by the counter 222. According to another embodiment, the counter 222 and/or duration determining unit 224 may also be part of the recording device 100. Since the recording device 100 provides a clock 160, the acceleration captured by the sensor 120 can be directly used by the con- | 222 and duration determination unit 224. In addition, according to | In this embodiment, the counter 222 and duration determination unit 224 store their resulting outputs in memory 170. Returning again to the embodiment shown in Figure 2, the data extraction unit 200 may further comprise an environmental calculation means 230 that calculates particular values of the recorded data captured by the noise sensor 130, light sensor 140 and/or temperature sensor 150. The environmental calculation means 230 may be an entity or data extraction unit unit 200. This entity or unit can be a set of circuits, such as an integrated circuit (IC), built for | The
| 42/70 : » . . to perform the functions of the environmental computing means 230. Alternatively, the entity or unit is a circuit capable of executing specific software or firmware that performs these functions. Preferably and also alternatively, the entity or unit is a processor, such as a microprocessor, which executes a conceptual component of software or firmware, where the execution of the conceptual component performs the environmental calculation functions below.
The environmental calculation means 230 may comprise a noise level unit 231, which determines whether an ambient noise exceeds a predefined level or threshold. In addition, the noise level unit 231 can also compare the captured noise values stored in the memory 170 with two or more thresholds to determine different noise levels. A noise event unit 232 may also be included in the environmental calculation means 230 and evaluates from the captured noise data whether a particular noise event has occurred. A noise event may be, for example, noise that exceeds a particular level over a predefined period of time, such as those levels determined by the noise level unit 231. In addition, the environmental calculation means 230 may include an average temperature unit 233 that calculates the average values of ambient temperature over certain time periods. For example, the ambient temperature can be averaged over 10-minute intervals, 30-minute intervals, or 1-hour intervals. The present invention is not limited to a particular time period for averaging ambient noise. So any other time period like 2, 4 or 6 hours might also be possible.
In addition, the calculation medium sets! 230 may also include a temperature change unit 234. The temperature change unit determines whether the temperature has changed between certain time points. For example, the temperature change unit 234 can determine whether the temperature has changed by a predefined amount of degrees between a time point and, for example, 5 or 10 minutes later. to the unit of
. temperature change 234 can also determine temperature changes during particular time periods which can be pre-set. 7 These time periods can be five minutes, ten minutes, 30 minutes | ts, 60 minutes or longer. The present invention is not limited to any particular time period, but may also be based on other predefined time periods.
A light level unit 235 included in environmental calculation means 230 determines whether light exceeds a particular value based on recorded light data. The light level unit may comprise a | 10 plurality of predefined thresholds with which the recorded light data | . are compared. Furthermore, the calculation means may comprise a light shift unit 236 for determining changes in data values | of light recorded.
Furthermore, the data extraction unit 200 may further comprise an additional calculation means 240 which calculates particular values of the recorded data captured by additional sensor(s) 180. The additional calculation means 240 may be a data extraction unit entity or unit 200. This entity or unit may be a set of circuits, such as an integrated circuit (IC), constructed to perform the functions of the environmental computing means 240. Alternatively, the entity or unit is a circuit capable of executing specific software or firmware that performs these functions. Preferably and also alternatively, the entity or unit is a processor, such as a microprocessor, which executes a conceptual component of software or firmware, where the execution of the conceptual component performs the environmental calculation functions below.
Additional Calculation Means 240 can be adapted to perform any necessary calculations based on the type of additional sensor(s)
180. For example, if additional sensor 180 captures pulse oximetry, additional calculating means 240 may calculate one or more blood saturation levels based on one or more predefined thresholds. In addition, if
| | 44/70 ” the additional sensor(s) allow the determination of the transit time | (PTT), the additional calculation means 240 performs the PTT calculation, ' ' which has already been described above. 1 In addition, the additional calculation medium 240 can also calculate caloric exchanges between the skin and the environment based on the captured skin temperature.
Also, a sympathetic nervous system activity can be determined by means of additional calculation 240 by comparing the electrical potentials captured from the skin with one or more thresholds.
Thus, one or more levels of skin temperature and/or skin electrical potentials can be calculated: The data extraction unit 200 and all its components, such as media or units 210 to 240, will access the recorded - stored data in memory 170 of recording device 100. As mentioned above, this data access can be implemented over a bus or a data connection.
The output of units 210 to 240 of data extraction unit 200 is also stored in a memory (not shown) of data extraction unit 200 for further determination.
In an additional embodiment, data extraction unit 200 is part of recording device 100. In that case, units 210 to 240 may use memory 170 to read recorded data values and to write calculated output values.
In connection with this embodiment, the combined device is capable of transmitting the data extracted by the data extraction units 210 to 240 to another device through a wired and wireless interface and data connection as described above.
According to yet another embodiment, the recording device 100 and the data extraction unit 200 are separated into one or more modules.
As already presented above, these modules can include all sensors and physiological units (110 to 122), the sensors and environmental units (130 to 150), and the additional sensor 180. In addition, each module will include the units of corresponding calculations (210 to 224; 230 to 236; 240) described in relation to the data extraction unit 200. Figure 3
-. illustrates a block diagram of a classification unit 300, which can | comprising a heart rate rating means 310, body movement rating means 320, environmental rating means 330 and/or additional rating means 340. Each means 310 to 340 | | 5 can be an entity or unit of classification unit 300. This Í | entity or unit may be a set of circuitry, such as an integrated circuit (IC), constructed to perform the functions of the respective means 310 to 340. Alternatively, the entity or unit is a circuit capable of executing specific software or firmware that performs these functions. Preferably and also alternatively, the entity or unit is a process. sador, like a microprocessor, that executes a conceptual component of a software or firmware, where the execution of the conceptual component . performs the functions described in more detail below.
As one skilled in the art will recognize, the classification unit 300 may comprise one or all of the means or units 310 to 340 | depending on the sensors installed in the recording device 100. For example, if the ambient sensors 130 to 150 are not present in the recording device 100, the classification unit 300 may not need an environmental classification unit 330, A classification unit 300 is capable of accessing the memory where the data emitted by the data extraction unit 200 and its subunits are stored. Therefore, the classification unit 300 provides an interface for wireless or wired data transmissions, such as a network interface, serial or parallel bus interface, etc.
The heart rate classification means 310 classifies the recorded data output from the heart rate calculation unit 210 either directly from the unit 210 or through a memory such as memory 170. heart rate, heart rate variability values, rhythm characteristics and/or events or heart rate changes. Each of these values, if determined by the heart rate calculation unit 210, can be classified.
AÊ > hs AAAACÔÊÊÁÊAA222222222222—25c2—52—ô2itliro” Ôi.º P PA3b.X 2é£,A.”. “ Â2ÊÉ,»órP2 O ir.“ OBA“..AOÂêt“OOO US o C— O 46/70 o For example, the average HR can be classified into an average, high, intermediate and low. In addition, heart rate variability can also be classified as, for example, very high, high, intermediate or low. The classical LF/HF ratio can be obtained from a spectral analysis of heartbeat intervals. Other ranks may have a different number of ranks, such as 5, 7, or 10 levels. The present invention is not limited to any specific number of classes. The classification means of HR 310 can be modified to distinguish between more or less classes as necessary.
During wakefulness, the average heart rate may vary consi- . from 60 to 80 beats/minute during rest, to 170 to 190 during very heavy exercise. The maximum heart rate value depends on the person's age and previous training. During sleep, the average heart rate can be as low as 40 beats/minute. Young, physically well-trained adults can reach an even lower value during sleep, such as 35 beats/minute. Thus, the classes into which the heart rate classification means 310 classifies the recorded data can be adjusted differently for the waking state and for the sleep state. In addition, classes can be adjusted to the tested/registered person based on age and training status. person's physical mind. | Furthermore, the HR rhythm can be classified as, for example, irregular, irregular, regular, and so on. Similarly, HR events or changes can be classified as acceleration, deceleration, or an evoked response. As noted above, the present | invention is not limited to these classes, but may include more or less | classes. To deal with future discoveries, the classification means classes | HR 310 can be changed if necessary.
Furthermore, as noted above, classification unit 300 may include a body movement classification (BM) means or unit 320 that can classify recorded body movement data.
Each move can be classified according to its duration (in
the seconds) and its intensity (counts per second). As noted above, the number of movements during each second is recorded on device 100. In case there is no movement, the count will be 0 during the second considered.
The BM classification means 320 produces data output from the body motion calculation unit 220, either directly from the unit 220 or through a memory such as memory 170. The BM classification means 320 may use the intensity of body movement and/or its duration calculated by the calculation unit of BM 220. The classification means of BM 320 can perform one or more classifications of body movement. For example, the BM 320 classification means classifies the tested person's BM into three different classes: large movement (LM), . such as a change in posture, small movement (SM), such as the movement of a limb or a hand, and contractions (TM), such as very short movements of the extremities of the body that occur during REM sleep.
In addition, the BM intensity can be classified into some ranges, such as 1 to 2, 3 to 5, and 6 to 10 counts per second. Classes can also be less precise, such as many, limited in number, sometimes or few. Combinations of the two classifications or successive classifications can also be made, such as many movements that usually occur continuously, without contractions over a long period or a few isolated small BMs.
The classification unit 300 may also include an environmental classification means 330 that classifies the environmental factor values recorded from environmental calculation unit 230 and/or subunits 231 to 236.
For example, noise levels calculated from the noise level unit 231 can be classified, for example, into low, intermediate or high level noise. Also, the noise events determined by the noise event unit 232 can be classified by their amplitude, duration, slopes of the rise and fall periods. For example, a noise event can be classified as highly variable, a short but loud noise event, or at a low level but over a long period of time.
THE SS COS THE CS 48/70 | .. odo of time. | The environmental classification means or unit 330 can also classify the average temperature and temperature changes calculated by the average temperature unit 233 and temperature change unit 234 respectively.
For example, the average temperature over a particular period of time can be classified as high, medium or low or as variable.
In this case, the environmental classification means 330 can also take into account the time of day that the average temperature is calculated.
For example, a particular average temperature might be | 10 considered to be high overnight while the same average temperature. day is classified as intermediate during the day.
