WO2006096135A1 - Systeme et procede pour controler la fatigue mentale - Google Patents

Systeme et procede pour controler la fatigue mentale Download PDF

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Publication number
WO2006096135A1
WO2006096135A1 PCT/SG2006/000046 SG2006000046W WO2006096135A1 WO 2006096135 A1 WO2006096135 A1 WO 2006096135A1 SG 2006000046 W SG2006000046 W SG 2006000046W WO 2006096135 A1 WO2006096135 A1 WO 2006096135A1
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WO
WIPO (PCT)
Prior art keywords
sensor
brain
sensors
person
scalp
Prior art date
Application number
PCT/SG2006/000046
Other languages
English (en)
Inventor
Xiaoping Li
Xinbo Qian
Wu Chun Ng
Ning Ning
Kaiquan Shen
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National University Of Singapore
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Publication date
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Publication of WO2006096135A1 publication Critical patent/WO2006096135A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/16—Devices for psychotechnics; Testing reaction times ; Devices for evaluating the psychological state
    • A61B5/165—Evaluating the state of mind, e.g. depression, anxiety
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
    • A61B5/291—Bioelectric electrodes therefor specially adapted for particular uses for electroencephalography [EEG]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/369—Electroencephalography [EEG]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/48—Other medical applications
    • A61B5/4806—Sleep evaluation
    • A61B5/4809—Sleep detection, i.e. determining whether a subject is asleep or not
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network

Definitions

  • the present invention relates broadly to a method and system for monitoring mental fatigue, to a sensor for monitoring brain activities, to a method of categorizing a measured electrical or magnetic field of a human brain, to a data storage medium having stored thereon code means for instructing a computer to execute a method of monitoring mental fatigue of a person, to a data storage medium having stored thereon code means for instructing a computer to execute a method of categorizing a measured electrical or magnetic field of a human brain, and to a headband for mounting the sensors.
  • an electroencephalogram is a test to detect abnormalities in the electrical activity of the brain.
  • EEG electroencephalogram
  • electrodes are placed on the skull over multiple areas of the brain to detect and record patterns of electrical activity and check for abnormality.
  • EEG is used to help diagnose the presence and type of seizure disorders, to look for causes of confusion, and to evaluate head injuries, tumours, infections, degenerated diseases, and metabolic disturbances that affect the brain.
  • a person In order to be subjected to an EEG 1 a person typically has to enter a specially designed room at a healthcare provider's premises, with multiple electrodes and associated cables connected to proprietary systems being applied to the person scalp, while the person is lying on their back on a table or in a reclining chair in closed proximaty to the equipment.
  • a system for monitoring brain activities comprising: one or more sensors for measuring an electric field or a magnetic field of a brain; a processing system; and a transmission system, wherein the transmission system is coupled between the sensors and the processing system for transferring a signal representative of the electric or magnetic field to the processing system; and wherein the processing system processes the received signal for identification of brain activities.
  • the sensors may comprise micro spikes for intrusive measuring the electrical field of the brain.
  • the micro spikes may be arranged for penetrating a dead skin layer of a person's scalp.
  • the sensors may comprise protrusions formed on a main body of the sensor, the micro spikes being formed on the protrusions, whereby parting of a person's hair for enabling contact of the micro spikes with the scalp is facilitated.
  • Each micro spike may comprise a shoulder structure around a tip of the micro spike, for further facilitating the parting of the person's hair for enabling contact of the micro spikes with the scalp while limiting excessive penetration into the scalp.
  • the sensors may comprise non-intrusive capacitive coupling sensors.
  • the sensors may comprise comb shaped sensing heads for measuring the electric or magnetic field of the brain, whereby parting of a person's hair for enabling contact of the sensor head with the scalp is facilitated.
  • the sensors may be disposed in an enclosure for shielding of the sensor from interfering noise.
  • the sensing heads of the sensors may comprise a sensing layer of high dielectric constant.
  • a thickness of the layer may be determined such that an output of the sensor is substantially insensitive to a thickness variation of the sensors.
  • the system may further comprise a headband for mounting the sensors.
  • the headband may be arranged for mounting the sensors at various locations of the headband.
  • the system may further comprise sensor casings in which the sensors are mounted in a biased manner for biasing the sensors against the person's head when the headband is worn.
  • a surface of the casings may be coated by metal layer or have a metal sheet adhered thereto to provide shielding to the sensor, contained circuitry, or both.
  • the system may further comprise an agitator in each sensor casing stimulating a vibrating movement of the sensor in the sensor casing so as to facilitate parting of the person's hair for enabling contact with the scalp of the head.
  • the system may further comprise a spring for the force control of the sensor for enabling proper contact of the micro spikes or sensor head with the scalp while limiting excessive penetration into the scalp.
  • a person's body may be used as a transmission medium of the transmission system.
  • the system may further comprise a body transmitter; a body wireless relay; and/or a body receiver.
  • the body transmitter, the body wireless relay; and/or the body receiver may be coupled to the body via a single electrode.
  • the transmission frequency may range from about 10 kHz to about 100 kHz and the voltage of the transmitting signals may range up to about 10 V.
  • the system may further comprise a reader for providing a power supply and a control instruction and for receiving the signal representative of the electric or magnetic field; and one or more transponders for receiving the power supply and the control instruction from the reader and sending the signal representative of the electric or magnetic field to the reader.
