WO2022171861A1 - Vêtement de compression avec électrodes en tissu sur mousse - Google Patents

Vêtement de compression avec électrodes en tissu sur mousse Download PDF

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Publication number
WO2022171861A1
WO2022171861A1 PCT/EP2022/053504 EP2022053504W WO2022171861A1 WO 2022171861 A1 WO2022171861 A1 WO 2022171861A1 EP 2022053504 W EP2022053504 W EP 2022053504W WO 2022171861 A1 WO2022171861 A1 WO 2022171861A1
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WO
WIPO (PCT)
Prior art keywords
electrode
electrodes
fabric layer
skin
compression garment
Prior art date
Application number
PCT/EP2022/053504
Other languages
English (en)
Inventor
Mohammad FILFIL
Original Assignee
Paragit Solutions Aps
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 Paragit Solutions Aps filed Critical Paragit Solutions Aps
Publication of WO2022171861A1 publication Critical patent/WO2022171861A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6802—Sensor mounted on worn items
    • A61B5/6804—Garments; Clothes
    • A—HUMAN NECESSITIES
    • A41—WEARING APPAREL
    • A41D—OUTERWEAR; PROTECTIVE GARMENTS; ACCESSORIES
    • A41D1/00—Garments
    • A41D1/002—Garments adapted to accommodate electronic equipment
    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/251—Means for maintaining electrode contact with the body
    • A61B5/256—Wearable electrodes, e.g. having straps or bands
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/25—Bioelectric electrodes therefor
    • A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
    • A61B5/296—Bioelectric electrodes therefor specially adapted for particular uses for electromyography [EMG]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6813—Specially adapted to be attached to a specific body part
    • A61B5/6824—Arm or wrist
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/683—Means for maintaining contact with the body
    • A61B5/6831—Straps, bands or harnesses

Definitions

  • the invention relates to a compression garment for sensing an electrical signal at the skin of a user by means of at least one pair of electrodes, wherein each of said electrodes comprise a conductive fabric layer and a viscoelastic foam padding, and wherein a barrier region is provided in a space between said electrodes, the barrier region comprising a hydrophobic fabric portion and a viscoelastic foam padding.
  • Health data monitoring by tracking biometric parameters using a wearable electronic device during periods of physical activity can provide insights into various aspects of the wearer’s physical condition and overall health, for example making it possible to non-invasively detect cardiac stress events which could otherwise be unperceivable.
  • Such wearable devices may be apparatuses that can be worn directly on the skin at various parts of the human body and are typically used to track a variety of biometric parameters, e.g. heart rate and/or periods of physical activity, to provide convenient and non-intrusive data collection of health- or fitness- related data to an end user.
  • monitoring a patient’s health data over a prolonged period of time may enable a medical practitioner to diagnose a medical issue or to monitor the progression of a preexisting condition.
  • wearable heart rate monitoring devices exist which comprise a sensor configured to obtain an electrocardiography by means of a skin-contacting electrode provided at the skin of a heart patient for real-time detection of a rare cardiovascular phenomena, such as myocardial infarction or arrhythmia.
  • Other wearable monitoring devices exist for obtaining a surface electromyography by means of at least one and preferably a plurality of skin-contacting electrodes provided at the skin of a geriatric person and/or a Parkinson’s patient for detecting the onset of myopathic conditions, such as tremors, tetanic seizures or neuropathic disorders.
  • a common trait of sensing arrangements for studying patient electrophysiology by means of skin-contacting electrodes e.g. to obtain an electrocardiography (ECG), a surface electromyography (sEMG), an electroencephalography (EEG) and the like, is that electrosensing is affected by patient motion.
  • Some rhythmic motions such as shivering or tremors, can create an illusion of cardiac arrhythmia.
  • any unintended movements of a skin-contacting electrode relative to the skin can create an illusion of muscle activity or negatively impact its signal-to-noise ratio.
  • Such data artefacts may appear in distorted signals caused by a secondary internal or external sources, such as unreliable electrode skin-contact or interference from an electrical device, which can reduce the accuracy and trustworthiness of said health data.
  • wearable electrode includes a first layer of a first material, a second material positioned on the first material, the second material having a first compressive strength, a third material positioned on the second material, the third material having a second compressive strength different than the first compressive strength and a fourth material including a conductive element positioned on the third material, positioned around the second material, and joined to the first material.
  • wearable devices which comprise a plurality of skincontacting electrodes aimed towards an improved quality of electrode-to-skin contact for sensing an electrical signal, e.g. of muscle activity, at the skin of a user.
  • a technological solution is therefore needed to reliably monitor the muscle activity of a non-sedentary user for extended periods of time using a wearable sensor system, wherein the wearable sensor system provides electrodes configured for skin-contact to detect an electrical signal indicative of muscle activity at the skin of said user.
  • wearable devices including a plurality of skin-contacting electrodes suffer from various drawbacks that among others affect how long the device is comfortable to wear, how adaptive the electrode are to user movement and how resilient the electrodes are towards changes in skin conductivity or the like. Health data based on longterm monitoring of muscle activity is therefore difficult for end users to obtain using commercially available electrode systems.
  • a wearable garment which comprises a plurality of fabric electrodes and wherein the garment is configured to help maintain the plurality of electrodes in contact with the skin of a user wearing the garment.
  • the garment is made up of a stretchable fabric which is breathable and permits gases, such as volatile organic compounds and sweat to come through, thereby allowing it to be worn over the skin for many days.
  • electrodes may be made of electrically conducting fabrics.
  • a compression garment for sensing an electrical signal at the skin when worn by a user comprising:
  • a stretchable fabric layer configured to maintain said electrodes in contact with the skin of a user wearing the compression garment
  • each electrode comprises:
  • a barrier region is provided in a space between said first electrode and said second electrode, the barrier region comprising:
  • hydrophobic fabric portion configured to be maintained in contact with the skin, such as by extending in said space;
  • the compression garment disclosed herein is for sensing an electrical signal at the skin when worn by a user.
  • the compression garment is provided in a form and with a function suitable for being worn by a user, for example worn on a user extremity.
  • a compression garment may be a piece of clothing that fits tightly around the skin of at least one part of a human body.
  • a compressive function of the compression garment may be provided at varying degrees of compression.
  • the degree of compression of the compression garment may be adjustable to fit a particular user by means of one or more adjustable fastening means, e.g. hook-and-loop fasteners, zippers or laces.
  • the compression garment provides at least enough compression to hold the compression garment against the force of gravity when worn at parts of the body for which it is intended.
  • the compression garment may be configured for being held to the skin by elastic tension, such as by the compression garment being made of a stretchable fabric or elastic material.
  • the compression garment may provide enough adjustability or stretch that “one size fits all” at least for most prospective users in an age group. Further, the compression garment may provide increased support for an infirm patient’s joints or limbs during flexion and extension movements.
  • a compressive garment may provide compression of 20-30 mmHg or higher, which may be sufficient to prevent or reduce the occurrence of various medical disorders relating to blood circulation in the legs. It may be advantageous to provide sensing of an electrical signal at the skin while providing a compressive function to the skin, for example as part of a health monitoring system for post-operative care or the like.
  • the degree of compression provided by the compression garment may be 10-25 mmHg or lower, which may be sufficient to enable a substantially skin-tight fit of the compression garment against the skin of a user wearing said garment.
  • the electrical signal may be a indicative of an electromagnetic field which exhibits variations in time and/or space, such as an electrical potential difference or a time-varying electrical current, such as an electrophysiological signal of the human body.
  • Sensing an electrical signal at the skin may provide that e.g. an electrocardiography (ECG), a surface electromyography (sEMG), an electroencephalography (EEG) and the like is obtainable by means of an electronic circuit configured with a processor.
  • ECG electrocardiography
  • sEMG surface electromyography
  • EEG electroencephalography
  • the compression garment comprises at least one pair of electrodes made of fabric materials.
  • the at least one pair of electrodes may be one pair of electrodes.
  • the at least one pair of electrodes may be a plurality of pairs of electrodes. Having a pair of electrodes consisting of a first electrode and a second electrode provides that skin contact can be made with said pair of electrodes, so that a circuit is completed via the epidermis and/or the subcutaneous tissue located along conducting pathways between the first electrode and the second electrode.
  • an electrical potential difference between a first electrode and a second electrode comprised in a pair of skin-contacting electrodes and placed a distance apart may be indicative of one or more electrophysiological factors including skin conductivity, muscle activity as well as the quality of the electrode-tissue interface itself.
  • the at least one pair of electrodes includes a first electrode and a second electrode.
  • a pair of electrodes may comprise a first electrode and a second electrode.
  • the first electrode and the second electrode may be configured for maintaining contact with the skin of a user at two substantially separate skin-contacting regions.
  • the pair of electrodes is provided on or as part of a backing material such that the electrodes form an integral part of the backing, the first electrode and the second electrode may be at a fixed position relative to each other, i.e. a distance apart.
  • the compression garment comprises a stretchable fabric layer. Having a stretchable fabric layer provides that the compression garment may provide compression and/or friction against the skin of a user wearing the compression garment due to an elastic tension resulting from stretching the stretchable fabric layer when worn by the user.
  • the compression garment may comprise one or more skin-contacting regions configured for being maintained in contact with the skin of a user.
  • the compression garment is configured to be worn by a user by positioning the stretchable fabric layer substantially circumferentially around an extremity of the user, such as by wearing a sleeve on an arm or a sock on a foot. In some embodiments, the compression garment is configured to be worn by a user by positioning the stretchable fabric layer on or around the torso of the user.
  • the stretchable fabric layer is configured to maintain the electrodes in contact with the skin of a user wearing the compression garment.
  • the stretchable fabric layer is stretchable, so that the at least one pair of electrodes can be maintained in contact with the skin by providing a compressive force inwardly towards the skin when the stretchable fabric layer is stretched from a substantially unaffected state. Thereby, a compressive function of the compression garment is provided at the electrodes.
  • the stretchable fabric layer may act as a backing material for affixing the electrodes.
  • Providing such a backing material in the form of a stretchable fabric layer for affixing the electrodes allows for at least one pair of electrodes to be kept securely in place at the skin of a user while also providing good adaptation to the user’s physique.
  • fixating the first electrode and the second electrode in a pair of electrodes relative to each other so that any relative movement thereof is prevented or reduced when the compression garment is worn may provide fewer artefacts due to slippage.
  • a compression garment comprising a stretchable fabric layer may provide a compression and/or friction force that maintains the at least one pair of electrodes against the skin because this improves the electrode skin-contact.
  • the need for maintaining skin-contacting electrodes in proper contact with the skin may be detrimental to the comfort of a user wearing said wearable device, and thus it is desirable to provide a solution which is comfortable and can remain securely in place at the skin for extended periods of time so that artefacts in the health data are reduced.
  • use of adhesives at the skin to provide such contact is generally detrimental to long-time comfort as it may place undue restrictions on daily activities, such as showering, cause skin irritation and/or require a degree of hair removal.
  • the electrodes are made of fabric materials.
  • An electrode may be made essentially of fabric materials, such as woven materials, textiles or nonwoven fabrics made from individual fibers, threads, filaments or tows of fibers.
