• 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:
    The invention relates to a device for monitoring (1) the breathing of a user comprising: - a textile support (2) comprising a tubular part (21) formed by knitting an electrically insulating main thread, the tubular part (21) being adapted to coat the bust of the user, - at least one breathing sensor (3, 4) formed by knitting a sensing wire (17), the sensing wire (17) comprising an inner core of electrically insulating material and an outer sheath surrounding the inner core, the outer sheath being formed of electrically conductive material, wherein the breathing sensor (3, 4) forms a conductive strip (31, 41) having a first end (311). , 411) and a second end (312, 412) positioned at a distance from each other, the ends being adapted to be connected to an apparatus for measuring the electrical resistance of the conductive strip (31, 41).
    公开号:FR3033233A1
    申请号:FR1551896
    申请日:2015-03-06
    公开日:2016-09-09
    发明作者:Marion Gouthez；Sylvain Zorman；Pierre-Yves Frouin
    申请人:Bioserenity SAS；
    IPC主号:
    专利说明:

    [0001] FIELD OF THE INVENTION The invention relates to a breathing monitoring device, in the form of a garment that can be worn by the user.
    [0002] STATE OF THE ART In order to continuously monitor the physiological state of a user, it is known to fix sensors in textile structures intended to form a garment. Such sensors make it possible, for example, to measure an electrocardiographic signal representative of the cardiac activity of a user wearing the garment. However, such sensors can sometimes be cumbersome, thereby causing a lack of comfort for the user. In addition, the assembly of these sensors on the garment and their electrical connection can be complex. EP 1 506 738 discloses an elastic garment comprising textile sensors. The sensors include, on the one hand, flexible textile electrodes applied against the skin for collecting electrical signals generated by the body for the production of an electrocardiogram or an electromyogram, and on the other hand, a mechanical deformation sensor. used to measure the user's breathing movements. The electrodes are formed by weaving or knitting an elastic conductive yarn. The mechanical deformation sensor comprises a non-knitted elastic conductive yarn. The elastic conductive yarn is obtained by wrapping a non-stretchable conductive yarn around a core made of non-conductive elastic yarn, that is to say that the conductive yarn is wound helically around the non-conductive elastic yarn. When the elastic conductive yarn is stretched, the yarn elongates and the turns neighboring the winding deviate from each other, causing a measurable change in electrical resistance which is a function of the elongation of the elastic conductive wire. US 2007/0171024 discloses a garment in which is integrated a gauge to track the breathing of the user who wears the garment. The garment comprises a textile base woven from non-conductive yarns. The gauge is formed by a conductive thread covered with a non-conductive yarn, and woven through the textile base, at the level of the abdominal region or at the chest of the user. The conductive wire is made of ultrafine wire twisted with textile fibers or textile fibers mixed with metal fibers. The respiratory movements of the user cause elongation or contraction of the conductive wire. Changing the length of the wire leads to a change in the electrical properties of the wire.
    [0003] In such a garment, the connection of the conducting wire to a measuring apparatus requires first stripping of the conducting wire, that is to say of eliminating the non-conducting wire which surrounds it, in order to be able to realize a electrical contact between the conducting wire and a connecting cable.
    [0004] In addition, wrapping the conductive yarn with a non-conductive yarn increases the total diameter of the conductive yarn, which increases the manufacturing costs of the garment and can create discomfort for the user wearing the garment.
    [0005] SUMMARY OF THE INVENTION An object of the invention is to provide a device for monitoring the breathing of a user, which has both improved comfort and minimizes the manufacturing steps necessary for the realization of the device.
