KR101669436B1 - Head wearable type apparatus and method for managing state of user - Google Patents

Abstract

The present invention relates to a hair-wearing device for managing the state of a user, the analysis result of an EEG signal measured by using a pair of electrodes positioned between a wearer's mouth, A value representing the state of the user is calculated on the basis of a combination of analysis results of the CBF signal measured using at least one pair of optical electrodes located between the inside of the sphere and the scalp of the user, A signal for stimulation is generated and output to a pair of electrodes, thereby achieving a light weight shortening of the head wearable apparatus.

Description

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a head wearable device for managing a user's state,

The present invention relates to a head wearable device for managing a user's state and a method for managing the state of a user, and more particularly to a head wearable device for managing a user's state using a bio- will be.

2. Description of the Related Art In recent years, bio-signal technology for diagnosis of a body condition using a human bio-signal has been developed to improve the accuracy of the diagnosis and to replace the conventional invasive diagnostic technique due to various advantages such as non-invasiveness and promptness It is becoming a major medical technology of the future. Imaging apparatuses such as MRI (Magnetic Resonance Imaging), CT (Computed Tomography), and PET (Positron Emission Tomography) can diagnose the body disease or diagnose the body state very accurately by providing high quality medical images. However, such an image diagnostic apparatus is expensive and can not be carried because of its large size.

On the other hand, medical diagnostic apparatuses using brain signals such as brain conduction signals, brain conduction signals, cerebral blood flow signals, and fMRI (functional resonance imaging) signals are being developed as portable medical diagnostic apparatuses because they are relatively inexpensive and small in size. However, the medical diagnostic device based on the bio-signal of the brain has a disadvantage that the diagnostic accuracy is lower than that of MRI, CT, and PET. In order to improve the accuracy of the diagnosis, a diagnosis is made with a large number of sensors attached to the head, so that there is a limit to the user wearing such a medical diagnostic apparatus and everyday life.

The present invention provides a hair-wearing device which is excellent in portability and wearability, and is capable of daily life in a wearable state, while accurately diagnosing a user's condition and preventing various accidents caused by an abnormal condition of a user. The present invention also provides a method of managing the state of a user that minimizes the number of electrodes required to measure an EEG signal and the number of optical electrodes required to measure a CBF signal so that such a head wearable device can be realized.

According to an aspect of the present invention, there is provided a head wearable device for managing a state of a user, comprising: An EEG measuring unit for measuring an EEG signal representing electroencephalography (EEG) generated on the scalp of the user by using at least one pair of electrodes positioned between the inner side of the wearer and the scalp of the user; A CBF measuring unit for measuring a CBF signal indicating cerebral blood flow (CBF) flowing under the scalp of a user using at least one pair of photoelectrodes positioned between the inner side of the wearer and the scalp of the user; A signal processing unit for calculating a value indicating a state of the user based on a combination of an analysis result of the EEG signal measured by the EEG measuring unit and an analysis result of the CBF signal measured by the CBF measuring unit; A signal generator for generating a signal for stimulating a user's scalp according to a state value calculated by the signal processor and outputting the signal to the at least one pair of electrodes; And a switching unit for connecting the at least one pair of electrodes to either the EEG measuring unit or the signal generating unit under the control of the signal processing unit.

Wherein the signal processor controls the signal generator so that the stimulus signal is generated if the state value calculated by the signal processor indicates that the user is in an abnormal state and the stimulus signal generated by the signal generator is generated by the at least one pair And the signal generator generates the stimulus signal under the control of the signal processing unit, and the switching unit controls the at least one pair of electrodes from the EEG measurement unit according to the control of the signal processing unit And can be connected to the signal generator.

Wherein the signal processing unit is based on a combination of an analysis result of the EEG signal measured for a predetermined time from the time when the switching unit is controlled so that the stimulation signal is output to the at least one pair of electrodes and an analysis result of the CBF signal measured during the predetermined time And outputs a warning message indicating that the user's state is abnormal if the calculated state value indicates that the user's state is abnormal, and the hair-wearing device monitors the user's state of the warning message output by the signal processing unit To a remote terminal managed by a supervisor of the mobile communication terminal.

Wherein the signal processing unit comprises: an EEG analyzing unit for calculating a feature value of each EEG section by analyzing the signal measured by the EEG measuring unit according to the EEG interval; A CBF analyzing unit for calculating characteristic values of each CBF section by analyzing the signals measured by the CBF measuring unit by CBF intervals; A state calculating unit for calculating the state value based on a combination of the feature value calculated by the EEG analyzing unit and the feature value calculated by the CBF analyzing unit; And a controller for controlling the switching unit such that the at least one pair of electrodes is connected to either the EEG measuring unit or the signal generating unit according to the magnitude of the state value calculated by the state calculating unit.

Wherein the controller controls the switching unit such that the at least one pair of electrodes is connected to either the EEG measuring unit or the signal generating unit according to a result of comparing the state value calculated by the state calculating unit and the state threshold value, The state threshold may be varied according to information entered by the user or medical professional.

Wherein the length of the CBF section is a multiple of at least two times the length of the EEG section, and the state calculating section calculates, if at least one of the characteristic values of the EEG sections of the respective EEG sections indicates that the user's state is abnormal, The state value may be calculated based on a combination of a feature value of one CBF section including a time zone of one EEG section and a feature value of a plurality of EEG sections forming the same time zone as the CBF section .

The state calculator may calculate the state value by multiplying an average of the feature values of the plurality of EEG sections and feature values of the CBF section by different weights. The weights multiplied by the feature values of any one of the CBF intervals and the feature values of the plurality of EEG intervals may be varied according to information input by a user or a medical professional.

According to an aspect of the present invention, there is provided a method of managing a user's condition using a bio-signal of the brain, comprising: dividing an EEG signal representing an EEG generated on a user's scalp into unit time lengths of an EEG section, Dividing the CBF signal representing the cerebral blood flow into a time length unit of the CBF interval and extracting the CBF signal; Calculating a characteristic value of each EEG section by analyzing the EEG signal extracted for each EEG section by EEG section and analyzing the CBF signal extracted for each CBF section by CBF section to calculate a characteristic value of each CBF section; Calculating a value indicating a state of the user based on the calculated feature value of each EEG section and the feature value of each CBF section; And controlling a signal generator for generating a signal for stimulating a user's scalp such that a signal for stimulating a user's scalp is generated according to the calculated state value.

The number of electrodes required for the measurement of the EEG signal and the number of electrodes necessary for measuring the CBF signal are calculated by calculating a value representing the state of the user based on the combination of the analysis result of the EEG signal representing the electroencephalogram and the analysis result of the CBF signal representing the cerebral blood flow, It is possible to realize the light and small size of the head wearable device which can manage the state of the user by using the electrodes for EEG signal measurement and stimulus signal output together. As a result, it is possible to provide a hair-wearing device which is excellent in portability and wearability and is capable of daily life in a worn state while accurately diagnosing a user's condition, thereby preventing various accidents caused by a user's abnormal condition, for example, a sleeping condition .