  • an electrode made of fabric materials includes at least one fabric made of a more conductive material than the other fabric materials, so that at least one of the fabric materials is conductive.
  • the electrodes have an exterior made of fabric materials.
  • the electrodes may be dry or semi-dry electrodes made from fabric materials which offer improved flexibility, wearing comfort and can be bonded easily to other support fabric material by use of thermoformable materials, adhesives, stitching etc.
  • a semi-dry electrode may require only a small amount of electrolyte fluid for skin-contact.
  • a dry electrode is configured to act as a conductor between the skin and the electrode substantially without a electrolytic fluid layer therein between, e.g. as opposed to a wet electrode which may require an electrode gel to reduce skin resistance.
  • the electrodes made of fabric materials are conductive fabric electrodes.
  • Fabric electrodes may comprise one or more layers of fabric materials.
  • the one or more layers of fabric materials may include at least one conductive fabric layer.
  • the at least one conductive fabric layer may be two or more conductive fabric layers provided in abutment of each other, so that the conductive fabric layers form a conductive pathway from one of said conductive fabric layers to another.
  • the compression garment comprises a bonding means affixing the fabric materials of said electrodes to the stretchable fabric layer.
  • the bonding means provides that one or more of the fabric materials that make up the electrodes are affixing to the stretchable fabric layer, so that each of the electrodes are kept in place relative to the compression garment and to each other.
  • the bonding means may be adhesives, stitching, thermoplastic welding or similar means suitable for joining fabric materials. Flexibly affixing fabric materials to the stretchable fabric layer helps to maintain said fabric electrodes in contact with the skin and may also provide a semi-impermeable membrane ensuring that the electrode remains dry when in use.
  • the bonding means is connecting the fabric materials of the electrodes to the stretchable fabric layer, such as by irremovably affixing or directly connecting at least one of said fabric materials to the stretchable fabric layer.
  • Each electrode in each pair of electrodes may comprise a conductive fabric layer substantially electrically isolated from the other electrode in that pair of electrodes.
  • the first electrode and the second electrode of a pair of electrodes may each comprise a conductive fabric layer, such as a patch of conductive fabric.
  • a conductive fabric layer of one electrode being substantially electrically isolated from a conductive fabric layer of another electrode, measurements of an electrical signal at one electrode may be substantially unaffected by electrical shorting via any direct pathways to the other electrode, relative to which said electrical signal is measured. This allows differential measurement of electrical signals indicative of changes in the conductivity of the skin between a pair of electrodes with an increased accuracy due to that electrode being substantially electrically isolated from the other electrode. It is typically desirable to avoid bridging of the electrodes e.g. due to electrical shorting.
  • each electrode in a pair of electrodes in the at least one pair of electrodes comprises a conductive fabric layer which is substantially electrically isolated from another electrode in that pair of electrodes. This provides that the pair of electrodes are configured to measure electrical signals at the skin between that pair of electrodes, such that a surface electromyography can be obtained.
  • the conductive fabric layer of the first electrode of a pair of electrodes is substantially electrically isolated from the conductive fabric layer of the second electrode of that pair of electrodes, and preferably from all other electrodes.
  • the conductive fabric layer may be a fabric layer comprising silver or silver chloride threads.
  • the conductive fabric layer may be a woven textile comprising silver or silver chloride threads woven into said woven textile.
  • the conductive fabric layer may be a conductive textile made of metal strands woven into a textile or may be made of a conductive yarn, which is e.g. made conductive by metal-coating.
  • a thin surface layer of conductive material is deposited onto a substantially non-conductive or at least less conductive fabric layer to form a hybrid conductive fabric layer which is primarily conductive across said thin surface layer.
  • in-woven conductive threads provide conductivity through the layer.
  • a polymer top layer is provided substantially covering the conductive fabric layer to form a skin-contacting region.
  • the polymer top layer may be made of a polymeric material, such as silicone, and comprise metal strands or a metal matrix embedded in the polymeric material.
  • the metal strands or metal matrix may include silver or silver chloride threads.
  • the polymer top layer provides a skin-compatible and flexible skincontacting surface, which may be about as conductive as the conductive fabric layer to which it is affixed.
  • a hydrophobic fabric portion of a barrier region extending in a space between a pair of electrodes may be configured to be maintained in contact with the skin between the skin-contacting regions of that pair of electrodes.
  • a pair of electrodes may provide two skin-contacting regions.
  • Each electrode in each pair of electrodes may comprise a viscoelastic foam padding provided between the conductive fabric layer and the stretchable fabric layer.
  • Foam padding may provide a viscoelastic effect when undergoing deformation, i.e. that in response to a stress being applied to a viscoelastic material which makes up a part of said foam padding, the viscoelastic material comprises a viscous component that dissipates an amount of energy as heat while undergoing plastic deformation, after which time, the viscoelastic material fully recovers its initial undeformed shape due to an elastic component of the viscoelastic material.
  • a viscoelastic material has an elastic component, which tends to provide that the viscoelastic material has a linear stress-strain response for smaller or slowly varying amounts of strain, and a viscous component, which tends to provide dampening or resistance to changes in strain. It is understood that a viscoelastic material may exhibit material properties that mix or combine material properties associated with elastic materials and viscous materials. Viscoelastic materials may exhibit temperature-dependent or time- dependent strain e.g. as a result of secondary bond stretching or polymer chain reconfiguration.
  • the viscoelastic foam padding provides a memory foam effect. The memory foam effect may enable electrodes made of fabric materials to have improved adaption to skin.
  • a viscoelastic foam padding is provided in a cavity formed between the conductive fabric layer and the stretchable fabric layer.
  • the first electrode and the second electrode of a pair of electrodes may comprise a viscoelastic foam pads in a cavity formed between a conductive fabric layer and the stretchable fabric layer.
  • each fabric electrode comprises one or more viscoelastic foam pads provided substantially between the conductive fabric layer and the stretchable fabric layer.
  • Each viscoelastic foam pad may extend in two mutually perpendicular directions substantially parallel to a substantially planar skin-contacting region of the electrode.
  • one or more viscoelastic foam pads are comprised in and/or shared between the pair of electrodes.
  • the inventors have found that by providing a viscoelastic foam padding between the conductive fabric layer of an electrode made of fabric materials and the stretchable fabric layer of the compression garment, it is possible to integrate fabric electrodes into a wearable apparatus which is comfortable to wear, where the electrode adapt to user movement and where the electrodes are resilient towards stretching. It may be advantageous that the compression garment for sensing electrical signals at the skin of the user is comfortable to wear because this allows for tracking of biometric parameters using a wearable electronic device during periods of physical activity or for longer periods of time, such as more than 12 hours or a number of days.
  • each electrode in that pair of electrodes may be configured for contacting the skin of a user wearing the compression garment at a skin-contacting region provided at that electrode.
  • the first electrode of a pair of electrodes may be configured for contacting the skin of a user wearing the compression garment in a primary position and the second electrode of that pair of electrodes may be configured for contacting the skin of a user wearing the compression garment in a secondary position.
  • a barrier region is provided in a space between the first electrode and the second electrode.
  • the barrier region may act to fill out the space between the pair of electrodes.
  • the barrier region may be configured for contacting the skin of a user wearing the compression garment in a tertiary position.
  • the barrier region is configured to be provided onto the skin of a user at a tertiary position being substantially between a primary position and a secondary position of the first electrode and the second electrode, respectively, where they are brought into contact with the skin of said user wearing the compression garment.
  • the barrier region comprises a hydrophobic fabric portion which is configured to be maintained in contact with the skin.
  • the hydrophobic fabric portion may be a stretch of hydrophobic fabric, a patch cut from a hydrophobic fabric layer or another fabric layer treated with a hydrophobic treatment, water-repellant agent or the like.
  • the hydrophobic fabric portion is a fabric layer having a hydrophobic surface configured to be maintained in contact with the skin.
  • the hydrophobic fabric portion may be provided in a geometrical shape, such as a hydrophobic fabric layer cut according to a two-dimensional template shape, so that the barrier region forms a substantially similar shape around the first electrode and the second electrode.
  • the barrier region may comprise a hydrophobic fabric layer extended in the space between the first electrode and the second electrode of a given pair of electrodes.
  • a hydrophobic fabric layer may be a piece of fabric that provides a hydrophobic effect to repel or at least reduce the attraction of water molecules to said piece of fabric.
  • the hydrophobic fabric layer is a fabric layer, such as woven or non-woven textile, which is treated with a hydrophobic substance, such as a cotton fabric which is treated with silicon dioxide or titanium dioxide nanoparticles.
  • the hydrophobic fabric layer is a fabric layer which has been treated with a water-repellent agent.
  • the hydrophobic fabric layer is a fabric layer onto which a thin film of hydrophobic nanoparticles has been deposited, for example using plasma deposition techniques, such as pulsed plasma deposition.
  • the hydrophobic fabric layer has been treated with a thin film of hydrophobic nanoparticles and a water-repellent agent, such as fluorocarbon.
  • the hydrophobic fabric layer provides a hydrophobic function to prevent wetting of a skin-contacting region provided by the compression garment, such as a skin-contacting region of at least one pair of electrodes or a barrier region provided between a pair of electrodes.
  • the barrier region being water-repellent or at least providing a hydrophobic function to the space between the pair of electrodes is advantageous because, in combination with a compressive function provided by the stretchable fabric layer, the barrier region prevents ingress of or divert away sweat from a skin-contacting region of adjacent electrodes and/or the barrier region.
  • a hydrophobic function of the hydrophobic fabric layer may be provided at varying degrees of hydrophobicity.
  • the degree of hydrophobicity of a hydrophobic surface is measured by the contact angle of the liquid-vapor interface of a water droplet where the liquid-vapor interface meets the hydrophobic surface, the latter being horizontal.
  • the hydrophobic fabric layer may provide a hydrophobic effect, wherein the contact angle of water on a treated surface of the hydrophobic fabric layer is 90° or higher, such as between 100° and 150°, such as more than 125°.
  • the hydrophobic fabric layer may provide a super-hydrophobic effect, wherein the contact angle of water on a treated surface of the hydrophobic fabric layer is 150° or higher, such as ca. 165°.
  • the hydrophobic fabric layer provides at least enough of a hydrophobicity to prevent wicking of moisture from the skin through the hydrophobic fabric layer or to keep absorbent materials provided adjacent to the hydrophobic fabric layer dry.
  • the hydrophobic fabric portion may be configured for being held to the skin by elastic tension, such as by the compression garment being made of a stretchable fabric or elastic material, so that a hydrophobic surface of the hydrophobic fabric portion fits tightly onto the skin when compressed and forms a substantially water-tight seal at the barrier region.
  • the barrier region having a hydrophobic fabric portion extending as a top layer in the space between a pair of electrodes may provide that the barrier region becomes substantially depleted of water-based liquids, e.g. bodily fluids, and in particular of water-based liquids containing electrolytes, such as sweat or serous fluid.
  • the barrier region may prevent or reduce negative effects of electrolytic fluids which could accumulate between the electrodes, such as electrical shorting due to sweat.