    [0006] This object is achieved in the context of the present invention by means of a user's breathing monitoring device comprising: a textile support comprising a tubular portion formed by knitting an electrically insulating majority thread, the tubular part being capable of coating the bust of the user, at least one breathing sensor formed by knitting a detection yarn, the detection yarn forming a plurality of stitches, the detecting yarn comprising at least one internal core electrically insulating material and an outer sheath surrounding the inner core, the outer sheath being formed of electrically conductive material so as to create electrical contacts between the meshes of the sense wire. The respiration sensor forms a conductive strip having a first end and a second end positioned at a distance from each other, the ends being adapted to be connected to an apparatus for measuring the electrical resistance of the conductive strip. The conductive strip is positioned relative to the tubular portion so that when the user's torso is coated with the textile backing, the conductive strip is stretched and swaged alternately due to the user's breathing, stretching. and the retraction of the conductive strip having the effect of modifying the electrical contacts between the meshes of the detection wire within the conductive strip, causing a modification of the electrical resistance of the conductive strip. In such a device, the sensing wire is not insulated, which allows the use of a smaller, less expensive and lighter wire. In addition, the connection of the detection wire to the measuring device does not require prior stripping of the detection wire. In addition, the successive meshes of the detection wire form multiple contacts of the outer sheath with itself. It is mainly the modification of these electrical contacts during the stretching and retraction of the conductive strip which generates a change in electrical resistance, and not a stretching or contraction of the wire itself. The proposed device may furthermore have the following characteristics: the detection wire comprises at least one core of polymer material, preferably polyamide; in a first possibility, the sheath of the detection wire is formed by covering the internal core with a wire of conductive material, preferably silver, - according to a second possibility, the sheath of the detection wire is formed by coating the inner core with a layer of conductive material, preferably silver, 3033233 4 the wire may consist of several non-conductive filaments, each filament being coated with an outer layer of conductive material, preferably silver, in which case the coated filaments may be twisted together, the tubular part is formed by knitting the majority thread and an elastic thread, - the conductive strip at least partially surrounds the bust of the user, preferably at least sternum and / or abdominals, and 10 extends on the belly and / or the back of the user, - the conductive strip can extend both on the belly and on the back of the user the tubular portion and the breathing sensor are formed by circular knitting in a single operation, the strand and the sensing yarn being alternately knitted, during knitting, the sensing yarn is cut when the yarn The device further comprises an insulating layer disposed between the conductive strip and the skin of the user when the user is coated with the textile support, the device further comprises a sheath fixed on the tubular part. and connection cables located within the sheath for connecting the ends of the conductive strip to the apparatus for measuring electrical resistance.
    [0007] BRIEF DESCRIPTION OF THE DRAWINGS Other features and advantages will become apparent from the description which follows, which is purely illustrative and not limiting and should be read with reference to the appended figures, in which: FIG. 1 schematically represents a view of In front of a breathing monitor according to a possible embodiment of the invention, FIG. 2 is a diagrammatic view of a rear view of the breathing monitor, FIG. FIG. 4 schematically represents the device 5 including a sheath and connection cables, FIGS. 5A and 5B are diagrammatic views of detail, respectively from the back and from the location of the device, FIGS. 6 and 7 schematically represent a mesh forming a breathing sensor, when the sensor is in the rest state and in the stretched state, Figures 8 and 9 show diagrammatically a conductive wire forming meshes, when the conductive wire is in the state of rest and in the stretched state respectively, - Figure 10 schematically shows the structure of a non-conductive wire used to form the textile support; - Fig. 11 schematically shows the structure of a conductive wire used to form the sensor according to a first possibility; - Fig. 12 schematically represents the structure of a conductive wire used to form the sensor according to a second possibility; FIG. 13 schematically shows the structure of a conductive wire used to form the sensor according to a third possibility; FIG. 14 is an equivalent circuit diagram of the sensor of FIG. and a device for measuring the electrical resistance of the conductive strip, FIG. ics of electrical resistance variations recorded from the respiration sensor. DETAILED DESCRIPTION OF AN EMBODIMENT In FIGS. 1 to 4, the breathing tracking device 1 shown comprises a textile support 2 and a plurality of sensors 3 and 4 integrated in the textile support 2 to follow the breathing of a patient. user. The textile support 2 is in the form of a garment, such as a T-shirt for example, suitable for coating the body of the user.