In the same way, temperature changes can be classified as variables or are- | : able, either as abrupt or long-term changes depending on the duration of change determined by the temperature change unit | 15 234 : In addition, the light levels calculated by the light level unit 235 can also be classified by means of environmental classification 330 into particular classes as variable or stable or as light, dark, etc.
Also, the light level changes calculated by the light change unit 236 can also be classified by the environmental rating means 330 into particular classes like slow change, fast change, etc.
The environmental rating means 330 can also form classes of two or more values calculated by the units of the environmental rating means 230, for example from units 231 to 236. For example, the determined light level may be taken into account when classifying - the temperature change remains.
For example, a person stepping out of a building into warm outside air can be affected by an abrupt change in temperature as well as an increased light level.
Finally, the additional classification means or unit 340 can | 30 classify the extracted or calculated data by the additional calculation unit 240 (Figure 2). For example, blood oxygen saturation levels can be classified as low, medium, and high.
Again, other classes and a different number of classes are possible.
Furthermore, in the case that pulse transit times (PTTs) are calculated by the ! ' of additional calculation 240, PTTs will also be classified into classes such as short, medium and long.
Depending on the additional sensor(s) employed 180, other classes of data can be derived.
The temperature | Skin care will be classified into classes such as low, medium or high.
Similarly, the electrical potentials of the skin will be classified into classes, such as high, moderate or low.
Regarding heart rate classification means 310.0 body movement classification means 320, environmental classification means 330 and additional classification means 340, it will be noted that the classes into which particular data are classified can be - set by a user.
For example, if particular classes are essential in the future, classification unit 300 can be adapted as well. 15 well to take the new classes into account.
On the other hand, the clas- ; existing ses that are of less interest may be removed from the rating means or units 310 to 340. In addition, any limits stored on one of the means 310 to 340 can be modified to adjust the rating unit functions 300 Returning to Figure 4 now, this shows a means of determination 400 to determine an alert state, a sleep stage, a sleep stage transition and/or a sleep event of the tested person.
The determining means or determining device 400 may include evaluating means 410, such as a sleep status determination unit 410. The determining means or determining device 400 may further comprise a sleep stage determining unit 420 and an activity determination unit 430. The determination means 400 and its sub-means 410 to 430 can be an entity or unit.
This entity or unit may be a set of circuits, such as an integrated circuit (IC), constructed to perform the determination and other functions described below. Alternatively, the entity or unit is a circuit capable of running software or firmware.
the specific re that performs the functions of the determination means 400 as will be described in more detail below. Preferably and also alternative- | In mind, the entity or unit is a processor, such as a microprocessor, that executes a conceptual component of software or firmware, where the execution of the conceptual component performs these functions. | The evaluation means 410 is optional as the recording device can only be used during the sleep periods of the tested/enrolled person. If the recording device is worn during a period- | Over a longer period of time including waking periods and sleeping periods, the assessment means 410 assesses whether the person being tested is in a waking or sleeping period. This assessment, also referred to co- ! Mo determination of surveillance status, can be performed by analyzing the ! . elaborated data from the 300 classification unit (Figure 3), when analyzing the | data calculated by the data extraction unit 200 and/or a combi- ! nation of classes and calculated data. In other words, the classes determined from the captured and recorded data are taken into account when determining the vigilance status of the tested person. Also, recorded data or a combination of recorded data and classified data may form the basis for further determinations. This may particularly include heart rate data and/or classes (from the 210 / 310 unit) and/or body movement data and/or classes (from the 220 / 320 unit). Additionally, if present, environmental classes and/or additional classes of units 230 / 330 and 240 / 340 can also be used to determine surveillance status or at least verify surveillance status.
The Table | the following provides HR, BM, and environmental classes from which the wakefulness state determination unit 410 can determine that the tested person is in a waking state or a sleeping state.
51/70 | the Table | | E ee | mo utoregder | HR regia few Small moves | many, generally | not too many, isolating Environmental Noise rare events Basically, large variations in heart rate and/or the occurrence of numerous movements, in particular large movements, will be present during wakefulness and not during sleep.
Also, sudden variations in environmental physical factors, such as numerous noises, or frequent changes in ambient temperature or ambient light, will be indi- | captives of a movement and therefore an awake person. | If it is determined that the person's surveillance status is a | waking state, the activity determination unit 430 determines an activity level, such as resting, moderately active, or very active.
This determination will be based on the number and sequence of large and small movements, such as numerous by an active person and small | by a person at rest, as well as elaborate HR data such as higher mean levels, more HR events or changes, greater HR variability, and more irregular rhythm in the very or moderately active person than in the resting person.
Exemplary HR classes and BM classes of an awake and active person are shown in the column "Wake (W)" of Table |! below.
If the test subject's wakefulness state is determined as the sleep state, the sleep stage determination unit 420 distinguishes between different sleep stages and/or identifies sleep events. no, This distinction and identification may be based on the heart rate classes identified by the 310 unit. In addition, the distinction and identification may also be based on the body movement classes identified by the 320 unit and/or variability classes of heart rate.
In addition, the sleep stage unit 420 can also distinguish between different sleep stages and can identify sleep stage transitions and/or sleep events using a cross-comparison between HR and BM data. The cross comparison. you can, for example, compare HR classes and BM classes within a temporal relationship. This temporal relationship can include classes that “are based on data captured at the same time point or within the same time period. In addition, classes can also be base- | 15 adasem HR data captured before or after the capture of BM data Or vice versa. Cross-comparison can be performed according to some specific rules and criterion values like those given in Table |! below. Table II Vigil (W) | Light sleep | Pro sleep | Deep REM sleep HR High W minus 5 |LS minus 5| Enter We at 20 b/min | at 10 b/min LS Variability- | big small | very small of quena z Rhythm regular regular Very irregular Changes | many none | few and or short HR events Large yes yes moves Small yes yes no ES moves | [Contractions| “no | no | no | sm As shown in Table II, large movements (LM) and small movements (SM) can be observed during wakefulness and during sleep.
it sleep.
However, their number and especially their succession will be somewhat different in these two different surveillance states.
During wakefulness, LM and SM will be numerous and sometimes occur continuously.
This will depend on the individual's activity and the amount of these motor activities that will be used to qualify periods of intense motor activity | and periods of low motor activity.
During sleep, LM and SM will be ' | infrequent and most of the time separated by long periods of | | immobility.
Furthermore, contractions (MT) will be observed only during sleep and particularly during REM sleep phases.
TM will last. one or two seconds only and the number of counts per second will be low.
TM will occur by bursts separated by a few seconds or de- | - hundreds of seconds.
In addition, the wakefulness state unit 410 and the sleep stage determination unit 420 take into account that heart rate and body motility are related as body movement induces an increased need for oxygen delivery to the body. the muscles.
Therefore, any bodily movement is performed by an increased heart rate which is of the HRA type.
A large or prolonged BM is accomplished by a larger and longer increase in HR.
The cessation of BM is followed after a variable time by a reduction in HR and a return to its previous level.
The temporal relationship between HR and BM provides a satisfactory indication of the current situation.
For example, if the individual is moving voluntarily, an HRA occurs along with the BM.
If the individual is internally aroused (during sleep), an HRA precedes a BM by approximately 6 to 8 heartbeats.
If the individual is responding to an external stimulus, such as noise, an HRA occurs with or without a BM.
When these are combined, a BM can occur within less than the first 5 heartbeats of an HRA.
If the individual is involuntarily moved by someone, for example a companion, a BM occurs first and then an HRA occurs after a few seconds.
Furthermore, if a pulse oximetry implemented with an additional sensor (see Figure 2) is present, the above-described interrelationship of BM and HR can be: verified with rated blood saturation levels from the same period of time.
An arousal is a sudden brain activation.
This may be associated with an abrupt shift from a "deep" stage of NREM sleep to a "lighter" stage of NREM sleep, or from REM sleep to | wakefulness, with the possibility of awakening as the end result.
Arousal may be accompanied by increased heart rate as well as mo- | bodily movements. . In addition, while environmental factors do not need to be recorded, their respective values and combinations can also be used by the wakefulness state determination unit 410 and the sleep stage determination unit 420 to determine or check for l 15 sleep stages, sleep stage transitions, or sleep events identified.
The noise level, ambient temperature and ambient light should be more | or less constant if the individual is in the same environment.
During sleep, for example, the ambient temperature and ambient light should not change much.
Its value and stability will be indicative of very stable environmental conditions.
In contrast, during the waking period, these environmental values will often change if the individual is moving from one place to another, for example, going out, using a | car, etc.
Extreme values will still be indicative of severe environmental conditions (very low or very high ambient temperature, high noise level, etc). The effects of these environmental conditions on the HR will be evaluated by units 410 to 430 of the determination device 400 to measure the possible limitations and impact of the physical environment on the individual. : Additionally, the sleep staging unit 420 can identify a sleep event.
The sleep event occurs during sleep spontaneously or in response to external stimuli.
For example, symptoms of sleep disorders such as sleep apnea, restless legs, nightmares, night terrors, etc. can be identified by specific changes
fo 3**:N JA 7a EÂ$A2AAA“AA-- AHAUUM"“L.) 0 07Tp7 . "> 2Ô2ÓI r PC) P. 55 *iÊl.ÊSuMàtim MuiusÉMMM*OiOS!S!NSíPúÀOSÔSÕ“S SS “OSS ôS ôÚÔA“ASSOSSÊSSASSSSMe*SSSSA2o 9ºOºÔSSS“SÔS SS SS SRS 55/70 in heart rate and body movements.
In such cases, environmental data such as an ambient noise level is often very valuable.
The noise of an individual's final breath in sleep apnea and snoring, or talking and screaming during a nightmare or night terror are additional signs that confirm physiological changes.
A sleep event
m sudden awakening due to ambient noise will be identified by the !
physiological changes and the previous noise event.
But here too, | | the main changes observed in the physiological data and environmental values will be used to confirm or to identify the origin of the cause.
sado sleep event Í | . An example of using logged information from the sensor(s) | additional(s) 180 (Figure 2) consists of pulse transit times (PTTs). :
- If the calculated and classified data from these sensors are | available, a conclusion can be drawn about blood pressure art- | rial of the tested/registered person during particular time periods.
A | blood pressure is then used by the sleep staging unit 420 to determine and/or verify sleep stages and/or sleep stage transitions and/or particular sleep events.
Thus, a sudden change in blood pressure can be indicative of a sleep disorder due to an environmental event with a noise.