  • the presence of sweat may in some cases tend to negatively impact the signal-to-noise ratio of an electrical signal being detected by means of a pair of closely spaced surface electrodes at the skin, e.g. used for obtaining sEMG measurements with a pair of electrodes in a bipolar configuration. It may therefore be advantageous if a barrier region provided in a space between two closely spaced skincontacting electrodes act to prevent or reduce the negative effects of electrical shorting due to presence of sweat at the skin because the measurement accuracy of the electrodes is affected by changes in skin conductivity and the like.
  • a viscoelastic foam padding may be provided between the hydrophobic fabric layer and the stretchable fabric layer.
  • the memory foam effect provided by a viscoelastic foam padding in the electrodes and/or the barrier region may improve contact of the conductive fabric layer and/or the hydrophobic fabric layer, respectively, despite the bumps or imperfections of the skin by providing resiliency to plastic deformation and a restorative force towards a shape substantially conforming with said skin features.
  • providing viscoelastic foam pads as a flexible and skin-conforming cushioning at both the electrodes and the barrier region therein-between may offer increased user comfort when wearing the compression garment very tight to provide a higher degree of compression during periods of physical activity and/or for longer periods of time, such as more than 12 hours or a number of days.
  • the barrier region may comprise a viscoelastic foam padding provided between the hydrophobic fabric layer and the stretchable fabric layer.
  • one or more viscoelastic foam pads are comprised in and/or shared between the barrier region and one or both of the electrodes in the pair of electrodes.
  • the viscoelastic foam padding provides a memory foam effect.
  • the memory foam effect may enable the barrier region between two electrodes to also have improved adaption to skin in a similar manner as the memory foam effect provided at the electrodes themselves.
  • a viscoelastic foam padding is provided in a cavity formed between the hydrophobic fabric layer and the stretchable fabric layer.
  • the barrier region between the first electrode and the second electrode of a pair of electrodes may comprise a viscoelastic foam pads in a cavity formed between the hydrophobic fabric layer and the stretchable fabric layer and extending in the space between the first electrode and the second electrode.
  • one or more barrier regions are provided between each neighboring pair of electrodes in a plurality of electrodes made of fabric materials.
  • the barrier region comprises one or more viscoelastic foam pads provided substantially between the hydrophobic fabric layer and the stretchable fabric layer. Each viscoelastic foam pad may extend in two mutually perpendicular directions substantially parallel to a substantially planar skin-contacting region of the barrier region, such as e.g. co-planar with the electrodes.
  • the inventors have found that by providing a viscoelastic foam padding between the hydrophobic fabric layer of the barrier region provided in a space between a pair of electrodes and the stretchable fabric layer of the compression garment, it is possible to integrate pairs of fabric electrodes into a wearable apparatus which is comfortable to wear, where the electrodes are kept substantially fixed relative to each other and neighboring electrodes are resilient towards electrical shorting due to sweat. It may furthermore be advantageous that the compression garment provides for good skin contact for both the electrodes and the barrier region by the memory foam effect of the viscoelastic foam pads ensuring a comfortable tight fit when compressed.
  • the compression garment for sensing electrical signals at the skin of the user is enabled to be comfortably worn by a user being mostly non-sedentary for a prolonged period of time without having to exchange, refit or adjust parts of the compression garment for the electrodes to work optimally.
  • wear comfort may be important to ensure sufficient collection of health data of good fidelity, i.e. substantially without data artefacts or with minimal wear interruptions.
  • the bonding means is a bonding layer made of a thermoformable material.
  • the bonding layer may be made of a thermoformable polymeric material, such as a vinyl polymer. Having a bonding layer made of a thermoformable material to affix the fabric materials of the electrodes and the like may provide that manufacturing of the fabric electrodes can be made simpler or cheaper, e.g. by stacking layers and bonding them together by heat-presssing.
  • the bonding layer may be made from a heat-pressable material, such as a vinyl polymer.
  • the bonding layer may be configured for attaching fabric materials of the electrodes to other fabric materials, synthetic textiles, plastics or the like.
  • the conductive fabric layer is disposed through an opening in the bonding layer to form a skin-contacting region.
  • the bonding layer is configured to expose or maintain one or more fabric materials of the electrodes at one or more skin-contacting regions.
  • the fabric materials of the electrodes being affixed to the stretchable fabric layer by the bonding layer may include a conductive fabric layer, a hydrophobic fabric layer, a (fabric) backing layer or combinations thereof.
  • the hydrophobic fabric portion of the barrier region is disposed through another opening in the bonding layer to form another skin-contacting region.
  • the hydrophobic fabric layer may be affixed to a part of the compression garment by the bonding layer, such as to the stretchable fabric layer or a backing layer.
  • the hydrophobic fabric portion is a layer affixed to the stretchable fabric layer by another bonding layer which is arranged circumferentially to and/or substantially concentrically with the first electrode and/or the second electrode.
  • the hydrophobic fabric portion may be hydrophobic fabric layer.
  • the hydrophobic fabric layer may be affixed to a part of the compression garment by another bonding layer, such as to the stretchable fabric layer or a backing layer.
  • the hydrophobic fabric layer is disposed through another opening in the bonding layers to form another skin-contacting region around said electrode.
  • Forming another skin-contacting region around an electrode may provide that bodily fluids, such as sweat secreted from the skin at or near the electrode, are prevented from traversing and/or escaping the another skin-contacting region of the barrier region formed around said electrode. It may be advantageous e.g. that sweat present at an electrode is prevented from reaching moisture-sensitive or conductive parts of the compression garment, such as the other electrodes. For example, this may help to prevent bridging of two electrodes by promoting an improved electrical contact of the skin with each electrode due to the presence of an electrolytic fluid.
  • the hydrophobic fabric layer may be affixed between two substantially concentric or nonoverlapping rings of bonding layers, e.g. substantially centered on an electrode.
  • each of the electrodes in the at least one pair of electrodes comprises a backing layer abutting or proximate the stretchable fabric layer, and wherein the viscoelastic foam padding of the electrode is provided between the conductive fabric layer and the backing layer.
  • the backing layer may provide added rigidity to the fabric electrodes, which enables the viscoelastic foam padding to have improved adaptation to the skin of the user by maintaining compression thereon. It is advantageous to provide a fabric electrode with a backing layer to improve the skin-contact because measurements with said electrode are less prone to signal noise.
  • the barrier region comprises a backing layer abutting or proximate the stretchable fabric layer, and wherein the viscoelastic foam padding of the barrier region is provided between the hydrophobic fabric portion and the backing layer, such as between two abutting layers.
  • the backing layer may provide added rigidity to the barrier region or parts thereof, which enables the viscoelastic foam padding to have improved adaptation to the skin of the user by maintaining compression thereon. It is advantageous to provide a barrier region with a backing layer to improve the skin-contact because hydrophobic action of the hydrophobic fabric layer may prevent or reduce presence of sweat between the electrodes, which negatively impacts the electrical isolation of the electrodes.
  • the bonding means affixes a hydrophobic fabric material to the stretchable fabric layer and/or to a backing layer connected to the stretchable fabric layer.
  • the bonding means may be configured to maintain the hydrophobic fabric material at one or more skin-contacting regions extending in a transversal direction, such as transversal direction substantially perpendicular to a longitudinal direction defined between a first electrode and a second electrode in a pair of electrodes. It is understood that the longitudinal and transversal directions are substantially along the surface of the skin of a user wearing the garment.
  • the bonding means may be configured to expose or impart the hydrophobic fabric material onto the skin of a user, thereby forming a barrier region at the skin in the space between a pair of electrodes and extending in a transversal direction relative to that pair of electrodes.
  • the hydrophobic fabric layer is flexible, so that the hydrophobic fabric material may be bent from a substantially flat sheet in a undeformed state into a sheet having the geometrical shape of the skin-contacting region, i.e. so that the hydrophobic fabric layer conforms to the surface of the skin.
  • At least the hydrophobic fabric portion or the barrier region is configured to deform under compression provided by the stretchable fabric layer, such that a bodily fluid is repelled from or diverted around said barrier region by maintaining said hydrophobic fabric portion in contact with the skin.
  • the hydrophobic fabric layer provides a skin-tight “seal” against the skin of the user to diverted away any sweat e.g. with assistance of gravity or the user’s movements.
  • the barrier region extends in a transversal direction relative to a longitudinal axis defined between the first electrode and the second electrode.
  • a shortest path between the first electrode and the second electrode around the barrier region is at least 25% longer than an overall shortest path between said first electrode and said second electrode measured substantially along the skin of a user wearing said compression garment, such as between 50% and 900% longer, such as about 100%-200% longer.
  • the barrier region protrudes a distance from the stretchable fabric layer substantially equal to a distance protruded by a skin-contacting region of the first electrode and/or the second electrode. This may provide the advantage that the barrier region can be maintained in good contact with the skin by a substantially equal compression effected by the stretchable fabric layer as for the electrodes.
  • each electrode comprises a conductive lead in contact with the conductive fabric layer of that electrode.
  • the at least one pair of electrodes may be two or more pairs of electrodes, each pair having a first electrode and a second electrode and a barrier region provided in a space therein between.
  • each electrode being substantially electrically isolated from the other electrodes includes a conductive lead in contact with the conductive fabric layer of that electrode. It may however be possible to arrange a plurality of conductive leads such that each lead is in contact with the conductive fabric layer of more than one electrode, for example if one or more electrodes are coupled together in parallel e.g. to reduce complexity.
  • the conductive lead is substantially contained between at least two of the stretchable fabric layer, the bonding means, a backing layer or the fabric materials of the electrode, preferably between the stretchable fabric layer and a layered bonding means, such that the conductive lead is prevented from contacting the skin of a user wearing said compression garment.
  • the bonding layer is a substantially non-conductive polymer layer, such as polypropylene layer.
  • a non-conductive polymer material for the bonding layer provides bonding which is stretchable, resilient and non-absorbent in addition to being non- conductive, whereby bridging of the electrodes is avoided.
  • the compression garment is a compression sleeve configured to fit and be retained on the arm of a user, optionally by a retaining means.
  • the compression sleeve may be configured to be worn on the underarm. It is advantageous that a compression sleeve is configured to be retained on the arm of a user while sensing an electrical signal at the skin of said user because such a wearable sensor system can then be held in place at an easily accessible position while continually and unobtrusively functioning to detect said electrical signal.
  • the compression garment is configured to be worn on or at an extremity of the user, such as a sleeve wearable on an arm, such as a sock wearable on a foot, such as a compression garment wearable at an elbow joint, a knee joint or the like, and preferably in the form of a sleeve worn on the forearm.
  • a sleeve wearable on an arm such as a sock wearable on a foot
  • a compression garment wearable at an elbow joint, a knee joint or the like such as a compression garment wearable at an elbow joint, a knee joint or the like, and preferably in the form of a sleeve worn on the forearm.
  • the compression garment comprises at least one reference electrode, said at least one reference electrode provided adjacent the at least one pair of electrodes and configured to be maintained in contact with the skin of the user by means of the stretchable fabric layer.