    [0008] In the embodiment illustrated in FIGS. 1 to 4, the sensors include two breathing sensors 3 and 4. The breathing sensors 3 and 4 make it possible to detect the respiratory movements of the thoracic cage and / or the abdomen. of the user wearing the garment. The textile support 2 comprises a tubular portion 21 adapted to surround the bust of the user. The tubular portion 21 has a neck 24 for the passage of the head, a front 25 (visible in Figure 1) adapted to cover a ventral portion 10 of the user and a behind 26 (visible in Figure 2) adapted to cover a back part of the user. The tubular portion 21 is formed by simultaneously knitting a majority of electrically insulating ground wire and an elastic wire. The majority ground wire 16 is schematically shown in FIG. 10. The majority ground wire 16 is a synthetic wire, formed of a polymeric material, such as polyamide (PA) wire or polyester wire ( PES). The elastic yarn (not shown) is a thermoplastic elastomer yarn or a polyurethane derivative, known as Lycra® (sold by Invista). The elastic thread may be wrapped or double-wrapped. The bottom yarn 16 and the elastic yarn are knitted together so that the bottom yarn exactly overlies the elastic yarn. Each breathing sensor 3 and 4 extends around the user's chest in an area between the top of the sternum and the lower belly. Each respiration sensor 3 and 4 is formed by knitting an electrically conductive sensing wire. As illustrated in FIGS. 11 to 13, the detection wire 17 comprises at least one inner core 171 made of electrically insulating material and an outer sheath 172 surrounding the inner core, the outer sheath 172 being formed of electrically conductive material. The electrically insulating material of the core 171 may be a polymer, such as polyamide, for example. The conductive material of the outer sheath 172 may be a metal, preferably a biocompatible metal, such as silver.
    [0009] According to a first possibility (illustrated in FIG. 11), the sheath 172 of the detection wire 17 is formed by wrapping the inner core 171 with a wire 173 made of conductive material. In other words, the wire 173 made of conductive material is helically wound around the inner core 171. According to a second possibility (illustrated in FIG. 12), the sheath 172 of the detection wire is formed by embedding the inner core. 171 with a layer 174 of conductive material. The coating can be carried out by a vacuum deposition technique by sputtering, for example, conductive material. According to a third possibility (illustrated in FIG. 13), the detection wire 17 consists of a bundle of conductive filaments 175 twisted together. Each conductive filament comprises a core 171 of insulating material coated with an outer layer 172 made of conductive material, preferably silver. As can be seen in FIGS. 1 to 4, the first breathing sensor 3 forms a first conductive strip 31 extending around the user's chest at the sternum, when the wearer is wearing the garment. The first conductive strip 31 may comprise several branches extending parallel to each other around the bust of the user.
    [0010] More specifically, in FIGS. 1 to 4, the first conductive strip 31 comprises two longitudinal branches 311, 312 extending parallel to one another. Each longitudinal branch 311, 312 extends in the direction of knitting, that is to say parallel to the direction of a row.
    [0011] In addition, each longitudinal branch 311, 312 extends both on the front and on the back of the garment. The first band 31 also includes junction portions 313, 314 extending transversely to the knitting direction, and electrically connecting the longitudinal legs 311, 312 to each other at their ends. The first branch 311 is interrupted at a central axis X of the front of the garment (virtual axis passing through the user's navel). The first band 31 forms an electric circuit having two ends 315, 316 located at a distance from each other, on either side of the central axis X. The ends 315 and 316 of the first band 31 are clean. to be electrically connected to an apparatus for measuring the electrical resistance of the first conductive strip 31. Each leg 311, 312 has a width of between 1 and 50 rows of cells. The second respiration sensor 4 forms a second conductive strip 41 extending around the user's chest at the abdominals. The second conductive strip 41 is similar to the first conductive strip 31. The second conductive strip 41 comprises two branches 411, 412 extending parallel to each other around the bust of the user and two joining portions 413, 414. first branch 411 is interrupted at a central axis X. The second conductive strip 41 also has two ends 415 and 416 located at a distance from each other, on either side of the X axis , and adapted to be electrically connected to an apparatus for measuring the electrical resistance of the second conductive strip 41.
    [0012] The tubular portion 21 and the breathing sensors 3 and 4 are formed by circular knitting in a single operation. The insertion of the wires is called "through the embroidery". Thus, the ground wire 16 (with the elastic wire) forming the tubular main portion 21 and the sensing wire 17 forming the sensors 3 and 4 are alternately knitted during the knitting operation. In other words, during the knitting operation, the baseline 16 ceases to be knitted when the detecting yarn 17 is knitted. Likewise, the detection yarn 17 ceases to be knitted when the bottom yarn 16 is knitted.
