The invention relates to a device for monitoring breathing, as a clothing item which may be worn by the user.
In order to continuously monitor the physiological condition of a user, it is known to fix sensors in textile structures intended to form a clothing item. Such sensors for example allow measurement of an electrocardiographic signal which is representative of the heart activity of a user who wears the clothing item.
However, such sensors may sometimes prove to be bulky, causing consequently a lack of comfort for the user. Further, the assembling of these sensors on the clothing item and their electric connection may prove to be complex.
Document EP 1 506 738 describes an elastic clothing item comprising textile sensors. The sensors include flexible textile electrodes applied against the skin used for collecting electric signals generated by the body for the elaboration of an electrocardiogram or an electromyogram on the one hand, and a mechanical deformation sensor used for measuring the respiratory movements of the user on the other hand. 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-extensible conductive yarn around a core consisting of non-conductive elastic yarn, i.e. the conductive yarn is helically wound around the non-conductive elastic yarn. When the elastic conductive yarn is stretched, the yarn elongates and the neighbouring turns of the winding move away from each other, causing a measurable change in electric resistance which depends on the elongation of the elastic conductive yarn.
Document US 2007/0171024 describes a clothing item in which is integrated a gauge giving the possibility of monitoring the breathing of the user who wears the clothing item. The clothing item comprises a textile base woven from non-conductive yarns. The gauge is formed by a conductive yarn gimped with a non-conductive yarn, and woven through the textile base, at the abdominal region or at the breast of the user. The conductive yarn consists of ultra-fine metal yarns twisted with textile fibres or textile fibres mixed with metal fibres. The respiratory movements of the user cause an elongation or a contraction of the conductive yarn. The change in the length of the conductive yarn causes a change in the electric properties of the yarn.
In such a clothing item, the connection of the conductive yarn to a measuring apparatus requires first stripping the conductive yarn, i.e. removing the non-conductive yarn which surrounds it, in order to be able to make an electric contact between the conductive yarn and a connecting cable.
Further, the wrapping of the conductive yarn with a non-conductive yarn increases the total diameter of the conductive yarn, which increases the costs for making the clothing item and may generate discomfort for the user who wears the clothing item.
An object of the invention is to propose a device for tracking the breathing of a user, which both has improved comfort and which minimizes the manufacturing steps required for making the device.
This object is attained within the scope of the present invention by means of a device for monitoring breathing of a user comprising:
The breathing sensor forms a conductive band having a first end and a second end positioned at a distance from each other, the ends being able to be connected to an apparatus for measuring the electric resistance of the conductive band.
The conductive band is positioned relatively to the tubular portion so that when the chest of the user is covered with the textile support, the conductive band is stretched and shrunk alternately because of the breathing of the user, the stretching and the shrinking of the conductive band having the effect of modifying the electric contacts between the stitches of the detection yarn within the conductive band, causing modification of the electric resistance of the conductive band.
In such a device, the detection yarn is not insulated, which allows the use of a smaller yarn, less costly and more lightweight. In addition, the connecting of the detection yarn to the measuring apparatus does not require any preliminary stripping of the detection yarn.
Further, the successive stitches of the detection yarn form multiple contacts of the external sheath with itself. It is mainly the modification of these electric contacts during the stretching and the shrinking of the conductive band which generates a modification of the electric resistance, and not a stretching or contraction of the actual yarn.
The proposed device may further have the following features:
Other features and advantages will further become apparent from the description which follows, which is purely illustrative and non-limiting and should be read with reference to the appended figures, wherein:
In
The textile support 2 appears as a clothing item, such as a tee-shirt for example, able to cover the body of the user.
In the embodiment illustrated in
The breathing sensors 3 and 4 allow detection of the respiratory movement of the thorax cavity and/or of the abdomen of the user who wears the clothing item.
The textile support 2 comprises a tubular portion 21 able to surround the chest of the user.
The tubular portion 21 has a neck 24 for letting through the head, a front 25 (visible in
The tubular portion 21 is formed by simultaneous knitting of an electrically insulating, majority ground yarn, and of an elastic yarn.
The majority ground yarn 16 is schematically illustrated in
The elastic yarn (not shown) is a yarn made of a thermoplastic elastomer or in a polyurethane derivative, known under the brand of Lycra® (marketed by the company Invista). The elastic yarn may be wrapped (in French “guipé”) or double-wrapped (in French “double-guipé”).
The ground yarn 16 and the elastic yarn are knitted together so that the ground yarn exactly covers the elastic yarn.
Each breathing sensor 3 and 4 extends around the chest of the user in an area located between the top of the sternum and the bottom of the belly.
Each breathing sensor 3 and 4 is formed by knitting an electrically conductive detection yarn.
As illustrated in
The conductive material of the external sheath 172 may be a metal, preferably a biocompatible metal, such as silver.
According to a first possibility (illustrated in
According to a second possibility (illustrated in
According to a third possibility (illustrated in
As this is visible in
More specifically, in
Each longitudinal branch 311, 312 extend along the knitting direction, i.e. parallel to the direction of a row.
