WO2024048413A1 - Dispositif de mesure d'ondes cérébrales - Google Patents

Dispositif de mesure d'ondes cérébrales Download PDF

Info

Publication number
WO2024048413A1
WO2024048413A1 PCT/JP2023/030501 JP2023030501W WO2024048413A1 WO 2024048413 A1 WO2024048413 A1 WO 2024048413A1 JP 2023030501 W JP2023030501 W JP 2023030501W WO 2024048413 A1 WO2024048413 A1 WO 2024048413A1
Authority
WO
WIPO (PCT)
Prior art keywords
frequency
connection interval
communication control
measurement
detection electrode
Prior art date
Application number
PCT/JP2023/030501
Other languages
English (en)
Japanese (ja)
Inventor
伸吾 岡嶋
Original Assignee
株式会社村田製作所
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by 株式会社村田製作所 filed Critical 株式会社村田製作所
Publication of WO2024048413A1 publication Critical patent/WO2024048413A1/fr

Links

Images

Classifications

    • 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
    • A61B5/30—Input circuits therefor
    • A61B5/307—Input circuits therefor specially adapted for particular uses
    • A61B5/31—Input circuits 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]

Definitions

  • the present invention relates to an electroencephalogram measuring device that transmits measurement results wirelessly.
  • Patent Document 1 describes a wearable electroencephalogram measuring device.
  • the electroencephalogram measurement device of Patent Document 1 includes an electroencephalogram electrode, an electric wiring section, an electroencephalogram measurement module, and a communication module.
  • the electroencephalogram electrode inputs the detected electroencephalogram signal to the electroencephalogram measurement module through the electrical wiring section.
  • the electroencephalogram measurement module measures electroencephalograms from electroencephalogram signals.
  • the communication module transmits the brain wave measurement results to the outside.
  • an object of the present invention is to suppress the influence of intermittent wireless communication on brain wave measurement results.
  • An electroencephalogram measuring device includes a detection electrode that detects brain waves using electrical signals, and a main body device that is connected to the detection electrode by a cable.
  • the main device includes a measurement unit that generates measurement data using electrical signals, and a communication control unit that wirelessly communicates measurement data at a predetermined connection interval frequency. Set the same as .
  • noise generated in intermittent communication is suppressed by the filter that suppresses noise at the frequency of the commercial power source included in the frequency band used for electroencephalogram measurement.
  • An electroencephalogram measuring device includes a detection electrode that detects brain waves using electrical signals, and a main body device that is connected to the detection electrode by a cable.
  • the main device includes a measurement unit that generates measurement data using electrical signals, and a communication control unit that wirelessly communicates measurement data at a predetermined connection interval frequency. Set the connection interval frequency to a different frequency. With this configuration, even if noise from intermittent communication (connection interval frequency) occurs, the effect on brain wave measurement is small.
  • An electroencephalogram measuring device includes a detection electrode that detects brain waves using electrical signals, and a main body device that is connected to the detection electrode by a cable.
  • the main device includes a measurement unit that generates measurement data using electrical signals, and a communication control unit that wirelessly communicates measurement data at a predetermined connection interval frequency. Set with . With this configuration, the accumulation of noise at connection interval frequencies due to multiple communications is suppressed, and the noise level at each connection interval frequency is suppressed.
  • An electroencephalogram measuring device includes a detection electrode that detects brain waves using electrical signals, and a main body device that is connected to the detection electrode by a cable.
  • the main device includes a measurement unit that generates measurement data using electrical signals, and a communication control unit that wirelessly communicates measurement data at a predetermined connection interval frequency. Set higher than the off frequency. In this configuration, noise at the intermittent communication frequency (connection interval frequency) is suppressed by the filter.
  • FIG. 1 is a functional block diagram of an electroencephalogram measuring device according to a first embodiment.
  • FIG. 2 is a time chart showing an example of a communication protocol executed by the electroencephalogram measuring device according to the first embodiment.