As described above, defects in the analysis result of the EEG signal are compensated by the analysis result of the CBF signal while the number of the electrodes required for the measurement of the EEG signal and the number of the optical electrodes required for the measurement of the CBF signal are minimized, Can accurately diagnose the user's state so that it can be supplemented by the analysis result of the EEG signal. In particular, since a value indicating the state of the user is calculated on the basis of the combination of the feature value of each EEG section forming the same time zone and the feature value of each CBF section, the defect of the analysis result of the EEG signal is analyzed Defects in the analysis result of the CBF signal can be compensated by the analysis result of the EEG signal, so that the error of the user's condition diagnosis can be reduced.

In addition, if a stimulus signal is applied to the user's scalp but the user can not escape from the abnormal state, a message indicating that the user's state is abnormal is sent to the remote terminal of the supervisor, As a result, it becomes possible for the user to take all necessary measures to return to the normal state.

The length of the CBF section is set to a multiple of at least two times the length of the EEG section, and based on the combination of the feature values of one CBF section and the feature values of the plurality of EEG sections forming the same time period as any one CBF section The defect of the analysis result of the EEG signal is compensated by the analysis result of the CBF signal and the defect of the analysis result of the CBF signal can be compensated by the analysis result of the EEG signal, Can be reduced.

In addition, the state value of the user can be calculated by multiplying each of the feature values of the plurality of EEG sections and the feature values of one CBF section by different weights, and the user's state value can be calculated. And may vary depending on the information. Accordingly, the state of the user can be more accurately diagnosed in consideration of the characteristics of the EEG signal, the characteristics of the CBF signal, and the characteristics of the user. Further, the state threshold value, which is compared with the state value of the user to diagnose the state of the user, is variable according to the information input by the user or the medical professional, so that the state of the user can be diagnosed more accurately in consideration of the personal characteristics of the user .

FIG. 1 is a view showing the appearance of a head wearable device according to an embodiment of the present invention.
FIG. 2 is a view showing a state in which the head wearable apparatus shown in FIG. 1 is worn.
Fig. 3 is a configuration diagram of the electronic device 4 shown in Fig.
4 is a configuration diagram of the EEG measuring unit 41 shown in FIG.
5 is a block diagram of the CBF measuring unit 42 shown in FIG.
Fig. 6 is a configuration diagram of the signal processing unit 43 shown in Fig.
7 is another configuration diagram of the electronic device 4 shown in Fig.
8 is a flowchart of a method for managing user status according to another embodiment of the present invention.

Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. Representative examples of biological signals of the brain include electroencephalography (EEG) signals, magnetoencephalography (MEG) signals, cerebral blood flow (CBF) signals, and fMRI (functional magnetic) signals. The embodiments described below relate to a head wearable device that manages the state of a user by using an electroencephalogram signal and a cerebral blood flow signal among these signals. Hereinafter, a head wearable device for managing a user's status can be simply referred to as a "head wearable device ", and a method for managing a user's status using a bio-signal of a user's brain is briefly referred to as & Method, " the electroencephalogram signal can be referred to briefly as an "EEG signal ", and the cerebral blood flow signal can be briefly referred to as a" CBF signal ".

FIG. 1 is a view showing an outer appearance of a head wearable device according to an embodiment of the present invention, and FIG. 2 is a view showing a state where a head wearable device shown in FIG. 1 is worn. Referring to FIGS. 1-2, the head wearable device according to the present embodiment includes a wearer 1, a pair of electrodes 2, a pair of optoelectrodes 3, 4, and a battery 5. Each of the pair of electrodes 2 and the pair of photoelectrodes 3 can be electrically connected to the electronic device 4 through a wire embedded in the wearer's mouth. Likewise, the battery 5 can also be electrically connected to the electronic device 4 via a wire embedded in the wearer's mouth 1. For the sake of simplification of the drawing, electric wires built in the wearer's mouth 1 are omitted. These electronic elements may be connected by wires exposed to the outside of the wearer's mouth 1, but it is preferable that the electronic elements are connected by electric wires built in the wearer's mouth 1 considering the appearance and disconnection of the head wearable device.

Although a pair of electrodes 2 and a pair of photoelectrodes 3 are shown in Figs. 1-2, the state of the user can be more accurately managed by using a larger number of electrodes and optical electrodes. Hereinafter, an embodiment will be described in which a state of a user is managed by using only a pair of electrodes 2 and a pair of photoelectrodes 3 in order to realize light weight shortening of a head wearable apparatus. However, it is understood that a larger number of electrodes and photo electrodes can be used by those skilled in the art.

The wearer 1 is worn on the user's head and has a shape easy to wear on the user's head. As shown in Figs. 1-2, the wearer 1 has a rectangular plate-shaped frame 11 adhered to the forehead of a user and a pair of legs 11 attached to both ends of the frame, And a rubber band 12 fixed to the forehead. The wearing tool 1 may be modified into various shapes such as a hat or a helmet shape in addition to the band shapes shown in FIGS. The frame 11 of the wearer 1 may be made of a flexible material such as a rubber material so as to be bent according to the shape of the user's forehead. A pair of electrodes 2 and a pair of photoelectrodes 3 are provided inside the frame of the wearer's mouth 1.

As shown in Fig. 1, two pairs of elastic protrusions are formed on the inner side of the frame of the wearer's mouth. A pair of electrodes 2 are provided in the center hole of one pair of the projections of the pair of projections and a pair of photoelectrodes 3 are provided in the other pair of center holes, And the pair of photoelectrodes 3 can be attached to the forehead of the user more tightly. These protrusions may be made of a rubber material integrally with the frame 11 of the wearer's mouth. As described above, since the inside of the wearer's mouth 1, on which the pair of electrodes 2 and the pair of photoelectrodes 3 are provided, is closely attached to the forehead of the user, the EEG signal generated from the frontal lobe of the user's brain and the CBF The signal can be measured.

The pair of electrodes 2 are attached to the inside of the wearer's mouth 1 and are positioned between the inside of the wearer's mouth 1 and the scalp of the user as the wearer's mouth 1 is covered with the user's head. As shown in Figs. 1-2, in the present embodiment, the pair of electrodes 2 are located between the inside of the wearer 1 and the scalp of the user's forehead region, and are formed on the scalp of the user's forehead region And detects an electrical signal. The pair of electrodes 2 may be composed of a reference electrode 21 corresponding to the ground and a detection electrode 22 spaced apart from the reference electrode 21 to detect a potential difference between the scalp and the scalp. Depending on the state of the user's mind and body, different electrical activities occur in the cerebral cortex, and a potential difference that is different from the other is detected between the pair of electrodes 2 contacting the user's scalp.