An additional example for detecting a sleep event involves measuring blood oxygen saturation called "pulse oximetry" with an additional sensor 180 (Figure 2). Measured and classified data from this "pulse oximetry" may be associated with movement data. - are classified and to the noise level by the sleep staging unit 420. If there is a detected noise, for example the noise that occurs at the end of the apnea (sigh), the sleep staging unit- on the 420 can determine whether there was also a short movement and an associated reduction in blood oxygen saturation.
If these determinations are positive, this is automatically identified as a sleep event associated with sleep apnea.
Thus, during sleep, any occurrence of a noise event
| 56/70 -. gone will be detected and its possible impact on HR and BM will be evaluated.
The test person's sleep can be interrupted by noise and the consequences' can be important in terms of sleep structure and sleep fragmentation.
Therefore, the impact of nighttime noise on sleep can be determined.
In addition, sudden changes in ambient temperature may not be expected when the individual is resting or sleeping.
These changes can occur when the individual is changing places.
During sleep, the ambient temperature can differ from a neutral condition. This can be very hot in summer or very cold in winter. . These conditions can impact and disrupt sleep.
If these extreme values are observed, an assessment of sleep structure and possible disturbance will be performed.
Finally, the ambient light level may differ depending on | of the place where the individual lives.
This can also vary depending on the individual's movements during the day.
Its value will be important to determine if the conditions of the environment that it sleeps are those of a low lighting level as expected.
As noted above, recording device 100 (see Figure 2) may include an actuator, such as a button, to mark events | particulars by the tested/registered person.
The determination device ' | 400, i.e. unit 410, 420 and/or 430, could then identify the marked events within the recorded data and use this information when determining the wake state, sleep stage or a sleep stage transition, and /or a sleep event, respectively.
Since the marked event can be predefined in the system, the determining device 400 | is able to clearly identify the associated wake and sleep states.
Furthermore, more than one event (type) can be marked using different buttons or actuation types.
This can even help the determination device400 with its tasks.
This also allows training the device determination 400 or the classification performed by the device 300 as described in more detail below.
-. The determination device 400 also determines transitions from one stage to another as illustrated in Figure 8 in a healthy individual.
These transitions can also be determined by the wakefulness state determination unit 410 and/or sleep stage determination unit 420. Figure 8 shows a wake state as well as a deep sleep, light sleep, and sleep stage. paradoxical sleep (REM). As indicated by the arrows, a transition from one state/stage to another is possible between most of these.
However, a transition from wakefulness to deep sleep or from paradoxical sleep to deep sleep will not occur without the intermediate light sleep state. . Transitions from one stage to another can be divided into descending transitions, that is, those that start from wakefulness or a lighter sleep stage and result in a deeper sleep stage, and ascending transitions, that is, those that that range from a deeper stage of sleep to a lighter stage of sleep or wakefulness.
These two types of transitions are preceded and accompanied by specific changes.
Exemplary criteria used by the wakefulness state unit 410 and the sleep state unit 420 for the two types of transitions are given in Table III (downward transitions) and Table |V (upward transitions) below. | | o Table 1ll (Descending transitions Descending transitions- | Heart rate- | Body movement- | "Observations . Descending aca ral from Wake to So- | Strong reduction of | BM disappears | When mild no RHRA occurs; progressively | awakening; returns HR becomes regular the transition occurs-| to LS when lar and varies less when not o- | HR returns to vel; runs more movement- | value prior to | Transition when ment awakens | there is no HRA for 30s from waking to so- This transition | in the deep Never occurs ' from waking to so- | Strong reduction of | No BM during- | This transition is in REM RHRA; during transition, job observed only Í Transition when | however can occur- | in narcolepsy there is no HRA rer TM when falling asleep; : for 30s; after awakening HR becomes irregular a short LS is | home; HRV increases usually present From light sleeper to | Reduction of R- | No BM is | First transi- deep HRA; HR very | present during night | r; several minutes an-| re very fast- HRV is very pe- | transition tes | mind; the following are longer | Light sleeper to! HRV increases i- | No LM or | This transition is unexpectedly REM, | SM, however TM [highly check-until o- |generally occurs | vel due to strong HRA rush; by explosions | HR periodicity becomes very phase occurrence | irregular REM (see figure '1 From REM to sleep) This transition seo | [Em
-. Table IV (Ascending Transitions) . Ascend Transitions-| heart rate | Body movement-| "Observations . acaral teeth from deep sleep | In most of the | Before transition- | This transition to light or wakeful cases there is a | tion, a | usually occurs HRA accompanies- | LM change | after a long | an LM. | or posture accompanying |period of immobilization- If transitioning to | accompanied by a total jity or after LS: RHAEHRV| large HRA. the occurrence of are moderate- | If transitioning to Jum mentally greater external events |LS: BM disappear-| (eg, rumble in DS. ce. from above) If it transitions to | If it transitions to W: RHRA and HRV | W: BM is much greater pressure.| feels and repeated. ' From deep sleep This transition to REM sleep is never observed. From paralyzed REM sleep A first HRA|TM disappears and |In the elderly population- light or wakeful sleep | is usually a- | BM is usually | sa, the phases of lia accompanied by | associated with this REM sleep generates a BM transition.
The fre- | mind end If carried over to | frequency and inten- | due to an LS: RHRA is BM approximation | transition to W. closely to |help distinguish [This new stage same, but HR| between a transi- Jé usually man- Ú is regular and HRV is | çãoparaLSou | had during al- ' reduced. for W. few minutes.
If transitioned to W: RHRA is noticeably higher and HRA is frequent and associated with BM.
In accordance with a further aspect of the present invention, the determination device 400 is capable of self-improvement.
Since the device has recorded data from several days or weeks at hand, it can adjust the units of determination according to the behavior of the tested/enrolled person.
If a first combination of the classes and/or HR or BM data is found to clearly identify sleep, a specific sleep stage, sleep stage transition or sleep e-'wind, the determination device 400 can search for combinations. similar ones that are not distinctive as the first combination, but are found more frequently.
Thus, the device 400 can adjust the sleep identification criteria, sleep stage, sleep stage transition and sleep event.
In addition, the determination device 400 can also transmit data to the classification unit 300 to configure the classification algorithms.
In this way, the classification can be adjusted to: better identify sleep, sleep stages, sleep stage transitions and/or sleep events. - These techniques can also be used to improve the device 400 and unit 300 for better detection of the surveillance state Using the recorded data, the device 400 can build profiles of the person tested to obtain average levels, peaks and variations of HR, BM, environmental and/or other captured data.
This can then be used to adjust the rating and determination of unit 300 and device 400 to the daily/nightly behavior of the person being tested.
It can also be used to identify changes induced by a new medical treatment for the person being tested or to assess whether that treatment is resulting in an improvement or deterioration in that person's health status.
Similarly, the device 400 can be improved by gathering information obtained from large groups of registered people.
Thus, the device can better assess data for a specific age group or sex.
Sleep physiology is very different in children, young adults, or the elderly, but within an age group, sleep characteristics are very similar.
Therefore, the device 400 can integrate the collected data to better assess the normality of the individual recorded data compared to the characteristics of the same age or sex group. The determination device 400 can be connected to the classification unit 300 (Figure 3). ) through a data connection to k 61/70:. access the different classes issued by the classification unit 300, This data connection can be implemented as a wireless or wired connection.
For example, a wireless connection might be based on wireless LAN, Bluetooth, infrared data communication, or another wireless communication technique.
Wired data communication can be implemented with a universal serial bus (USB), Firewire, LAN, or other network connection.
The data connections between the devices and units described 100 to 400 can also be used to transfer the analysis results to the classification unit 300, the data extraction unit 200: and/or the recording device 100. Each of these devices may be able to display or otherwise output the analysis results.
For example, in the case of a wearable device, a display can be integrated where the tested/registered person can manipulate the analysis results.
In addition, a printer can be connected to one of the | positive 100 to 400 to print the analysis results.
Additionally, the determination device 400 may be able to send an analysis report that includes the results over a network connection.
For example, the device 400 can send an email or data packet to a predefined recipient, such as the tested/registered person or medical staff or supervising physician.
The determination device 400 may also send or allow access to the raw recorded data (see memory 170 of Figure 2), to the output of the data extraction unit 200 and/or to the output of the classification unit 300. A person trained staff can conduct additional analysis of data received or accessed to verify results | of analysis or to provide adjustments to the means and units described above in relation to Figures 2 to 4. In the case of a record that lasts several consecutive days or weeks, a description of the significant changes that occur over the long period may be emphasized and commented according to the situation.
As examples, this may be the case during a medical treatment of a patient or during a training period of an athlete or during a period of dyssynchrosis of a person who is |
.. traveling.
According to another embodiment, the classification unit " 300 is part of the determination device 400 which together form an analysis device.
In this case, a data connection is established; 5 between the determining device 400 and the data extraction unit | 200 (Figure 2) or a memory such as memory 170, where the extracted data is stored.
Data connection can be implemented in the same way as noted above.
According to yet another embodiment, the devices and units 100,200,300 and 400 are combined into one device.
In that case, the . processors and memories of devices and drives can be shared, this reduces production costs.
This combined device can then be connected to a display device or printer to output the wake states and/or sleep stages determined over the recording time.
However, the present invention is not limited to a specific implementation of the different devices and units 100, 200, 300 and 400. It will be appreciated that any combination of the same devices, units and their components are within the scope of the present invention.
Now with reference to Figure 5, the present invention also defines a method of determining sleep stages, such as that performed by the devices and units described above in relation to Figures 2 to 4. The method illustrated in Figure 5 begins with the detection of a heart rate at step 510 of a person to be tested.
This heart rate detection can be performed by a sensor, for example, capturing a pulse wave from the person being tested and deriving a heart rate from it.
Furthermore, in step 520, a body movement of the tested person is detected.
This detection can be based on an acceleration sensor or another sensor capable of recording a person's movement.
As noted above, body movement detection is focused on skeletal muscle movement.
For example, eye movement
-. or movement of any bowels or the person's heart are not of interest since a determination of all stages of sleep is not possible from these movements individually. A skeletal muscle movement can be a movement of a limb such as the person's arms and legs, torso, or head. Each of these movements will generally produce a movement of the person's wrist or ankle where step 520 detection can occur. The detected heart rate is then classified at step 530 into particular classes as already described above with respect to Figure 3. A calculation of an average heart rate, rate variability. heart rate, heart rate changes or rhythm characteristics as described above in relation to Figure 2 may precede the heart rate classification.