Further, each longitudinal branch 311, 312 extends both on the front and on the rear of the clothing item.
The first band 31 also comprises junction portions 313, 314 extending transversely to the knitting direction, and electrically connecting the longitudinal branches 311, 312 with each other at their ends.
The first branch 311 is interrupted at a central axis X of the front of the clothing item (a virtual axis passing through the navel of the user).
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 able to be electrically connected to an apparatus for measuring the electric resistance of the first conductive band 31.
Each branch 311, 312 has a width comprised between 1 and 50 rows of stitches.
The second breathing sensor 4 forms a second conductive band 41 extending around the chest of the user at the abdominal muscles.
The second conductive band 41 is similar to the first conductive band 31. The second conductive band 41 comprises two branches 411, 412 extending parallel with each other around the chest of the user and two junction portions 413, 414. The first branch 411 is interrupted at a central axis X. The second conductive band 41 thus also has two ends 415 and 416 located at a distance from each other, on either side of the axis X, and able to be electrically connected to an apparatus for measuring the electric resistance of the second conductive band 41.
The tubular portion 21 and the breathing sensors 3 and 4 are formed by circular knitting in a single operation. The insertion of the conductive yarns is said to be “by means of embroidery” (in French “par le biais de la broderie”).
Thus, the ground yarn 16 (with the elastic yarn) forming the main tubular portion 21 and the detection yarn 17 forming the sensors 3 and 4 are knitted alternately during the knitting operation.
In other words, during the knitting operation, the ground yarn 16 stops being knitted when the detection yarn 17 is knitted. Also, the detection yarn 17 stops being knitted when the ground yarn 16 is knitted.
Further, as illustrated in
On the other hand, the ground yarn 16 is not cut so that non-knitted portions 166 of the ground yarn appear on the back of the clothing item behind the junction portions 313, 314 (also along the edges of the junction portions 413, 414) of the breathing sensors.
Moreover, the device 1 for monitoring breathing comprises one or several pockets attached on the textile support by crimping of a metal part of the type of press buttons, eyelets or rivets, by sewing, welding or thermally bonding. These additional pockets allow the insertion of electronic components into the clothing item, such as a battery or a measuring apparatus for example. In order to limit the displacement of the electronic components with respect to the textile support, the dimensions of each pocket are less than the dimensions of the component which 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
The device 1 for monitoring breathing further comprises a central sheath 5 (visible in
The connection of the breathing sensors 3 and 4 is achieved in the following way. An exposed end of a connecting cable 51, 52, 53, 54 is sandwiched between an end 315, 316, 415, 416 to be connected and an added conductive textile part. The textile part is attached by adhesive bonding on the end 315, 316, 415, 416 by means of an adhesive. For example the adhesive used is an adhesive based on polyprocaprolactone (PCL).
The ground yarn 16 is knitted so as to form a plurality of rows.
Also, the detection yarn 17 is knitted so as to form a plurality of rows.
The knitting technique used for the detection yarn 17 is weft-knitting (i.e. the stitches formed by a same continuous yarn are positioned in a same row), preferably with a Jersey base. The same knitting technique may be used for the ground yarn 16.
Each row consists of a plurality of successive stitches. The stitches of a same row form loops alternatively curved in one direction and then in the other, so that the stitches of the row are alternatively interlaced with the stitches of the immediately lower row and with the stitches of the immediately upper row.
As illustrated in
As illustrated in
The separation of the stitches thus causes a reconfiguration of the contact points P within the conductive band 31, which has the effect of modifying the electric resistance of the conductive band 31.
More specifically, as this is illustrated in
On the other hand, as this is illustrated in
Thus, by measuring the variations in electric resistance of the conductive band 31, it is possible to detect the respiratory movements of the user.
The same principle applies to the conductive band 41.
The apparatus 61 comprises a voltage generator 611, and a first resistor 612. The voltage generator 611 generates a low input voltage U1, of the order of 10 millivolts.
The output voltage U2 generated on the terminals of the conductive band is equal to:
U2=U1*R/(R+R612)
wherein R is the resistance of the conductive band 31, R612 is the resistance 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 band 31, it is possible to infer therefrom the resistance R of the conductive band 31.
The resistance of the conductive band 31 directly depends on its extension. The measured variations of resistance may be processed in order to monitor breathing parameters, such as the breathing rate of the user or the amplitude of the breathing cycles.
The device 1 may further comprise one or several insulating layers (not shown), positioned between the conductive band(s) 31 and 41, and the skin of the user when the user is covered with the textile support 2. The insulating layer(s) may be formed with an extensible fabric or membrane. The insulating layer(s) give the possibility of electrically insulating the skin of the user from the conductive bands 31 and 41 in which the electric current flows.
Number | Date | Country | Kind |
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1551896 | Mar 2015 | FR | national |
Filing Document | Filing Date | Country | Kind |
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PCT/EP2016/054706 | 3/4/2016 | WO | 00 |