• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    In one aspect, the present disclosure relates to a portable device (10) for acquiring electroencephalographic (EEG) signals transmitted by a user. The portable device comprises a flexible support (11) for marrying a localized region of the user's skull and a set of sensors (13) of electrical signals generated by the neuronal activity of the user, arranged on said support (11). ) so as to form contacts with the scalp when the device is worn by the user. For each sensor, an electronic circuit for filtering and amplifying the electrical signals detected by said sensor is integrated in the flexible support (11) and forms with said sensor an active electrode. The portable device further comprises a housing (12) comprising an electronic signal processing chain from said electronic filtering and amplifying circuits, said housing being mechanically connected to the flexible support to form, with said support, an attachment means to a garment or accessory (101) to be worn by the user.
    公开号:FR3077723A1
    申请号:FR1851287
    申请日:2018-02-15
    公开日:2019-08-16
    发明作者:Sid Kouider；Hao Zhang；Antoine Goupille；Jeanne Vicerial；Guillaume Ployart；Arthur Biancarelli；Gaelle Gervais
    申请人:Ecole Des Hautes Etudes En Sciences Sociales；Ecole Nat Superieure Des Arts Decoratifs；Centre National de la Recherche Scientifique CNRS；Paris Sciences et Lettres Quartier Latin；Ecole Normale Superieure de Paris；
    IPC主号:
    专利说明:

    Technical field of the invention
    The present invention relates to portable devices for the acquisition of electroencephalographic (EEG) or portable surface electroencephalograph signals, as well as methods of acquisition of electroencephalographic signals using these electroencephalographs.
    State of the art
    Surface electroencephalography is used to measure variations in diffuse electrical potentials on the surface of the skull. These variations in electrical potentials are commonly called electroencephalographic signals or EEG signals.
    A first difficulty relates to the reliability of the devices making it possible to capture the EEG signals. In fact, given the very small amplitude of the variations in electrical potentials to be measured (of the order of a few microvolts), it is necessary to ensure maximum conductivity between the electrode and the scalp in order to obtain an EEG signal. exploitable, and therefore perfect contact, which can be difficult due in particular to the user's hair.
    Several technical solutions are used today in current devices to meet the constraint of signal reliability.
    Some surface electroencephalographs are equipped with gel electrodes, in which contact is made by means of a gel or a conductive liquid, which easily penetrates through the user's hair to reach the scalp. . The gel reduces the electrical impedance and thus the interference with surrounding signals. This solution provides good conductivity at any point on the scalp. However, this type of device requires technical assistance for the installation of the electrodes. In particular, this solution is time consuming (the gel is placed and the conductance checked on each electrode one by one). In addition, it limits the duration of use of the device to a few hours (the gel dries, contact is no longer ensured).
    More recently, we have seen the development of surface electroencephalographs equipped with so-called "active" dry electrodes. Such electrodes are for example described in the patent application published US 20133066183. The active dry electrodes have the function of capturing the variations of electric potentials on the surface of the scalp, of filtering and amplifying them. The analog signals thus obtained are then converted into digital signals by means of one or more analog to digital converters controlled by a microcontroller. This receives the data to analyze it, to store it or to transmit it to another device.
    In active dry electrodes, contact with the scalp is made by means of solid conductive elements or "sensors" connected to an electronic circuit making it possible to compensate for the increase in impedance due to the absence of gel. The active electronic component ensures signal capture comparable to that of a gel electrode. An additional advantage of the active electrode is that it makes it possible to filter and / or amplify the signals, and thus to improve the signal to noise ratio. However, the main difficulty with this technique is access to the scalp.
    Current solutions generally use polymer-based and pimple sensors by exerting significant pressure to reach the user's scalp (see for example the published patent application US 2015141788. If this approach can allow good contact with the scalp , it has the major disadvantage of being very uncomfortable, especially for prolonged use.
    Another difficulty in the design of surface electroencephalographs concerns the acceptability of the EEG to the general public, which imposes aesthetic constraints, comfort and ease of use.
    In fact, systems intended for the medical or research field generally comprise a cap, made of elastic or waterproof fabric, with locations intended to accommodate the sensors, the electronic circuits connected to the sensors and the acquisition chain box. They are thus formed of three distinct elements that the operator / operator must assemble for each use.
