Bioimpedance measurement configuration

Abstract

This document discloses a garment made of a flexible material, comprising: a first measuring electrode integrated into the garment at a first position; a second measuring electrode integrated into the garment at a second position different from the first position; and a measuring circuit system configured to measure bioimpedance by using the first measuring electrode and the second electrode and transmit the measured bioimpedance, and to measure an electrocardiogram by using at least one or the other of the first measuring electrode and the second electrode, wherein the garment is an upper body garment, wherein the first measuring electrode is deployed above the heart level and the second measuring electrode is deployed below the heart level.

Description

Technical Field

[0001] The present invention relates to the field of physiological or biometric measurements, and in particular to a measurement arrangement for measuring bioimpedance from a human body. Background Art

[0002] A typical configuration for measuring bioimpedance includes a set of disposable measurement electrodes for contacting the skin, a measurement circuit system for measuring the bioimpedance from one or more electrodes, and a processing circuit system for processing the measurement data. A communication circuit system for transmitting the processed measurement data in a wired or wireless manner may also be provided. Summary of the invention

[0003] The invention is defined by the subject-matter of the independent claims.

[0004] Embodiments are defined in the dependent claims. BRIEF DESCRIPTION OF THE DRAWINGS

[0005] In the following, the present invention will be described in more detail by means of preferred embodiments with reference to the accompanying drawings, in which

[0006] Figure 1 illustrates a garment including a measurement circuit system according to an embodiment;

[0007] Figure 2 is an embodiment of a measurement circuit system;

[0008] Figure 3 and Figure 4 illustrates additional embodiments of electrode placement in clothing;

[0009] Figure 5 illustrates an embodiment of an arrangement for switching the mode of one or more electrodes of a garment;

[0010] Figure 6 A flow chart illustrating a process for configuring the operation of electrodes of a garment according to an embodiment of the present invention;

[0011] Figure 7 and Figure 8 An embodiment for synchronizing bioimpedance measurements with the cardiac cycle is illustrated;

[0012] Fig. 9 illustrates a flow chart of a process for performing motion compensation on a bioimpedance measurement signal according to an embodiment of the present invention;

[0013] Fig.10 illustrates the stages and intermediate products of a manufacturing process for producing an electrode according to an embodiment of the present invention;

[0014] Fig.11 and Fig.12An embodiment of a layered structure of electrodes in clothing is illustrated;

[0015] Fig.13 and Fig.14 An embodiment of a detachable electronic module for use with clothing is illustrated;

[0016] Fig.15 A process for providing training guidance according to an embodiment of the present invention is illustrated;

[0017] Fig.16 illustrates a process for adjusting the duration of a rest period of an interval workout according to an embodiment of the present invention;

[0018] Fig.17 A process for adjusting the duration of a work period of an interval workout according to an embodiment of the present invention is illustrated;

[0019] Fig.18 The diagram shows that when using Fig.16 and Fig.17 The process of giving instructions during physical exercise is an example of;

[0020] Fig.19 illustrates a process for monitoring a user's fatigue level during exercise according to an embodiment of the present invention;

[0021] Fig. 20 A block diagram of an apparatus according to an embodiment of the present invention is illustrated; and

[0022] Fig.21 Embodiments for reducing undesired electrical coupling between measurement electrodes are illustrated. DETAILED DESCRIPTION

[0023] The following embodiments are illustrative. Although the specification may refer to "one", "an" or "some" embodiments in several places in the text, this does not necessarily mean that each reference refers to the same (one or more) embodiments, or that a particular feature only applies to a single embodiment. Individual features of different embodiments may also be combined to provide other embodiments.

[0024] Figure 1An embodiment of a garment 100 made of a flexible material is illustrated. The garment comprises: a first measurement electrode 120 integrated into the garment at a first position, a second measurement electrode 122 integrated into the garment at a second position different from the first position, and a measurement circuit system 114 configured to measure bioimpedance by using the first measurement electrode and the second electrode and transmit the measured bioimpedance, and to measure an electrocardiogram (ECG) by using at least one or the other of the first measurement electrode and the second electrode, wherein the garment is an upper body garment, wherein the first measurement electrode is disposed above the heart level and the second measurement electrode is disposed below the heart level.

[0025] In an embodiment, the garment is a shirt, a vest or a suspender. The garment may also be a bra or any other garment designed as a base layer to contact the skin of the person 110 (user). The garment may be made of one or more of the following materials: nylon, polyamide, spandex, polyester, cotton and wool.