  • the reference electrode is preferably made of fabric materials, e.g. consisting essentially of one or more fabric materials.
  • the at least one reference electrode is configured to be maintained in contact with the skin at a body part with a substantially greater bony prominence than provided at the electrodes, such as around a wrist portion.
  • bony prominence refers to areas where bones are close to the surface of a human body i.e. areas of the body with limited subcutaneous tissue over the bones. It may be advantageous to provide the reference electrode at a body region with substantially less muscular prominence compared to the position of the electrodes because this may allow improved cancellation of a common mode noise affecting measurements at the electrodes by also using the reference electrode in a bi-polar configuration.
  • the at least one pair of electrodes may comprises three or more electrodes, wherein at least two of said three or more electrodes are arranged into one pair of electrodes by being provided in a nearest proximity to one another, such as within 5 cm.
  • a third electrode of said three or more electrodes may be a reference electrode.
  • the reference electrode comprises a conductive fabric layer substantially electrically isolated from the at least one pair of electrodes, i.e. from a first electrode and a second electrode of a pair of electrodes.
  • the reference electrode comprises a viscoelastic foam padding provided between the conductive fabric layer and the stretchable fabric layer.
  • the viscoelastic foam padding may be provided between the conductive fabric layer and a backing layer, such as a backing layer affixed to and/or abutting the stretchable fabric layer.
  • the barrier region forms a substantially lemniscate shape around the first electrode and the second electrode.
  • the lemniscate shape formed around the first electrode and the second electrode of a pair of electrodes may be a geometrical surface having the shape of a lemniscate, a figure-eight or an “-symbol.
  • the first electrode may be provided at a first interior region of the lemniscate shape and the second electrode provided a second interior region of the lemniscate shape, such that bodily fluids like sweat are kept within said interior regions and/or repelled therefrom by maintaining said hydrophobic fabric portion in contact with the skin. It is advantageous that the barrier region may be provided around the first electrode and the second electrode so that the presence of sweat can be maintained a controllable or substantially constant level.
  • providing a mostly fixed amount of an electrolytic fluid, such as sweat, at each of the interior regions of the lemniscate shape may simultaneously help to increase the electrical conductivity of the skin-electrode interface while preventing bridging between the electrodes.
  • the viscoelastic foam paddings of the electrodes and/or the barrier region are memory foam slabs with a height of at least 0.5 mm, such as more than 1mm, between 2 mm and 10 mm, and preferably between 1 mm and 3 mm.
  • a surface feature is provided at a skin-contacting region formed by one or more of the stretchable fabric layer, the bonding means, the conductive fabric layer or the hydrophobic fabric portion.
  • the skin-contacting region may be understood as a region with a skin-electrode interface.
  • the surface feature may be configured to form channels for venting moisture when pressed against the skin of a user, such as a plurality of ridges formed by stitching the barrier region.
  • the viscoelastic foam pads may include a dense memory foam which increases the thermal insulation of the area closest to each electrode because of the viscoelastic foam padding provided behind a conductive fabric layer making up a skin-contacting region. Providing a skin-tight electrode with increased thermal insulation to the skin may in some circumstances increase perspiration, thus making the bridging problem between closely spaced surface electrodes worse.
  • a surface feature at or adjacent to each viscoelastic foam pad such as surface features in the form of a cross-sectional ripple or wavy skin-electrode interface as viewed along the skin, the surface feature may act to form air channels at the skin-electrode interface.
  • Surface features may indentations, protrusions or like geometrical shapes formed at a skin-electrode interface.
  • the skin-contacting region having surface features may allow moisture to evaporate and cool the skin.
  • the surface feature is one or more air channels.
  • a wearable sensor system comprising a compression garment for sensing an electrical signal at the skin of a user as set out in the first aspect.
  • the wearable sensor system comprises an electronic device operably connectable to said compression garment having a processor and a sensor circuit configured to measure an electrical signal by means of the at least one pair of electrodes.
  • the electrodes are operably connectable by means of said conductive leads to the electronic device in a bipolar electrode configuration, said sensor circuit including a differential signal acquisition element configured to compare said electrical signals to obtain a surface electromyography.
  • the electronic device comprises a communication means, such as a wireless communication interface, configured to transmit data to a user terminal, such as a smart phone.
  • a communication means such as a wireless communication interface
  • a user terminal such as a smart phone.
  • the electronic device comprises a data memory, such as a computer- readable storage, configured to store data representing electrical signals measured at the skin of a user, said data being obtained over an extended period of time of the user wearing the wearable device, such as several days.
  • the electronic device may comprise an energy reservoir, such as an electrical battery, configured to provide power to the electrical circuit for an extended period of time.
  • a fastening means may be provided at the electronic device and/or at the compression garment to allow detachably affixing the electronic device to the compression garment.
  • the electronic device is irremovably fixed to the compression garment, such as by the electronic circuit being a flexible printed circuit board which is sown, bonded or otherwise affixed to or between one or more fabric layers.
  • personal health tracking systems and associated software exist that provide connectivity to smart wearable devices so that the wearer can be provided with real-time health data at a user terminal, for example to alert the wearer of said device of a potential medical issue requiring some form of user action or assistance.
  • real-time health data may be processed to automatically characterize past and/or current levels of physical activity of the user, e.g. using said health data to dichotomize between sedentary and non-sedentary periods of the user.
  • a method of estimating a level of muscle activity of a user being mostly non-sedentary for an extended period of time using a wearable sensor system as set out in the second aspect comprising the steps of: reversibly attaching the conductive leads to the sensor circuit, activating the electronic device, such as by means of a user interface, measuring a sequence of electrical signals at the skin of the user during the period of time the wearable sensor system is worn, comparing electrical signals to obtain a surface electromyography, and calculating a time-series of an estimated level of muscle activity of the user based on the surface electromyography.
  • the calculated time-series may be provided to an end user by data transmission, or alternatively, the estimated level of muscle activity may be presented via a display.
  • the method may provide an improved solution for estimating a level of muscle activity of a user, which remains operable and comfortable to wear when the user is mostly non-sedentary for an extended period of time.
  • a compression garment for sensing an electrical signal at the skin when worn by a user, the compression garment comprising:
  • a stretchable fabric layer configured to maintain said electrodes in contact with the skin of a user wearing the compression garment
  • each electrode in the plurality of electrodes comprises:
  • the plurality of electrodes includes a pair of electrodes substantially electrically isolated from each other, and wherein a barrier region is provided in a space between that pair of electrodes, the barrier region comprising:
  • hydrophobic fabric portion configured to be maintained in contact with the skin, such as by extending in said space.
  • the polymer top layer is made of a polymeric material.
  • the polymer top layer is made from a conductive polymeric material, such as a flexible and intrinsically conducting polymer.
  • the polymer top layer comprises metal strands or a metal matrix embedded in the polymeric material.
  • the polymeric material is polymerized siloxane, polysiloxane or silicone.
  • the polymeric material may include conductivity-enhancing dopants.
  • the polymer top layer may be provided substantially covering the conductive fabric layer to form a skin-contacting region.
  • a hydrophobic fabric layer is configured to be maintained in contact with the skin by forming another skin-contacting region between the pair of electrodes.
  • at least a part of the polymer top layer of the electrodes covers the hydrophobic fabric layer.
  • the hydrophobic fabric portion is a fabric sheet with a polymeric hydrophobic top layer.
  • the conductive fabric layer is a fabric layer which is made conductive by means of the polymer top layer being conductive.
  • the hydrophobic fabric portion is preferably extended in the space between a pair of electrodes so that any substantially straight line between the skin-contacting regions of one electrode and another electrode in that pair of electrodes, with the line being “drawn” substantially along the skin, intersects with the hydrophobic fabric layer.
  • Each electrode may comprise a viscoelastic foam padding provided between the conductive fabric layer and the stretchable fabric layer.
  • the barrier region between the pair of electrodes being substantially electrically isolated from each other may comprise a viscoelastic foam padding provided between the hydrophobic fabric layer and the stretchable fabric layer.
  • the barrier region may be affixed to the stretchable fabric layer and/or to one or more fabric materials of the electrodes.
  • Figure 1 illustrates a compression garment in a first embodiment having two pairs of fabric electrodes, wherein a barrier region extends transversally in a space between a first electrode and a second electrode of each pair of fabric electrodes.
  • Figure 2 illustrates a planar view of the compression garment in a first embodiment, e.g. as illustrated in Fig. 1 , wherein the compression garment is essentially formed from a stretchable fabric layer which is substantially flat and stitched together.
  • Figure 3 is a schematic representation of a compression garment in one or more embodiments, wherein a barrier region extends transversally in a space between a first electrode and a second electrode, said electrodes being substantially round.
  • Figure 4a illustrates a cross-sectional view of a fabric electrode according to one or more embodiments, e.g. as illustrated in Fig. 3, wherein a foam pad and a backing layer is provided between a conductive fabric layer and a stretchable fabric layer.
  • Figure 4b illustrates another cross-sectional view of a barrier region according to one or more embodiments, e.g. as illustrated in Fig. 3, wherein another foam pad is provided between a hydrophobic fabric layer and a stretchable fabric layer.
  • Figure 5a illustrates a cross-sectional view along a longitudinal axis defined between an electrode pair according to one or more embodiments, e.g. as illustrated in Fig. 3, wherein a fabric material of each electrode is affixed to a stretchable fabric layer by means of separate bonding layers made of a thermoformable material.
  • Figure 5b illustrates a cross-sectional view along a longitudinal axis defined between an electrode pair according to one or more embodiments, e.g. as illustrated in Fig.
  • Figure 5c illustrates a cross-sectional view along a longitudinal axis defined between an electrode pair according to one or more embodiments, e.g. as illustrated in Fig. 3, wherein a backing layer is provided abutting a stretchable fabric layer and extending substantially along a plurality of separate foam padded regions provided for each of the electrodes in the pair and a barrier region in a space between the electrodes.
  • Figure 6 illustrates a compression garment in a second embodiment having two pairs of fabric electrodes, wherein a barrier region extends circumferentially around each electrode in each pair of electrodes in a co-annular space being substantially symmetrically arranged between said electrodes and forming a lemniscate shape.
  • Figure 7 illustrates a planar view of the compression garment in a second embodiment, e.g. as illustrated in Fig. 6, wherein the compression garment is essentially formed from a stretchable fabric layer which is substantially flat and stitched together, and wherein the electrodes are bonded together in pairs.
  • Figure 8 illustrates a compression garment in a third embodiment having two pairs of fabric electrodes, wherein a barrier region extends circumferentially around each electrode in an annular space arranged substantially concentrically to the electrode.
  • Figure 9 illustrates a planar view of the compression garment in a second embodiment, e.g. as illustrated in Fig. 8, wherein the compression garment is essentially formed from a stretchable fabric layer which is substantially flat and stitched together, and wherein the electrodes are bonded individually.
  • Figure 10 illustrates a user wearing a compression garment in the form of a sleeve comprising a pair of electrodes and a reference electrode connected by conductive leads to an electronic device removably attached to the sleeve.