    [0013] In addition, as shown in Figs. 5A and 5B, the sensing wire 17 is cut when the ground wire 16 is knitted. In FIG. 5A, the cut ends 176 of the detection wire 17 appear on the back of the garment along the edges of the joining portions 313, 314 (likewise along the edges of the joining portions 413, 414) of the sensors. breathing. In contrast, the strand 16 is not cut so that non-knitted portions 166 of the strand appear on the back of the garment behind the joining portions 313, 314 (likewise along the edges of the garments). junction portions 413, 414) of the breathing sensors. Furthermore, the breathing monitoring device 1 comprises one or more pockets fixed on the textile support by crimping a metal part such as press studs, eyelets or rivets, by sewing, welding or heat sealing. These additional pockets allow the insertion of electronic components into the garment, such as a battery or a measuring device for example. In order to limit the displacement of the electronic components relative to the textile support, the dimensions of each pocket are smaller than the dimensions of the component that it receives. The insertion of the component into the pocket is possible because of the elastic properties of the textile support. In particular, the device 1 comprises a pocket 6 (visible in FIGS. 1 to 4) and a resistance measuring device 61 (visible in FIG. 3) housed in the pocket 6. The pocket 6 is positioned on the textile support 2 so as to be located on a shoulder of the user when the user wears the garment. This position minimizes the annoyance created by the presence of the device when the user is lying. The resistance measuring device 61 is able to measure and record the resistance variations of the conductive strips 31 and 41, in order to follow the breathing of the user.
    [0014] The breathing monitoring device 1 further comprises a central sheath 5 (visible in FIG. 4) fixed on the tubular part 21 along the central axis X and electrical connection cables 51 to 54 located inside. of the sheath 5 to connect each of the sensors to the measuring apparatus 61. The central sheath extends along the central axis X of the garment. The central sheath 5 is preferably fixed on the back of the device. The connection of the breathing sensors 3 and 4 is carried out as follows. A stripped end of a connecting cable 51, 52, 53, 54 is sandwiched between an end 315, 316, 415, 416 to be connected and a piece of conductive textile attached. The piece of textile is fixed by gluing on the end 315, 316, 415, 416 using an adhesive. The glue used is for example a glue based on polyprocaprolactone (PCL).
    [0015] Figures 6 and 7 schematically illustrate the structure of the conductive strip 31 forming the breathing sensor 3, respectively in the idle state and in the stretched state. The baseline 16 is knitted to form a plurality of rows.
    [0016] Likewise, the sensing thread 17 is knitted to form a plurality of ranks. The knitting technique used for the sensing yarn 17 is a gathered knit (i.e. the stitches formed by the same continuous thread are arranged in the same rank), preferably Jersey base.
    [0017] The same knitting technique can be used for the baseline 16. Each row is composed of a plurality of successive stitches. The stitches of the same rank form curved loops alternately in one direction and then in the other, so that the stitches of the row are interlaced alternately with the stitches of the immediately lower stitch and with the stitches of the next higher stitch. As illustrated in FIG. 6, when the conductive strip 31 is in the idle state, the cells of the same rank are in contact with one another in a plurality of contact points P. As illustrated in FIG. 7 when the conductive strip 31 is stretched in a direction Y parallel to the direction of knitting (i.e., the direction of a row), the meshes of the sense wire 17 move apart from each other, which reduces the number of contact points P between the meshes.
    [0018] 3033233 11 The spacing of the mesh thus causes a reconfiguration of the contact points P within the conductive strip 31, which has the effect of modifying the electrical resistance of the conductive strip 31. More specifically, as illustrated in FIG. 8, when the conductive strip 31 is in the idle state, an electric current can flow along the detection wire 17 via the contact points P along the dotted line. On the other hand, as illustrated in FIG. 9, when the conductive strip 31 is stretched, these contact points disappear, which increases the effective electrical resistance of the sense wire 17. Thus, by measuring the electrical resistance variations of the conductive strip 31, it is possible to detect the respiratory movements of the user. The same principle applies to the conductive strip 41.