The pair of photoelectrodes 3 are attached to the inner side of the wearer's mouth 1 and are positioned between the inner side of the wearer's mouth 1 and the scalp of the user as the wearer's mouth 1 is covered with the user's head. 1-2, the pair of photoelectrodes 3 are positioned between the inside of the wearer 1 and the scalp of the user's forehead region, And detects electrical signals generated by fluctuations in cerebral blood flow. The pair of photoelectrodes 3 may be composed of a light emitting element 31 corresponding to a light source and a light receiving element 32 outputted from the light emitting element 31 and detecting light passing through a tissue under the scalp of the user . According to the state of mind and body of the user, different forms of cerebral blood flow are generated below the scalp. As a result, electric signals (electric signals) which are changed differently from each other in the light receiving element 32 among the pair of light electrodes 3, Is detected.

Biological tissues contain chromophore that transmit light with a wavelength in the near infrared region relatively well and vary in degree of light absorption depending on the oxidation state. The biological signal technology that diagnoses the body disease or diagnoses the condition of the body using the characteristics of the living tissue is called near-infrared spectroscopy (NIRS). Representative chromophores present in brain tissue include oxidized hemoglobin, reduced hemoglobin, and the like. When the user is in a state of awakening, that is, when the metabolic activity of the body is strong, the amount of oxidized hemoglobin in the cerebral blood flow increases. On the other hand, when the user is in a sleep state, that is, when metabolic activity of the human body is low, the amount of oxidized hemoglobin in the cerebral blood flow decreases.

As described above, the amount of oxidized hemoglobin in the cerebral blood flow under the scalp changes according to the state of the user, thereby changing the extent of light absorption by the cerebral blood flow. In the present embodiment, the near-infrared spectroscopy is employed to emit light having a wavelength in the near-infrared region on the scalp, and the light-receiving element 32 detects light having different intensities according to the state of the user. The light emitting device 31 may be implemented as a near-infrared LED (light emitting diode), and the light receiving device 32 may be implemented as a photodiode. Meanwhile, the state of the user may be diagnosed by considering the change of the hemoglobin in addition to the change of the oxidative hemoglobin in the cerebral blood flow. In addition to the light intensity information detected by the light receiving element 32, May be diagnosed.

The human brain can be divided into the frontal lobe responsible for thinking and memory, the temporal lobe responsible for hearing and movement, the parietal lobe responsible for spatial perception and perception, and the occipital lobe responsible for visual perception. In this embodiment, the EEG signal is detected from electrical activity of the cerebral cortex near the frontal lobe to detect whether the user is awake or in a state of sleep, and the CBF signal is detected from the cerebral blood flow change under the scalp near the frontal lobe. A pair of electrodes 2 and a pair of photoelectrodes 3 may be provided at the positions shown in FIGS. 1-2, but are merely examples. In order to measure the EEG signal and the CBF signal more faithfully, .

 The electronic device 4 measures and analyzes an EEG signal indicating an electroencephalogram (EEG) generated on the user's scalp from an electrical signal detected by the pair of electrodes 2 provided on the wearer's mouth 1, (CBF) signal indicative of cerebral blood flow flowing under the scalp of the user is measured and analyzed from the electrical signal detected by the controller (3). Then, the electronic device 4 calculates a value representing the state of the user based on the combination of the analysis result of the EEG signal and the analysis result of the CBF signal, and outputs a signal for stimulating the scalp of the user according to the state value thus calculated And outputs it to the pair of electrodes 2.

If the state of the user is diagnosed based on the analysis result of the EEG signal measured using only the pair of electrodes 2, the error of the user's state diagnosis may be increased. Similarly, if the state of the user is diagnosed based on the analysis result of the CBF signal measured using only the pair of photoelectrodes 3, the error of the user's state diagnosis can be increased. Accordingly, in the present embodiment, the defect of the analysis result of the EEG signal is compensated by the analysis result of the CBF signal, and the analysis result of the CBF signal is analyzed by the analysis result of the EEG signal and the CBF By using the result of the analysis of the signal complementarily, the error of the user's condition diagnosis can be reduced.

That is, in this embodiment, by diagnosing the state of the user based on the combination of the analysis result of the EEG signal and the analysis result of the CBF signal, only the pair of electrodes 2 and the pair of photoelectrodes 3 are used to obtain a more accurate state Diagnosis was made possible. As a result, it is possible to provide a hair-wearing device capable of accurately and diagnosing a user's condition while being excellent in portability and wearability since the hair-wearing device according to the present embodiment can be thinned and shortened.

A battery (5) is installed in a wearer (1) to supply power to the electronic device (4). As described above, since the head-wearable device according to the present embodiment drives the electronic device 4 by using the power of the battery 5 attached to the wearer's mouth 1, it operates independently of the other devices . Accordingly, the user can freely perform the operation even if wearing the head wearable device according to the present embodiment. As shown in FIGS. 1-2, the electronic device 4 and the battery 5 are worn to improve the appearance of the hair-wearing device according to the present embodiment and to minimize the inconvenience of the wearer of the present embodiment. And can be installed in a form embedded in the sphere 1. It is understood that the electronic device 4 and the battery 5 may be attached to the outer surface of the wearer 1 by those skilled in the art.

Fig. 3 is a configuration diagram of the electronic device 4 shown in Fig. 3, the electronic device 4 includes an EEG measuring unit 41, a CBF measuring unit 42, a signal processing unit 43, a signal generating unit 44, a switching unit 45, and a user interface 46 ). Those skilled in the art will appreciate that the electronic device 4 may further include other components in addition to the components described above. For example, the electronic device 4 may further include a component for outputting a sound that gives auditory stimulation to the user when the user's state is abnormal.

The EEG measuring unit 41 measures an EEG signal representing the electroencephalogram on the user's scalp using a pair of electrodes 2 positioned between the inside of the wearer 1 and the scalp of the user. The EEG measuring section 41 detects an electrical signal output from the pair of electrodes 2, that is, an electric signal indicating a potential difference between the pair of electrodes 2, under the control of the signal processing section 43, And measures the EEG signal from the thus received signal.

The CBF measuring unit 42 measures a CBF signal indicative of cerebral blood flow under the scalp of the user by using a pair of photoelectrodes 3 positioned between the inside of the wearer 1 and the scalp of the user. The CBF measuring unit 42 receives the electrical signal output from the light receiving element among the pair of the optical electrodes 3 under the control of the signal processing unit 43 and measures the CBF signal from the received signal.

The signal processing unit 43 analyzes the EEG signal measured by the EEG measuring unit 41, analyzes the CBF signal measured by the CBF measuring unit 42, and analyzes the analysis result of the EEG signal and the CBF signal A value indicating the state of the user is calculated. Since the user's state of mind and body changes with time, EEG and CBF signals measured at different time zones can represent different states of the user. Therefore, in order to diagnose the user's condition based on the combination of the analysis result of the EEG signal and the analysis result of the CBF signal, it is necessary to detect the state of the user from the light receiving element of the pair of electrodes 2 and the pair of light electrodes 3 The EEG signal and the CBF signal are measured for the electrical signal, and the user's condition must be diagnosed based on the combination of the analysis result of the measured EEG signal and the analysis result of the CBF signal.