  • the system may further comprise a reader for providing a control instruction and for receiving the signal representative of the electric or magnetic field; and one or more transponders with power source for receiving the control instruction from the reader and sending the signal representative of the electric or magnetic field to the reader.
  • An anti-collision protocol may be employed in the reader to read data from multiple transponders.
  • the reader may be installed on a structure for positioning the reader above the person's head.
  • the reader may be installed below a ceiling of a vehicle and for placement above the person's head.
  • the detected brain activities may include mental fatigue, sleep onset and blackout.
  • a sensor for monitoring brain activities comprising micro spikes for intrusive measuring of the electrical field of the brain.
  • the micro spikes may be arranged for penetrating a dead skin layer of a person's scalp.
  • the sensors may comprise protrusions formed on a main body of the sensor, the micro spikes being formed on the protrusions, whereby parting of a person's hair for enabling contact of the micro spikes with the scalp is facilitated.
  • Each micro spike may comprise a shoulder structure around a tip of the micro spike, for further facilitating the parting of the person's hair for enabling contact of the micro spikes with the scalp while limiting excessive penetration into the scalp.
  • a sensor for monitoring brain activities comprising a comb shaped sensing head for measuring the electric or magnetic field of the brain, whereby parting of a person's hair for enabling contact of the sensor head with the scalp is facilitated.
  • the sensor may be disposed in an enclosure for shielding of the sensor from interfering noise.
  • the sensing head of the sensor may comprise a sensing layer of high dielectric constant.
  • a thickness of the layer may be determined such that an output of the sensor is substantially insensitive to a thickness variation of the sensors.
  • a method of monitoring mental fatigue of a person comprising the steps of: measuring an electric field or a magnetic field of a brain; transferring a signal representative of the electric or magnetic field; and processing the received signal for identification of a mental fatigue level of the person.
  • a method of categorizing a measured electrical or magnetic field of a human brain comprising the steps of: detecting miscommunications between cortex regions in an activation stream of an auditory response of the brain; measuring an electric field or a magnetic field of a brain; and categorizing the measured electric field or magnetic field of the brain into different mental fatigue levels based on the detetced miscommunications between the cortex regions in the activation stream of the auditory response of the brain.
  • a data storage medium having stored thereon code means for instructing a computer to execute a method of monitoring mental fatigue of a person, the method comprising the steps of: measuring an electric field or a magnetic field of a brain; transferring a signal representative of the electric or magnetic field; and processing the received signal for identification of a mental fatigue level of the person.
  • a data storage medium having stored thereon code means for instructing a computer to execute a method of categorizing a measured electrical or magnetic field of a human brain, the method comprising the steps of: detecting miscommunications between cortex regions in an activation stream of an auditory response of the brain; measuring an electric field or a magnetic field of a brain; and categorizing the measured electric field or magnetic field of the brain into different mental fatigue levels based on the detetced miscommunications between the cortex regions in the activation stream of the auditory response of the brain.
  • a headband for mounting the sensors, arranged for mounting the sensors at various locations of the headband.
  • the headband may further comprise sensor casings in which the sensors are mounted in a biased manner for biasing the sensors against the person's head when the headband is worn.
  • a surface of the sensor casings may be coated by metal layer or have a metal sheet adhered thereto to provide shielding to the sensor, contained circuitry, or both.
  • Each sensor casing may further comprise an agitator for stimulating a vibrating movement of the sensor in the sensor casing so as to facilitate parting of the person's hair for enabling contact with the scalp of the head.
  • Each sensor casing may 'further comprise a spring for the force control of the sensor for enabling proper contact of the micro spikes or sensor head with the scalp while limiting excessive penetration into the scalp.
  • Figure 1 shows a schematic diagram of a brain activity.
  • Figure 2 shows a schematic diagram of a mental fatigue monitoring system.
  • Figure 3 shows a schematic perspective view of an assembly of a bioelectrical potential sensor and a pre-processing signal conditioning circuit.
  • Figure 4a shows a schematic perspective view of a modification of the bioelectrical potential sensor.
  • Figure 4b shows a schematic cross-sectional view of a micro spike of the bioelectrical potential sensor.
  • Figure 5a shows a schematic perspective view of another modification of the bioelectrical potential sensor.
  • Figure 5b shows a schematic side view of the bioelectrical potential sensor.
  • Figure 6 shows a schematic diagram of a capacitive coupling bioelectrical potential sensor contacting a scalp.
  • Figure 7 shows a graph indicating a non-linear relationship between a capacitance of 1 cm 2 of a dielectric material layer of a sensing head and a thickness of the dielectric material layer.
  • Figure 8a shows a schematic perspective view of a headband.
  • Figure 8b shows a schematic cross-sectional view of an assembly of a sensor casing and the bioelectrical potential sensor. .
  • Figure 9a shows a schematic diagram of a wireless body transmission system.
  • Figure 9b shows a schematic circuit diagram of a body transmitter of the system.
  • Figure 9c shows a schematic circuit diagram of a body wireless relay of the system.
  • Figure 9d shows a schematic circuit diagram of a body receiver of the system.
  • Figure 10a shows a schematic diagram of another wireless transmission system.
  • Figure 10b shows a schematic circuit diagram of a reader of the system.
  • Figure 10c shows a schematic circuit diagram of a transponder of the system.
  • Figure 11 shows a schematic diagram of functional cortex regions of a human brain to illustrate a principle of labeling a measured electrical field of the brain for mental fatigue levels by detecting miscommunications between the cortex regions.