    [0019] Fig. 14 is a block diagram of an electrical circuit of an apparatus 61 for measuring the electrical resistance of the conductive strip 31. The apparatus 61 comprises a voltage generator 611, and a first resistor 612. The generator voltage 611 generates a low input voltage U1 of the order of 10 millivolts. The output voltage U2 generated across the conductive strip is: U2 = U1 * R / (R + R612) where R is the resistance of the conductive strip 31, R612 is the value of the resistor 612 and U1 is the input voltage generated by the generator 611. By measuring the voltage between the ends 315 and 316 of the conductive strip 31, it is possible to deduce the resistance R of the conductive strip 31.
    [0020] Fig. 15 is a diagram showing variations in the resistance of the conductive strip 31 measured over time when the device 1 is worn by a user breathing.
    [0021] The resistance of the conductive strip 31 is directly a function of its elongation. The measured resistance variations can be processed to monitor breathing parameters, such as the user's breathing rate or the range of breathing cycles.
    [0022] The device 1 may further comprise one or more insulating layer (s) (not shown), arranged between the conductive strip (s) 31 and 41, and the skin of the user when the user is coated with the textile backing 2. The at least one insulation layer (s) may be formed of an extensible fabric or membrane. The at least one insulating layer (s) makes it possible to electrically isolate the user's skin from the conductive strips 31 and 41 in which the electric current flows.
    权利要求:
    Claims (12)
    [0001]
    REVENDICATIONS1. Device for monitoring (1) the breathing of a user comprising: - a textile support (2) comprising a tubular part (21) formed by knitting a predominantly electrically insulating bottom wire (16), the tubular part (21) ) being adapted to coat the bust of the user, - at least one breathing sensor (3, 4) formed by knitting a sensing thread (17), the sensing thread (17) forming a plurality of stitches, the detection wire (17) comprising at least one inner core (171) of electrically insulating material and an outer sheath (172) surrounding the inner core (171), the outer sheath (172) being formed of electrically conductive material so creating electrical contacts between the meshes of the sensing wire, wherein the breathing sensor (3, 4) forms a conductive strip (31, 41) having a first end (311, 411) and a second end (312, 412). ) positioned at a distance from each other, the extr mites being adapted to be connected to a device for measuring the electrical resistance of the conductive strip (31, 41), and the conductive strip (31, 41) is positioned relative to the tubular portion (21) so that when the bust of the user is coated with the textile support (2), the conductive strip (31, 41) is stretched and swaged alternately due to the user's breathing, stretching and retraction of the conductive strip (31, 41) having the effect of modifying the electrical contacts between the meshes of the detection wire (17) within the conductive strip (31, 41), causing a modification of the electrical resistance of the conductive strip (31, 41).
    [0002]
    2. Device according to claim 1, wherein the detection wire (17) comprises at least one core (171) of polymeric material, preferably polyamide. 3033233 14
    [0003]
    3. Device according to one of claims 1 and 2, wherein the sheath (172) of the detection wire (17) is formed by wrapping the inner core (171) with a wire of conductive material, preferably silver . 5
    [0004]
    4. Device according to one of claims 1 and 2, wherein the sheath (171) of the detection wire (17) is formed by coating the inner core (171) with a layer of conductive material, preferably silver .
    [0005]
    5. Device according to one of claims 1 to 4, wherein the detection wire (17) consists of several conductive filaments (175), each conductive filament (175) comprising a core (171) coated with an outer layer (172) of conductive material, preferably silver.
    [0006]
    The device of claim 5, wherein the coated filaments (175) are twisted together.
    [0007]
    7. Device according to one of claims 1 to 6, wherein the tubular portion (21) is formed by knitting the majority thread (16) and an elastic thread.
    [0008]
    8. Device according to one of claims 1 to 7, wherein the conductive strip (31, 41) surrounds the bust or part of the bust of the user, preferably at the height of the sternum and / or abdominals, and extends on the ventral part and / or on the dorsal part of the user.