Accordingly, the signal processing unit 43 outputs the EEG signal and the CBF signal simultaneously to the electrical signal output from the pair of electrodes 2 and the electrical signal output from the light receiving element among the pair of the optical electrodes 3 at the same time And controls the EEG measuring unit 41 and the CBF measuring unit 42 so as to be measured. The EEG measuring unit 41 and the CBF measuring unit 42 are controlled by the signal processing unit 43 such that the electrical signals output from the pair of electrodes 2 and the pair of optical electrodes 3 Receiving the electrical signal output from the light receiving element at the same time and terminating. As a result, the electrical signals output from the pair of electrodes 2 and the electrical signals output from the light receiving elements of the pair of optical electrodes 3 are input to the signal processing unit 43 at the same time.

The signal generator 44 generates a signal for stimulating the user's scalp according to the state value calculated by the signal processor 43 and outputs the signal to the pair of electrodes 2. That is, the signal generator 44 does not generate a signal for stimulating the user's scalp if the state value calculated by the signal processor 43 indicates that the user's state is normal. On the other hand, if the state value calculated by the signal processing unit 43 indicates that the user is in an abnormal state, the signal generating unit 44 generates a signal for stimulating the user's scalp and outputs the signal to the pair of electrodes 2 . When the stimulation signal is output to the pair of electrodes 2, an electric signal is applied to the scalp area where the pair of electrodes 2 are in contact with each other. As a result, the user's state can be changed from an abnormal state to a normal state have.

The signal generator 44 generates a stimulus signal under the control of the signal processor 43. The signal processor 43 controls the signal generator 44 to generate a stimulus signal if the state value calculated by the signal processor 43 indicates that the user is in an abnormal state, And controls the switching unit 45 so that the stimulation signal is output to the pair of electrodes 2. [ In the present embodiment, it is preferable that only a pair of electrodes 2 are attached to the wearer's mouth 1 as much as possible in order to make the hair-wearing apparatus as shown in FIG. Accordingly, the pair of electrodes 2 attached to the wearer 1 are also used for measuring the EEG signal and also for outputting the stimulus signal.

For example, when the normal state of the user is awake and the abnormal state of the user is a sleep state, the user's state can be switched from the sleep state to the awakening state by the stimulation signal output to the pair of electrodes 2. When the head wearable device according to the present embodiment is worn by a soldier, a driver of a car, an airplane pilot, etc., the user can prevent various accidents caused by falling into a sleeping state. The intensity of the stimulus signal output to the pair of electrodes 2 may vary according to the sensitivity of the user to the electrical stimulus, but it is preferred that the stimulus signal does not exceed 80 mA maximum.

The signal processing unit 43 may control the signal generating unit 44 so that the intensity of the signal for stimulating the user's scalp is changed according to the information input by the user or the medical professional through the user interface 46. [ The signal generator 44 may change the strength of the signal for stimulating the scalp of the user under the control of the signal processor 43 and may generate the stimulus signal having the changed intensity. For example, the signal generator 44 may change the intensity of the stimulation signal according to the user's age, sex, height, weight, and the like. Further, the signal generator 44 may change the intensity of the stimulation signal according to the value set by the user or the medical diagnosis.

The switching unit 45 connects the pair of electrodes 2 to either the EEG measuring unit 41 or the signal generating unit 44 under the control of the signal processing unit 43. The switching unit 45 is provided with a pair of electrodes 2 under the control of the signal processing unit 43 so that an electrical signal detected by the pair of electrodes 2 can be transmitted to the EEG measuring unit 41 EEG measuring unit 41 as shown in FIG. In other words, when the state value calculated by the signal processing unit 43 does not exist or the state value calculated by the signal processing unit 43 indicates that the user is in a normal state, the switching unit 45 switches The pair of electrodes 2 are separated from the signal generating unit 44 and connected to the EEG measuring unit 41 according to the control.

On the other hand, when the state value calculated by the signal processing unit 43 indicates that the user is in an abnormal state, the switching unit 45 outputs the pair of electrodes 2 to the EEG measuring unit 41 And connects it to the signal generator 44. [ For example, when the state value calculated by the signal processing unit 43 indicates that the user is in a state of awakening, the switching unit 45 separates the pair of electrodes 2 from the signal generating unit 44, (41) so that electrical signals detected by the pair of electrodes (2) can be transmitted to the EEG measuring unit (41). The switching unit 45 separates the pair of electrodes 2 from the EEG measuring unit 41 when the state value calculated by the signal processing unit 43 indicates that the user is in the sleep state, So that the user can be awakened by the stimulation signal output by the pair of electrodes 2. [ The switching unit 45 may be implemented by a switching transistor, a relay, or the like.

The user interface 46 receives information from a user or a medical professional and outputs the information to the signal processing unit 43. The user interface 46 may be implemented with a dip switch, a rotary switch, or the like. Examples of information entered by a user include user body information such as age, gender, height, weight, etc. of the user, EEG threshold information set by the user or medical professional, state threshold information set by the user or medical professional, The weight information on the analysis result of the EEG signal set by the medical professional, the weight information on the analysis result of the CBF signal, and the strength information of the stimulus signal set by the user or the medical professional. The user interface 46 may output some information to the user. Examples of the information output to the user include user status information, user input information as described above, and the like. The user interface 46 may be implemented as a touch screen or the like.

4 is a configuration diagram of the EEG measuring unit 41 shown in FIG. Referring to FIG. 4, the EEG measuring unit 41 includes an EEG receiving unit 411, an EEG amplifying unit 412, an EEG filter 413, and an EEG analog-to-digital converter (ADC). It will be understood by those skilled in the art that the connection relation of the components of the EEG measuring unit 41 can be modified. For example, the EEG measuring unit 41 as described above amplifies and filters the electrical signals input from the pair of electrodes 2, and the EEG receiving unit 411, the EEG filter 413, the EEG amplifying unit 412 ), And an EEG ADC 414 in this order to filter and amplify an electrical signal input from the pair of electrodes 2.

The EEG receiving unit 411 receives the EEG signal from the pair of electrodes 2 via the switching unit 45 under the control of the signal processing unit 43 in order to synchronize the EEG signal measurement and the CBF signal measurement, Starts and ends reception of the electrical signal. The EEG amplifying unit 412 amplifies the electrical signal received by the EEG receiving unit 411. The EEG amplifying unit 412 may be implemented as a differential amplifier suitable for amplifying a fine signal input from the pair of electrodes 2. [ The EEG filter 413 removes a noise component of an electrical signal input from the pair of electrodes 2 by filtering the electrical signal amplified by the EEG amplifying unit 412. For example, the EEG filter 413 can pass the frequency band of 4-26 Hz of the electrical signal input from the pair of electrodes 2 and block the remaining frequency band corresponding to the noise component. The EEG filter 413 may be implemented as a band pass filter. The EEG ADC 414 converts the analog signal filtered by the EEG filter 413 into a digital signal. The digital signal output from the EEG ADC 414 is input to the signal processing unit 43 as an EEG signal.