The detected body movements are classified in step —S40 as explained above in relation to Figure 3. Also, a calculation of duration and intensity of body movement can precede classification.
Based on the identified heart rate classes and body movement classes, the person's sleep stage and/or a sleep stage transition can be determined in step 550. This determination can be preceded by the determination of a surveillance state. The determination at step 550 is described in more detail above with respect to Figure 4.
Furthermore, according to step 560 one or more sleep events are detected as also described above with respect to Figure 4.
Also, in a step 555, a combination of a particular heart rate class and body movement class is identified when performing a cross-comparison. This identification can be performed in relation to a particular period of time. For example, as described above, one determines whether a particular heart rate class and a particular body movement class from data captured during the same period or within a close temporal relationship has been determined. gives. Other combinations can be a heart rate class for | |
*. that precedes or follows a certain class of body-movement | ral or vice versa. ' " All of these identified combinations can then be used for the sleep stage determination in step 550. Exemplary combinations are shown above in Table |. Referring to Figure 6, to improve the classification of the HR data, the present The invention also provides for the recovery of missing or abnormal pulse wave interval (PWI) data.
For example, the heart rate calculation unit 210 (Figure 2) can perform the steps described in relation to Figure 6. . In detail, as also explained above, successive pulse wave intervals (PWI) are recorded in a step 610 to - then retrieve the instantaneous heart rate.
The PWis of more than | 2500 msec. (milliseconds) correspond to an instantaneous heart rate of less than 24 beats/minute (b/min). These PWis are considered missing PWI data.
Also, intervals shorter than 300 msec. correspond to an instantaneous heart rate of more than 200 beats/minute and are considered suspect PWiIs.
Therefore, a determination is made at step 620 whether a registered PWI is within the 300 msec range. at 2500 msec. (0.3s to 2.5s). | If the PWI is within this range, the PWI is considered correct! to and can be used for further calculations or sorting HR data.
If the PWI is not within this range, the method proceeds to step640 in case the PWI is greater than 2500 msec.
Then it is determined in step 650 whether the PWI is longer than 10 seconds.
If so, this range is considered to be missing data.
If the PWI is shorter than 300 msec. (step 680), the method proceeds to step 690, determining whether the shortest number of PWis | 30 than 300 msec. is less than 3. If the number of these short PWils is greater than Or equal to 3, these intervals are also considered to correspond to missing data.
I 9.) |Nm“ss eR :7-22a 22" .n ) n ss. ia) O 2 2 1 , 11 5i*Wa A“ AAA A" aT 2a Aa EDAaAA Ô PN U [TN TA AAAIAAAS3ATTTIA (NA NA3IA O CS="Ã an E nu“222 Aa ZA“. -Á " —a=— " ,sT,0P M" 0 dM , . º . 65/70 :, Missing data will not be recovered as these will correspond to a technical problem in the recording process. If only the "missing data" is related to the pulse wave recording, then a fault will be caused in the pulse detection system or by an incorrect positioning of the recording device. missing data is related to all logging channels, this is due to a memory or battery failure. registration positive, Under certain conditions, the missing PWI (2.5 s < PWI < 10 s) and the suspect PWI (PWI < 0.3 if XPWI < 3) can be retrieved in step 670. To do this, first it turns out that at enos 10 - PW! precede the absent or suspect PWI and that at least 10 PWI | the same happens in the normal range (0.3 s < PWI < 2.5 s). If applicable, the missing PWI or the suspected PWI is replaced by the mean value of the preceding 10 normal PWIs and the 10 succeeding normal PWIs.
The present invention utilizes the fact that changes in sleep stages are accompanied by changes in vegetative (heart rate) and motor (movement) functions. Considering these two variables and their temporal relationships, the present invention makes it possible not only to distinguish these stages but also to determine very precisely the moment when sleep stage transitions occur. Some specific examples of these transitions are provided in Figures 10 to 13. | For example, Figure 10 shows a transition from light sleep to REM sleep. This figure represents a 20-minute period recording. In the upper part of this two electroencephalograms (EEG) and two electro-oculograms (EOG) are recorded. The vertical arrow indicates the exact transition from light sleep to REM sleep as determined using the conventional sleep stage score by visually analyzing the top four traits. The lower part of the figure shows the records of an average of . heart rate in a short time (measuring time is approximate- |
| 66/70 -o mind 5 seconds) and body movements. The left half of the figure shows that heart rate variability is small in light sleep" except when the individual is moving. The two movements that occur during light sleep are accompanied by large increases in heart rate (change in heart rate of about 20 beats.) The right half of the figure shows that during REM sleep, heart rate variability is large and that numerous observed heart rate changes (except the largest) are not accompanied by Thus, this sudden change in the relationship between heart rate and body movements is specific to the transition from light sleep to REM sleep (see also table II!) Figure 11 shows a transition from deep sleep to light sleep. Here again, a period of 20 minutes is considered. The same traits as in figure 10 are present here. The exact transition from deep sleep to light sleep, as determined by visual analysis of EEGs and EOGs, is indicated by a vertical arrow. In the left part of the figure, it is observed that the heart rate variability is very small in deep sleep and that no body movement is present during this stage of sleep (see also tables |! and IV). The transition to light sleep is accompanied by two movements that induce large changes in heart rate. So, heart rate variability is greater than in deep sleep.
Figure 12 shows a short transition from light sleep to wakefulness and a return to light sleep. This time, due to the short duration of the night wake up, the recording duration is only 5 minutes. The two transitions are marked by vertical lines. Here, the awakening episode lasts for 1 minute and 40 seconds only (the distance between two vertical gray lines corresponds to 10 seconds). The transition from light sleep to wakefulness is accompanied by a large and long body movement (about 30 seconds) and the heart rate is greatly increased. Immediately after the movement, the heart rate maintains a higher value than in previous light sleep, indicating the individual's waking state (see also the table below).
gai 2 O 0 AS RS SS ER RR RS 67/70 - la IV). The return to a much lower heart rate value, comparable to that observed before the wakeful episode, is followed by the transition from wakefulness to light sleep. Figure 13 shows a short transition from REM sleep to wakefulness and a return to the REM stage of sleep afterwards. Here too, for a better understanding of the changing characteristics, the recording time is only 5 minutes and the waking episode duration is only 1 minute and 10 seconds. In the left part of the figure, REM sleep is characterized by a highly variable heart rate where changes are not due to body movements, but to very irregular heartbeats. (see also table |I). The waking episode is accompanied by a sharp increase in heart rate accompanied by a large body movement that lasts about 30 seconds. After a return to a heart rate value comparable to that observed before awakening, the individual returns to REM sleep and their characteristic variable heart rate unrelated to body movements.
These few examples demonstrate that sleep stages, sleep stage transitions and/or sleep events can be determined by analyzing heart rate and body movements and their temporal relationships. As described above, this analysis can be performed by setting parameters such as average heart rate, heart rate variability, body movement, etc. and by classifying each of these parameters in at least one class. Together with the criteria that define the established sleep stages indicated above, these data make it possible to precisely determine sleep, sleep stages, and/or sleep stage transitions. This complementary approach is the only way to obtain an objective hypnogram equivalent to that derived from the visual analysis of polysomnography.
The present invention allows recording, calculating and classifying physiological and/or environmental data to produce a comprehensive report of sleep structure and sleep quality after exploring the recorded and classified data. The report will include statistical data such as | AND
. wake up time, rest time, time in bed, sleep time, sleep quality, time to fall asleep, time and percentage of time spent in different sleep stages, number of sleep stage changes, number of movements, number of awakenings, etc. The sleep structure of a given night should be compared with previous records of the | same individual, if desired. This could be done to assess a change in sleep structure and quality due to a change in the environment or to assess the effects of a pharmacological treatment or for a- | tracking sleep changes due to a desynchrosis, etc. | 10 Another advantage of the present invention is that the registration of the . environmental physical res will help in the assessment of related sleep disorder | to the possible variations of these factors during the sleep period. Ambient noise can disrupt sleep and reduced sleep duration is due to possible delay time to fall asleep, nighttime awakenings and early late awakenings. In some cases, the noise does not wake up the person who is sleeping, but it produces excitations, changes in the sleep stage, and cardiovascular changes. Room temperature can also have a significant effect on the structure and quality of sleep. Thus, a high or low ambient temperature will be accompanied by numerous awakenings, reduced amount of deep sleep and REM stages with an increase in body motility. This disturbance may explain the daily fatigue felt by the person who sleeps poorly, although not consciously related to the nocturnal environment. All these effects are detected by the system and method of the present invention. The final report on sleep structure and sleep quality may include specific information about environmental factors that may be disrupting the individual.
Furthermore, the existence of abnormal events that occur during sleep or sleep pathologies is generally ignored by the population | general. The system of the present invention can detect some of these events and pathologies using information derived from biological variables and/or information derived from environmental factors recorded by the device.
. For example, snoring and its associated obstructive sleep apnea syndrome will be detected by variations in heart rate and body movement occurring at the end of the apnea, but also from the noise recording that detects snoring and the final breath.
Specific oximetry (blood oxygen saturation level) and blood pressure measurements could easily be associated with specific records of the present invention to assess the severity of symptoms.
Sleep events such as abnormal movement eg restless legs syndrome can be detected by the accelerometer.
Sleepwalking can be detected by the above modifications and by the simultaneous changes in parameters. environmental.
Abnormal sleep periods such as insomnia or hypersomnia can be measured and quantified.
Narcolepsy can be detected by the shorts | - sudden sleep episodes that occur during wakefulness and also by the onset of REM sleep or advanced first stage of REM sleep.
Other sleep events such as night terror attacks and nightmares can also be detected by a combination of biological and physical measures.
Finally, the system can also be very valuable in the field of neuropsychiatric disorders.
In fact, several observations suggest important links between sleep and mental disorders.
For neuropsychiatric disorders, the link is most evident, as for major mood disorders such as depression, schizophrenia, degenerative aging disorders, and Parkinson's disease.
For most of these diseases mentioned above, sleep is a satisfactory biomarker that contributes to a better diagnosis as well as a more accurate assessment and quantification of the therapeutic effect of pharmacological or physiological treatments.
Interestingly enough, it is becoming increasingly evident that some cognitive disorders seen in these pathologies are significantly improved if sleep is improved or normalized.
From a chronobiological point of view, continuous recording performed by the present invention over several days or weeks will also allow the normality of the person's basic circadian and ultradian rhythms to be assessed.
In many pathologies, these rhythms are profoundly disturbed.
dos and its return to normal can be highly indicative of the clinical course of the disease or the effectiveness of a particular treatment.