  • Figure 12 shows a schematic diagram of a signal processing system for measuring mental fatigue level of the brain.
  • Figure 13 is a schematic drawing illustrating a computer system for implementing the signal processing system of Figure 12.
  • FIG. 1 shows a schematic diagram of a brain activity.
  • a neuronal group 104 fires electric impulses (neuronal activation) to other neuronal groups in the brain, forming an electrical field 106 and a magnetic field 108 of the brain.
  • the activities of the brain 102 can be detected by measuring either the electrical field 106 or the magnetic field 108 of the brain 102.
  • Mental fatigue is a brain activity associated with a change of a neuronal activation status in the brain 102.
  • a method of measuring mental fatigue is to measure either the electrical field 106 or the magnetic field 108 of the brain 102 in association with the change of the neuronal activation status at different levels of mental fatigue.
  • sleep onset The transit from conscious state e.g. awake to unconscious state e.g. asleep of the brain is generally termed as sleep onset. Sleep onset is also associated with the change of the neuronal activation status in the brain 102. A method of measuring sleep onset is to measure either the electrical field 106 or the magnetic field 108 of the brain 102 in association with the change of the neuronal activation status of sleep onset in the brain 102.
  • Blackout or loss of consciousness is also associated with the change of the neuronal activation status in the brain 102.
  • a method of measuring blackout or loss of consciousness is to measure either the electrical field 106 or the magnetic field 108 of the brain 102 in association with the change of the neuronal activation status of blackout or loss of consciousness in the brain 102.
  • FIG. 2 shows a schematic diagram of a brain activity monitoring system 200.
  • the system 200 is used for measuring human mental fatigue level, sleep onset and blackout.
  • the system 200 comprises three device units.
  • a first device unit 202 comprises a headband 204 and an analog signal processor 206.
  • the analog signal processor 206 is a circuit board that can be attached to the headband 204.
  • the headband 204 comprises sensors 208 for measuring an electric field or a magnetic field of the brain.
  • the second device unit 210 of the system 200 comprises a digital signal processing system 212 and an execution device 214.
  • the digital signal processing system 212 is coupled to the execution device 214.
  • Outputs of the execution device 214 can take a number of forms such as visual signals and audible alarms.
  • the third device unit is: a wireless transmission system 216.
  • the analog signal processor 206 and the digital signal processing system 212 are coupled to the wireless transmission system 216.
  • the digital signal processing system 212 can be embedded in the wireless transmission system 216.
  • the electric or magnetic signals are measured by the sensors 208 of the headband 204.
  • the signals are sent to the analog signal processor 206.
  • the analog signal processor 206 comprises a protection circuit for human-to-electric interface, filters for high-frequency noise filtering and powerline interference rejection, amplifiers for low- noise pre-amplifying and selective gain amplifying, circuits for sensor impedance testing, and analog-to-digital converters (ADC).
  • the wireless transmission system 216 transmits the signals to the embedded digital processing system 212.
  • the digital signal processing system 212 executes programs for processing the brain activity data.
  • the digital processing system 212 is interfaced with a keyboard, a display, a warning sound beeper, a flash memory for data storage, and RS232 and RS488 ports for computer connection.
  • a digital signal processor of the digital processing system 212 controls the operation of the brain activity monitoring system 200, activates the execution device 214 for action taking and executes a program for signal-noise separation, artefact removal and brain activity pattern identification for human mental fatigue, sleep onset and blackout.
  • Epidermis which is the most superficial layer of the skin, provides a first barrier of protection for the body from foreign substances.
  • the outermost layer of dead cells in the epidermis is Stratum Corneum, which acts as a fluid barrier and. is highly electrically insulated.
  • the other layer in the epidermis is known as the living epidermis.
  • the living cells in the living epidermis consist of liquid and are therefore electrically conductive.
  • Beneath the living epidermis is the dermis, which is made up of tiny blood vessels and nerve endings that are densely woven into the flexible connective tissue. The dermis is where pain originates.
  • Figure 3 shows a schematic perspective view of an assembly of a bioelectrical potential sensor 302 and a pre-processing signal conditioning circuit 304.
  • Signal and power lines of the circuit 304 are connected to the analog signal processor 206 ( Figure 2) via connecting pins 306 of the circuit 304.
  • a conductive disposable layer 308, which may be made of a conductive polymer or a metal by moulding, stamping, casting, lithography, or any possible means, with micro spikes 310 is attached onto the sensor 302.
  • the bioelectrical potential signal received by the sensor 302 via the micro-spikes 310 forms the input into the circuit 304.
  • the micro spikes 310 penetrate a scalp (not shown) for a depth of about 20 to 30 ⁇ m and measure the bioelectrical potential on the scalp.
  • the electric signal is sent to the circuit 304 for filtering and amplification.
  • the signal is later sent to the analog signal processor 206 ( Figure 2) via the connecting pins 306.
  • Figure 4a shows a schematic perspective view of a modification of the bioelectrical potential sensor 402.
  • the sensor 402 is made of conductive materials, such as metals or conductive polymers, and is designed for use on hairy skin surface.
  • the sensor 402 comprises six individual protrusions in the form of islands 404 disposed along the circumference of the sensor 402.
  • the islands 404 are disposed such that a set of three islands 404 is facing another corresponding set of three islands 404.
  • Each island 404 is spaced apart for a distance of about 2.75 mm to 7 mm and is about 1 mm high to allow easy parting of the hair when the sensor 402 is used on the scalp.