    Portable devices for acquiring EEG signals have been proposed which allow a user to dispense with the assistance of a specialized technician. Patent application US 2002/0029005, for example, describes a headgear for the acquisition of EEG signals with predetermined locations for the electrodes and adjustable elastic bands enabling contact of the electrodes against the scalp. However, such a device remains complex in its use because of the large number of separate and adjustable parts.
    The patent application US 2017/0027466 also describes a portable device for the acquisition of EEG signals usable without assistance, and in which the number of removable and adjustable mechanical parts is reduced, allowing a simpler and faster use for an inexperienced user. . To do this, the EEG signal acquisition device comprises a central part intended to be positioned on the top of the head and able to house all of the electronic components. From the central part extend around the head long and short arms at the end of which are positioned sensors. At least some of these arms are elastic or have spring functions which allow the gripping of the head by adapting to its contour, with sufficient force to ensure the necessary contact of the sensors with the scalp. In addition to the lack of discretion of such a device, it has the disadvantage of being very uncomfortable since, except for maintaining a straight head position vertically, the gripping force passes exclusively through the sensors, which and generates very localized high pressure points.
    The devices described, even if they make it possible to dispense with the technical support of an operator and propose solutions making it possible to ensure satisfactory contact with the scalp of the user, lack the necessary discretion, in particular for large applications. audience, such as video games, training, sleep aid, etc.
    The present description proposes portable surface electroencephalographs equipped with active dry electrodes which offer, in addition to excellent signal quality, great ease of use, comfort for the user and great discretion. Such portable surface electroencephalographs may be used in hospitals, for example on an outpatient basis in the context of clinical diagnosis, but also allow the emergence of new fields of application for electroencephalography.
    ABSTRACT
    According to a first aspect, the present description relates to a portable device for the acquisition of electroencephalographic (EEG) signals emitted by a user, the device comprising:
    - a flexible support intended to marry a localized region of the user's skull;
    - a set of sensors for the detection of electrical signals generated by the neural activity of the user, arranged on said support so as to form contacts with the scalp when the device is worn by the user;
    - for each sensor, an electronic circuit for filtering and amplifying the electrical signals detected by said sensor, said electronic circuit being integrated in the flexible support and forming with said sensor an active electrode;
    a housing comprising an electronic chain for processing the signals from said electronic filtering and amplification circuits, said housing being mechanically connected to the flexible support to form, with said support, a means of attachment to a garment or accessory intended to be worn by the user.
    In the device thus described, the electronic components ensuring the various electronic functions are distributed between the flexible support and the housing, the latter cooperating mechanically to form a means of attachment to a garment or accessory. This allows both to make the support intended to be in contact with the skull of the user more flexible and thinner, typically less than 10 mm thick, or even less than 5 mm thick, and to make the device extremely easy to use, without losing quality in EEG signals acquired. The portable device thus described therefore has performances at least comparable to those of state-of-the-art devices, but also ease of use and ergonomics compatible with consumer applications.
    The portable device applies to humans but can also be applied to certain animals, the device, non-invasive, having qualities of precision and comfort suitable for use in animal research.
    The number of sensors arranged on the flexible support depends on the application. This number can for example be between 2 and 128, or even more. Depending on the application envisaged, the support can either cover a limited area of the skull to measure the cerebral activity generated by a specific area of the brain, for example the visual, auditory, motor, somatosensory, or prefrontal cortex, or extend over the entire surface of the skull. The number of sensors can be determined according to the surface covered by the support and the desired spatial resolution.
    According to one or more exemplary embodiments, the flexible support and the housing are mechanically connected by an attachment point, for example an off-center attachment point to form, between the housing and the support, a gap allowing a garment to pass through. and / or an accessory. Advantageously, said gap is between 2 mm and 5 mm.
    According to one or more exemplary embodiments, the attachment point is flexible, making it possible to form an attachment means in the form of a "clip" or clamp.
    According to one or more exemplary embodiments, the attachment point also allows electrical contact between the electronic components housed in the flexible support and those housed in the housing.
    According to one or more exemplary embodiments, the attachment point is detachable.
    According to one or more exemplary embodiments, the electronic signal processing chain housed in the rigid housing comprises one or more analog / digital converters (ADC) intended to transform the signals coming from the electronic filtering and amplification circuits into digital signals and a microcontroller, in particular for transmission to an external processing unit and / or storage of said digital signals. The rigid housing can of course house other electronic elements, for example a battery, and / or other types of sensors, for example an accelerometer and / or a gyroscope.