权利要求:
Claims (15)
[1]
1. A system for determining a person's sleep, a sleep stage and/or a sleep stage transition, the system comprising: heart rate detection means (110) configured to detect a person's heart rate; motion detecting means (120) configured to detect movement of a person's body part, wherein the movement is caused by a skeletal muscle of the body; recording means (170) configured to record frequency. detected heart rate and detected body part movement; heart rate classification means (310) configured to classify the person's recorded heart rate into at least one heart rate class and at least one heart rate class variability; motion classification means (320) configured to classify the recorded motion into at least one motion class; and determining means (400) configured to determine the person's sleep, a sleep stage, a sleep stage transition, and/or a sleep event based at least partially on at least one heart rate class, at least a heart rate class variability, and at least one movement class, wherein the determining means is configured to identify a combination of a heart rate class, a heart rate class variability, and a movement class within a period of time, and to determine sleep, a sleep stage and/or a sleep stage transition based on the identified combination.
[2]
A system as claimed in claim 1, comprising: heart rate calculating means (210) configured to | calculate the average heart rate, a variability value, a rhythm characteristic, and/or an event or change in heart rate from the
| 2/5 -. recorded heart rate, where the heart rate classification means is , configured to classify the person's heart rate based on the calculated average heart rate, variability value, characteristic S derhythm, and/or event or heart rate change
[3]
A system as claimed in claim 1 or 2, wherein the | determination means are further configured to identify a specific combination of a heart rate class, a va- | heart rate class variability, and a movement class within a specific time period, e.g. wherein the determining means is configured to determine | disrupt sleep, sleep stage, a sleep stage transition, and/or a “sleep event based on the specific combination identified.
[4]
A system as claimed in claim 1 or 3, wherein the | motion detecting means comprises motion capturing means (120) configured to capture an acceleration of the person's body part, wherein the recording means is further configured to record the captured acceleration, and wherein the system comprises: movement calculating means (220) configured to calculate, based on recorded acceleration values, at least an intensity and/or duration of each movement of the person's body part.
[5]
A system according to claim 4, wherein the movement classification means are configured to classify each movement of the body part into at least one major movement (LM), a small movement (SM) or a contraction. (TM), based on the calculated intensity and/or duration of each movement, and/or configured to classify each LM, SM and/or TM at least into frequency classes and/or duration classes.
[6]
6. System according to one of claims 1 to 5, which additionally comprises: environmental capture means (130, 140, 150) configured to capture at least one environmental factor, in which the recording means are added in tionally configured to record at least one environmental factor! captured; and ' environmental classification means (330) configured to classify at least some values of at least one recorded environmental factor into at least one environmental class, wherein the determining means are further configured to determine sleep, sleep stage, the person's sleep stage transition and/or a sleep event based at least partially on at least one environmental class.
[7]
A system according to claim 6, wherein the environmental capturing means are configured to capture a noise level, an ambient temperature and/or an ambient light, the system additionally comprising: - ambient calculation means (230 ) configured to calculate at least one noise level and/or average noise event based on the recorded noise level, and/or calculate at least one level and/or average ambient temperature change and/or variation based on the recorded ambient temperature, and/or calculate at least one ambient light level and/or ambient light level change based on the recorded ambient light.
[8]
The system of claim 1, wherein at least one heart rate class comprises an average heart rate class.
[9]
9. System according to one of the claims | to 8, wherein the means of determination are further configured to determine a transition from wakefulness to sleep and/or a transition from one sleep stage to another and/or a transition from sleep to wakefulness and/or a direct causal effect of at least one environmental factor recorded in a sleep stage transition or a sleep-to-wake transition.
[10]
A system as claimed in one of claims 1 to 9, further comprising: evaluation means (410) configured to evaluate a person's sleep or wakefulness state based on at least one heart rate class, at least a frequency class variability | Lo
[11]
] 4/5 - cardiac, and at least one movement class, at least one environmental class, and/or any combination thereof. " 11. A system for determining a person's sleep, a sleep stage and/or a sleep stage transition, comprising: a wearable device configured to detect and record a person's heart rate and configured to detect and record movement of a part of the person's body where the movement is caused by a skeletal muscle of the body; an analysis device configured to classify the person's recorded heart rate into at least one heart rate class and at least one heart rate class variability, configured to classify recorded movement into at least one class of movement, and configured to determine sleep, a sleep stage, a sleep stage transition, and/or a sleep event of the person with based at least partially on at least one heart rate class, at least one heart rate class-Ca variability, and at least one movement class; and data connection configured to communicate data representing recorded heart rate and recorded movement from the wearable recording device to the analysis device.
[12]
12. A method of determining a person's sleep, a sleep stage and/or a sleep stage transition, the method comprising: detecting (510) the person's heart rate; record the detected heart rate; detect (520) a movement of a person's body part, where the movement is caused by a skeletal muscle of the body; record detected movement; classify (530) the person's recorded heart rate into at least one heart rate class and at least one heart rate class variability; classify (540) the recorded movement into at least one movement class; and fr-iSBMÃm“NÉ"0A""%2 o 5 a a " p>2170 /1 Í 9%. S>IEAZ . AP ld), 2. = == a 0 2 . -loj """"6:S 2 sP AA 1 5 º/“"Z Ã2A)A[a A»aaA0AA7M)íAAT 1 ,T yJ"%so P lr A. =º“|TS —º 2 Ps 0 0 p. 0 ““ 5/5 .. determine (550) the person's sleep, a sleep stage, a sleep stage transition, and/or a sleep event based at least Í partially on at least one heart rate class, at least one heart rate class variability, and at least one movement class.
[13]
A method according to claim 12, the method comprising: identifying (555) a: specific combination of a heart rate class, a heart rate class variability and a movement class within a period of time specific, e.g. wherein the determination comprises determining sleep, a sleep stage, and a sleep stage transition based on the specific identified combination.
[14]
A method according to claim 12 or 13, the method comprising: capturing at least one environmental factor; register at least one environmental factor captured; classify at least some values of at least one environmental factor recorded in at least one environmental class; and determining a person's sleep or wakefulness state based at least partially on at least one environmental class.
[15]
15. Method according to claim 14, the method comprising: determining a direct causal effect of at least one recorded environmental factor on a sleep stage transition or a sleep-to-wake transition based at least partially in at least one environmental class.
i 1n2 Hypnogram of a young adult Wake 7 Ú REM sleep 1 .- " 7 Sleep stage 1 E + | Sleep stage 2 Á r j i Sleep stage 3 E: = * Sleep stage 4- 1
FT IT TT TT TA o 1 2 3 4 5 6 HA &Hours;
' ' oO] a | | E | to | : Â e $ q É Se = o E & ê n 8 E E SO) | ff es s s s s s s s y s 2) Ss À : ] Ss o |: s a s e E e E s 8 3 S 8 : o ê « e ÉS Ss =| ss sh 5 $ 2 S sl => õ | : o 8 Tr oo Ss o Ss 5 8 É z 3 zã s zaltelloco ENs ESSES RO 8 É 2 | is 3 & Idls 3 2/98 Su EN SW Ns e: 2 x & 2 EN. if“ EN Ss) SME ê 8 s |: s SN3E 2 sl sNs30sS| 30 2) 1s 8 3 2 8 E E TsNsSWSNSNSAI =: 2 3): a and sE | s| =| =|=2/ ss]: &| |nd: Be 38| [2s|2|s|s|s ss]: : 3 à s s E E 5º 5 = Is salt E Bal Ze ss) ss Is 3 E sl = z 1 ss > Ss; 35 - E pr 8 | $ E : : if D2E BLUQUWSW 35 ss
RE ê Ss É o =) 2 | | 8 o) ] - S Dx Fx os o E Ss 3 «= 8 o) 8 s E 3 > ã x) 8 = 3 : . . 3 2 5 is 8 SI] & FE s to Faith What if 38 SS 83 5 3 8 7 35 3: 3 EM 3 1|: | 32/38 to s=| 32) 332 These 5 5 e. EE) |: Fo 8 ss) >=%5 sENSS 5 ã 22 Is the 5 e SE 3s NSS or 2 FE |LZ2L24 | 3: 85 | 5