  • FIG. 3(A) is a graph showing an example of the frequency characteristics of the input signal to the main device when using the electroencephalogram measuring device of the first embodiment
  • FIG. 3(B) is a graph showing the input signal of the measuring section.
  • 2 is a graph showing an example of a frequency spectrum of .
  • FIG. 4 is a graph showing an example of the frequency characteristics of the input signal to the main device when the electroencephalogram measurement device of the second embodiment is used.
  • FIG. 1 is a functional block diagram of an electroencephalogram measuring device according to a first embodiment.
  • FIG. 2 is a time chart showing an example of a communication protocol executed by the electroencephalogram measuring device according to the first embodiment.
  • FIG. 3(A) is a graph showing an example of the frequency characteristics of
  • FIG. 5 is a time chart showing an example of a communication protocol executed by the electroencephalogram measuring device according to the third embodiment.
  • FIG. 6 is a graph showing an example of the frequency characteristics of the input signal to the main device when using the electroencephalogram measuring device of the third embodiment.
  • FIG. 7 is a graph showing an example of the frequency characteristics of the input signal to the main device when using the electroencephalogram measuring device of the fourth embodiment.
  • FIG. 1 is a functional block diagram of an electroencephalogram measuring device according to a first embodiment.
  • the electroencephalogram measuring device 10 includes a first detection electrode 21, a second detection electrode 22, a first cable 31, a second cable 32, and a main unit 40.
  • the main device 40 includes an AFE 41 , an ADC 42 , a measurement section 43 , a communication control section 44 , an antenna 45 , and a battery 49 .
  • the main device 40 has a casing made of resin, metal, or the like.
  • AFE 41, ADC 42, measurement section 43, communication control section 44, antenna 45, and battery 49 are housed in a housing.
  • the antenna 45 is housed in the housing so that communication with the outside is possible.
  • the casing is preferably of a size that allows it to be carried by the person whose brain waves are to be measured.
  • the AFE 41, ADC 42, measurement section 43, and communication control section 44 are realized by electronic components etc. mounted on a circuit board. That is, the AFE 41, ADC 42, measurement section 43, and communication control section 44 are realized by electronic circuits. The AFE 41, ADC 42, measurement section 43, and communication control section 44 are driven by receiving power from a battery 49.
  • the antenna 45 is a known antenna, and has a shape that can at least transmit radio waves with specifications (frequency, etc.) to be described later.
  • the battery 49 is a primary battery or a secondary battery, and may be detachable from the main device 40. Although it is possible to omit the battery 49 and replace it with a power supply unit connected to a commercial power source, the battery 49 is preferable. By using the battery 49, noise generated by the power supply unit can be prevented, and noise superimposed on electrical signals based on brain waves, which will be described later, can be suppressed.
  • the first detection electrode 21 is connected to the AFE 41 of the main device 40 through a first cable 31 .
  • the second detection electrode 22 is connected to the AFE 41 of the main device 40 through a second linear cable 32 .
  • the first detection electrode 21 and the second detection electrode 22 are attached to the skin of the subject's head in order to measure brain waves.
  • the first detection electrode 21 and the second detection electrode 22 detect brain waves as electrical signals and output them to the AFE 41 of the main device 40 through the first cable 31 .
  • the electrical signal is a signal that includes an electrical signal that reflects the brain waves of the subject and other electrical signals, and is an analog signal.
  • AFE41 is an analog front end circuit and includes an amplifier circuit and a filter. Note that the AFE 41 may include at least one of an amplifier circuit and a filter, but preferably includes both. AFE 41 amplifies and filters the electrical signal.
  • the filter is a low-pass filter, and suppresses noise that causes AD conversion errors in the subsequent ADC 42 and unnecessary high-frequency components during brain wave measurement.
  • the cutoff frequency of the filter is set between the upper end frequency of the frequency band of the brain wave measurement range and the frequency of the high frequency component to be suppressed.
  • the AFE 41 outputs the electrical signal after amplification processing and filter processing (for example, low-pass filter processing, etc.) to the ADC 42.
  • filter processing for example, low-pass filter processing, etc.