5 is a block diagram of the CBF measuring unit 42 shown in FIG. Referring to FIG. 4, the CBF measuring unit 42 includes a CBF receiving unit 421, a CBF amplifying unit 422, a CBF filter 423, and a CBF ADC (Analog-Digital Converter) 424. Those skilled in the art will appreciate that the connection relationship of the components of the CBF measuring unit 42 can be modified. For example, the CBF measuring unit 42 as described above amplifies and filters an electrical signal input from the light receiving element 32, and includes a CBF receiving unit 421, a CBF filter 423, a CBF amplifying unit 422, And a CBF ADC 424 in this order to filter and amplify an electrical signal input from the light receiving element 32. [

The CBF receiving unit 421 starts reception of the electrical signal input from the light receiving element 32 via the switching unit 45 under the control of the signal processing unit 43 in order to synchronize the measurement of the EEG signal and the measurement of the CBF signal And ends. The CBF amplifying unit 422 amplifies the electrical signal received by the CBF receiving unit 421. If the output of the signal input from the light receiving element 32 is sufficient to measure the CBF signal, the CBF amplifying section 422 may be omitted. The CBF filter 423 removes the noise component of the electrical signal input from the light receiving element 32 by filtering the electrical signal amplified by the CBF amplifying unit 422. For example, the CBF filter 423 can pass a frequency band of 0.2 Hz or less of the electrical signal input from the light receiving element 32, and block the remaining frequency band corresponding to the noise component. The CBF filter 423 may be implemented with a low pass filter. The CBF ADC 424 converts the analog signal filtered by the CBF filter 423 into a digital signal. The digital signal output from the CBF ADC 424 is input to the signal processing unit 43 as a CBF signal.

Fig. 6 is a configuration diagram of the signal processing unit 43 shown in Fig. 6, the signal processing unit 43 includes an EEG extracting unit 431, an EEG analyzing unit 432, a CBF extracting unit 433, a CBF analyzing unit 434, a state calculating unit 435, 436). Those skilled in the art will appreciate that the signal processing unit 43 may further include other components in addition to the components described above. For example, if the EEG measuring unit 41 and the CBF measuring unit 42 do not have an ADC as described above and an analog signal is output from them, the signal processing unit 43 converts the analog signal into a digital signal And may further include components. The signal processor 43 may be implemented as a microprocessor and a memory.

The EEG extracting unit 431 divides the EEG signal measured by the EEG measuring unit 41 according to the control of the controller 436 and divides the EEG signal into time length units of the EEG window. Since the EEG signal measured by the EEG measuring unit 41 is continuously inputted to the signal processing unit 43, the EEG signal measured by the EEG measuring unit 41 must be divided into a certain length in order to analyze the EEG signal. The EEG interval refers to a time interval corresponding to a unit in which the EEG signal is divided into a predetermined length for the analysis of the EEG signal. In order to enable the user's diagnosis to be made from the electrical signal detected by the pair of electrodes 2 and the electrical signal detected by the light receiving element 32 at the same time, the extraction of the EEG section is performed in the CBF section Should be synchronized with the extraction of Accordingly, the EEG extractor 431 extracts the EEG signal under the control of the controller 436. [

The EEG analyzing unit 432 analyzes the EEG signal measured by the EEG measuring unit 41 for each EEG interval to calculate a characteristic value of each EEG interval. More specifically, the EEG analyzing unit 432 calculates the average power value of the alpha band, the average power of the theta band, and the average power of the beta band for the EEG signal extracted for each EEG interval by the EEG extractor 431 , The feature value of each EEG section is calculated by dividing the power average value of the beta band by the sum of the power mean value of the alpha band and the power mean value of the theta band according to the following equation (1).

EEG signals appear in various waveforms according to brain activity. They can be classified into gamma band signals, beta band signals, alpha band signals, theta band signals, and delta band signals depending on the frequency. The signal in the gamma band occurs when the waveform is in a state of extreme arousal or excitement as a waveform having a frequency of 30 Hz or more. The signal in the beta band is a waveform with a frequency in the 14 to 30 Hz band, which appears when in an anxious or tense state. The signal in the alpha band is a waveform with a frequency in the 8-13 Hz range and appears in a mentally stable state. The signal in the theta band appears as a waveform with a frequency in the 4 to 8 Hz range when sleepy. The signal in the delta band is a waveform with a frequency in the range of 0.1 to 4 Hz and appears in the sleep state.

In the present embodiment, since only a pair of electrodes 2 are used for light-weight shortening of the head wearable device, the state of the user is diagnosed based on only one of the signals of the various frequency bands The error of the user's condition diagnosis can be increased. Accordingly, in this embodiment, a combination of the power average value of the alpha band, the power average value of the theta band, and the power average value of the beta band is used as a value for diagnosing the user's state in order to reduce errors in the diagnosis of the user's condition. That is, even if there is a defect in the analysis of the signal of one of the bands, it can be secured by analysis of signals of the other bands.

For example, the EEG analyzing unit 432 performs a short-term Fourier transform on the EEG signal extracted for each EEG section by the EEG extracting unit 431, , The alpha band, and the theta band, respectively. Then, the EEG analyzing unit 432 calculates a power average value of the power spectrum of the beta band of each EEG section, a power average value of the power spectrum of the alpha band, and a power average value of the power spectrum of theta band. Then, the EEG analyzing unit 432 calculates the feature value of each EEG section by dividing the power average value of the beta band by the sum of the power average value of the alpha band of each EEG section and the power average value of the seta band according to Equation (1) .

The CBF extracting unit 433 divides the CBF signal measured by the CBF measuring unit 42 under the control of the controller 436 and divides the CBF signal into time length units of the CBF interval. Since the CBF signal measured by the CBF measuring unit 42 is continuously inputted to the signal processing unit 43, the CBF signal should be divided into a certain length in order to analyze the CBF signal measured by the CBF measuring unit 42. The CBF section refers to a time interval corresponding to a unit in which the CBF signal is divided into a certain length for the analysis of the CBF signal. As described above, since the extraction of the CBF section must be synchronized with the extraction of the EEG section, the CBF extraction section 433 extracts the CBF signal under the control of the control section 436. [

The CBF analyzing unit 434 analyzes the signals measured by the CBF measuring unit 42 for each CBF interval to calculate characteristic values of each CBF interval. In more detail, the CBF analyzing unit 434 calculates a characteristic value of each CBF interval by calculating an average value of the CBF signal intensity extracted for each CBF interval by the CBF extracting unit 433. FIG. For example, the CBF analyzing unit 434 integrates the CBF signal extracted for each CBF section by the CBF extracting unit 433 for each CBF section, and divides the integrated value by the length of the CBF section, The characteristic value of the CBF section can be calculated. This method is very simple because it merely integrates the waveform of the electrical signal detected by the light receiving element 32, so that it is possible to shorten the light weight and shortness of the hair-wearing device. However, Since the change of cerebral blood flow is not considered, the error of the user's condition diagnosis may increase.