    According to one or more exemplary embodiments, the flexible support is perforated; for example, the flexible support comprises a plurality of branches on which are arranged at least a portion of said sensors. This structure gives greater flexibility to the support and allows better adaptation to the shape of the skull.
    For example, the sensors are distributed over 2 to 6 branches.
    According to one or more exemplary embodiments, the branches are parallel, which makes it possible to apply a more uniform pressure on the sensors even when the garment or utensil does not cover the entire support, and makes it easier to understand the movement of translation that 'a user can do to set up the device.
    According to one or more exemplary embodiments, 2 or more branches can be connected to a central part, by means of flexible lateral branches.
    According to one or more exemplary embodiments, 3 or more branches can be arranged in parallel in the form of a comb.
    According to one or more exemplary embodiments, each sensor is mounted mobile on said flexible support, for example by means of a mechanical connection of the spring type, which makes it possible to improve contact with the scalp.
    According to one or more exemplary embodiments, the mechanical connection of the spring type comprises a leaf spring forming a point contact with a base of said sensor, allowing mobility of the sensor along several axes.
    According to one or more exemplary embodiments, said leaf spring ensures electrical contact of said sensor with said filtering and amplification circuit.
    According to one or more exemplary embodiments, each sensor comprises a base intended to be arranged in a housing of the flexible support, in electrical contact with said filtering and amplification circuit.
    According to one or more exemplary embodiments, each sensor comprises a plurality of conductive strips, arranged on said base, said conductive strips being intended to form linear contacts with the scalp when the device is worn by the user.
    Such a linear contact makes it possible to have a larger contact surface and therefore better sensitivity and better comfort for the user.
    According to one or more exemplary embodiments, the conductive strips are arranged in a substantially parallel manner. When at least part of the sensors are arranged on parallel branches of the support, the conductive strips are advantageously parallel to said branches.
    According to one or more exemplary embodiments, each sensor comprises two conductive strips. The number of two conductive strips is a good compromise since it allows the contact pressure to be distributed while maintaining good measurement accuracy.
    According to one or more exemplary embodiments, the edge-to-edge spacing between said two conductive strips is greater than 2 mm, in order to allow the hair to pass. Advantageously, said spacing is less than 50 mm, advantageously less than 10 mm so as not to lose precision. For example, said spacing is between 2 mm and 6 mm.
    According to one or more exemplary embodiments, the conductive strips include a conductive polymer coating forming a conductive layer intended to come into contact with the user's scalp.
    According to one or more exemplary embodiments, the conductive strips have at least one point (conductive or not) intended to come into contact first with the scalp when the support is positioned on the skull. This point has the effect of spreading the hair when the device is put in place, so as to expose the user's scalp to the conductive strips.
    According to a second aspect, the present description relates to a garment or accessory connected for the acquisition of electroencephalographic (EEG) signals comprising a portable device according to the first aspect.
    This garment or accessory can for example be a headband, a head covering, a helmet, etc.
    According to a third aspect, the present description relates to a method of acquiring electroencephalographic (EEG) signals transmitted by a user by means of a portable device according to the first aspect, comprising:
    - the measurement of electrical signals generated by the user's neural activity by means of said sensors in contact with the user's scalp;
    - the processing of electrical signals from said filtering and amplification circuits by means of the electronic processing chain arranged in said housing.
    According to one or more exemplary embodiments, said processing of the electrical signals comprises the analog / digital conversion of the electrical signals from said filtering and amplification circuits and the transmission of said digital signals to an external processing unit and / or the storage of said signals digital.
    BRIEF DESCRIPTION OF THE FIGURES
    Other advantages and characteristics of the invention will appear on reading the description, illustrated by the following figures which represent:
    - FIGS. 1A - 1E, different views of a first example of a portable device for the acquisition of EEG signals according to the present description;
    - FIGS. 2A-2C, different views of a second example of a portable device for the acquisition of EEG signals according to the present description;
    - FIGS. 3A and 3B, different views of a third example of a portable device for the acquisition of EEG signals according to the present description;
    - FIG. 4, an example of an electronic architecture for the reception and processing of EEG signals by means of a portable device according to this description;
    - FIGS. 5A, 5B, exemplary embodiments of a sensor according to this description and FIG. 5C, another example of a sensor according to the present description;
    - FIG. 6, an exemplary embodiment of a sensor mounted mobile on the flexible support.