  • each island 404 comprises several micro spikes 406 on a conductive disposable layer.
  • Each individual micro spike 406 is spaced apart for a distance of about 300 ⁇ m to part any hairs that were not separated by the islands 404.
  • Figure 4b shows a schematic cross-sectional view of a micro spike 406.
  • a height of a sharp tip 408 of the micro spike 406 is about 30 ⁇ m, which is sufficient to pierce through the Stratum Corneum (dead skin, about 10-20 ⁇ m) and into the conductive living epidermis (about 30-100 ⁇ m).
  • the sharp tip 408 of the micro spike 406 is not long enough to reach the dermis (about 1-2mm) and cause pain to the subject.
  • the micro spike 406 has a shoulder 410 of a length of about 50 ⁇ m at each side of the tip 408.
  • the shoulders 410 prevent the entire spike 406 from piercing into the scalp. Since the average diameter of hair is about 100um, the tip 408 and the shoulders 410 allow the hair to slide off from the tip 408 and into the spacing between two micro spikes 406. This prevents any obstruction of penetration of the micro spikes 406 into the scalp by any remaining hair.
  • the sensor 402 further comprises a hole 412 on the back of the sensor 402.
  • the hole 412 is used to attach the sensor 402 to the preprocessing signal conditioning circuit 304 ( Figure 3).
  • FIG. 3 shows a schematic perspective view of another modification of the bioelectrical potential sensor 502.
  • the sensor 502 is made of conductive materials, such as metals or conductive polymers, and is designed for use on smooth surface skin.
  • Figure 5b shows a schematic side view of the sensor 502.
  • a top surface 504 of the sensor 502 is covered by only sharp tips 506 of micro spikes on a conductive disposable layer (not shown) with a height of about 30 ⁇ m. Since there are only sharp tips 506 on the sensor 502, there is no risk of the whole of the micro spikes (not shown) penetrating the scalp. Further, the pressure on a test subject due to the headband (not shown) will be spread over a larger surface area, and thus reducing or alleviating pain to the test subject.
  • the senor 502 further comprises a hole 508 on the back of the sensor 502.
  • the hole 508 is used to receive the pre-processing signal conditioning circuit 304 ( Figure 3).
  • the tips 506 penetrate a scalp (not shown) for a depth of about 20 to 30 ⁇ m and measure the bioelectrical potential on the scalp.
  • the electric signal is sent to the circuit 304 ( Figure 3) for filtering and amplification.
  • the signal is later sent to the analog signal processor 206 ( Figure 2) via the connecting pins 314 ( Figure 3).
  • FIG. 6 shows a schematic diagram of a capacitive coupling bioelectrical potential sensor 602 in contact with a scalp 604.
  • the sensor 602 comprises a sensing head 606 and a processing circuit 608.
  • the sensing head 606 is coupled to the processing circuit 608.
  • the signal processing circuit 608 is coupled to a signal conditioning circuit (not shown).
  • the sensing head 606 is disposed in an enclosure 609.
  • the enclosure 609 provides shielding from interfering noise for the sensing head 606.
  • the sensing head 606 comprises a comb shaped conductive base 610 coated with a thin layer 611 of high dielectric constant material.
  • the sensing head 606 further comprises grooves 612 for holding the hair 614. When measuring the electrical field, the sensing head 606 of the sensor 602 contacts the scalp 604 and the hair 614 is held within the grooves 612.
  • the sensing head 606 receives an electric signal from the scalp 604 by capacitive coupling.
  • the negative charges on the layer 610 will increase until an equilibrium is reached and vice versa, thus forming a displacement current that makes the voltage change on the sensing head 606 coupled to that on the scalp 604.
  • the signal is sent to the processing circuit 608 and the processed signal is sent to the signal conditioner (not shown).
  • Figure 7 shows a graph indicating a non-linear relationship between a capacitance of 1 cm 2 of the dielectric material layer 611 ( Figure 6) of the sensing head 606 ( Figure 6) and the thickness of the layer 611 ( Figure 6).
  • Sampled materials of the layer 611 ( Figure 6) have a dielectric constant of 8, 500 and 1000 respectively.
  • the curve 702 shows that a 5 ⁇ m variation in the thickness (as the thickness varies from 1 to 6 ⁇ m) will result in an 80% drop in the capacitance from about 7.08 to 1.41 nF.
  • the curve 706 shows that a 10 ⁇ m variation in the thickness (as the thickness varies from 190 to 200 ⁇ m) will only result in a 6% drop in the capacitance from about 4.66 to 4.42 nF.
  • STO Strontium Titanium Oxide
  • Figure 8a shows a schematic perspective view of a headband 802.
  • a plurality of sensor casings 804 is disposed on the headband 802.
  • the headband 802 is made of an elastic and high strength material such as acrylic-based photopolymer material.
  • the design of the headband 802 takes into account the contours of an average human head and the positioning of the sensors (not shown).
  • the dimensions of the headband 802 are slightly smaller than the dimensions of a head of an average person.
  • the headband 802 has to be stretched to fit onto the head. The stretching of the headband 802 provides a force which keeps the headband 802 in place.
  • a band part 806 of the headband 802 comprises two arrays of small holes 808 disposed along respective edges of the band part 806.
  • the holes 808 allow the sensor casing 804 to be snapped onto the headband 802 along the band part 806 to adjust the position of the sensor casings 804 according to a head size of a test subject.
  • Fig. 8b shows a schematic cross-sectional view of an assembly of the sensor casing 804 and a bioelectrical potential sensor 810.