Alternatively, the CBF analyzing unit 434 may apply the modified Beer-Lambert law to the CBF signal extracted for each CBF region by the CBF extracting unit 433, thereby adjusting the concentration of oxidized hemoglobin in each CBF region The change in hemoglobin concentration and the change in hemoglobin concentration can be calculated, and the characteristic value of each CBF section can be calculated from the changes in concentration of oxidized hemoglobin and the concentration of reduced hemoglobin in each CBF section. Since the concentration of oxidized hemoglobin and the concentration of reduced hemoglobin can be calculated from two wavelengths, for example, a CBF signal having a wavelength of 690 nm and a CBF signal having a wavelength of 830 nm, A pair of optical electrodes may be additionally provided and the control unit 436 modulates the light emitting element 31 at two frequencies so that the light receiving element 32 can receive signals of two wavelengths.

The state calculating unit 435 calculates a value indicating the state of the user based on the combination of the feature value calculated by the EEG analyzing unit 432 and the feature value calculated by the CBF analyzing unit 434. [ The EEG signal has a high temporal resolution but a low spatial resolution. On the other hand, the CBF signal measured by near-infrared spectroscopy has higher spatial resolution but lower time resolution than EEG signal. In other words, the EEG signal is less reliable than the CBF signal, indicating the state of mind and body, but the state of mind and body can be expressed with shorter intervals. In this embodiment, the length of the CBF section is set to be at least twice as long as the length of the EEG section in order to improve the accuracy of the user's condition diagnosis while making the head wearable device thin and short using the characteristics of the EEG signal and CBF characteristics. Set to multiples.

When the length of the CBF section is a multiple of at least two times the length of the EEG section, the feature values of several EEG sections are calculated when the feature value of one CBF section is calculated. In this embodiment, if at least one of the feature values of the plurality of EEG intervals indicates that the user is in an abnormal state, the feature value of the CBF interval forming the same time zone as the plurality of EEG intervals is calculated, If none of them indicates that the user's state is abnormal, the computation of the feature values of the CBF interval that forms the same time zone as the multiple EEG intervals is skipped.

That is, if the feature value of at least one EEG interval among the feature values of each EEG interval indicates that the user's state is abnormal, the state calculating unit 435 calculates the feature of one CBF interval including the time zone of at least one EEG interval Value and a feature value of a plurality of EEG sections forming the same time zone as the CBF section. In this way, since a value indicating the state of the user is calculated on the basis of the combination of the feature value of each EEG section forming the same time zone and the feature value of each CBF section, the defect of the analysis result of the EEG signal is And the defect of the analysis result of the CBF signal can be compensated by the analysis result of the EEG signal, so that the error of the user's condition diagnosis can be reduced.

For example, the state calculator 435 compares the feature value of at least one EEG section among the feature values of each EEG section with the EEG threshold value, and if the state value calculated by the result state calculating section 435 is EEG A value indicating a state of the user based on a combination of a feature value of one CBF section including a time zone of at least one EEG section and a feature value of a plurality of EEG sections forming a same time zone as the CBF section . Here, the EEG threshold can be varied according to the information input by the user or the medical professional through the user interface 46. The minimum value of the feature value indicating the sleep state may vary depending on the user's personal characteristics.

In this way, since the feature of the CBF section is not considered, only the characteristic value of the shorter EEG section is considered, and the user's state is diagnosed first, so that the user can be diagnosed at shorter intervals. As a result, the real-time condition diagnosis of the user becomes possible. As described above, if the modified Beer-Lambert law is applied to calculate the feature value of each CBF section, the amount of computation of the CBF analyzing unit 434 is increased to require a high-performance microprocessor. High-performance microprocessors are more expensive and larger than typical microprocessors. Since high-performance peripheral devices are required for interfacing with a high-performance microprocessor, it is difficult to reduce the size of hair-worn devices. As described above, since the feature value of the CBF section is calculated only for the EEG section indicating that the user's state is abnormal, the state calculating section 435 can omit the feature value calculation of the CBF section in most sections, The signal processing unit 43 can be implemented with the microprocessor of the present invention, and as a result, the head-wearable device of a light-weight small-size can be manufactured at low cost.

The state calculating unit 435 multiplies the feature values of the plurality of EEG sections and the feature values of one CBF section forming the same time period with the average of the plurality of EEG sections by multiplying them by different weights according to the following equation A value indicating the state of the user may be calculated. Since the scale of the feature value of the EEG section and the scale of the feature value of the CBF section may be different from each other, in order to match the scale of the feature value of the EEG section with the scale of the feature value of the CBF section, Each feature value of a CBF interval can be multiplied by a different weight. If the number of the plurality of EEG sections is N, the average of the feature values of the plurality of EEG sections can be calculated by dividing the sum of the feature values of the plurality of EEG sections by N, as described in Equation (2).

In addition, since the reliability of the feature value of any one CBF section may be higher than the average of the feature values of the plurality of EEG sections for the reason described above, the reliability of the feature value of any one of the plurality of EEG sections may be higher than that of the weight value a The magnitude of the weight b multiplied by the feature value of one CBF interval may be large. In addition, the weights multiplied by the average of the feature values of the plurality of EEG intervals and the feature values of any one of the CBF intervals may be varied according to the information input by the user or the medical professional through the user interface 46. [ For example, humans generally decrease cerebral blood flow as age increases after age 65. That is, the weight b multiplied by each feature value of the CBF section according to the age input by the user through the user interface 46 can be reduced.

The control unit 436 controls the switching unit 436 such that the pair of electrodes 2 is connected to either the EEG measuring unit 41 or the signal generating unit 44 according to the magnitude of the state value calculated by the state calculating unit 435, (45). For example, the control unit 436 controls the EEG measuring unit 41 and the signal generating unit 44 (see FIG. 4) based on the result of comparison between the state value calculated by the state calculating unit 435 and the state threshold value, The switching unit 45 controls the switching unit 45 so that the switching unit 45 is connected to either one. The control unit 436 compares the state value calculated by the state calculating unit 435 with the state threshold value and if the state value calculated by the state calculating unit 435 is equal to or greater than the state threshold value, 2) to be connected to the signal generating unit 44. [0050] The control unit 436 controls the switching unit 45 to connect the pair of electrodes 2 to the EEG measuring unit 41 when the state value calculated by the state calculating unit 435 is less than the state threshold value .