    DETAILED DESCRIPTION
    FIGS. 1A - 1D respectively represent a front view, a first side view, a back view and a second side view of a first example of a portable device 10 for the acquisition of EEG signals according to the present description, while that FIG. 1E illustrates a view of the device worn by a user.
    The portable device as illustrated in FIGS. IA to 1D comprises a flexible support 11 intended to match a localized region of the skull of a user, for example the occipital region at the back of the skull, and a housing 12 mechanically and electronically connected to the flexible support 11. On the support, are arranged a set of sensors 13 for the detection of electrical signals generated by the neural activity of the user. An additional electrode 13b known as grounding or “bias” is provided to suppress the common mode of the signals measured by the other sensors. As will be described in more detail below, each sensor may comprise a plurality of conductive lamellae (in this example two conductive lamellae 131, 132), for example arranged in a substantially parallel manner, so as to form linear contacts with the scalp when the device is worn by the user; these conductive strips can also be deformable by pressure on the user's scalp. Each sensor forms with an electronic circuit for filtering and amplifying the electrical signals (not shown in FIGS. IA - 1D) an active electrode. The signals from the electronic filtering and amplification circuits are processed by an electronic chain comprising, for example, as will be described below, one or more analog / digital converters (ADC) and a microcontroller allowing in particular the storage and / or the transmission to the outside of the device of the processed signals. The electronic chain is integrated in the housing 12 while the electronic filtering and amplification circuits of the active electrodes are integrated in the flexible support. The separation of the electronic components respectively in the support on which the sensors are arranged and in the housing allows greater design flexibility of the support 11, in particular in terms of shape, fineness and mechanical flexibility. Thus, for example, the thickness Xs of the flexible support can advantageously be less than 10 mm, for example between 2 mm and 10 mm, and can advantageously be less than 5 mm, for example between 2 mm and 5 mm. The housing can of course house other electronic elements necessary for the operation of the device, for example a battery and / or other types of sensors, for example an accelerometer and / or a gyroscope. In the example of FIGS IA - 1D, the box 12 is moreover equipped with an on / off switch 122 and with a connection port 123, for example a USB port.
    Furthermore, as illustrated in FIGS 1A - 1E, the support 11 and the housing 12 cooperate to form a means of attachment to a garment or accessory intended to be worn by the user. Thus in this example, the case 12 is connected to the support 11 by an off-center attachment point 121 to form, between the case and the support, a gap allowing a garment and / or an accessory to pass, typically a gap of a few millimeters, for example between 2 mm and 5 mm. In this example, the attachment point is flexible so as to form a clamp or "clip", through which the garment or an accessory can be passed, for example a headband 101 as illustrated in FIG. 1E. The elastic band can then be used to press the flexible support against the skull 100 of the user. The attachment point 121 also forms an electrical connection between the filtering and amplification circuits of the active electrodes and the electronic chain of the housing. For example, the attachment point includes a sleeve inside which electrical connections can pass. The attachment point can also be detachable.
    Advantageously, the shape of the support is designed so as to guarantee an equitable distribution of the pressure between the different sensors when the device is worn by the user. In the example of FIGS 1A - 1D, the flexible support 11 is perforated, and comprises external branches 111, 112 connected to a central part 110 by means of lateral branches 113, 114 which confer flexibility to the assembly. The sensors are arranged on the outer branches and the central part. In this example, the central part 110 is substantially round and is superimposed on the housing, the round shape of the housing facilitating gripping with the hand.
    In the example of FIGS IA to 1E, two outer branches are shown, arranged laterally to, with the central part, allow a distribution of the sensors on the area of interest of the skull. Depending on requirements, other branches supporting sensors could be provided; for example a third and fourth branch for positioning sensors on the lateral parts of the skull.
    Of course, other shapes are possible for the flexible support 11, in particular perforated shapes.
    Thus, FIGS. 2 A - 2C illustrate a second example of a portable device 20 for the acquisition of EEG signals according to the present description.
    FIGS. 2A and 2B respectively illustrate a front view and a side view, while FIG. 2C shows the device 20 worn by a user by means of a strip 101. The portable device comprises a flexible support 21 intended to fit a localized region of the skull of a user and a rigid case 22 mechanically and electronically connected to the flexible support 11 The flexible support 21 is intended to support, as in the previous example, sensors 13, each sensor forming, with a filtering and amplification circuit (not shown) an active electrode.