  • the sensor casing 804 can be made of the same material as the headband 802.
  • the sensor 810 is slotted into the sensor casing 804 from a bottom opening of the sensor casing 804.
  • Wire leads (not shown) send the signal from the sensor to a pre-processing signal conditioning circuit 812 which is attached to the sensor 810.
  • a spring 814 is attached to an inner top surface of the sensor casing 804. The spring 814 ensures that the pressure of the sensor 810 on the scalp is sufficient to prevent a break in the contact between the sensor 810 and the scalp.
  • a surface 820 of the sensor casing 804 can either be coated with a metal layer or adhered with a metal sheet to provide shielding for the sensor and/or the pre-processing signal conditioning circuit 812.
  • the pre-processing signal conditioning circuit 812 can be coupled to the surface 820.
  • a vibration mechanism e.g. an agitator 818 is used on the sensor to clear any hair underneath the sensor.
  • the agitator 818 is placed at a side wall of the sensor casing 804, with one end protruding outside the sensor casing 804 and the other end disposed near the spring 814.
  • the spring will vibrate which in turn vibrates the sensor 810 to part the hair so that the sensor 810 will be in direct contact with the scalp.
  • a motor driven vibrator may be used to provide vibration or movement to the sensor 810.
  • Figure 9a shows a schematic diagram of a wireless body transmission system 900.
  • the system 900 uses the human body as a transmission medium as compared to air used in the conventional radio frequency (RF) transmission systems.
  • the system 900 comprises a body transmitter 902, a body wireless relay 904 and/or a body receiver 906.
  • the preconditioned brain activity signals are transmitted from the body transmitter 902 to the body wireless relay 904 and/or the body receiver 906.
  • the body transmitter 902 can be placed on the body, near the head, e.g. neck or shoulder.
  • the body wireless relay 904 and body receiver 906 can be placed on various locations of the body, e.g. wrist band and waist band.
  • the body transmitter 902, the body wireless relay 904 and body receiver 906 are coupled to the body via a single electrode, in contrast to other human body communication methods which require two electrodes for data transmission.
  • the transmission-frequency ranges from about 10kHz to 100kHz, depending on the number of sensors required.
  • the transmitted signals may include analog signals as well as digital signals.
  • the maximum voltage of the transmitting signals is about 10V.
  • the data transmission is established between the body transmitter 902 and the body wireless relay 904 or the body receiver 906, by coupling signal currents into the human body or by electrostatic coupling.
  • Using the human body as a transmission medium has the advantages of small power consumption and little influence by electromagnetic noise. Because the signals pass through the human body, electromagnetic noise and interference have little influence on the transmissions, while the signals are largely contained by skin. These characteristics are superior to those of radio-based network technologies, such as Bluetooth or Infrared (IrDA). Low power consumption can also be achieved by body transmission because its higher power efficiency as compared to radio frequency transmissions.
  • Figure 9b shows a schematic circuit diagram of the body transmitter 902 of the system 900.
  • the body transmitter 902 comprises a transmitting electrode 908, an interface circuit 910, a battery 912 and a modulator or voltage to frequency converter 914.
  • the body transmitter 902 is coupled to the analog signal processor 206 ( Figure 2) via a wire 916 and is coupled to the human body via the transmitting electrode 908.
  • the battery 912 provides power supply to the interface circuit 910 and the modulator or voltage to frequency converter 914.
  • the interface circuit 910 is coupled to the modulator or voltage to frequency converter 914.
  • the interface circuit 910 adjusts the input signals to a suitable level for the modulator or voltage to frequency converter 914, which then modulates the frequencies and transmits electric signals via the electrode 908.
  • FIG. 9c shows a schematic circuit diagram of the body wireless relay 904 of the system 900.
  • the body wireless relay 904 comprises a receiving electrode 918, a demodulator or frequency to voltage converter 920, a signal conditioning circuit 922, radio frequency (RF) modules 924, a battery 926, and optionally a storage device 928.
  • the relay 904 is coupled to the human body via the receiving electrode 918.
  • the receiving electrode 918 receives the electric signals transmitted from body transmitter 902.
  • the demodulator or frequency to voltage converter 920 converts the modulated frequency signals to baseband signals.
  • the signal conditioning circuit 922 adjusts the signals to match the input requirement of the RF modules- 924.
  • the RF modules 924 can use any of the current wireless technologies for portable devices, e.g.
  • the RF modules 924 and an antenna 930 transmit the signals to a remote digital processing system 212 ( Figure 2).
  • the battery 926 supplies power to all the circuits of the relay 904.
  • the storage device 928 is optional and can be used to store the baseband signal to a micro storage device, e.g. micro-harddisk, and memory card, if required.
  • Figure 9d shows a schematic circuit diagram of the body receiver 906 of the system 900.
  • the body receiver 906 comprises a receiving electrode 932, a demodulator or frequency to voltage converter 934 and an embedded digital processing system 936.
  • the receiving electrode 932 receives the signals transmitted through the human body from the transmitter 902 ( Figure 9b).
  • the received signals are demodulated to baseband signals by a demodulator or frequency to voltage converter 934.
  • the baseband signals are provided to the embedded digital processing system 936 for identifying the brain activities locally.
  • the system 900 can be implemented such that the transmitter 902 can either transmit the signals to the digital processing system 212 ( Figure 2) via the relay 904 where signal processing is done remotely or to the body receiver 906 where signal processing is done locally. Both the relay 904 and the body receiver 906 can be provided in an implementation to allow both remote and local signal processing.