  • Figure 11a illustrates a planar view of a first assembly for a compression garment in a first embodiment, e.g. as illustrated in Figs. 1-3, wherein the assembly comprises backing layers for electrodes and barrier region atop a stretchable fabric layer.
  • Figure 11 b illustrates a planar view of a second assembly to be stacked on top of a first assembly for a compression garment in a first embodiment, e.g. as illustrated in Fig. 11a, wherein the assembly further comprises two patches of a conductive fabric each connected to a lead and a hydrophobic fabric arranged therein between.
  • Figure 11 c illustrates a planar view a third assembly to be stacked on top of a first assembly and a second assembly for a compression garment in a first embodiment, e.g. as illustrated in Figs. 11 a-11 b, wherein the assembly further comprises bonding means in the form of a thermoformable material layer with a plurality of openings.
  • Exemplary examples are described herein with reference to cross section illustrations that are schematic illustrations of idealized examples, wherein like reference numerals refer to like elements throughout the specification. As such, variations from the shapes of the illustrations as a result, for example, of manufacturing techniques and/or tolerances, are to be expected. Thus, examples described herein should not be construed as limited to the particular shapes of regions as illustrated herein but are to include deviations in shapes that result, for example, from manufacturing. For example, a region illustrated or described as flat may have rough and/or nonlinear features. Moreover, sharp angles that are illustrated may be rounded. Thus, the regions illustrated in the figures are schematic in nature and their shapes are not intended to illustrate the precise shape of a region and are not intended to limit the scope of the present claims. Some of the parts which are not associated with the description may not be provided in order to specifically describe exemplary examples of the present disclosure.
  • FIG. 1 is an perspective illustration of a compression garment 100 for sensing an electrical signal at the skin of a user according to a first embodiment of the present disclosure.
  • the compression garment 100 is for example a compression sleeve 101 , as shown here for illustration purposes, which is configured to fit and be retained on the arm of a user.
  • the compression garment 100 may be a sock, a knee brace, a chest strap or a similar close-fitting compression garment 100.
  • the compression garment 100,101 comprises at least one pair of electrodes 110, 110a-b made of fabric materials. In this illustration, only one pair of electrodes 110 is visible from the current view point.
  • a second pair of electrodes 110 substantially identical or equivalent to the pair of electrodes 110 may be provided at another position than the position of the pair of electrodes 110 shown here.
  • a pair of electrodes 110 includes a first electrode 110a and a second electrode 110b. The first electrode 110a and the second electrode 110b are provided a distance apart, as for example shown here.
  • the compression garment 100 in the form of compression sleeves 101 are shown in their “inside out” or reversed state unless otherwise noted.
  • the electrodes 110,11 Oa-b are shown on an outside surface of the sleeve 101 but it is to be noted that the illustrated garments 100,101 and their constituent parts are generally flexible or resilient enough to be turned from their “inside out” state into a regular “right side out” or operable state, wherein the electrodes 110,11 Oa-b are provided at an inner surface of the sleeve 101 such that said electrodes 110,11 Oa-b are maintained in contact with the skin of a user wearing the sleeve 101 on an arm.
  • the compression garment 100,101 comprises a stretchable fabric layer 120.
  • the stretchable fabric layer 120 is made of a stretchable fabric material, which may for example be formed into a substantially tubular shape making up a substantial part of the compression sleeve 101.
  • the stretchable fabric layer 120 may be formed into a suitable shape for the compression sleeve 101 from a substantially flat sheet 120 of stretchable fabric.
  • a tubular shape may for example be formed from a substantially rectangular sheet 120 of a stretchable fabric where two opposite sides of said sheet are bonded together by stitching 146 where said two opposite sides overlap.
  • the stretchable fabric layer 120 is configured to maintain the electrodes 110,11 Oa-b in contact with the skin of a user wearing the compression garment 100,101 .
  • the compression provided by stretching of the stretchable fabric layer 120 to a circumference suitable for fitting onto an arm may be sufficient to maintain the electrodes 110,11 Oa-b in contact with the skin.
  • the friction provided by compressing e.g. fabric materials of the electrodes 110, 110a-b onto the skin may maintain the fabric electrodes 110,11 Oa-b securely in place.
  • the compression garment 100,101 comprises bonding means 140 in the form of a bonding layer for affixing the fabric materials 130 of the electrodes 110,110a-b to the stretchable fabric layer 120.
  • the bonding layer 140 may be made from a sheet of a heat-pressable material, which is cut or otherwise arranged into a shape suitable for affixing the fabric electrodes 110,11 Oa-b to the stretchable fabric layer 120.
  • the bonding layer 140 may be made from a thermoformable material, such as vinyl polymer. Having a thermoformable bonding layer 140 may provide that one or more of the fabric materials of the electrodes 110,11 Oa-b can be affixed to the stretchable fabric layer 120, or optionally to a backing layer or another fabric material, by means of heat-pressing e.g. using a two-piece mold for applying heat and pressure.
  • the bonding layer 140 may be made from a substantially non-conductive polymer material, such as polypropylene. Employing a substantially non-conductive polymer layer as the bonding layer 140 may provide that the electrodes 110,11 Oa-b remain substantially electrically isolated from each other when affixed to the garment 100.
  • the bonding layer 140 shown here is provided at a periphery of each of the fabric electrodes 110a-b so that fabric materials of one electrodes 110a; 110b is provided a distance apart from fabric materials of the other electrode 110b;110a.
  • Each electrode 110,11 Oa-b in the pair of electrodes 110,11 Oa-b comprising a first electrode 110a and a second electrode 110b is shown here comprising a conductive fabric layer 130.
  • the conductive fabric layer 130 is shown as a substantially circular patch of a conductive fabric, which may be a woven textile comprising silver or silver chloride threads woven into said woven textile.
  • the conductive fabric layer 130 of the first electrode 110a is electrically connected to a conductive lead 132 which is represented by a thick solid line terminating at the boundary of the conductive fabric layer 130 of the first electrode 110a.
  • the conductive fabric layer 130 of the second electrode 110a is electrically connected to another conductive lead 132 here represented by another thick solid line terminating at the boundary of the conductive fabric layer 130 of the second electrode 110b.
  • Each of the electrodes 110,11 Oa-b shown here may comprise a viscoelastic foam padding 160 (not shown) provided between the conductive fabric layer 130 and the stretchable fabric layer 120.
  • the viscoelastic foam padding may be a substantially circular slab of a certain height, such as few millimeters, which is provided between the substantially circular patch 130 of a conductive fabric and the stretchable fabric layer 120, and thus the viscoelastic foam padding 160 is not depicted here as it may be entirely covered by the conductive fabric layer 130 and the bonding layer 140.
  • the compression sleeve 100,101 is shown having at least one pair of electrodes 110,110a-b represented by the first electrode 110a and the second electrode 110b being provided in relative close proximity to each other, such as having a distance between them of 1-10cm measured from respective conductive fabric layers 130.
  • a space 115 is provided between the first electrode 110a and the second electrode 110b.
  • a stretch of hydrophobic fabric 180 is shown extended substantially co- planar with the stretchable fabric layer 120 in the space 115 provided between the pair of fabric electrodes 110a, 110b.
  • a barrier region 114 may be formed in such a space 115 between the first electrode 110a and the second electrode 110b e.g. by the hydrophobic fabric layer 180 being configured to be maintained in contact with the skin of the user between skin-contacting regions where the two electrodes 110,11 Oa-b would then be in contact with said skin.
  • the barrier region 114 extends transversally in the space between the first electrode 110a and the second electrode 110b of the pair of electrodes 110,11 Oa-b. Extending transversally in this example be understood as extending in a transversal direction in plane with the stretchable fabric layer 120, said transversal direction defining e.g. an axis of substantial mirror symmetry between the pair of electrodes 110,11 Oa-b.
  • the conductive fabric layer 180 is shown as a substantially elongated dumbbell-shaped patch of a hydrophobic fabric, which may be a fabric treated with a water-repellent agent, such as fluorocarbon, and/or a thin film of hydrophobic nanoparticles.
  • the barrier region 114 shown here may comprise a viscoelastic foam padding 160 (not shown) provided between the hydrophobic fabric layer 180 and the stretchable fabric layer 120.
  • the viscoelastic foam padding may be a substantially elongated or oval slab of a certain height, such as few millimeters, which is provided between the substantially elongated dumbbell-shaped patch 180 of a hydrophobic fabric and the stretchable fabric layer 120.
  • the viscoelastic foam padding 160 is likewise not depicted here as it may be entirely covered by the hydrophobic fabric layer 180 and the bonding layer 140, as discussed in relation to the electrode padding above.
  • the bonding layer 140 may be provided for affixing the fabric materials of the electrodes 110,11 Oa-b and the barrier region 114 to adjacent parts of the stretchable fabric layer 120 and/or each other.
  • the bonding layer 140 is provided as a border of a certain width between adjoining fabric materials, so that the bonding layer 140 may be arranged with a consistently large contact area to bond well with said fabric materials while not taking up too much skin contact area.
  • the compression sleeve 100,101 comprises a reference electrode 111 , which may also be made of fabric materials in an identical manner or substantially similar to the fabric electrodes 110,110a-b.
  • the reference electrode 111 is provided adjacent the pair of electrodes 110,11 Oa-b and is configured to be maintained in contact with the skin of a user wearing the compression sleeve 100,101 by means of the stretchable fabric layer 120.
  • the compression sleeve 100,101 has a substantially tubular shape to function as a sleeve.
  • the far end of the tubular sleeve 101 is here shown with a narrower opening than the other end of the tubular sleeve 101 , which has a larger circular opening.
  • the reference electrode 111 is provided proximate a narrow end of the compression sleeve 100,101 whereby the reference electrode 111 is configured to be maintained in contact with the skin at a wrist portion of the arm of a user where there may be a substantially greater bony prominence than at an underarm portion, where the electrodes 110,11 Oa-b are configured to be kept in skin contact.
  • the reference electrode 111 comprises a conductive fabric layer 130, which may be substantially electrically isolated from the other electrodes 110,11 Oa-b.
  • the bonding layer 140 affixes the conductive fabric layer 130 to the stretchable fabric layer 120.
  • a viscoelastic foam padding may be provided between the conductive fabric layer 130 and the stretchable fabric layer 120 in a similar manner, e.g. to provide cushioning to the reference electrode 111 so that the reference electrode 111 can be maintained in contact with the skin of a user wearing the compression sleeve 101 ,101 by a compression force provided by stretching of the stretchable fabric layer 120.
  • the conductive fabric layer 130 of the reference electrode 111 is electrically connected to a conductive lead 132 which is represented by a thick solid line terminating at the boundary of the conductive fabric layer 130 of the reference electrode 111.
  • a conductive lead 132 which is represented by a thick solid line terminating at the boundary of the conductive fabric layer 130 of the reference electrode 111.
  • FIG. 2 is an illustration of a planar view of a compression garment 100 according to a first embodiment of the present disclosure, e.g. as illustrated in Fig. 1 , or with a slight disembodiment thereof included to better illustrate the first embodiment.