[0026] exist Figure 1 In an embodiment, when the user 110 wears the clothing, the first measurement electrode 120 is deployed above the heart level, and the second measurement electrode 122 is deployed below the heart level. The measurement circuit system 114 can be set in a housing at any position in the clothing, and the signal lines 116, 118 can connect the measurement electrodes 120, 122 to the measurement circuit system 114. The signal line can be integrated into the clothing.

[0027] Let us now refer to an embodiment of the illustrated device Figure 2 1 and 2 to describe the structure of the measurement circuit system 114 in more detail. The apparatus may include at least one processor 204 and at least one memory 220, the at least one memory 220 storing a computer program 228, the computer program 228 including program instructions for configuring at least one processor to perform the embodiments described herein. The apparatus may also include a user interface 214, the user interface 214 including at least a display device and a user input device.

[0028] Bioimpedance measurement can be performed by arranging the signal feeding electrode 210 in the clothing and further arranging the measuring electrode 212 in the clothing. The measuring electrode 212 may include electrodes 120, 122. The measuring circuit system 114 may be configured to control signal feeding and measurement, for example, in the following manner. One or more processors 204 may control the current generator 202 to output current to the feeding electrode 210. The current generator 202 may be a signal synthesizer that is capable of outputting alternating currents of various frequencies. Bioimpedance measurement can be used to estimate body composition, and multiple frequencies may be output for this purpose.

[0029] When the current generator outputs current to the body, the processor 204 can configure the voltage measurement circuit system 206 to measure the voltage between the measurement electrodes 212 and obtain voltage measurement data from the measurement electrodes. The knowledge of the measured voltage U and the applied current I can then be used to calculate the bioimpedance Z according to the well-known formula Z=U / I.

[0030] The measurement circuit system 114 may also include or have access to at least one memory 220. The memory 220 may store computer program code including instructions that may be read and executed by the processor(s) 204 and configure the above-described operations of the processor(s). The memory 220 may also store a configuration database 224 that defines parameters for the processor(s), for example, parameters for current feed control.

[0031] The apparatus may also include a communication circuit system configured to transmit the measurement data acquired by the measurement circuit system to an external device, such as a smart phone or a wrist computer. The external device may be a training computer configured to monitor the physical exercise performed by the user. The communication circuit system may be a wireless communication circuit system supporting a wireless communication protocol, such as ANT, ANT+ or (e.g. Bluetooth ).

[0032] As used in this application, the term "circuitry" refers to all of the following: (a) hardware-only circuit implementations, such as implementations in analog and / or digital circuitry only, and (b) combinations of circuitry and software (and / or firmware), such as, as applicable: (i) a combination of (one or more) processors or (ii) portions of (one or more) processors / software, including (one or more) digital signal processors, software, and (one or more) memories that work together to enable the device to perform various functions, and (c) circuits that require software or firmware to operate (even if the software or firmware is not actually present), such as (one or more) microprocessors or portions of (one or more) microprocessors. The definition of "circuitry" applies to all uses of this term in this application. As another example, as used in this application, the term "circuitry" would also cover implementations of only a processor (or multiple processors) or a portion of a processor and its accompanying software and / or firmware.

[0033] The techniques and methods described herein can be implemented by various means. For example, these techniques can be implemented in hardware (one or more devices), firmware (one or more devices), software (one or more modules), or a combination thereof. For hardware implementations, the (one or more) devices of the embodiments can be implemented in one or more application-specific integrated circuits (ASICs), digital signal processors (DSPs), digital signal processing devices (DSPDs), programmable logic devices (PLDs), field programmable gate arrays (FPGAs), graphics processing units (GPUs), processors, controllers, microcontrollers, microprocessors, other electronic units designed to perform the functions described herein, or a combination thereof. For firmware or software, the implementation can be performed by a module (e.g., a process, a function, etc.) of at least one chipset that performs the functions described herein. The software code can be stored in a memory unit and executed by a processor. The memory unit can be implemented inside or outside the processor. In the latter case, as known in the art, it can be communicatively coupled to the processor via various means. In addition, the components of the system described herein can be rearranged and / or supplemented by additional components to facilitate the implementation of the various aspects described therein, etc., and they are not limited to the precise configurations set forth in the given figures, as will be recognized by those skilled in the art.

[0034] Other physiological characteristics, such as cardiac stroke volume, can be calculated based on the measured bioimpedance. Patent publication US 2002 / 0193689 discloses a method for calculating cardiac stroke volume by using bioimpedance and ECG, and in some embodiments, the processor 204 can adopt this method.