  • the ADC 42 is an AD conversion circuit (analog-digital conversion circuit), converts an analog electrical signal into a digital signal, and outputs the digital signal to the measurement section 43.
  • the measurement unit 43 generates measurement data using electrical signals based on brain waves converted into digital signals (hereinafter referred to as "brain wave signals"). For example, the measurement unit 43 performs Fourier transform on the brain wave signal to generate a frequency spectrum of the brain wave signal. The measurement unit 43 measures the desired level (magnitude) of the brain wave from the frequency spectrum of the brain wave signal. The measurement unit 43 generates measurement data (measurement results) using the brain wave level.
  • the measuring unit 43 measures the level of the ⁇ wave from the spectrum intensity from 2 Hz to 4 Hz.
  • the measurement unit 43 measures the level of the ⁇ wave from the spectrum intensity from 4 Hz to 8 Hz.
  • the measurement unit 43 measures the level of ⁇ waves from the spectrum intensity from 8 Hz to 13 Hz.
  • the measurement unit 43 measures the level of ⁇ waves from the spectrum intensity from 13 Hz to 30 Hz.
  • the measurement unit 43 measures the level of ⁇ waves from the spectral intensity from 30 Hz to 300 Hz.
  • the measurement unit 43 then generates measurement data using the levels of these various brain waves.
  • the measurement unit 43 outputs measurement data to the communication control unit 44.
  • the communication control unit 44 wirelessly communicates with an external device such as a PC through the antenna 45. At this time, the communication control unit 44 transmits the measurement data using a predetermined communication technology, such as Bluetooth (registered trademark) or BLE (Bluetooth Low Energy).
  • a predetermined communication technology such as Bluetooth (registered trademark) or BLE (Bluetooth Low Energy).
  • FIG. 2 is a time chart showing an example of a communication protocol executed by the electroencephalogram measuring device according to the first embodiment.
  • Figure 2 shows only data channels.
  • the external device When Bluetooth (registered trademark) shifts from the advertising channel to the data channel, the external device (master) transmits a packet to the electroencephalogram measuring device 10 (slave device) (Rx in FIG. 2), and the electroencephalogram measuring device 10 transmits a packet to the external device
  • a reply packet (a packet indicating continuation of wireless communication) is transmitted to (Tx in FIG. 2).
  • the communication control unit 44 of the electroencephalogram measuring device 10 transmits measurement data using the predetermined connection interval frequency fci.
  • the frequency of intermittent communication (connection interval frequency) fci may be superimposed on the frequency spectrum component of the brain wave signal, which results in noise (noise due to intermittent communication).
  • the first cables 31 and 32 are antennas that receive noise due to intermittent communication. It functions as. As a result, noise due to intermittent communication is likely to be superimposed on the brain wave signal.
  • the first cables 31 and 32 are provided with a noise shield mechanism, the superposition of noise due to intermittent communication can be suppressed.
  • the first cables 31 and 32 are provided with a noise shielding mechanism, the first cables 31 and 32 are difficult to bend and become heavy, which may impair usability and lead to an increase in cost.
  • the first cables 31 and 32 do not include a noise shielding mechanism. In this case, noise due to intermittent communication is likely to be superimposed on the electroencephalogram signal.
  • first cable 31 and the second cable 32 are connected to the casing of the main device 40, the casing of the main device 40 and the first cable 31 and the second cable 32 are necessarily close to each other. Placed. Therefore, noise due to intermittent communication is likely to be superimposed on the electrical signals transmitted through the first cable 31 and the second cable 32.
  • FIG. 3(A) is a graph showing an example of the frequency characteristics of the input signal to the main device 40 when using the electroencephalogram measurement device of the first embodiment
  • FIG. It is a graph showing an example of a frequency spectrum of a signal. Note that the frequency band ZF in FIGS. 3(A) and 3(B) is the frequency band of the brain wave measurement target.
  • the communication control unit 44 of the electroencephalogram measuring device 10 sets the connection interval frequency fci to be the same as the frequency fac of a commercial power source placed around the electroencephalogram measuring device 10 and used as a power source for electronic devices and the like. As a result, as shown in FIG. 3A, noise due to intermittent communication at the connection interval frequency fci overlaps with commercial power supply noise on the frequency axis.