The fact that the state value calculated by the state calculating unit 435 is equal to or greater than the state threshold value means that the user's state is abnormal and that the state value calculated by the state calculating unit 435 is less than the state threshold value, Is in a normal state. The control unit 436 controls the state calculator 435 to calculate the state value calculated by the state calculator 435 such as when the state value calculated by the state calculator 435 is less than the state threshold value or when there is no state value calculated by the state calculator 435 The switching unit 45 is controlled so that the pair of electrodes 2 are connected to the EEG measuring unit 41 in all cases except when the state value is equal to or greater than the state threshold value. Here, the state threshold can be varied according to the information input by the user or medical professional via the user interface 46. [ The minimum value of the state value indicating the sleep state may vary depending on the user's personal characteristics.

The control unit 436 performs all control operations of the signal processing unit 43 as described above. For example, when the EEG signal and the CBF signal are simultaneously applied to the electrical signal output from the pair of electrodes 2 and the electrical signal output from the light receiving element among the pair of the optical electrodes 3 at the same time And controls the EEG measuring unit 41 and the CBF measuring unit 42 so as to be measured. The control unit 436 controls the signal generating unit 44 to generate a stimulation signal if the state value calculated by the state calculating unit 435 indicates that the user is in an abnormal state, And controls the switching unit 45 so that the generated stimulation signal is output to the pair of electrodes 2. The controller 436 receives the information input by the user or the medical professional through the user interface 46, generates information to be displayed to the user, and outputs the information to the user interface 46.

7 is another configuration diagram of the electronic device 4 shown in Fig. 7, the electronic device 4 includes an EEG measuring unit 41, a CBF measuring unit 42, a signal processing unit 43, a signal generating unit 44, a switching unit 45, a user interface 46, And a communication unit 47, as shown in Fig. The electronic device 4 shown in Fig. 7 includes an EEG measuring unit 41, a CBF measuring unit 42, a signal processing unit 43, a signal generating unit 44, a switching unit 45, And further includes a communication unit 47 in addition to the user interface 46. [ The EEG measuring unit 41, the CBF measuring unit 42, the signal processing unit 43, the signal generating unit 44, the switching unit 45, and the user interface 46 are the same as the components shown in Fig. 3 Only the operation of the communication unit 47 and the operation of the signal processing unit 43 according to the addition of the communication unit 47 will be described below.

The signal processing unit 43 measures the result of analysis of the EEG signal measured for a predetermined time from the time when the control unit 45 controls the signal for stimulating the scalp of the user to be output to the pair of electrodes 2, And outputs a warning message indicating that the user's state is abnormal if the state value calculated based on the combination of the analysis result of the CBF signal indicates that the user is in an abnormal state. Here, the predetermined time is longer than the maximum time that the stimulus signal is applied to the user's scalp and can be switched to the awakening state, and the user is switched to the awakening state after the stimulus signal is applied to the scalp of the user It is shorter than the minimum time to enter the sleep state.

The communication unit 47 transmits the warning message output by the signal processing unit 43 to the remote terminal 100 managed by the supervisor who monitors the status of the user. It is preferable that the communication unit 47 transmits the warning message to the remote terminal 100 via the wireless network in order to minimize the inconvenience of the user and maximize the free activity of the user. Examples of the wireless network include a Wi-Fi network, and examples of the remote terminal 100 include a PC (personal computer), a smart phone, and the like.

When a stimulus signal is applied to the scalp of a user, the user's state generally changes from a sleep state to a state of awakening. However, the user may not be switched to the awakening state even if a stimulus signal is applied to the user's scalp for some reason. For example, the user may not switch to an awakening state if he or she is in a fainting state due to an accident or when the strength of the stimulus signal is insufficient to awaken the user. As described above, in the present embodiment, when a stimulus signal is applied to the user's scalp but the state is not switched to the awakening state, a message indicating that the user's state is abnormal is transmitted to the remote terminal 100 of the supervisor, The perceived surveillance enabled the user to take appropriate action.

8 is a flowchart of a method for managing user status according to another embodiment of the present invention. Referring to FIG. 8, the user state management method according to the present embodiment is a method for managing the state of a user using bio-signals of a user's brain, in which the signal processing unit 43 shown in FIG. . Therefore, even if the following description is omitted, the contents described above with respect to the signal processing unit 43 shown in Fig. 7 also apply to the user management method described below.

In step 81, the signal processing unit 43 divides and extracts the EEG signal measured from the electric signal output from the pair of electrodes 2 by the time length unit of the EEG section, and extracts the electric signal from the electric signal output from the light receiving element 32 The measured CBF signal is divided by time length unit of CBF interval and extracted. When the length of the CBF section is a multiple of at least twice the length of the EEG section, the EEG signals of the multiple EEG sections are extracted when the CBF signal of one CBF section is extracted.

In step 82, the signal processor 43 calculates the feature value of each EEG section by analyzing the EEG signal extracted for each EEG section in step 81. In step 81, the CBF signal extracted for each CBF section is analyzed by CBF section Thereby calculating characteristic values of each CBF section. When the length of the CBF section is a multiple of at least twice the length of the EEG section, the feature values of several EEG sections are calculated when the feature value of one CBF section is calculated. If all of the feature values of the EEG intervals do not indicate that the user is in an abnormal state, the calculation of the feature values of the CBF interval that forms the same time zone as the multiple EEG intervals may skip and return to step 81.

In step 83, the signal processing unit 43 calculates a value indicating the state of the user based on the combination of the feature value of each EEG section calculated in step 82 and the feature value of each CBF section. When the length of the CBF section is a multiple of at least twice the length of the EEG section, the average of the characteristic values of the plurality of EEG sections and the characteristic values of one CBF section forming the same time period as the plurality of EEG sections are different And a value indicating the state of the user may be calculated by multiplying the weights by the weights.

In step 84, the signal processing unit 43 compares the state value calculated in step 85 with the state threshold value. As a result, if the state value calculated in step 85 is greater than or equal to the state threshold value, that is, if the state of the user is abnormal, the process proceeds to step 85 or step 85. If the state value calculated in step 85 is less than the state threshold value, that is, if the user's state is normal, the process returns to step 81. If the state value calculated in step 85 is equal to or greater than the state threshold value and the state value calculated immediately before the state value calculation in step 85 is less than the state threshold value, that is, if the immediately preceding state of the user is a normal state, If the state value calculated immediately before the state value calculation in step 85 is equal to or greater than the state threshold value, that is, if the previous state of the user is abnormal,

The case where the user's previous state is in the normal state but the current state of the user is changed to the abnormal state is shown as "abnormal A" in FIG. 8, and even if the user's electric state is abnormal, The case where the current state of the user remains unhealthy is shown as "abnormal B" in Fig.

The signal processing unit 43 controls the signal generating unit 44 to generate a signal for stimulating the user's scalp so that the stimulation signal generated by the signal generating unit 44 is applied to the pair of electrodes 2, And controls the switching unit 45 to output the output signal. The signal processing unit 43 controls the signal generating unit 44 and the switching unit 45 so that a signal for stimulating the user's scalp is generated for a time sufficient for the user to switch from the sleep state to the awakening state do. The signal processing unit 43 controls the switching unit 45 so that the electric signal detected by the pair of electrodes 2 is transmitted to the EEG measuring unit 41. [ After returning from step 86 to step 81, measurement and analysis of each of the EEG signal and the CBF signal are performed for a predetermined time as described above.