  • the compression garment 100 is shown in the form of a compression sleeve 101 which is essentially formed from a stretchable fabric layer 120 which is a substantially flat rectangular sheet of stretchable fabric, such as a nylon/spandex composite fabric.
  • a tubular shape of the compression sleeve 100,101 is shown laid out in a flattened shape, e.g. by opposite sides of the substantially flat rectangular sheet 120 not yet having been stitched together by a row of stitching 146 to form a tube.
  • the compression sleeve 100,101 comprises at least one pair of electrodes 110,11 Oa-b.
  • two pairs of electrodes 110,11 Oa-b are shown.
  • One pair of electrodes is shown comprising a first electrode 110a and a second electrode 110b shown in a pairwise arrangement, such as e.g. illustrated in Fig. 1.
  • Another pair of electrodes 110 is shown in a like arrangement, the pair of electrodes 110 also comprising two electrodes 110 arranged similarly to the pair of electrodes shown comprising the first 110a and second electrodes 110b.
  • Having more than one pair of electrodes 110,110a-b may provide that the electrical signal detected at the skin of a user may be obtained with an increased accuracy by e.g. having an electrical circuit coupled to a greater number of electrodes 110,11 Oa-b, and optionally a reference electrode 111 , via conductive leads 132.
  • FIG 3 is a schematic illustration of part of a compression garment 100 according to one or more embodiments of the present disclosure.
  • the compression garment 100 comprises a stretchable fabric layer 120, which may act as a backing for affixing other fabric materials in addition to providing a compressive function to the skin of a user wearing the garment 100, as for example discussed in relation to Figs. 1-2.
  • the compression garment 100 comprises a pair of fabric electrodes 110a, 110b.
  • Each of the electrodes 110a, 110b comprise a substantially circular patch of conductive fabric 130, which is affixed to the stretchable fabric layer 120 by a ring of a bonding means 140 arranged substantially concentrically to the circular conductive fabric patch 130.
  • the conductive fabric layer 130 may be exposed through an opening in the bonding layer 140 affixing the electrode 110a-b to the stretchable fabric layer 120.
  • a circular skincontacting region may be formed of the electrode 110a-b where a part of the conductive fabric layer 130 is exposed through said opening in the bonding layer 140.
  • the conductive fabric layer 130 is exposed in a circular region having a first diameter D1 , as is illustrated for the first electrode 110a.
  • the bonding means 140 is arranged as a annular ring of a bonding material, such as a heat-pressable and/or thermoformable material, which is centered on the circular region of the first electrode 110a and extends from an inner diameter substantially equal to the first diameter D1 to an outer diameter D2 greater than the first diameter D1.
  • the bonding means 140 may e.g. have been stacked over or atop parts of the conductive fabric layer 130, such that said parts of the conductive fabric layer 130 are covered and thus not visible from the view point being illustrated here.
  • the pair of fabric electrodes 110a, 110b are affixed separately to the stretchable fabric layer 120 such that the fabric electrodes 110a, 110b are provided a distance apart from each other measured along a longitudinal axis defined between points B and B’ passing through the centers of said fabric electrodes 110a, 110b.
  • a transversal axis defined between points A and A’ is also shown passing through only the center of a first electrode 110a, the transversal axis intersecting the longitudinal axis at a substantially right angle. Both the transversal axis A-A’ and the longitudinal axis B-B’ are seen as being parallel to or following the stretchable fabric layer 120.
  • a barrier region 114 is shown extending transversally A-A’ in a space 115 between a first electrode 110a and a second electrode 110b of a pair of electrodes 110a-b.
  • the barrier region 114 has an elongated rectangular shape which extends transversally, i.e. along a transversal axis A-A’, relative to a longitudinal axis B-B’ defined between the first electrode 110a and the second electrode 110b.
  • the barrier region 114 may extend in the space 115 in a number of different ways, for example as shown here.
  • the barrier region 114 comprises a hydrophobic fabric layer 180 which is extended in said space 115 and affixed to the stretchable fabric layer 120 by bonding means 140.
  • the barrier region 114 is shown with an elongated rectangular patch of hydrophobic fabric 180, which is affixed to the stretchable fabric layer 120 by a rectangular surrounding shape of a bonding means 140 arranged substantially circumferentially or peripherally to the rectangular hydrophobic fabric patch 180.
  • the hydrophobic fabric layer 180 may be exposed through another opening in the bonding layer 140 affixing the barrier 114 to the stretchable fabric layer 120.
  • a rectangular skin-contacting region may be formed of the barrier 114 where a part of the hydrophobic fabric layer 180 is exposed through said another opening in the bonding layer 140.
  • the hydrophobic fabric layer 180 is exposed in a rectangular region having a first width W1 , as is illustrated for the barrier region 114.
  • the bonding means 140 affixing the barrier 114 to the stretchable fabric layer 112 is arranged as a rectangular outline of a bonding material, such as a heat-pressable and/or thermoformable material, which is centered on the rectangular region of the barrier 114 and extends longitudinally between the electrodes 110a, 110b from an opening having the first width W1 to an second width W2 greater than the first width W1.
  • the bonding means 140 may e.g. have been stacked over or atop parts of the hydrophobic fabric layer 180, such that said parts of the hydrophobic fabric layer 180 are covered and thus not visible from the view point being illustrated here.
  • the longitudinal axis B-B’ defines a longitudinal direction between a first electrode 110a and a second electrode 110b of the pair of fabric electrodes 110a, 110b which may in some embodiments span the overall shortest pathway P’ between the first electrode 110a and the second electrode 110b measured along an skin-contacting side of the compression garment 100 substantially in a straight line along the plane of the stretchable fabric layer 120, or similarly along the skin of a user wearing said compression garment.
  • the overall shortest pathway P’ between the pair of fabric electrodes 110a, 110b along the skin is shown traversing the barrier region 114 in a substantially straight line P’ represented as a thick dash-dotted line.
  • a shortest path P between the first electrode 110a and the second electrode 110b around the barrier region 114 is shown as a piecewise linear curve P represented as a thick dash- dotted line.
  • the shortest path P is shown following a pathway avoiding the barrier region 114 is the shortest possible way between the electrodes 110a-b.
  • the barrier region 114 provides that the shortest path P is at least 25% longer than an overall shortest path P’ between the first electrode 110a and the second electrode 110b measured substantially along the skin of a user wearing the compression garment 100.
  • providing a barrier region 114 in this way extending in the space between two closely spaced electrodes 110a-b may be adapted or modified to make the shortest path P around the barrier region 114 even longer compared to the overall shortest path P’, such as between 50% and 900% longer, such as about 100%-200% longer. It is furthermore contemplated that by maintaining a skin-contacting region formed of the hydrophobic fabric layer 180 in good contact with the skin of a user wearing the compression garment 100, e.g. by a compressive function of the stretchable fabric layer 120, may act to divert or reduce the presence of sweat in the space 115 between the two electrodes 110a-b. By less of a substantially electrically-conductive electrolytic fluid, i.e.
  • the compression garment 100 provides that weakly conductive pathways along the skin, e.g. path P’, do not contribute significantly to bridging of the electrodes 110a-b.
  • Figure 4a is an illustration of a cross-sectional view V1 of an electrode 110 made of fabric materials according to one or more embodiments, e.g. as illustrated in Fig. 3.
  • the cross- sectional view V1 is provided across the transversal direction A-A’ of the electrode 110 from the view point V1 illustrated in Fig. 3 from point B towards B’.
  • a stretchable fabric layer 120 is illustrated as a backing material for affixing electrodes 110 to the compression garment 100, but in other embodiments another semi-rigid fabric or non-fabric backing layer may be provided as a stand-in for this layer 120.
  • the electrode 110 provides a skin-contacting region 112 protruding a small height H from the stretchable fabric layer 120, thereby providing for increased skin contact.
  • the fabric electrode 110 comprises a conductive fabric layer 130 being draped over a viscoelastic foam pad 160, which is provided between the conductive fabric layer 130 and the stretchable fabric layer 120.
  • the fabric electrode 110 comprises a back layer 150 provided between the viscoelastic foam pad 160 and the stretchable fabric layer 120, thereby e.g. giving an certain rigidity to an underside of the foam pad 160.
  • An outer portion of the conductive fabric layer 130 shown abutting or adjacent to the stretchable fabric layer 120 is affixed to the stretchable fabric layer 120 by a bonding layer 140, which substantially surrounds the fabric electrode 100, e.g. as illustrated in Fig. 3.
  • a bonding layer 140 shown as two parts may be a single layer 140.
  • the conductive fabric layer 130 is shown having a fitted dimension D’, which may be within the range of an inner diameter D1 and an outer diameter D2 of a ring-shaped bonding layer 140, e.g. as discussed in relation to Fig. 3, so that the bonding layer 140 is provided with enough contact area to bond the conductive fabric layer 130 to the stretchable fabric layer 120, thereby acting to affix the fabric materials 130 and constituent parts 150,160 of the electrode 110 to the compression garment 100.
  • a conducting lead 132 is provided in electrical contact with the conductive fabric layer 130 by being affixed thereto by the bonding layer 140.
  • the conductive lead 132 is substantially contained between the stretchable fabric layer 120 and the bonding layer 140.
  • the conductive leads 132 are prevented from causing a short circuit by contacting the skin of a user wearing the compression garment 100.
  • Figure 4b is an illustration of another cross-sectional view V2 of a barrier region 114 according to one or more embodiments, e.g. as illustrated in Fig. 3.
  • another cross-sectional view V2 is provided as a longitudinal cut-through across the barrier region 114 e.g. from the view point V2 illustrated in Fig. 3, i.e. viewed along a direction parallel to the direction from point A towards point A’ illustrated in Fig. 3.
  • a stretchable fabric layer 120 is illustrated as a backing material for affixing the barrier 114 to the compression garment 100, but in other embodiments another semi-rigid fabric or non-fabric backing layer may be provided as a stand-in for this layer 120.
  • the barrier 114 provides a skin-contacting region 112 protruding a small height H’ from the stretchable fabric layer 120, thereby providing for increased skin contact.
  • the barrier region 114 may protrude a distance H’ from the stretchable fabric layer 120, which is substantially equal to a distance H protruded by either or both of a first electrode 110a and a second electrode 110b, e.g. as illustrated in Fig. 4a, of a pair of fabric electrodes 110,11 Oa-b between which the barrier 114 is provided, e.g. as illustrated in Fig. 3. This may provide that both the pair of electrodes 110,110a-b and the barrier region 114 are provided in substantially equally good skin contact.
  • the barrier region 114 comprises a hydrophobic fabric layer 180 being draped over a viscoelastic foam pad 160, which is provided between the hydrophobic fabric layer 180 and the stretchable fabric layer 120.
  • the barrier 114 may comprise a back layer 150 provided between the viscoelastic foam pad 160 and the stretchable fabric layer 120, as e.g. illustrated in Fig. 4a for the electrode 110, although not shown here.
  • An outer portion of the hydrophobic fabric layer 180 shown abutting to the stretchable fabric layer 120 is affixed to the stretchable fabric layer 120 by a bonding layer 140, which substantially surrounds the barrier region 114, e.g. as also illustrated in Fig. 3.