    In this example, the support 21 is also perforated to allow better flexibility. It includes in this example a given number of branches 211 - 215 all arranged in parallel and on which the sensors 13 are arranged. Although a grounding electrode is not shown in these figures, it can of course be provided, as in the previous example. In this example again, the branches 211 - 215 which carry the sensors are connected by lateral branches 216-217 which give flexibility to the assembly.
    In this example, the housing 22 and the support 21 to which it is connected by an attachment point 221, cooperate to form, as in the previous example, a means of attachment to a garment or accessory. Thus, as illustrated in FIG. 3C, a strip 101 can be inserted into the gap formed between the support 21 and the housing 22 to hold the device 20 against the skull 100 of the user.
    FIGS. 3 A - 3B illustrate a third example of a portable device 30 for the acquisition of EEG signals according to the present description.
    In this example again, the portable device 30 comprises a flexible support 31 and a housing 32 mechanically connected to form a means of attachment to a garment or utensil. Furthermore, the support 31 and the housing 32 are electrically connected. The support 31 is, in this example, perforated so as to form a central part 310 and a set of external branches 311 - 314 connected to the central part by lateral branches 315 - 318 which make it possible to confer flexibility on the support. In this example as in that of FIGS. IA - 1E, the central part 310 of the support is substantially round and its shape is superimposed on that of the housing 32 to allow better grip by a user. A set of sensors 13 are arranged on the central part and on the external branches of the support 31, as well as a grounding electrode 13b.
    In the examples illustrated in the preceding figures, in particular FIGS. 1E, 2C, 3B, the portable device (respectively 10, 20 and 30) is applied against the skull of the user by means of a strip 101. It is easily understood that the attachment means formed by the housing and the support can be applied to any other type of clothing or accessory, for example a cap or any type of headgear, for example with an elastic band intended to pass between the support and the case, a headset (for wearing on the top of the skull), a virtual or augmented reality helmet, a site helmet, a bicycle helmet, a surgeon's cap, a protective mask etc. The attachment means formed from the support and the housing can be adapted to the type of garment or accessory to which it is intended to be attached. Any type of device, Velcro tab, press button, mechanical or magnetic attachment can be provided to facilitate the maintenance of the garment or accessory in the attachment means formed by the flexible support and the case.
    In practice, we can come "clip" the portable device on the garment or accessory, before it is worn by the user, or on the contrary, we can come "clip" the portable device on the garment or the 'accessory once the latter positioned on the head of the user.
    As illustrated in the preceding figures, the conductive strips can advantageously all be substantially parallel, which makes it possible to position the support on the skull by a movement of translation parallel to the direction of the conductive strips, for example from the top of the head downwards of the head when it is a device intended to be worn in an occipital region of the skull. For reasons of comfort and quality of contact, in fact, the translational movement preferably follows the direction and direction of the implantation of the hair.
    The different branches of the supports which support the sensors can also be substantially parallel, and parallel to the direction of the conductive strips, as appears for example in FIGS. 1A - 1E and 2A - 2C. This has aesthetic, mechanical and ergonomic effects. Indeed, the parallel branches make it possible to correctly apply the pressure at the level of the sensors with a strip which does not entirely cover the support. Thus, the strip presses on the parallel branches and plates the electrodes at the ends. The branches thus arranged parallel to the conductive strips make it possible to minimize the visible part of the support when it is worn and facilitate the understanding of the movement of translation necessary for the installation of the device.
    FIG. 4 illustrates an example of an electronic architecture for the reception and processing of EEG signals by means of a portable device according to this description.