  • FIG 10a illustrates another wireless transmission system 1000, namely Near Field Telemetry System for Brain Activity Monitoring.
  • the system 1000 comprises a reader 1001 and a plurality of transponders (not shown).
  • Each transponder (not shown) can be integrated with the pre-processing signal conditioning circuit (compare e.g. 304 in Figure 3) of the sensor (compare e.g. 302 in Figure 3).
  • Each transponder (not shown) is connected to the analog signal processor 206 ( Figure 2) which may be on the headband 1002.
  • the transponders (not shown) can be connected to each other by wires, if required.
  • the reader 1001 can be placed at various locations, e.g. at the top of the chair 1003 where the test subject 1004 is seated. Alternatively,- it can be placed as a suspender below the ceiling of a vehicle and above the test subject 1004.
  • a typical range for the reading distance between the reader 1001 and the transponder (not shown) is about 0.2 to about 10 meters. The maximum reading distance is 10 meters.
  • the test subject 1004 will not be monitored when the test subject 1004 is out of the range of reading distance.
  • FIG. 10b shows a schematic diagram of various modules of the reader 1001.
  • the reader 1001 comprises a power module 1005, a modulation circuitry 1006, a demodulation circuitry 1008, an antenna 1010 and an interface circuit 1012.
  • the interface circuit 1012 is coupled to the embedded digital processing system 836 ( Figure 8d) via a bus 1014, which provides power to the power module 1005 of the reader 1001 and receives data transmitted from the interface circuit 1012.
  • the power module 1005 supplies power to the modulation circuitry 1006 and the demodulation circuitry 1008.
  • the power module 1005 and the modulation circuitry 1006 modulate the impedance of the antennas 1010.
  • the antennas 1010 may be in the shape of coils.
  • the demodulation circuitry 1008 recovers the sensor data.
  • FIG. 10c shows a schematic diagram of various modules of the transponder 1016.
  • the transponder 1016 can either be active or passive, e.g. can be active if the transponder 1016 comprises a power source.
  • the transponder 1016 comprises a power supply and modulation circuitry 1018, a demodulation circuitry 1020, a digital logic circuitry 1022, an analog to digital converter (ADC) 1024, an antenna 1026 and an interface circuitry 1028.
  • the power supply and modulation circuitry 1018 of an active transponder 1016 comprises a battery (not shown) that supplies power to the transponder 1016.
  • the power supply and modulation circuitry 1018 may contain a power converter that provides a regulated direct current (DC) voltage from the alternating current (AC) induced on the antenna 1026. This DC power is supplied to other modules in the transponder 1016 and also to the analog signal processor 206 ( Figure 2) and/or the active electrodes via bus 1030.
  • DC direct current
  • AC alternating current
  • the demodulation circuitry 1020 recovers the commands sent from the reader 1001 ( Figure 10b), and passes the recovered commands to the digital logic circuitry 1022.
  • the digital logic circuitry 1022 controls other modules in the transponder 1016.
  • the interface circuit 1028 supplies power to and receives the sensor data from the analog signal processor 206 ( Figure 2) via bus 1030.
  • the sensor data is then digitized by the ADC 1024 and sent to the digital logic circuitry 1022, and in turn to the power supply and modulation circuitry 1018.
  • the reader 1001 When sending a signal to the transponder 1016, the reader 1001 generates a modulated magnetic field by inputting a time varying current into the antenna 1010.
  • the transponder 1016 detects this as a modulation of the voltage induced on the antenna 1026.
  • the modulated voltage signals contain control instructions to the transponder 1016.
  • the modulated voltage signals can be rectified to provide a DC voltage as a power supply to the transponder 1016, and/or the analog signal processor 206 ( Figure 2), and/or the bioelectrical potential sensors (not shown).
  • the transponder 1016 When sending a signal to the reader 1001, the transponder 1016 modulates an impedance of the antenna 1026 and a magnetic field and thus a current through the antenna 1010 of the reader 1001.
  • the demodulation circuitry 1008 of the reader 1001 demodulates the signal and extracts the information sent from the transponder 1016.
  • An anti-collision protocol may be employed in the demodulation circuitry 1008 to read all the data sent from all the transponders 1016 within certain reading cycles.
  • RFID Radio Frequency Identification
  • near field inductive coupling between the reader 1001 and each passive transponder 1016 provides both a power and a communication solution.
  • the transponders 1016 and the analog signal processor 206 ( Figure 2) and/or the bioelectrical potential sensors (not shown) do not need an on-board power supply.
  • the power and data communication between the reader 1001 and the transponder 1016 may employ load modulation.
  • the working frequency can be of different frequency bands, ranging from few kilohertz to several hundreds megahertz.
  • the reader 1001 provides the power supply, which is inductively coupled to the transponder 1016 through antenna 1010 which may contain tuned circuits like an inductor and a capacitor (not shown).
  • the proposed Near Field Telemetry System for Brain Activity Monitoring 1000 can bring many advantages. For example, again the movement of the test subject 1004 is not restricted by any wire. Moreover, the sensors, the analog signal processor 206 ( Figure 2) and the transponders 1016 on the headband do not necessarily contain an on-board energy source. Thus, the weight of the devices placed on the head of the test subject 1004 will be largely reduced.