[0035] exist Figure 1 In an embodiment of the present invention, the electrodes 120, 122 can be used as both feeding electrodes through which current is applied and as voltage measurement electrodes. A switching mechanism can be applied that switches the function of the electrodes 120, 122 between current feeding and voltage measurement. The switching mechanism can perform time division multiplexing, connecting the electrodes to the current generator 202 or the voltage measurement circuit system depending on the desired function of the electrodes 120, 122 under the control of the processor 204.

[0036] In another embodiment, one or more of the electrodes 120 and 122 are also configured to measure ECG. In this case, the switching mechanism can also control the electrode to switch to a differential amplifier, which is used as a front end in ECG measurement.

[0037] Figure 3 and Figure 4 Additional measurement configurations according to other embodiments are illustrated. Figure 3In an embodiment of the present invention, there are additional electrodes 124, 126, 130, 132. In this configuration, electrodes 120 and 122 can be used as current feeding electrodes, and electrodes 124 and 126 can be measurement electrodes. Figure 3 As shown in , each electrode is set at a different position. The positions of electrodes 120 to 126 can be selected so that the line drawn from measurement electrode 124 to measurement electrode 126 intersects the line drawn from feeding electrode 120 to feeding electrode 122. This provides symmetry between current feeding and voltage measurement. Electrodes 130 and 132 can be configured as ECG measurement electrodes and deployed at any position in the clothing.

[0038] Figure 4 An embodiment is illustrated in which electrodes 124, 126, 130, 132 are replaced by electrodes 134 and 136 which, by using a switching mechanism, are configured to function both as voltage measurement electrodes for bioimpedance measurement and as ECG measurement electrodes. Also in this embodiment, the feed electrodes and the measurement electrodes are arranged so that the above-mentioned lines will intersect.

[0039] exist Figure 3 and Figure 4 In an embodiment of the present invention, one of the feeding electrodes is above the heart level, and the other feeding electrode is below the heart level. In a similar manner, one of the measuring electrodes is above the heart level, and the other measuring electrode is below the heart level.

[0040] The garment may have a back side arranged to face the back side of the user, and also have a front side arranged to face the front side of the user. Figure 1 , 3 In any of the embodiments of and 4, the electrode(s) 120, 124, 134 deployed above heart level may be deployed in the neck or shoulder region of the garment, at least on the back side of the garment. This improves skin contact during physical exercise, such as running. In an embodiment, the electrode(s) above heart level are elongated and extend from the back side of the garment to the front side of the garment, over the shoulders of the user. During exercise, the shoulder region of the garment typically has the best skin contact, and this embodiment further improves skin contact.

[0041] The electrode(s) 122, 126, 136 deployed below the heart level may be deployed in the chest region of the garment, wherein the garment is arranged to fit snugly at the location of the second electrode. The snug fit may be achieved by elastic material of the garment or by straps in the garment.

[0042] In accordance with the above combination Figure 3 and Figure 4In an embodiment modified from the described embodiment, at least some of the electrodes may be deployed on opposite sides of the human body. For example, one or more or even all of the electrodes 122, 126, 130, 132, 136 may be deployed on the back side of the body. Those electrodes deployed below the heart level may be deployed on the back side or either side of the clothing. In an embodiment, the clothing includes one or more electrodes deployed below the heart level on the back side and (one or more) additional electrodes deployed below the heart level on the front side.

[0043] In an embodiment, the feeding electrode may have a different shape from the measuring electrode. For example, the measuring electrode may be elongated, while the feeding electrode may have a circular or dot shape. The dot shape enables a more accurate determination of the current path between the feeding electrodes, thereby simplifying the system configuration. The elongated measuring electrode provides better skin contact for the measurement, thereby improving the measurement accuracy.

[0044] Figure 5 The block diagram of the measurement circuit system including the switching mechanism 520 is illustrated. The switching mechanism 520 can be implemented by one or more switches, which perform the switching of the function of at least one measurement electrode between ECG measurement and bioimpedance measurement. The switching mechanism 520 can include one or more electronic switches.