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---

公开号 | 公开日

---

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---

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---

WO2012156427A1|2012-11-22|

---

EP2524647A1|2012-11-21|

---

EP3701860A1|2020-09-02|

---

JP6333170B2|2018-05-30|

---

IL229317A|2017-08-31|

---

IL229317D0|2014-01-30|

---

KR102090968B1|2020-03-20|

---

RU2013156072A|2015-06-27|

---

US20140088378A1|2014-03-27|

---

CN103717125B|2016-04-13|

---

KR20140058441A|2014-05-14|

---

EP2712300A1|2014-04-02|

---

RU2634624C2|2017-11-02|

---

US9820680B2|2017-11-21|

---

CN103717125A|2014-04-09|

---

JP2014516681A|2014-07-17|

引用文献:

---

公开号 | 申请日 | 公开日 | 申请人 | 专利标题

---

---

US4836219A|1987-07-08|1989-06-06|President & Fellows Of Harvard College|Electronic sleep monitor headgear|

---

JP2780465B2|1990-08-30|1998-07-30|松下電器産業株式会社|Sleep state determination device|

---

IL100080A|1991-11-19|1994-12-29|Sleep Disorders Diagnostic And|Monitor system for determining the sleep stages of a person|

---

JP3149616B2|1993-04-07|2001-03-26|松下電器産業株式会社|Control device for air conditioner|

---

SE508285C2|1994-06-07|1998-09-21|Biosys Ab|Method and apparatus for assessing wakefulness and drowsiness at various stages between wakefulness and sleep in a way that is not monitored non-interfering|

---

US5902250A|1997-03-31|1999-05-11|President And Fellows Of Harvard College|Home-based system and method for monitoring sleep state and assessing cardiorespiratory risk|

---

JP3788126B2|1999-08-26|2006-06-21|松下電工株式会社|Sleep state determination device|

---

JP2002034955A|2000-07-26|2002-02-05|Matsushita Electric Works Ltd|System and method for judging sleeping condition and midway awakening, and recording medium recording program for judging sleeping condition and midway awakening|