  • Figure 11 shows a schematic diagram of functional cortex regions of a human brain to illustrate a principle, recognized by the inventors, of categorizing a measured electrical or magnetic field of the brain into various mental fatigue levels by detecting miscommunications between the cortex regions in the activation stream of auditory response of the brain.
  • the human brain consists of a brain stem 1101, a temporal lobe 1102, an auditory cortex 1103, a prefrontal lobe 1104, a frontal lobe 1105, a motor cortex 1106, a parietal lobe 1107, an occipital lobe 1108 and a cerebellum 1109.
  • the auditory cortex 1103 of the brain is activated.
  • the prefrontal lobe 1104 is activated for interpretation of the received command and for decision-making.
  • the prefrontal lobe 1104 activates the motor cortex 1106 which sends and coordinates the test subject's reaction to the command.
  • Mental fatigue causes miscommunications between these cortex regions and thus affects the subject's ability to respond to the auditory command correctly.
  • the deterioration of the performance of the test subject in response to the auditory commands directly reflects the level of subject's mental fatigue.
  • a method for collecting data of the bioelectrical potential on the scalp associated with mental fatigue of different levels by measuring the levels of miscommunication between the cortex regions in association with the mental fatigue levels is derived based on the above-mentioned findings.
  • An auditory vigilance task (AVT) is used to collect objective mental fatigue scoring method.
  • the AVT is programmed such that four audio commands (left, right, up, down) of 500 ms duration each are randomly arranged in one command set.
  • Each AVT test session has 50 command sets and takes about 3 minutes. There is an interval of about 1.5 seconds between each command set.
  • the test subject is required to concentrate and press the corresponding pre- specified buttons within 1.5 seconds after hearing each complete command set.
  • the AVT score is calculated as a percentage of correct responses with respect to the total number of commands.
  • the performance of 'each test subject i.e. the highest AVT score to the lowest AVT score, is evenly divided into five levels from fatigue level 1 to 5 respectively.
  • the scalp bioelectrical potential data which is measured during the AVT test using the brain activity monitoring system 200, is categorised into the corresponding mental fatigue levels of the calculated AVT score.
  • Figure 12 shows a schematic diagram of a signal processing system 1200 for measuring mental fatigue level of the brain.
  • Data acquisition is performed by a brain acquisition module 1201 and the brain activity signals are sent to the pre-processing module 1202.
  • de-noising or decomposition methods e.g. Independent Component Analysis are used to separate signals and noise (e.g. 50Hz hardware noise) from the data captured from the scalp.
  • the artefacts or unwanted signals such as electrocardiogram (ECG) and electrooculogram (EOG), are automatically removed by identifying the artefacts through artefact modelling.
  • ECG electrocardiogram
  • EOG electrooculogram
  • the signals are then provided to the feature extraction module 1203.
  • Statistical features or frequency features such as dominant frequency in any frequency band are extracted from the pre-processed signal of any recorded channel.
  • methods such as Support Vector Machine based Recursive Feature Elimination (SVM-RFE) are employed to select an optimal subset of features from the pool of extracted features.
  • SVM-RFE Support Vector Machine based Recursive Feature Elimination
  • system 1200 includes but is not limited to the use for measuring mental fatigue level.
  • the method and system can be implemented on a computer system 1300, schematically shown in Figure 13. It may be implemented as software, such as a computer program being executed within the computer system 1300, and instructing the computer system 1300 to conduct the method of the example embodiment.
  • the computer system 1300 comprises a computer module 1302, input modules such as a keyboard 1304 and mouse 1306 and a plurality of output devices such as a display 1308, and printer 1310.
  • the computer module 1302 is connected to a computer network 1312 via a suitable transceiver device 1314, to enable access to e.g. the Internet or other network systems such as Local Area Network (LAN) or Wide Area Network (WAN).
  • LAN Local Area Network
  • WAN Wide Area Network
  • the computer module 1302 in the example includes a processor 1318, a Random Access Memory (RAM) 1320 and a Read Only Memory (ROM) 1322.
  • the computer module 1302 also includes a number of Input/Output (I/O) interfaces, for example I/O interface 1324 to the display 1308, and I/O interface 1326 to the keyboard 1304.
  • I/O Input/Output
  • the components of the computer module 1302 typically communicate via an interconnected bus 1328 and in a manner known to the person skilled in the relevant art.
  • the application program is typically supplied to the user of the computer system 1300 encoded on a data storage medium such as a CD-ROM or flash memory carrier and read utilising a corresponding data storage medium drive of a data storage device 1330.
  • the application program is read and controlled in its execution by the processor 1318.
  • Intermediate storage of program data maybe accomplished using RAM 820.
  • the described components in the system in accordance with present invention is not limited to fatigue measurement.
  • the sensors, headband and the casing can be used in the general electroencephalogram (EEG) recording or other biopotential signal measurements, and the headband can be extended to a bodyband for biopotential measurements.
  • EEG electroencephalogram
  • the shapes of the spikes of the sensors are not limited to the shapes described. Other shapes can be used, including differently shaped sensors.

Abstract

Procédé et système (200) pour contrôler les activités cérébrales. Le système comprend un ou plusieurs capteurs (208) pour mesurer un champ électrique ou un champ magnétique d’un cerveau, un système de traitement (212); et un système de transmission (216), le système de transmission étant couplé entre les capteurs (208) et le système de traitement (212) pour le transfert d’un signal représentatif du champ électrique ou magnétique au système de traitement ; et le système de traitement (212) traitant le signal reçu pour l’identification des activités cérébrales.