  • a bonding layer 140 shown as two parts may be a single layer 140, and may further be conjoined with a bonding layer 140 for one of the electrodes 110,11 Oa-b.
  • the hydrophobic fabric layer 180 is shown having a fitted width W’, which may e.g. be within the range of an first width W1 and an second width W2 of a substantially rectangular outline shape of the bonding layer 140, e.g. as discussed in relation to Fig. 3, so that the bonding layer 140 is provided with enough contact area to bond the hydrophobic fabric layer 180 to the stretchable fabric layer 120, thereby acting to affix the fabric materials 180 and the viscoelastic foam pad 160 of the barrier region 114 to the compression garment 100.
  • viscoelastic foam padding 160 illustrated here is another viscoelastic foam pad relative to the viscoelastic foam pads 160 of each electrode 110,110a-b.
  • one viscoelastic foam pad 160 may be provided between the stretchable fabric layer 120 and the conductive fabric layer 130 of each electrode 110,110a-b and another viscoelastic foam pad 160 is provided between the hydrophobic fabric layer 180 and the stretchable fabric layer 120.
  • the pads 160 may be shared.
  • the barrier region 114 is configured to allow deformation of the hydrophobic fabric layer 180 under compression provided by the stretchable fabric layer 120, such that a bodily fluid like sweat is repelled from or diverted around said barrier region 114 by maintaining said hydrophobic fabric layer 180 in contact with the skin of a user.
  • the viscoelastic foam pads 160 being provided within the electrodes 110,11 Oa-b and/or the barrier region 114 may be memory foam slabs with a height H of at least 2 mm, such as between 2 mm and 10 mm, preferably between 2 mm and 3 mm. Having a height of at least 2 mm may improve skin contact by allowing greater deformation.
  • Figure 5a is an illustration of yet another cross-sectional view V2 of a pair of fabric electrodes 110 with a barrier region 114 disposed therein between according to one or more embodiments, e.g. as illustrated in Figs. 1-3.
  • the cross-sectional view V2 is provided as a longitudinal cut-through between the pair of fabric electrodes 110 and across the barrier region 114 e.g. from the view point V2 illustrated in Fig. 3.
  • the electrodes 110 and barrier 114 are affixed to a stretchable fabric layer 120, which makes up a wearable portion of a compression garment 100, e.g. a tubular sleeve 101 as discussed in relation to Figs. 1-2.
  • the electrodes 110 may be made essentially from fabric materials 160 and the barrier region 114 may be essentially made from fabric materials 180, said fabric materials 160,180 being affixed to the stretchable fabric layer 120 by means of one or more bonding layers 140.
  • Each of the two electrodes 110 comprises a conductive fabric layer 130 for sensing an electrical signal at the skin of a user and a viscoelastic foam pad 160 is provided in a cavity formed between the conductive fabric layer 130 and the stretchable fabric layer 120, thereby providing a cushioning to improve the conformity of the electrode 110 to bumps or curvatures at the skin at least at skin-contacting regions 112 of the compression garment 100.
  • a fabric material 130 of each electrode 110 is affixed to the stretchable fabric layer 120 by means of two or more separate bonding layers 140 made of a thermoformable material.
  • the conductive fabric layer 130 of each electrode 110 can thereby be disposed through an suitable opening cut or formed in the bonding layer 140 to form a skin-contacting region 112 e.g. by heat-pressing the one or more bonding layers 140 onto a suitable stacking of fabric layers comprising the conductive fabric layer 130 and the stretchable fabric layer 120.
  • Each of the electrodes 110 is shown comprising a rigid or semi-rigid backing layer 150, which is provided abutting or proximate the stretchable fabric layer 120.
  • the viscoelastic foam pads 160 of each electrode 110 is therefore provided between the conductive fabric layer 130 and the backing layer 150 to provide support to the foam pads 160 so that only a one side facing the skin-contacting region 112 is deformed according to the bumps and curvature of the skin of the user.
  • the barrier region 114 comprises a backing layer 150, which is provided abutting or proximate the stretchable fabric layer 120, wherein the viscoelastic foam pad 160 is provided similarly between the hydrophobic fabric layer 180 and the backing layer 150.
  • the barrier 114 comprises a hydrophobic fabric layer 180 extended in a longitudinal direction between the two electrodes 110.
  • the hydrophobic fabric layer 180 is affixed at the edges to the stretchable fabric layer 120 by another bonding layer 140, which may be arranged peripherally along an outline defined by the edges of the hydrophobic fabric layer 180, as e.g. illustrated in Fig. 3.
  • another bonding layer 140 may be separately arranged circumferentially to and/or substantially concentrically with one of the two electrodes 110.
  • the hydrophobic fabric layer 180 is here shown disposed through another opening in a bonding layer 140 affixing the barrier 114 to the stretchable fabric layer 120 to form another skin-contacting barrier region 114.
  • the barrier 114 is here shown with a rigid or semi-rigid backing layer 150, which provide support to the foam pad 160.
  • Figure 5b is an illustration of yet another cross-sectional view V2 of a pair of fabric electrodes 110a-b with a barrier region 114 disposed therein between according to one or more further embodiments, e.g. as illustrated in Figs. 1-3.
  • Fig. 5a which illustrates embodiments where the electrodes 110a-b and barrier region 114 are somewhat further apart, the fabric materials 130 of the electrodes 110 and the fabric material 180 of the barrier region 114 are here provided closer together.
  • the bonding layers 140 affixing the electrodes 110a-b and the barrier 114 to the stretchable fabric layer 120 are in this example not directly abutting the stretchable fabric layer 120 at the electrode-barrier interface, which may prevent the bonding layer 140 from forming sufficient mechanical contact to facilitate bonding. Instead, a stitching 146 may be sewn through the bonding layer 140 and the stretchable fabric layer 120 or via the fabric materials 130,160 to affix the electrodes 110a-b and the barrier 114 to the stretchable fabric layer 120 of the compression garment 100.
  • Figure 5c is an illustration of yet another cross-sectional view V2 of a pair of fabric electrodes 110 with a barrier region 114 disposed therein between according to one or more yet further embodiments, e.g. as illustrated in Figs. 1-3.
  • the barrier region 114 here is not directly bonded onto the stretchable fabric layer 120.
  • a larger shared backing layer 150 is instead provided abutting the stretchable fabric layer 120 extending longitudinally between one electrode 110 and another electrode 110.
  • the backing layer 150 is shown provided at a position which provides backing support for three separate viscoelastic foam padded regions 160 provided within cavities of the two electrodes 110 and the barrier 114 positioned in the space between the electrodes 110.
  • a bonding layer 140 is shown at an electrode-barrier interface affixing the hydrophobic fabric material 180 to the backing layer 150.
  • the backing layer 150 is connected to the stretchable fabric layer 120 by another portion of bonding layer 140 provided at the far edges of the electrodes 110, thereby affixing both the electrodes 110 and the barrier 114 to the stretchable fabric layer 120 via the shared backing layer 150.
  • FIG. 6 is an perspective illustration of a compression garment 100 in the form of a sleeve 101 fitted with electrodes 110a-b for sensing an electrical signal at the skin of a user according to a second embodiment of the present disclosure.
  • a compression garment 100,101 is shown in a second embodiment having a barrier region 114 in a space 115 between a pair of electrodes 110,11 Oa-b, wherein said barrier region 114 extends further around the electrodes 110,110a-b to effectively surround them.
  • the compression garment 100,101 comprises at least one pair of electrodes 110,11 Oa-b made of fabric materials where only one pair of electrodes 110 is visible from the current view point.
  • the pair of electrodes 110 includes a first electrode 110a and a second electrode 110b, which are closely spaced relative to each other, i.e. are provided a smaller distance apart than e.g. illustrated for the first embodiment in Fig. 1 .
  • the barrier region 114 here comprises a hydrophobic fabric layer 180 which extends circumferentially around the first electrode 110a and the second electrode 110b and in a space 115 between said pair of electrodes 110,110a-b.
  • the barrier region 114 thus forms a substantially lemniscate shape around the first electrode 110a and the second electrode 110b.
  • the first electrode 110a is provided at a first interior region of the lemniscate shape and the second electrode 110b is provided a second interior region of the lemniscate shape, such that bodily fluids like sweat may be kept within said interior regions and/or repelled by said barrier region 114 e.g. when maintaining the hydrophobic fabric layer 180 in contact with the skin of a user.
  • the hydrophobic fabric layer 180 may extend in a co-annular space 115 being substantially symmetrically arranged between said pair of electrodes 110,11 Oa-b and forming a lemniscate shape, a figure-eight shape or the like.
  • An outer bonding layer 140 is shown having a similar lemniscate shape for affixing the hydrophobic fabric layer 180 to the stretchable fabric layer 120.
  • Interior edges of the hydrophobic fabric layer 180 thus make up two substantially circular regions, where another bonding layer 140 is shown affixing the fabric materials 130 of each electrode 110,11 Oa-b to the stretchable fabric layer 120, the hydrophobic fabric layer 180 or a backing layer made of another fabric or non-fabric material.
  • the conductive fabric layers 130 of each electrode 110,110a-b is disposed through an opening in the another bonding layer 140 being substantially circular rings of a bonding material to form skin-contacting regions of the electrodes 110,11 Oa-b.
  • the hydrophobic fabric layer 180 is disposed through another opening in the bonding layers 140 to form another skin-contacting barrier region 114 around each of said electrodes 110,110a- b.
  • This arrangement of lemniscate-shaped fabrics may provide for easier alignment of fabric materials 130 of each electrode 110,110a-b relative to the other electrodes 110b; 110a and/or to the fabric materials 180 of the barrier region 114 as bonding layers 140 may be bonded to interconnected parts.
  • Figure 7 is an illustration of a planar view of a compression garment 100 according to a second embodiment of the present disclosure, e.g. as illustrated in Fig. 6, or as a slight disembodiment thereof to better illustrate the second embodiment.
  • the compression garment 100 is shown in the form of a compression sleeve 101 which is essentially formed from a substantially flat rectangular sheet 120 of a stretchable fabric, such as a nylon/spandex composite fabric.
  • the compression sleeve 100,101 comprises at least one pair of electrodes 110,110a-b.
  • two pairs of electrodes 110,110a-b are shown.
  • One pair of electrodes is shown comprising a first electrode 110a and a second electrode 110b shown in a pairwise arrangement, such as e.g. illustrated in Fig. 6, the pair of electrodes 110a, 110b being surrounded by a barrier region 114 which extends around both the first 110a and the second electrode 110b.
  • a second pair of electrodes 110 is shown in lemniscate-shaped arrangement, that pair of electrodes 110 also comprising two electrodes 110 arranged similarly with a barrier region 114 extending around each of the two electrodes 110 of that pair.
  • FIG. 8 is an perspective illustration of a compression garment 100 in the form of a sleeve 101 fitted with electrodes 110a-b for sensing an electrical signal at the skin of a user according to a third embodiment of the present disclosure.
  • the compression garment 100,101 is shown in a third embodiment with a separate barrier region 114 extending around each of a first electrode 110a and a second electrode 110b, which are provided adjacent to each other, thereby forming a first pair of electrodes 110a-b.