---

JP2002219116A|2001-01-26|2002-08-06|Matsushita Electric Ind Co Ltd|Sleep cycle detector|

---

JP3877615B2|2002-03-11|2007-02-07|三洋電機株式会社|Sleep depth estimation device|

---

CA2492027C|2002-07-15|2012-10-02|Itamar Medical Ltd.|Body surface probe, apparatus and method for non-invasively detecting medical conditions|

---

US6878121B2|2002-11-01|2005-04-12|David T. Krausman|Sleep scoring apparatus and method|

---

US7787946B2|2003-08-18|2010-08-31|Cardiac Pacemakers, Inc.|Patient monitoring, diagnosis, and/or therapy systems and methods|

---

JP4023429B2|2003-10-07|2007-12-19|株式会社デンソー|Portable biological information monitor device|

---

US7524279B2|2003-12-31|2009-04-28|Raphael Auphan|Sleep and environment control method and system|

---

US20070249952A1|2004-02-27|2007-10-25|Benjamin Rubin|Systems and methods for sleep monitoring|

---

JP3987053B2|2004-03-30|2007-10-03|株式会社東芝|Sleep state determination device and sleep state determination method|

---

JP4528710B2|2005-11-09|2010-08-18|株式会社東芝|Sleep state measurement device, sleep state measurement method, and sleep state measurement system|

---

JP2007190126A|2006-01-18|2007-08-02|Daikin Ind Ltd|Sleep information management system|

---

JP2009297455A|2008-06-17|2009-12-24|Panasonic Electric Works Co Ltd|Sleeping state estimating device|

---

TW201019901A|2008-11-17|2010-06-01|Univ Nat Yang Ming|Sleep analysis system and analysis method thereof|

---

JP2010273752A|2009-05-27|2010-12-09|Kamata Toru|Sleep onset determination system|

---

JP5409148B2|2009-07-10|2014-02-05|三菱電機株式会社|Biological state acquisition device, biological state acquisition program, device provided with biological state acquisition device, and air conditioner|

---

EP2320293A1|2009-11-05|2011-05-11|Koninklijke Philips Electronics N.V.|Sleep element for improving the sleep of a person|

---

EP2648616A4|2010-12-07|2014-05-07|Earlysense Ltd|Monitoring, predicting and treating clinical episodes|US10631738B2|2012-07-31|2020-04-28|The Periodic Breathing Foundation, Llc|System for analyzing oximetry data|

---

CN104812432A|2012-11-29|2015-07-29|丰田自动车株式会社|Sleep control device and sleep control method|

---

RU2522400C1|2013-04-05|2014-07-10|Общество С Ограниченной Ответственностью "Хилби"|Method for determining human sleep phase favourable to awakening|

---

JP6187589B2|2013-08-07|2017-08-30|株式会社村田製作所|Trunk muscle contraction detector|

---

US10265013B2|2013-09-06|2019-04-23|Somnology, Inc.|System and method for sleep disorder diagnosis and treatment|

---

US10265014B2|2013-09-06|2019-04-23|Somnology, Inc.|System and method for sleep disorder diagnosis and treatment|

---

CN105530858A|2013-09-16|2016-04-27|皇家飞利浦有限公司|System and method for estimating cardiovascular fitness of a person|

---

WO2015042579A1|2013-09-23|2015-03-26|The Board Of Trustees Of The Leland Stanford Junior University|Monitoring and treating sleep disorders|

---

JP6247393B2|2013-11-28|2017-12-13|コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ．|Sleep monitoring device, sleep monitoring system, sleep monitoring method and corresponding computer program|

---

US20160249852A1|2013-12-03|2016-09-01|Sony Corporation|Information processing apparatus, information processing method, and program|

---

JP2017503566A|2013-12-19|2017-02-02|コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ．|Infant monitoring device|

---

CN104720746B|2013-12-20|2017-06-20|中国移动通信集团公司|A kind of sleep stage determines method and system|

---

CN104720748B|2013-12-24|2017-06-06|中国移动通信集团公司|A kind of sleep stage determines method and system|

---

EP2905006B8|2014-02-11|2017-06-07|Sorin CRM SAS|Device for discriminating the stages of sleep of a patient|

---

EP2904969B1|2014-02-11|2022-01-05|Sorin CRM SAS|Device for treating the sleep apnea syndrome in a patient by kinaesthetic stimulation|

---

TWI559901B|2014-04-14|2016-12-01|Quanta Comp Inc|Method and device of sleep detection|

---

CN103976717B|2014-04-15|2016-08-17|惠州市德赛工业研究院有限公司|A kind of various dimensions sleep quality monitoring method and system|

---

CN104055518A|2014-07-08|2014-09-24|广州柏颐信息科技有限公司|Fall detection wrist watch and fall detection method|

---

JP2016016144A|2014-07-09|2016-02-01|セイコーエプソン株式会社|Biological information processing system and method of controlling biological information processing system|

---

CN104127194B|2014-07-14|2016-05-04|华南理工大学|A kind of evaluating system of the depression based on heart rate variance analyzing method|

---

WO2016036114A1|2014-09-03|2016-03-10|Samsung Electronics Co., Ltd.|Electronic device and method for measuring vital signal|

---

AU2015318078B2|2014-09-15|2018-08-30|3M Innovative Properties Company|Impairment detection with biological considerations|

---

KR20170056635A|2014-09-15|2017-05-23|쓰리엠 이노베이티브 프로퍼티즈 캄파니|Impairment detection|

---

US9808185B2|2014-09-23|2017-11-07|Fitbit, Inc.|Movement measure generation in a wearable electronic device|

---

US10736517B2|2014-10-09|2020-08-11|Panasonic Intellectual Property Management Co., Ltd.|Non-contact blood-pressure measuring device and non-contact blood-pressure measuring method|

---

KR102354351B1|2014-12-04|2022-01-21|삼성전자주식회사|Electronic device for determining sleeping state and method for controlling thereof|

---

EP3031492B1|2014-12-08|2017-10-25|Sorin CRM SAS|System for treating a respiratory condition by kinesthetic stimulation, with stabilisation control of the stimulation|

---

EP3031491B1|2014-12-08|2019-01-30|Sorin CRM SAS|System for treating a respiratory condition by kinesthetic stimulation, with selection of stimulation strategies|

---

EP3031437B1|2014-12-08|2017-09-13|Sorin CRM SAS|Device for optimising treatment of sleep apnoea syndrome by kinesthetic stimulation|

---

WO2016092515A1|2014-12-11|2016-06-16|Koninklijke Philips N.V.|System and method for adjusting slow wave detection criteria|

---

US10856801B2|2014-12-18|2020-12-08|Koninklijke Philips N.V.|System and method for slow wave sleep detection|

---

TWI542322B|2014-12-22|2016-07-21|財團法人工業技術研究院|Method and system for detecting sleep event|

---

CN104434068A|2014-12-26|2015-03-25|上海翰临电子科技有限公司|Sleep analysis method and device based on environment monitoring|

---

JP6516846B2|2014-12-30|2019-05-22|日東電工株式会社|Device and method for sleep monitoring|

---

RU2712844C2|2015-02-26|2020-01-31|Конинклейке Филипс Н.В.|Processing device, system and method of processing accelerometer signals for use in monitoring vital signs of individual|

---

US20160262690A1|2015-03-12|2016-09-15|Mediatek Inc.|Method for managing sleep quality and apparatus utilizing the same|

---

US20160302680A1|2015-04-17|2016-10-20|Seiko Epson Corporation|Biological information processing system, biological information processing device, terminal device, method for generating analysis result information, and biological information processing method|

---

US10638965B2|2015-06-15|2020-05-05|Medibio Limited|Method and system for monitoring stress conditions|

---

AU2016278356A1|2015-06-15|2018-01-04|Medibio Limited|Method and system for assessing mental state|

---

FI126600B|2015-08-10|2017-03-15|Murata Manufacturing Co|Detection of sleep phenomenon using ballistocardiography|

---

US10582890B2|2015-08-28|2020-03-10|Awarables Inc.|Visualizing, scoring, recording, and analyzing sleep data and hypnograms|

---

JP6582788B2|2015-09-17|2019-10-02|富士通株式会社|Sleepiness detection device, sleepiness detection method, and sleepiness detection program|

---

JP6716888B2|2015-10-29|2020-07-01|Tdk株式会社|Respiratory analysis device, respiratory analysis method and program|

---

CN105476630A|2015-11-26|2016-04-13|北京期颐科技有限公司|Method for detecting traditional Chinese medicine visceral functions|