    As described above, the portable device according to the present description comprises a given number of active electrodes 41, for example between 2 and 128, advantageously between 2 and 64, advantageously between 4 and 16. Each active electrode 41 comprises a sensor 411 for the detection of the electrical signals generated by the neural activity of the user 100 and an electronic filtering and amplification circuit 412. For example, each electronic circuit 412 comprises a first-order high-pass analog filter, an amplifier and a filter first order analog low pass. Filters are used to remove signals received from frequency components that are unnecessary for the intended application. Amplification makes it possible to adapt the amplitude of the signals to the characteristics of the ADC and obtain maximum resolution during the conversion. As illustrated in FIG. 4, the portable device also comprises one or more reference electrodes 41r and a so-called “bias” or grounding electrode 41b. The active electrodes are connected to one or more analog-digital converters 42 (ADC), each ADC being able to convert the signals of a given number of active electrodes, for example between 1 and 128. The reference electrode is connected to all converters. The reference electrode (s) are preferably positioned in contact with the user's head in a region remote from that of the other active electrodes; for example, they can be connected using a connection port such as port 123 shown in FIG. IC and placed in contact with the ear, or held by the garment or accessory to which the portable device is attached. The converters 42 are controlled by a microcontroller 43 and communicate with it, for example by the SPI (“Serial Peripheral Interface”) protocol. The microprocessor encapsulates the data received and then transmits it to an external processing unit 44, for example a computer, a mobile phone, a virtual reality headset, an automotive or aeronautical computer system, for example of the on-board computer type of car or airplane, for example by Bluetooth, Wi-Fi (“Wireless Fidelity”) or Li-Fi (“Light Fidelity”) technology. All the components of the acquisition chain are powered by a battery (not shown in FIG. 4) housed in the housing.
    According to an operating mode of the portable device according to the present description, each active electrode measures a value of electric potential from which the potential measured by the reference electrode is subtracted (Ei = Vi - V re f), and it is the result of this difference which is digitized by means of the CAN 42 then transmitted by the microcontroller 43. To do this, as illustrated in FIG. 4, the device comprises a given number of active measurement electrodes, for example between 2 and 64, advantageously between 4 and 16 one or two active reference electrodes 41r and the additional grounding contact 41b (bias electrode ").
    FIGS 5A and 5B illustrate two views of an example of a sensor according to this description.
    In this example, the sensor 50 comprises a base 51 intended to be housed in a location of the flexible support (not shown) by means of a fixing device 52, and several conductive strips 53, 54. The conductive strips form a linear contact with the scalp when the device is worn by the user. Linear contact has the advantage of forming a fairly large contact surface with the scalp, allowing better sensitivity in receiving signals and better comfort for the user. Furthermore, when the conductive lamellae are arranged in a substantially parallel fashion, the linear contacts thus formed are compatible with a translational movement which spreads the hair when the device is put in place.
    The applicants have shown that the number of 2 conductive strips is optimal. With a single strip per sensor, there may be instability in the contact formed by the strip on the scalp and the distribution of pressure on a single strip can be uncomfortable for the user. The applicants have shown that 2 lamellae are adapted to cover a sufficiently small area of the skull and thus have good signal precision. The spacing between the slats responds to a compromise between the need to be able to let the hair pass, the measurement of the signal and the distribution of the pressure for the comfort of the user. Advantageously, the two strips are sufficiently spaced to be able to let the hair pass. For example, the edge-to-edge distance Xl between the two strips is greater than 2 mm. The maximum distance between the slats depends on the total surface that you want to cover and the number of sensors. But in order not to lose precision, it is preferable to have a distance of less than 50 mm, advantageously less than 10 mm. For example, the distance X1 is between 2 and 6 mm.
    In the example of FIGS 5A and 5B, the sensor 50 comprises a metallic structure 510 integrated into a plastic part 520. The metallic structure forms at the level of the base 51 a contact 511 which will ensure the passage of current with the circuit filtering and amplification and at each lamella 53, 54, an electrical contact area 512 with the scalp.
    At the level of contact with the scalp, the metal can be treated (silver plating / silver chloride for example).
    In the example shown that FIGS. 5A, 5B, the lamella at the level of the area of contact with the scalp is slightly concave, which makes it possible to marry the shape of the skull more naturally.
    As illustrated in FIGS 5A, 5B, the strips may have one or two points (541, 542 in FIG. 5B), one on each side of the sensor to keep the symmetry and allow the pivot of the sensor relative to the support. The tip on the bottom side of the sensor also serves to facilitate penetration of the sensor into the hair to reach the scalp. The tips are not necessarily conductive.
    As illustrated in FIGS 5A, 5B, the strips can be full, which gives them better rigidity.