  • Both a first barrier region 114 and a second barrier region 114 may be provided in a space 115 between said first electrode 110a and said second electrode 110b, e.g. the first electrode 110a being surrounded by a first barrier region 114 which extends around the first electrode 110a and the second electrode 110b being surrounded by a second barrier region 114 which extends around the second electrode 110a etc. such that a barrier region 114 is provided around each electrode 110,11 Oa-b.
  • the compression garment 100,101 here comprises at least one pair of electrodes 110,11 Oa-b made of fabric materials where only one pair of electrodes 110 is visible from the current view point.
  • any one pair of electrodes 110 may be seen to include a first electrode 110a and a second electrode 110b in more than one way.
  • Two given electrodes 110,11 Oa-b may be seen to belong to the same pair of electrodes 110,11 Oa-b e.g. when said two electrodes 110,11 Oa-b are closer to each other than to electrodes 110 of any other pairs of electrodes 110,110a-b.
  • Figure 9 is an illustration of a planar view of a compression garment 100 according to a third embodiment of the present disclosure, e.g. as illustrated in Fig. 8, or in a slightly modified disembodiment thereof to better illustrate the third embodiment.
  • the compression garment 100 is shown in the form of a compression sleeve 101 formed from a substantially flat rectangular sheet 120 of a stretchable fabric, such as a nylon/spandex composite fabric.
  • the compression sleeve 100,101 comprises at least one pair of electrodes 110,110a-b. In this illustration, two pairs of electrodes 110,110a-b are shown.
  • One pair of electrodes is shown comprising a first electrode 110a and a second electrode 110b which are provided adjacent to each other, such as e.g. illustrated in Fig. 8, each of the electrodes 110a, 110b being surrounded by a separate barrier region 114 which extends around the relevant electrode 110a, 110b.
  • a second pair of electrodes 110 is shown in a similar arrangement comprising two individually provided electrodes 110 each being surrounded similarly with a barrier region 114 extending around one of said two electrodes 110.
  • a much greater number of electrical signals may be detectable at the skin by any combination of two electrodes 110,110a-b substantially electrically isolated from each other and having at least one barrier region 114 provided in a space 115 extending between the other electrodes 110,11 Oa-b.
  • each of said four electrodes 110,110a-b have two separate barrier regions 114 between that electrode 110a and the other three electrodes 110,110b.
  • a barrier region 114 extending around each electrode 110,11 Oa-b e.g. in an annular space 115 arranged substantially centered at a circular electrode 110,110a-b, may enable that the electrodes 110,11 Oa-b can be maintained in good skin contact and remain substantially electrically isolated from each other in the presence of sweat.
  • FIG 10 is an illustration of a compression garment 100 in the form of a sleeve 101 for sensing an electrical signal 210 at the skin 108 of a user 102.
  • the compression garment 100 is wearable at a body part 104 of the user 102, which is illustrated here by the user 102 wearing the compression sleeve 101 on an arm 105.
  • the compression sleeve 101 comprises a stretchable fabric layer 120 which has a tube-like shape worn around the circumference of the underarm 105.
  • the compression sleeve 101 is worn tightly on the underarm 105 of a non-sedentary user 108, thus electrolytic fluids 106 in the form of sweat droplets are secreted by the skin 108.
  • the compression garment 100,101 is part of a wearable sensor system comprising an electronic device 200 having a processor 230 and a sensor circuit 220 configured to measure an electrical signal 210 at the skin 108 of the user 102 of by means of at least one pair of electrodes 110 and optionally a reference electrode 111.
  • One pair of electrodes 110 and a reference electrode 111 are connected by conductive leads 132 to the electronic device 200.
  • the electronic device 200 is removably attached to the sleeve 101 , preferably with the conductive leads 132 also being detachably connected to the electronic device 200, such as having conductive snap fasteners or electrical fittings for reversibly coupling each conductive lead 132 to a corresponding terminal of the sensor circuit 220.
  • the pair of electrodes 110 and the reference electrode 111 may be connectable by means of said conductive leads 132 to the electronic device 200 in a bipolar electrode configuration to eliminate or at least reduce common mode noise.
  • the sensor circuit 220 may include a differential signal acquisition element configured to compare electrical signals 210 to obtain a surface electromyography.
  • the electronic device 200 may comprise a hardware processor 230 configured with a set of instructions which when executed by the processor 230 causes the sensor circuit 220 to measure an electrical signal 210 and to process said signal 210 for obtaining a surface electromyography.
  • the electronic device 200 may comprises a communication means, such as a wireless communication interface, which is configured to transmit data of the surface electromyography to a user terminal, such as a smart phone.
  • the wearable sensor system may be used for estimating a level of muscle activity of the user 102 wearing the compression garment 100, e.g. where the user 108 is non-sedentary for an extended period of time and/or in the presence of sweat 106 at the electrodes 110, by carrying out a sequence of steps.
  • the steps may include putting on the compression garment 100, reversibly attaching the conductive leads 132 to the sensor circuit 220 and activating the electronic device 200, such as by means of a user interface.
  • the electronic device 200 may then proceed to measure a sequence of electrical signals 210 at the skin 108 of the user 102 during a period of time in which the wearable sensor system is worn.
  • the processor 230 may act to continually or occasionally perform one or more processing steps, e.g. to compare electrical signals 210 in order to obtain a surface electromyography. Then, a time-series of an estimated level of muscle activity of the user 102 can be derived from the measurements, e.g. based on the surface electromyography.
  • Figure 11 a is an illustration of a first assembly of fabric layers for manufacturing a compression sleeve 101 according to a first embodiment, e.g. as illustrated in Figs. 1-3.
  • the first assembly comprises three separate padding layers 160 having shapes substantially identical to the pair of electrodes 110a-b and the barrier region 114 e.g. shown in Fig. 2.
  • the top and bottom padding layers 160 are shown having a circular shape and the middle padding layer 160 is dumbbell-shaped to fit therein between.
  • the padding layers 160 are shown stacked atop a stretchable fabric layer 120.
  • Figure 11 b is an illustration of a second assembly to be stacked on top of a first assembly, e.g. as illustrated in Fig. 11a, for manufacturing a compression sleeve 101 according to a first embodiment, e.g. as illustrated in Figs. 1-3.
  • the illustration shows a second assembly of fabric layers comprising two conductive fabric layers 130 having a circular shape slightly larger than the corresponding circularly shaped two padding layers 160 shown in Fig. 11a.
  • Two conductive leads 132 are provided in electrical contact each with one of said two conductive fabric layers 130, so that the conductive fabric layers 130 are operably connectable to an electronic circuit or similar by means of said two conductive leads 132.
  • the second assembly comprises a hydrophobic fabric layer 180 having a dumbbell-shape also slightly larger than the corresponding dumbbell-shaped padding layer 160 shown in Fig. 11a.
  • Figure 11c is an illustration of a third assembly to be stacked on top of a second assembly, e.g. as illustrated in Fig. 11 b, for manufacturing a compression sleeve 101 according to a first embodiment, e.g. as illustrated in Figs. 1-3.
  • the illustration shows a third assembly of fabric layers comprising bonding means 140 in the form of a thermoformable material layer with a plurality of openings 142a-c.
  • the bonding means 140 is shown in the form of a bonding layer 140 made from a thermoformable material, wherein the bonding layer 140 has two circular openings 142a, 142c configured for exposing a correspondingly circularly shaped part of the conductive fabric layers 130 shown in Fig.
  • the bonding layer 140 has a dumbbell-shaped opening 142b configured for exposing a correspondingly dumbbell-shaped part of the hydrophobic fabric layer 180 shown in Fig.
  • the manufacture of a compression sleeve 101 may include acts of stacking and bonding the first, second and third assemblies together to form at least one pair of electrodes 110 and a barrier region 114 therein between.
  • a conductive fabric layer 130 is disposed through an opening 142a, 142c in the bonding layer 140 to form a skin-contacting region 112 of an electrode 110.
  • a hydrophobic fabric layer 180 is disposed through another opening 142b in the bonding layer 140 to form a skin-contacting barrier region 114.
  • a compression sleeve 101 can be assembled cheaper by a sequential process of arranging fabric materials 120,130,180 around foam pads 160 and heat-pressing with a thermoformable bonding layer 140 to bond the layers. Such a manufacturing process may also provide substantially water-tight sealing of openings where skin-contacting regions are provided for electrodes or barriers.

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Abstract

La présente invention concerne un vêtement de compression permettant de détecter un signal électrique au niveau de la peau lorsqu'il est porté par un utilisateur. Le vêtement de compression comprend au moins deux électrodes constituées de matériaux textiles, les deux électrodes comprenant une première électrode et une seconde électrode. Le vêtement de compression comprend en outre une couche de tissu étirable conçue pour maintenir des électrodes en contact avec la peau d'un utilisateur portant le vêtement de compression et un moyen de liaison fixant les matériaux textiles desdites électrodes à la couche de tissu étirable. En ce qui concerne lesdites deux électrodes, chaque électrode d'une paire d'électrodes comprend une couche de tissu conducteur électriquement sensiblement isolée de l'autre électrode de ladite paire d'électrodes ; et un rembourrage en mousse viscoélastique disposé entre la couche de tissu conducteur et la couche de tissu étirable. En ce qui concerne chaque paire d'électrodes, une région barrière est disposée dans un espace séparant la première électrode et la seconde électrode de ladite paire d'électrodes. La région barrière comprend une partie de tissu hydrophobe conçue pour être maintenue en contact avec la peau, par exemple en s'étendant dans ledit espace. La région barrière comprend en outre un rembourrage de mousse viscoélastique disposé entre la partie de tissu hydrophobe et la couche de tissu étirable.
PCT/EP2022/053504 2021-02-15 2022-02-14 Vêtement de compression avec électrodes en tissu sur mousse WO2022171861A1 (fr)

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DKPA202170068A DK181070B1 (en) 2021-02-15 2021-02-15 Compression garment with foam-backed fabric electrodes

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Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5795312A (en) * 1993-09-27 1998-08-18 The Kendall Company Compression sleeve
US20180271441A1 (en) 2017-03-23 2018-09-27 Intel Corporation Wearable electrode and method of fabrication
JP2019217304A (ja) * 2014-03-10 2019-12-26 エル．アイ．エフ．イー． コーポレーション エス．エー．Ｌ．Ｉ．Ｆ．Ｅ． Ｃｏｒｐｏｒａｔｉｏｎ Ｓ．Ａ． 生理学的監視用衣服

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5795312A (en) * 1993-09-27 1998-08-18 The Kendall Company Compression sleeve
JP2019217304A (ja) * 2014-03-10 2019-12-26 エル．アイ．エフ．イー． コーポレーション エス．エー．Ｌ．Ｉ．Ｆ．Ｅ． Ｃｏｒｐｏｒａｔｉｏｎ Ｓ．Ａ． 生理学的監視用衣服
US20180271441A1 (en) 2017-03-23 2018-09-27 Intel Corporation Wearable electrode and method of fabrication

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