[0045] In an embodiment, the switching mechanism 520 switches the functionality of the measurement electrodes between at least two of the following measurement modes: a full ECG mode in which all measurement electrodes are used to measure ECG, a full bioimpedance measurement mode in which all measurement electrodes are used to measure bioimpedance, and a hybrid measurement mode in which a first subset of measurement electrodes are used to measure ECG and a second subset of measurement electrodes are used to measure bioimpedance. The switching mechanism may be controlled by the processor 204. The processor 204 may include a mode selector circuit system 504 configured to select a mode based on the measurement mode. Figure 6 The flowchart of FIG. 1 performs a process for selecting a measurement arrangement.

[0046] refer to Figure 6, in block 600, the mode selector circuit system 504 selects the measurement mode. For example, the selection can be made based on a measurement profile, which is obtained based on user input. After selecting the full ECG mode in block 600, the process can proceed to block 604, where the mode selector configures the switching mechanism 520 to couple all electrodes 120 to 132 to the input of the ECG measurement circuit system 502. The ECG measurement circuit system 502 may include a plurality of differential amplifiers, and each pair of electrodes 120 to 132 may be connected to the input of one of the differential amplifiers. For example, the switching mechanism 520 may couple electrodes 120 and 122 to different inputs of one of the differential amplifiers, electrodes 124 and 126 to different inputs of another differential amplifier, and electrodes 130 and 132 to different inputs of yet another differential amplifier. In this way, the switching mechanism can implement a multi-channel ECG measurement arrangement in which two or more pairs of electrodes are connected to the ECG measurement circuit system 502. Mode selector 504 can also activate ECG measurement circuit system 502 to start multi-channel ECG measurement. ECG measurement circuit system 502 can combine ECG measurement signals received through different measurement channels. When only heart rate or heart activity is monitored, such as during physical exercise, the full ECG mode can be used.

[0047] After selecting the full bioimpedance mode in block 600, the process can proceed to block 602, where the mode selector 504 configures the switching mechanism 520 to couple all electrodes 120 to 132 for bioimpedance measurement. In the full bioimpedance mode, the switching mechanism 520 can couple at least one pair of electrodes for current feeding and at least one pair of electrodes for voltage measurement. In an embodiment, the current feeding electrodes can be coupled to a current generator 202 configured to feed a constant current. In an embodiment, the voltage measurement electrodes are coupled to a voltmeter 500, which is configured to measure the voltage between the voltage measurement electrodes when the current generator feeds current.

[0048] As above combined Figure 3 As described, in an embodiment using four electrodes (e.g., electrodes 120 to 126), electrodes 120 and 122 may be coupled to current generator 202 for current feeding, and electrodes 124, 126 are coupled to voltmeter 500. In an embodiment using six electrodes (e.g., electrodes 120 to 132), a measurement channel may be implemented by also coupling one or more of electrodes 130, 132 to voltmeter 500. For example, additional voltage measurements between electrodes 124 and 132 and / or between 124 and 130 may be implemented.

[0049] In an embodiment where only two electrodes are used, the switching mechanism can be configured to alternately switch the electrodes to the current generator 202 and the voltmeter 500 at a determined frequency. In this way, only two electrodes can be used when measuring bioimpedance. The voltmeter can be configured to measure voltage samples when the electrodes are coupled to the voltmeter, and not to obtain samples when the electrodes are coupled to the current generator.

[0050] For example, when measuring body composition, the full bioimpedance mode may be used. In the full bioimpedance mode, the current generator may be configured to output current at at least two frequencies simultaneously or in a time multiplexed manner.

[0051] After selecting the hybrid mode in block 600, the process can proceed to block 606, where the mode selector 504 configures the switching mechanism 520 to couple a subset of electrodes for bioimpedance measurement and another subset of electrodes for ECG measurement. For example, this mode can be used when measuring stroke volume and heart rate during physical exercise, or when measuring body composition and heart rate simultaneously.

[0052] In the hybrid mode, the switching mechanism may couple at least two electrodes to the ECG measurement circuitry 502, at least two electrodes to the current generator 202, and at least two electrodes to the voltmeter 500. Figure 3 In the embodiment of the present invention, each electrode can be configured to have a specific function in a fixed manner in the hybrid mode. For example, electrodes 120, 122 can be coupled to current generator 202, electrodes 124, 126 can be coupled to voltmeter 500, and electrodes 130, 132 can be coupled to ECG measurement circuit system 502.

[0053] When using a reduced set of electrodes (e.g. Figure 4 In an embodiment of the present invention (four electrodes in the embodiment of the present invention), the switching mechanism 520 can be configured to alternately switch the electrodes to the ECG measurement circuit system 502 and the voltmeter 500 at a determined frequency. The voltmeter can be configured to measure voltage samples when the electrodes are coupled to the voltmeter, and not to obtain samples when the electrodes are coupled to the ECG measurement circuit system. The ECG measurement circuit system 502 can be configured to measure ECG samples when the electrodes are coupled to the ECG measurement circuit system, and not to obtain samples when the electrodes are coupled to the voltmeter.