    FIG. 5C shows another embodiment of a sensor according to the present description. In this example, a conductive polymer, for example of the PEDOT: PSS type, forms a flexible layer 543 which can flatten on the scalp when pressure is applied and thus increase the contact surface. The pressure is then better distributed over the skull, which makes the device more comfortable. On the other hand, the contact surface is larger, and the electrical resistance at the interface between the skull and the sensor is lower, which results in better passage of EEG signals through the sensor. In addition, the flexible polymer absorbs the micromovements of the device relative to the user's scalp and improves the stability of the electrical properties at the interface, which makes it possible to reduce the artifacts, that is to say the variations in the measurements, independent of brain activity. Finally, these polymers have the advantage of being biocompatible.
    Of course, other shapes and / or coatings are possible to form a sensor according to the present description. For example, we could do without the metal part of the sensor using a conductive material other than metal for the structure of the sensor (such as a conductive polymer).
    FIG. 6 illustrates an example of a sensor 50 as described in FIGS 5A, 5B mounted in a flexible support 61. As illustrated in FIG. 6, the base 51 of the sensor can be removably mounted in a housing 65 of the support formed between two plates 62, 63 of the support. The sensor 50 is mounted movable relative to the flexible support 61 to allow the device to adapt to the different shapes of skulls. A metal blade 66 with spring effect provides electrical contact between the conductive area 511 of the base and the filtering and amplification circuit located on a flexible printed circuit 64 internal to the flexible support. The blade 66 provides, through punctual contact with the base of the sensor, mobility in translation on the vertical axis (perpendicular to the support), and in rotation about the 2 horizontal axes. These mobilities are constrained by the shapes of the sensor and its support.
    Although described through a certain number of detailed exemplary embodiments, the portable devices for the acquisition of electroencephalographic signals according to the present description include different variants, modifications and improvements which will be obvious to those skilled in the art, it being understood that these different variants, modifications and improvements are part of the scope of the object of the present description, as defined by the claims which follow.
    权利要求:
    Claims (13)
    [1" id="c-fr-0001]
    1. Portable device (10, 20) for the acquisition of electroencephalographic (EEG) signals emitted by a user, the device comprising:
    - a flexible support (11) intended to match a localized region of the user's skull;
    - a set of sensors (13) for the detection of electrical signals generated by the neural activity of the user, arranged on said support (11) so as to form contacts with the scalp when the device is carried by the 'user;
    - For each sensor, an electronic circuit for filtering and amplifying the electrical signals detected by said sensor, said electronic circuit being integrated in the flexible support (11) and forming with said sensor an active electrode;
    - A housing (12) comprising an electronic chain for processing the signals from said electronic filtering and amplification circuits, said housing being mechanically connected to the flexible support to form, with said support, a means of attachment to a garment or accessory (101) intended to be worn by the user.
    [2" id="c-fr-0002]
    2. Portable device according to claim 1, wherein the flexible support (11) is perforated and comprises a plurality of branches on which is arranged at least a portion of said sensors.
    [3" id="c-fr-0003]
    3. Portable device according to claim 2, wherein the flexible support (11) comprises a central part (110), the branches (111, 112) being connected to said central part by means of lateral branches (113, 114) flexible.
    [4" id="c-fr-0004]
    4. Portable device according to any one of the preceding claims, in which the flexible support and the housing are mechanically connected by a flexible attachment point, making it possible to form a clip-shaped attachment means.
    [5" id="c-fr-0005]
    5. Portable device according to any one of the preceding claims, in which each sensor is mounted mobile on said flexible support.
    [6" id="c-fr-0006]
    6. Portable device according to any one of the preceding claims, in which each sensor comprises a base (51) intended to be arranged in a housing (65) of said flexible support, in electrical contact with said filtering and amplification circuit.
    [7" id="c-fr-0007]
    7. Portable device according to claim 6, wherein said electrical contact is provided by a leaf spring (66), forming a point contact with said base.
    [8" id="c-fr-0008]
    8. Portable device according to any one of the preceding claims, in which each sensor comprises a plurality of conductive strips (53, 54), said conductive strips being intended to form linear contacts with the scalp when the device is carried by the 'user.
    [9" id="c-fr-0009]
    9. Portable device according to claim 8, wherein each sensor comprises two conductive strips.
    [10" id="c-fr-0010]
    10. Portable device according to any one of claims 8 or 9, wherein said conductive strips are arranged substantially parallel to each other.
    [11" id="c-fr-0011]
    11. Portable device according to any one of claims 8 to 10, in which the conductive strips comprise a conductive polymer coating forming a conductive layer intended to come into contact with the user's scalp.