PCT/SG2006/000046 2005-03-08 2006-03-08 Systeme et procede pour controler la fatigue mentale WO2006096135A1 (fr)

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WO2008148097A2 (fr) * 2007-05-25 2008-12-04 Massachusetts Institute Of Technology Architecture analogique basse puissance pour interfaces cerveau-machine
EP2172152A1 (fr) * 2008-10-06 2010-04-07 Nederlandse Organisatie voor toegepast-natuurwetenschappelijk Onderzoek TNO Électrode pour applications médicales
DE102009024866A1 (de) * 2009-06-09 2010-12-16 Abb Research Ltd. Verfahren und Einrichtung zur Überwachung der Hirnaktivität eines Menschen
CN102184415A (zh) * 2011-05-17 2011-09-14 重庆大学 一种基于脑电信号的疲劳状态识别方法
EP2368494A1 (fr) * 2010-03-24 2011-09-28 Brain Products GmbH Électrode sèche pour détecter des signaux EEG et dispositif de fixation pour maintenir l'électrode sèche
US8326396B2 (en) 2010-03-24 2012-12-04 Brain Products Gmbh Dry electrode for detecting EEG signals and attaching device for holding the dry electrode
WO2014020554A1 (fr) 2012-08-03 2014-02-06 Bernhard Wandernoth Dispositif de mesure de signaux bioélectriques, en particulier de signaux captés par des électrodes
CN104287727A (zh) * 2014-09-28 2015-01-21 青岛柏恩鸿泰电子科技有限公司 弹性干式软电极
CN104887222A (zh) * 2015-05-11 2015-09-09 重庆大学 可逆化脑电信号分析方法
WO2017025553A1 (fr) * 2015-08-11 2017-02-16 Bioserenity Procede de mesure d'un parametre electrophysiologique au moyen d'un capteur electrode capacitive de capacite controlee
WO2019042264A1 (fr) * 2017-08-26 2019-03-07 ZHONG, Daiyun Procédé et appareil de détection active de la fréquence d'activation neuronale au niveau d'un site fonctionnel dans un cerveau
US10514553B2 (en) 2015-06-30 2019-12-24 3M Innovative Properties Company Polarizing beam splitting system

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WO2008148097A3 (fr) * 2007-05-25 2009-02-19 Massachusetts Inst Technology Architecture analogique basse puissance pour interfaces cerveau-machine
US8332024B2 (en) 2007-05-25 2012-12-11 Massachusetts Institute Of Technology Low-power analog architecture for brain-machine interfaces
WO2008148097A2 (fr) * 2007-05-25 2008-12-04 Massachusetts Institute Of Technology Architecture analogique basse puissance pour interfaces cerveau-machine
EP2172152A1 (fr) * 2008-10-06 2010-04-07 Nederlandse Organisatie voor toegepast-natuurwetenschappelijk Onderzoek TNO Électrode pour applications médicales
DE102009024866A1 (de) * 2009-06-09 2010-12-16 Abb Research Ltd. Verfahren und Einrichtung zur Überwachung der Hirnaktivität eines Menschen
EP2368494A1 (fr) * 2010-03-24 2011-09-28 Brain Products GmbH Électrode sèche pour détecter des signaux EEG et dispositif de fixation pour maintenir l'électrode sèche
US8326396B2 (en) 2010-03-24 2012-12-04 Brain Products Gmbh Dry electrode for detecting EEG signals and attaching device for holding the dry electrode
CN102184415A (zh) * 2011-05-17 2011-09-14 重庆大学 一种基于脑电信号的疲劳状态识别方法
DE212013000177U1 (de) 2012-08-03 2015-03-11 Bernhard Wandernoth Vorrichtung zum Messen bioelektrischer Signale, insbesondere Signale, die von Elektroden aufgenommenwerden
WO2014020554A1 (fr) 2012-08-03 2014-02-06 Bernhard Wandernoth Dispositif de mesure de signaux bioélectriques, en particulier de signaux captés par des électrodes
CH706802A1 (de) * 2012-08-03 2014-02-14 Dr Bernhard Wandernoth Vorrichtung zum Messen bioelektrischer Signale, insbesondere Signale, die von Elektroden aufgenommen werden.
CN104287727A (zh) * 2014-09-28 2015-01-21 青岛柏恩鸿泰电子科技有限公司 弹性干式软电极
CN104887222A (zh) * 2015-05-11 2015-09-09 重庆大学 可逆化脑电信号分析方法
US10514553B2 (en) 2015-06-30 2019-12-24 3M Innovative Properties Company Polarizing beam splitting system
US11061233B2 (en) 2015-06-30 2021-07-13 3M Innovative Properties Company Polarizing beam splitter and illuminator including same
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WO2017025553A1 (fr) * 2015-08-11 2017-02-16 Bioserenity Procede de mesure d'un parametre electrophysiologique au moyen d'un capteur electrode capacitive de capacite controlee
FR3039979A1 (fr) * 2015-08-11 2017-02-17 Bioserenity Procede de mesure d'un parametre electrophysiologique au moyen d'un capteur electrode capacitive de capacite controlee
WO2019042264A1 (fr) * 2017-08-26 2019-03-07 ZHONG, Daiyun Procédé et appareil de détection active de la fréquence d'activation neuronale au niveau d'un site fonctionnel dans un cerveau
CN110831491A (zh) * 2017-08-26 2020-02-21 李小平 主动感测大脑中功能部位处神经元放电频率的方法和装置

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