[0054] In embodiments using alternating switching, the switching frequency may be higher than 60 Hertz (Hz).

[0055] When calculating stroke volume based on bioimpedance, the ECG measurement signal can be used to obtain a time reference for the stroke volume measurement. Figure 7An embodiment of a method for acquiring a set of bioimpedance samples for stroke volume estimation by the processor(s) 204 is illustrated. Figure 7 , the process includes measuring ECG signals and bioimpedance in a synchronized manner (block 700). The processor may maintain a time reference common to both measurements. When switching between ECG and voltage measurements, the switching frequency may be high enough to maintain satisfactory synchronization accuracy.

[0056] The processor can monitor the ECG signal for signatures. The R peak is a typical strong signature point that can be monitored. Figure 8 The bioimpedance signal is illustrated, and the ECG signal is illustrated below it. The R peak is circled in the ECG signal. After detecting the signature in the ECG signal in block 702, the processor can trigger the start of a new bioimpedance sample set in block 704 ( Figure 8 In this way, Figure 7 The process can generate multiple sets of bioimpedance samples, for example, for stroke volume measurement. Figure 7 The process also synchronizes the stroke volume estimation with the user's cardiac cycle.

[0057] In an embodiment, the processor performs averaging on the bioimpedance sample sets. The averaging may be smooth, where samples with the same index in the corresponding sample set are averaged. Figure 8 , which averaging will result in an average bioimpedance sample set calculated from multiple sample sets of bioimpedance samples. Figure 8 As shown, bioimpedance can be volatile and smoothing can improve the accuracy of stroke volume estimation.

[0058] In an embodiment, the processor can also estimate the breathing rate based on the signature. For example, the breathing rate can be calculated based on the phase of the ECG signal. In another embodiment, the breathing rate is calculated by measuring the RR interval of the ECG signal. The breathing rate can be detected based on the RR interval by using the following knowledge: the RR interval when the user inhales is shorter than the RR interval when the user exhales. By monitoring this periodicity in the RR interval, the breathing rate can be calculated. The processor can calculate the breathing rate by using the measured bioimpedance instead of ECG or as a supplement. In an embodiment, (one or more) processors 204 can perform motion compensation for bioimpedance measurement. Clothing may include one or more motion sensors integrated therein. In an embodiment, the motion sensor is integrated at the position of the measuring electrode (e.g., an electrode configured to measure voltage). In another embodiment, (one or more) motion sensors are included in the same housing as the measurement circuit system.

[0059] The motion sensor(s) may be configured to measure motion of the garment at the location(s) of the measurement electrodes, and the measurement circuitry may be configured to perform motion compensation on the measured bioimpedance based on the measured motion. Fig. 9 An embodiment for performing motion compensation by measurement circuitry 114 is illustrated.

[0060] refer to Fig. 9 In block 900, the processor(s) may acquire motion measurement data from the motion sensor(s). The processor(s) may be configured to attempt to detect a rhythm in the motion measurement data. Upon detecting the rhythm in block 902, the processor(s) may trigger a motion compensation algorithm to begin motion compensation.

[0061] In an embodiment, the rhythm is detected by calculating a Fourier transform of the motion measurement data and performing peak detection on the transformed data.If a frequency component above a determined threshold has been detected, then in block 902 the processor may determine that a rhythm has been detected.

[0062] In an embodiment, the motion compensation in block 904 includes an adjustment of the averaging window used in the above-mentioned smoothing (block 906). For example, the length of the averaging window, i.e., the number of sample sets to be included in the smoothing, can be determined based on the cadence. For higher cadences, a larger window can be selected. Instead of cadence, another criterion can be used, such as the training intensity obtained from the measured heart rate. For higher intensities, a larger window can be selected. In another embodiment, the size of the window also depends on or alternatively depends on an estimate of the signal-to-noise ratio of the bioimpedance measurement signal.

[0063] In an embodiment, the motion compensation in block 904 includes an interference suppression algorithm (block 908). The interference suppression may attempt to detect a signal component having a frequency of the determined rhythm and remove the signal component from the bioimpedance measurement signal.