  • the AFE 41 includes a commercial power supply noise suppression filter. Noise due to intermittent communication at the connection interval frequency fci and commercial power supply noise overlap on the frequency axis. Therefore, by matching the stopband of the suppression filter of the AFE 41 to the frequency of the commercial power supply noise, the suppression filter suppresses the commercial power supply noise as well as the noise due to intermittent communication at the connection interval frequency fci.
  • the measurement unit 43 can measure brain waves using the brain wave signal in which commercial power supply noise and noise due to intermittent communication at the connection interval frequency fci are suppressed. Thereby, the electroencephalogram measurement device 10 can suppress the influence of wireless communication on the electroencephalogram measurement results.
  • the electroencephalogram measuring device 10 when using the electroencephalogram measuring device 10 in a general environment (an environment that is different from an environment where there are no commercial power outlets, etc., or an environment where there is no other electronic equipment that uses commercial power), Power supply noise is unavoidable. Therefore, it is preferable that the electroencephalogram measurement device 10 includes a filter that suppresses commercial power supply noise.
  • an electroencephalogram measuring device 10 designed to be used in a general environment is equipped with a commercial power supply noise suppression filter.
  • the electroencephalogram measuring device 10 intended for use in a general environment can suppress noise at the connection interval frequency fci without the need to newly provide a filter for suppressing noise at the connection interval frequency fci.
  • connection interval frequency fci is the same as the frequency fac of the commercial power supply
  • the connection interval frequency fci includes complete coincidence, and within the range where the noise due to intermittent communication of the connection interval frequency fci can be suppressed by the commercial power supply noise suppression filter. Including different ranges.
  • a mode has been shown in which the AFE 41 is provided with a commercial power supply noise suppression filter, but a commercial power supply noise suppression filter may be provided at a stage prior to the measurement of brain waves in the measurement unit 43.
  • the electroencephalogram measuring device according to the second embodiment differs from the electroencephalogram measuring device 10 according to the first embodiment in that the measurement unit 43 sets a frequency band used for measurement, and the communication control unit 44 sets a connection. Different interval frequencies.
  • the other configurations of the electroencephalogram measuring device according to the second embodiment are the same as those of the electroencephalogram measuring device 10 according to the first embodiment, and a description of the similar parts will be omitted.
  • FIG. 4 is a graph showing an example of the frequency characteristics of the input signal to the main device 40 when the electroencephalogram measurement device of the second embodiment is used.
  • the measurement unit 43 sets a first frequency band ZF1 and a second frequency band ZF2 as frequency bands used for electroencephalogram measurement.
  • the first frequency band ZF1 is set to a lower frequency band than the second frequency band ZF2.
  • the upper end frequency f1u of the first frequency band ZF1 and the lower end frequency f2d of the second frequency band ZF2 are separated by a predetermined frequency.
  • the communication control unit 44 sets the connection interval frequency fci between the upper end frequency f1u of the first frequency band ZF1 and the lower end frequency f2d of the second frequency band ZF2. As a result, as shown in FIG. 4, noise due to intermittent communication at the connection interval frequency fci is not included in the first frequency band ZF1 and the second frequency band ZF2.
  • the measurement unit 43 can measure brain waves excluding the portion of the brain wave signal that is affected by noise due to intermittent communication at the connection interval frequency fci. Thereby, the electroencephalogram measuring device can suppress the influence of wireless communication on the electroencephalogram measurement results.
  • the communication control unit 44 sets the upper end frequency f1u of the first frequency band ZF1 lower than 133 Hz, and sets the lower end frequency f2d of the second frequency band ZF2 higher than 133 Hz.
  • the connection interval frequency fci can be set to 133 Hz. Therefore, the electroencephalogram measuring device can suppress the influence of wireless communication on the electroencephalogram measurement results without changing the general Bluetooth (registered trademark) connection interval frequency.