---

JP6397810B2|2015-12-10|2018-09-26|日本電信電話株式会社|Sleep / wakefulness determination device, sleep / wakefulness determination method, and program for driving the same|

---

CN105559751B|2015-12-14|2018-06-12|安徽华米信息科技有限公司|Monitor the method, apparatus and wearable device of micro- active state|

---

CN106913313B|2015-12-28|2020-07-10|中国移动通信集团公司|Sleep monitoring method and system|

---

CN108697379A|2016-01-07|2018-10-23|全球动力股份有限公司|For assessing dormant system and method|

---

KR20170089231A|2016-01-26|2017-08-03|삼성전자주식회사|Electronic device and controlling method thereof|

---

JP6624280B2|2016-03-28|2019-12-25|富士通株式会社|Information processing apparatus, information processing method and program|

---

WO2017179699A1|2016-04-15|2017-10-19|オムロン株式会社|Biological information analysis device and system, and program|

---

US10420501B2|2016-05-09|2019-09-24|Koninklijke Philips N.V.|Sleep monitoring|

---

CN106108843A|2016-06-17|2016-11-16|美的集团股份有限公司|A kind of user of determination sleeps the method and system of duration|

---

US10952666B2|2016-06-24|2021-03-23|Fresenius Medical Care Holdings, Inc.|System and method for managing nocturnal treatment|

---

CN109328034B|2016-06-27|2020-04-14|皇家飞利浦有限公司|Determining system and method for determining sleep stage of subject|

---

CN105902257B|2016-06-27|2019-06-04|安徽华米信息科技有限公司|Sleep state analysis method and device, intelligent wearable device|

---

CN106214121B|2016-07-13|2020-01-17|广东乐心医疗电子股份有限公司|Sleep reminding method and device and wearable device|

---

CN107647847A|2016-07-26|2018-02-02|纽沃凯生物科技（深圳）有限公司|Depth of sleep monitoring method and Depth of sleep monitor|

---

DE102016213916A1|2016-07-28|2018-02-01|Volkswagen Aktiengesellschaft|Infotainment system for a motor vehicle|

---

CN106388771B|2016-08-16|2019-06-28|惠州市德赛工业研究院有限公司|A kind of method and motion bracelet of automatic detection human body physiological state|

---

FI20165631A|2016-08-25|2018-02-26|Night Train Oy|Procedures and systems for determining a time window for a person's sleep|

---

US11207021B2|2016-09-06|2021-12-28|Fitbit, Inc|Methods and systems for labeling sleep states|

---

CN106333652B|2016-10-18|2019-10-29|首都医科大学|A kind of sleep state analysis method|

---

WO2018098719A1|2016-11-30|2018-06-07|华为技术有限公司|Sleep monitoring method, apparatus and terminal|

---

CN106725383A|2016-12-28|2017-05-31|天津众阳科技有限公司|Sleep state judgement system and method based on action and heart rate|

---

CN106725382A|2016-12-28|2017-05-31|天津众阳科技有限公司|Sleep state judgement system and method based on action and HRV measurements|

---

KR101908838B1|2017-02-09|2018-10-16|한국기술교육대학교 산학협력단|Apparatus for preventing sleep apnea|

---

CN106821336A|2017-04-05|2017-06-13|深圳市老乐健康科技有限公司|Sleep monitor method and system|

---

JP6298919B1|2017-06-07|2018-03-20|スマート ビート プロフィッツ リミテッド|Database construction method and database|

---

US11266346B2|2017-06-07|2022-03-08|Electronics And Telecommunications Research Institute|Method and apparatus for determining sleep state using biometric information and motion information|

---

CN107374223A|2017-08-28|2017-11-24|赛博龙科技有限公司|A kind of closed-loop system, device and intelligent pillow for detecting, analyzing sleep|

---

KR20200075859A|2017-10-29|2020-06-26|씨아오핑 리|Methods and devices for managing brain sleep mode|

---

CN107647849A|2017-11-02|2018-02-02|成都吱吖科技有限公司|A kind of Intelligent home device for improving sleep quality and sleep quality detection|

---

KR102004052B1|2017-11-09|2019-07-25|재단법인대구경북과학기술원|Apparatus and method for predicting physical stability|

---

CN107773831A|2017-11-27|2018-03-09|吴伟峰|A kind of nightmare wakes up system|

---

KR102007580B1|2017-12-14|2019-08-05|경북대학교 산학협력단|Method and apparatus for determining sleep stages using fractal property of heart rate variability|

---

CN108209874B|2018-01-03|2021-01-26|深圳北航新兴产业技术研究院|Automatic sleep staging method and device|

---

FI20185051A1|2018-01-19|2019-07-20|Night Train Oy|Method, apparatus, and system for detecting stages of sleep of person|

---

CN108836265A|2018-04-23|2018-11-20|广东美的制冷设备有限公司|Sleep state detection method, household electrical appliances and computer readable storage medium|

---

JP6670881B2|2018-04-26|2020-03-25|ミネベアミツミ株式会社|Biological condition monitoring system|

---

CN108937867A|2018-06-29|2018-12-07|出门问问信息科技有限公司|A kind of dormant monitoring method and device|

---

CN109199395A|2018-07-20|2019-01-15|渝新智能科技（上海）有限公司|A kind of sleep state recognition methods, device and equipment|

---

CN109125926A|2018-07-20|2019-01-04|渝新智能科技（上海）有限公司|A kind of sleep dynamic restoring method, device and equipment based on negative ion concentration|

---

WO2020043855A1|2018-08-29|2020-03-05|Sleep Advice Technologies S.R.L.|Photoplethysmography based detection of transitions between awake, drowsiness, and sleep phases of a subject|

---

KR102177740B1|2018-12-12|2020-11-11|재단법인대구경북과학기술원|Method for estimating congnitive ability, system thereof and wearable device therefor|

---

CN109674459A|2018-12-24|2019-04-26|深圳和而泰数据资源与云技术有限公司|A kind of method and device of data processing|

---

KR102140094B1|2019-01-16|2020-07-31|재단법인대구경북과학기술원|Device and method for determining state of sleep|

---

KR102239462B1|2019-03-19|2021-04-13|재단법인대구경북과학기술원|Method and system for creating learning data to determine physical stability and wearable device thereof|

---

CN111067503A|2019-12-31|2020-04-28|深圳安视睿信息技术股份有限公司|Sleep staging method based on heart rate variability|

---

CN111166286A|2020-01-03|2020-05-19|珠海格力电器股份有限公司|Dreamy travel detection method, storage medium and dreamy travel detection device|

---

DE102020210325A1|2020-08-13|2022-02-17|Volkswagen Aktiengesellschaft|Apparatus for alleviating symptoms of Willis-Ekbom disease in a motor vehicle, motor vehicle and computer program product|

---

CN113506626B|2021-09-03|2021-12-10|南通嘉蒂体育用品有限公司|Sleep characteristic data evaluation processing method and system based on wearable device|

---

RU2763641C1|2021-09-22|2021-12-30|Федеральное Государственное Бюджетное Образовательное Учреждение Высшего Образования "Тюменский Государственный Медицинский Университет" Министерства Здравоохранения Российской Федерации|Method for assessing the predicted shift in the corrected mean sleep phase according to the munich chrono-type questionnaire test when changing the time of daytime light exposure in individuals with a free work schedule|

---

RU2762612C1|2021-10-25|2021-12-21|Федеральное Государственное Бюджетное Образовательное Учреждение Высшего Образования "Тюменский Государственный Медицинский Университет" Министерства Здравоохранения Российской Федерации|Method for predicting the corrected mean sleep phase according to the munich test in persons aged 18 to 22 years inclusive with an increase in screen time|

法律状态:
2020-12-01| B06F| Objections, documents and/or translations needed after an examination request according [chapter 6.6 patent gazette]|

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2020-12-08| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|

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2021-04-06| B07A| Application suspended after technical examination (opinion) [chapter 7.1 patent gazette]|

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2021-07-20| B09B| Patent application refused [chapter 9.2 patent gazette]|

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2021-10-05| B09B| Patent application refused [chapter 9.2 patent gazette]|Free format text: MANTIDO O INDEFERIMENTO UMA VEZ QUE NAO FOI APRESENTADO RECURSO DENTRO DO PRAZO LEGAL |

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2021-12-07| B350| Update of information on the portal [chapter 15.35 patent gazette]|

优先权:

---

申请号 | 申请日 | 专利标题

---

EP11166629.3|2011-05-18|

---

EP11166629A|EP2524647A1|2011-05-18|2011-05-18|System and method for determining sleep stages of a person|

---

PCT/EP2012/059074|WO2012156427A1|2011-05-18|2012-05-15|System and method for determining sleep and sleep stages of a person|

---