In step 87, the signal processing unit 43 outputs a warning message indicating that the user's state is abnormal, so that the warning message is transmitted to the remote terminal 100 managed by the supervisor monitoring the user's state.

The above-described embodiments of the present invention can be embodied in a general-purpose digital computer that can be embodied as a program that can be executed by a computer and operates the program using a computer-readable recording medium. In addition, the structure of the data used in the above-described embodiments of the present invention can be recorded on a computer-readable recording medium through various means. The computer-readable recording medium includes a storage medium such as a magnetic storage medium (e.g., ROM, floppy disk, hard disk, etc.), optical reading medium (e.g., CD ROM,

The present invention has been described with reference to the preferred embodiments. It will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the spirit and scope of the invention as defined by the appended claims. Therefore, the disclosed embodiments should be considered in an illustrative rather than a restrictive sense. The scope of the present invention is defined by the appended claims rather than by the foregoing description, and all differences within the scope of equivalents thereof should be construed as being included in the present invention.

1 ... Wear
11 ... frame
12 ... rubber band
2 ... a pair of electrodes
21 ... reference electrode
22 ... detection electrode
3 ... A pair of photoelectrodes
31 ... light emitting element
32 ... receiving element
4 ... electronic device
41 ... EEG measuring unit
42 ... CBF measuring unit
43 ... signal processor
44 ... signal generator
45 ... switching part
46 ... User Interface
47 ... communication section
5 ... battery

Claims (9)

CLAIMS What is claimed is: 1. A head wearable device for managing a user's condition,
Wearable wear on the wearer's head;
An EEG measuring unit for measuring an EEG signal representing electroencephalography (EEG) generated on the scalp of the user by using at least one pair of electrodes positioned between the inner side of the wearer and the scalp of the user;
A CBF measuring unit for measuring a CBF signal indicating cerebral blood flow (CBF) flowing under the scalp of a user using at least one pair of photoelectrodes positioned between the inner side of the wearer and the scalp of the user;
A signal processing unit for calculating a value indicating a state of the user based on a combination of an analysis result of the EEG signal measured by the EEG measuring unit and an analysis result of the CBF signal measured by the CBF measuring unit;
A signal generator for generating a signal for stimulating a user's scalp according to a state value calculated by the signal processor and outputting the signal to the at least one pair of electrodes; And
And a switching unit connecting the at least one pair of electrodes to one of the EEG measuring unit and the signal generating unit under the control of the signal processing unit,
The signal processing unit
An EEG analyzer for calculating a feature value of each EEG section by analyzing the signal measured by the EEG measuring unit according to the EEG interval;
A CBF analyzing unit for calculating characteristic values of each CBF section by analyzing the signals measured by the CBF measuring unit by CBF intervals;
A state calculating unit for calculating the state value based on a combination of the feature value calculated by the EEG analyzing unit and the feature value calculated by the CBF analyzing unit; And
And a controller for controlling the switching unit so that the at least one pair of electrodes is connected to either the EEG measuring unit or the signal generating unit according to the magnitude of the state value calculated by the state calculating unit,
Wherein the state value includes a feature value of the calculated plurality of EEG intervals and a feature value of the calculated CBF interval as an average of the feature values of the plurality of EEG intervals and a feature value of the one CBF interval By multiplying different weights by a predetermined equation,
Wherein the state of the user includes a user's awakening state and a sleep state of the user. The method according to claim 1,
Wherein the signal processor controls the signal generator so that the stimulus signal is generated if the state value calculated by the signal processor indicates that the user is in an abnormal state and the stimulus signal generated by the signal generator is generated by the at least one pair Controls the switching unit to be outputted to the electrode,
The signal generator generates the stimulus signal under the control of the signal processor,
Wherein the switching unit disconnects the at least one pair of electrodes from the EEG measurement unit under the control of the signal processing unit and connects the at least one pair of electrodes to the signal generation unit,
Wherein the abnormal state includes a sleep state of the user. 3. The method of claim 2,
Wherein the signal processing unit is based on a combination of an analysis result of the EEG signal measured for a predetermined time from the time when the switching unit is controlled so that the stimulation signal is output to the at least one pair of electrodes and an analysis result of the CBF signal measured during the predetermined time And outputs a warning message indicating that the user's state is abnormal if the calculated state value indicates that the user's state is abnormal,
And a communication unit for transmitting a warning message output by the signal processing unit to a remote terminal managed by a supervisor for monitoring a state of the user,
And if the calculated state value is equal to or greater than a predetermined threshold value, the calculated state value indicates that the user's state is abnormal. delete The method according to claim 1,
Wherein the controller controls the switching unit such that the at least one pair of electrodes is connected to either the EEG measuring unit or the signal generating unit according to a result of comparing the state value calculated by the state calculating unit and the state threshold value,
Wherein the state threshold is variable according to information input by a user or a medical professional. 6. The method of claim 5,
The length of each CBF section is a multiple of at least two times the length of each EEG section,
Wherein the state calculator calculates a feature value of at least one of the feature values of the EEG interval, if the feature value of the at least one EEG interval indicates that the user is in an abnormal state, Wherein said state value is calculated based on a combination of feature values of a plurality of EEG sections forming a same time zone as any one CBF section. The method according to claim 6,
Wherein the state calculating unit calculates the state value by multiplying an average of the feature values of the plurality of EEG intervals and feature values of the one CBF section by different weights, 8. The method of claim 7,
Wherein the weights multiplied by the feature values of any one of the CBF intervals and the feature values of the plurality of EEG intervals vary according to information input by a user or a medical professional. A method for managing a user's condition using a bio-signal of a brain,
Dividing the EEG signal representing the EEG signal generated on the scalp of the user into time length units of the EEG section and extracting the CBF signal representing the cerebral blood flow flowing under the scalp of the user by dividing the CBF signal into time length units of the CBF section;
Calculating a characteristic value of each EEG section by analyzing the EEG signal extracted for each EEG section by EEG section and analyzing the CBF signal extracted for each CBF section by CBF section to calculate a characteristic value of each CBF section;
Calculating a value indicating a state of the user based on the calculated feature value of each EEG section and the feature value of each CBF section; And
And controlling a signal generating unit to generate a signal for stimulating a user's scalp so that a signal for stimulating the user's scalp is generated according to the calculated state value,
Wherein the state value includes a feature value of the calculated plurality of EEG intervals and a feature value of the calculated CBF interval as an average of the feature values of the plurality of EEG intervals and a feature value of the one CBF interval By multiplying different weights by a predetermined equation,
Wherein the state of the user includes a user's awakening state and a sleep state of the user.

Images