  • An electroencephalogram measuring device according to a third embodiment of the present invention will be described with reference to the drawings.
  • the electroencephalogram measuring device according to the third embodiment differs from the electroencephalogram measuring device 10 according to the first embodiment in the connection interval frequency set by the communication control unit 44.
  • the other configuration of the electroencephalogram measuring device according to the third embodiment is the same as that of the electroencephalogram measuring device 10 according to the first embodiment, and the explanation of the similar parts will be omitted.
  • FIG. 5 is a time chart showing an example of a communication protocol executed by the electroencephalogram measuring device according to the third embodiment.
  • Figure 5 shows only data channels.
  • FIG. 6 is a graph showing an example of the frequency characteristics of the input signal to the main device 40 when using the electroencephalogram measurement device of the third embodiment.
  • the communication control unit 44 sets the connection interval cycle to multiple types of cycles Tci1, Tci2, and Tci3. Note that although this embodiment has shown a mode in which the connection interval period is set to three types, the number of types is not limited to this.
  • the communication control unit 44 performs wireless communication using multiple types of connection interval frequencies fci1, fci2, and fci3.
  • the communication control unit 44 performs wireless communication at the connection interval frequency fci2 in the next packet after the packet that wirelessly communicated at the connection interval frequency fci1.
  • the communication control unit 44 performs wireless communication at the connection interval frequency fci3 in the next packet after the packet wirelessly communicated at the connection interval frequency fci2.
  • the communication control unit 44 performs wireless communication at the connection interval frequency fci1 in the next packet after the packet wirelessly communicated at the connection interval frequency fci3. That is, the communication control unit 44 performs wireless communication while sequentially selecting and repeating a plurality of types of connection interval frequencies fci1, fci2, and fci3.
  • the noise level (solid line in FIG. 6) due to intermittent communication at each of the connection interval frequencies fci1, fci2, and fci3 is reduced by using one type of connection interval frequency.
  • the level of noise due to intermittent communication (dotted line in FIG. 6) is lower than that in the case of the above case.
  • the electroencephalogram measuring device can suppress the influence of wireless communication on the brain wave measurement results.
  • the settings of the plurality of types of connection interval frequencies fci1, fci2, and fci3 are preferably in a predetermined order that is shared between the electroencephalogram measurement device and the external device. However, it may be random as long as the electroencephalogram measurement device and the external device perform processing that allows the next connection interval frequency to be shared (for example, the packet currently being transmitted includes information about the next connection interval frequency).
  • An electroencephalogram measuring device according to a fourth embodiment of the present invention will be described with reference to the drawings.
  • the electroencephalogram measuring device according to the fourth embodiment differs from the electroencephalogram measuring device 10 according to the first embodiment in the connection interval frequency set by the communication control unit 44.
  • the other configuration of the electroencephalogram measuring device according to the fourth embodiment is the same as that of the electroencephalogram measuring device 10 according to the first embodiment, and the explanation of the similar parts will be omitted.
  • FIG. 7 is a graph showing an example of the frequency characteristics of the input signal to the main device 40 when the electroencephalogram measurement device of the fourth embodiment is used.
  • the communication control unit 44 sets the connection interval frequency fci higher than the upper end frequency fcf of the electroencephalogram measurement frequency band ZF of the measurement unit 43. As a result, as shown in FIG. 7, noise caused by intermittent communication at the connection interval frequency fci does not fall into the brain wave measurement frequency band ZF. Thereby, the electroencephalogram measuring device can suppress the influence of wireless communication on the electroencephalogram measurement results.
  • EEG measuring device 21 First detection electrode 22: Second detection electrode 31: First cable 32: Second cable 40: Main unit 41: AFE 42: ADC 43: Measuring unit 44: Communication control unit 45: Antenna 49: Battery