    [12" id="c-fr-0012]
    12. Connected clothing for the acquisition of electroencephalographic signals (EEG) comprising a portable device according to any one of the preceding claims.
    [13" id="c-fr-0013]
    13. Method for the acquisition of electroencephalographic (EEG) signals emitted by a user by means of a portable device according to any one of the preceding claims, comprising:
    - the measurement of electrical signals generated by the user's neural activity by means of said sensors in contact with the user's scalp;
    - the processing of electrical signals from said filter circuits and
    5 amplification by means of the electronic processing chain arranged in said housing.
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    同族专利:
    公开号 | 公开日
    US20210030297A1|2021-02-04|
    EP3752057A1|2020-12-23|
    FR3077723B1|2020-03-13|
    JP2021517848A|2021-07-29|
    CN112384143A|2021-02-19|
    KR20210084343A|2021-07-07|
    CA3091295A1|2019-08-22|
    WO2019158534A1|2019-08-22|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    JP3626176B1|2004-09-29|2005-03-02|晶朗 木村|Electroencephalogram detection electrode and headset type electroencephalogram measurement apparatus|
    US20150112153A1|2013-10-22|2015-04-23|Neba Health, Llc|System and method for a compact eeg headset|
    US20160157777A1|2014-12-08|2016-06-09|Mybrain Technologies|Headset for bio-signals acquisition|
    WO2016140325A1|2015-03-05|2016-09-09|ニプロ株式会社|Electrode for detecting brain waves|
    WO2016166740A1|2015-04-16|2016-10-20|Universidade Do Minho|Cap with retractable electrode pins for use in eeg|
    US20170258400A1|2016-03-14|2017-09-14|The Nielsen Company , Llc|Headsets and electrodes for gathering electroencephalographic data|
    CN107049307A|2017-05-02|2017-08-18|臧大维|Full-automatic EEG signals read the helmet|WO2021148782A1|2020-01-21|2021-07-29|Prevayl Limited|Electronic device, a wearable article incorporating an electronic device and a system comprising an electronic device and a wearable article|US6161030A|1999-02-05|2000-12-12|Advanced Brain Monitoring, Inc.|Portable EEG electrode locator headgear|
    KR20050072965A|2004-01-08|2005-07-13|림스테크널러지주식회사|Active dry sensor module for measurement of bioelectricity|
    WO2013142316A1|2012-03-19|2013-09-26|Cognionics, Inc.|Transducer assemblies for dry applications of transducers|
    US9563184B2|2013-10-17|2017-02-07|Allan G Kern|Rate-based multivariable control with stability assurance|
    US20170027466A1|2014-04-01|2017-02-02|Trevor Austin Kerth|Headgear for dry electroencephalogram sensors|WO2021178319A1|2020-03-02|2021-09-10|Censyn, Inc.|Mobile electroencephalogram system and methods|
    法律状态:
    2019-02-28| PLFP| Fee payment|Year of fee payment: 2 |
    2019-08-16| PLSC| Publication of the preliminary search report|Effective date: 20190816 |
    2020-02-28| PLFP| Fee payment|Year of fee payment: 3 |
    2021-02-16| PLFP| Fee payment|Year of fee payment: 4 |
    2022-02-11| PLFP| Fee payment|Year of fee payment: 5 |
    优先权:
    申请号 | 申请日 | 专利标题
    FR1851287|2018-02-15|
    FR1851287A|FR3077723B1|2018-02-15|2018-02-15|PORTABLE ELECTROENCEPHALOGRAPHERS|FR1851287A| FR3077723B1|2018-02-15|2018-02-15|PORTABLE ELECTROENCEPHALOGRAPHERS|
    US16/970,271| US20210030297A1|2018-02-15|2019-02-12|Portable electroencephalography devices|
    KR1020207026191A| KR20210084343A|2018-02-15|2019-02-12|Portable EEG potential recording device|
    CA3091295A| CA3091295A1|2018-02-15|2019-02-12|Portable electroencephalography devices|
    PCT/EP2019/053454| WO2019158534A1|2018-02-15|2019-02-12|Portable electroencephalography devices|
    CN201980026161.9A| CN112384143A|2018-02-15|2019-02-12|Portable electroencephalogram machine|
    JP2020566877A| JP2021517848A|2018-02-15|2019-02-12|Portable electroencephalograph|
    EP19708238.1A| EP3752057A1|2018-02-15|2019-02-12|Portable electroencephalography devices|
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