    [0009]
    9. Device according to one of claims 1 to 8, wherein the tubular portion (21) and the breathing sensor (3, 4) are formed by circular knitting in a single operation, the ground wire (16) and the sensing thread (17) being alternately knitted. 20 25 30
    [0010]
    The device of claim 9, wherein, during knitting, the detecting yarn (17) is cut when the yarn is knitted (16). 3033233 15
    [0011]
    11. Device according to one of claims 1 to 10, further comprising an insulating layer disposed between the conductive strip (31, 41) and the skin of the user when the user is coated with the textile support (2). 5
    [0012]
    12. Device according to one of claims 1 to 10, further comprising a sheath attached to the tubular portion (21) and connecting cables located inside the sheath for connecting the ends (315, 316, 415, 416) of the conductive strip (31, 41) to the apparatus for measuring the electrical resistance. 10
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    PL3264983T3|2019-10-31|
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    RU2017131715A|2019-04-08|
    FR3033233B1|2017-03-31|
    EP3264983A1|2018-01-10|
    ES2719207T3|2019-07-09|
    CN107427220A|2017-12-01|
    KR101912730B1|2018-10-29|
    AU2016231255A1|2017-09-21|
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    法律状态:
    2016-02-05| PLFP| Fee payment|Year of fee payment: 2 |
    2016-09-09| PLSC| Publication of the preliminary search report|Effective date: 20160909 |
    2017-03-09| PLFP| Fee payment|Year of fee payment: 3 |
    2018-03-12| PLFP| Fee payment|Year of fee payment: 4 |
    2019-03-12| PLFP| Fee payment|Year of fee payment: 5 |
    2020-09-10| PLFP| Fee payment|Year of fee payment: 6 |
    2021-03-23| PLFP| Fee payment|Year of fee payment: 7 |
    优先权:
    申请号 | 申请日 | 专利标题
    FR1551896A|FR3033233B1|2015-03-06|2015-03-06|DEVICE FOR MONITORING A PHYSIOLOGICAL PARAMETER OF A USER IN THE FORM OF A CLOTHING|FR1551896A| FR3033233B1|2015-03-06|2015-03-06|DEVICE FOR MONITORING A PHYSIOLOGICAL PARAMETER OF A USER IN THE FORM OF A CLOTHING|
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    US15/554,522| US20180042551A1|2015-03-06|2016-03-04|Device in the form of a garment for monitoring a physiological parameter of a user|
    EP16709318.6A| EP3264983B1|2015-03-06|2016-03-04|Device in the form of a garment for monitoring a physiological parameter of a user|
    TW105106729A| TWI689263B|2015-03-06|2016-03-04|Device for monitoring a physiological parameter of a user as a clothing item|
    AU2016231255A| AU2016231255B2|2015-03-06|2016-03-04|Device in the form of a garment for monitoring a physiological parameter of a user|
    PL16709318T| PL3264983T3|2015-03-06|2016-03-04|Device in the form of a garment for monitoring a physiological parameter of a user|
    JP2017558403A| JP2018507081A|2015-03-06|2016-03-04|Device in the form of clothing for monitoring a user's physiological parameters|
    BR112017018979-8A| BR112017018979A2|2015-03-06|2016-03-04|device in the form of a garment to monitor a user's physiological parameter|
    ARP160100582A| AR104010A1|2015-03-06|2016-03-04|DEVICE FOR CONTROLLING A PHYSIOLOGICAL PARAMETER OF A USER AS A DRESS|
    CA2978601A| CA2978601C|2015-03-06|2016-03-04|Device in the form of a garment for monitoring a physiological parameter of a user|
    CN201680013663.4A| CN107427220A|2015-03-06|2016-03-04|Using the device of the form of the clothes for monitoring user's physiological parameter|
    PCT/EP2016/054706| WO2016142308A1|2015-03-06|2016-03-04|Device in the form of a garment for monitoring a physiological parameter of a user|
    KR1020177027945A| KR101912730B1|2015-03-06|2016-03-04|A garment-like device for monitoring a user's physiological parameters|
    MX2017011440A| MX364093B|2015-03-06|2016-03-04|Device in the form of a garment for monitoring a physiological parameter of a user.|
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