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Medical Informatics (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Physics & Mathematics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Psychiatry (AREA)
  • Psychology (AREA)
  • Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)

Abstract

L'invention concerne un dispositif de mesure d'onde cérébrale comprenant : une première électrode de détection et une deuxième électrode de détection qui détectent des ondes cérébrales en tant que signaux électriques ; et un dispositif de corps qui est connecté à la première électrode de détection et à la deuxième électrode de détection respectivement par le biais d'un premier câble et d'un deuxième câble. Le dispositif de corps comprend : une unité de mesure qui génère des données de mesure en utilisant des signaux électriques ; et une unité de commande de communication qui communique sans fil un résultat de mesure en utilisant une fréquence d'intervalle de connexion prescrite fci. L'unité de commande de communication règle la fréquence d'intervalle de connexion fci égale à une fréquence d'alimentation électrique commerciale fac.
PCT/JP2023/030501 2022-08-29 2023-08-24 Dispositif de mesure d'ondes cérébrales WO2024048413A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2022136248 2022-08-29
JP2022-136248 2022-08-29

Publications (1)

Publication Number Publication Date
WO2024048413A1 true WO2024048413A1 (fr) 2024-03-07

Family

ID=90099740

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/JP2023/030501 WO2024048413A1 (fr) 2022-08-29 2023-08-24 Dispositif de mesure d'ondes cérébrales

Country Status (1)

Country Link
WO (1) WO2024048413A1 (fr)

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2015208011A (ja) * 2015-05-22 2015-11-19 株式会社東芝 無線通信装置および制御方法
US20170127966A1 (en) * 2015-11-10 2017-05-11 Hong Yue Technology Corporation Electrode device for wearable or handheld apparatus
US20180116513A1 (en) * 2015-05-12 2018-05-03 Monitra Healthcare Private Limited Wire-free monitoring device for acquiring, processing and transmitting physiological signals
JP2020018693A (ja) * 2018-08-02 2020-02-06 パナソニックＩｐマネジメント株式会社 アクティブ電極、脳波計、制御装置、及び、制御方法

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20180116513A1 (en) * 2015-05-12 2018-05-03 Monitra Healthcare Private Limited Wire-free monitoring device for acquiring, processing and transmitting physiological signals
JP2015208011A (ja) * 2015-05-22 2015-11-19 株式会社東芝 無線通信装置および制御方法
US20170127966A1 (en) * 2015-11-10 2017-05-11 Hong Yue Technology Corporation Electrode device for wearable or handheld apparatus
JP2020018693A (ja) * 2018-08-02 2020-02-06 パナソニックＩｐマネジメント株式会社 アクティブ電極、脳波計、制御装置、及び、制御方法

Similar Documents

Publication Publication Date Title
US11828833B2 (en) Systems and methods for object detection by radio frequency systems
Piipponen et al. A biosignal instrumentation system using capacitive coupling for power and signal isolation
US8428701B2 (en) Electrode device and electrocardiographic measurement device
JP5129736B2 (ja) 耐磁場性増幅器および同左を使用する無線トランシーバ
KR101651537B1 (ko) 무선 통신을 이용한 심전도 측정 장치 및 방법
KR102153448B1 (ko) 광대역 무손실 부분방전 검출 및 노이즈 제거 장치
JP2014082735A (ja) 通信機器及び電子機器
WO2024048413A1 (fr) Dispositif de mesure d'ondes cérébrales
CN111263275A (zh) 具有集成磁感应线圈和rf天线的听力设备
WO2006091123A1 (fr) Radiothermotomographe a hyperfrequences
CN104269605A (zh) 一种电子设备
US20230314496A1 (en) Broadband lossless partial discharge detection and noise removal device
CN102955086A (zh) 一种波导转换开关屏蔽效能测试方法
Chen et al. A 90-μW penny-sized 1.2-gram wireless EEG recorder with 12-channel FDMA transmitter for month-long continuous mental health monitoring
US10395635B2 (en) Reducing radio frequency susceptibility in headsets
US20220031478A1 (en) Emg-amplifier unit
Helbig et al. Development and test of a massive MIMO system for fast medical UWB imaging
JP2019522204A (ja) センサをスマートデバイスに接続する総合システム
US11714115B2 (en) Instrument interfacing method and device thereof
TWI761746B (zh) 天線系統及其電子裝置
CN212909544U (zh) 一种多通道高隔离射频源设备
CN210899089U (zh) 多通道音频放大电路
ITVI990138A1 (it) Antenna multifunzione per autoveicoli
KR101801082B1 (ko) 노이즈 제거 기능을 구비한 액티브 부분방전 신호 검출 센서 장치
US10105071B2 (en) Method and device for acquiring ECG data and ECG detection system

Legal Events

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

Ref document number: 23860176

Country of ref document: EP

Kind code of ref document: A1