[0064] In yet another embodiment, motion compensation can include the use of auxiliary data. For example, when performing a stroke volume measurement and detecting a rhythm, a poor signal-to-noise ratio, or another indicator that motion compensation is needed, the processor can use the auxiliary data in the stroke volume estimation. For example, the processor can store a mapping table that maps training intensity or heart rate to stroke volume. After detecting that motion compensation is needed, the processor can calculate the stroke volume based at least in part on the mapping table. In an embodiment, the processor can only use the mapping table for stroke volume estimation after detecting that the rhythm is above a determined threshold or the signal quality is below another determined threshold.

[0065] Let us now describe some examples regarding implementation of electrodes and electronics in clothing.

[0066] In an embodiment, the material of the electrodes is thermoplastic polyurethane (TPU). Properties of TPU include elasticity, transparency, and resistance to oil, grease, and abrasion, which makes it suitable for use in clothing. Another option for the electrode material is silver.

[0067] In an embodiment, the electrodes are manufactured into the clothing by lamination or printing processes. By printing, the electrodes can be arranged to form an arbitrary pattern in the clothing. Fig.10 The process is illustrated with an intermediate product of the electrode during the process. First, a fabric layer 1000 is provided, wherein the fabric layer is a part of a garment or garment. Then, a heat transfer substrate 1002 is formed on the fabric at the expected location of the electrode and the signal line connecting the electrode to the measurement circuit system. Thereafter, an EMI shield 1004 can be deployed on the substrate. The EMI shield can be implemented by conductive ink printed on the substrate. The EMI shield 1004 can cover the expected location of the electrode and the signal line, thereby protecting both of them. Then, an additional substrate layer 1006 can be formed on the EMI shield to isolate the EMI shield from the electrode and the signal line. On the additional substrate layer 1006, conductive ink 1008 can be deployed to form the signal line and the electrical connection between the signal line and the electrode. Thereafter, a heat transfer cover layer 1010 can be deployed at the edge of the electrode position and further on the signal line to cover the signal line. This layer isolates the signal line and the conductive ink from the user's skin. Thereafter, the heat transfer cover layer can be covered with a heat transfer film including one or more through holes to enable electrical coupling to the conductive ink 1008. On top of the heat transfer film, an electrode layer 1012 is formed, for example, of a conductive thermoplastic. The hole(s) at the electrode location in the heat transfer film enables electrical coupling between the electrode layer and the conductive ink 1008.

[0068] In an embodiment, the electrodes are arranged to have a layered structure. Fig.11 Such an embodiment is illustrated in FIG. Fig.11 In an embodiment of the present invention, the first layer 1100 arranged to contact the skin is a conductive layer, for example made of TPU. This can form an electrode layer. The next layer may include a heat transfer film with (one or more) holes and a cover layer 1102, which isolates the first layer 1100 from the outside (e.g., the fabric of the clothing) and still provides electrical coupling for the electrode layer. Layer 1102 may include one or more holes for electrical coupling between the electrodes and the signal line. The signal line is Fig.111104 (such as a contact pad). The first layer 1100 may contact a contact point 1104 (such as a contact pad) through the hole(s) in the layer 1102, and a signal line (e.g., 116 or 118) may be brought to the contact point 1104. Another TPU layer 1108 may be disposed on the heat transfer cover layer. The TPU layer 1108 may be isolated from the contact point by an isolation member 1106. The heat transfer film 1110 or the substrate layer 1002 may then be provided as a coupling member to the garment 1112. The heat transfer film may act as a glue and may penetrate the fabric material of the garment, thereby securing the other layers to the garment.

[0069] exist Fig.12 In another embodiment shown in FIG. 1 , for example, an electromagnetic interference (EMI) shielding layer 1200 ( 1200.1 ) may be provided within the TPU layer 1108 or between the TPU layer 1108 and the heat transfer cover layer 1102. Fig.10 1004 in). The EMI shielding layer can be isolated from the contact point 1104, such as Fig.10 Embodiment of the invention.

[0070] Signal line 116 or 118 can be sewn into or arranged on the fabric. Signal line can be formed by conductive yarn. In an embodiment, EMI shielding is provided for signal line 116, 118 of the device. EMI shielding according to these embodiments can be suitable for any signal line of conductive electrical signal that is susceptible to EMI. Signal line can include electrical conductor, which can be formed by conductive line or threading worn in clothing, clothing or clothes. Electrical conductor can be isolated by insulating layer that protects electrical conductor and isolates electrical conductor. On electrical conductor, EMI shielding can be provided by arranging conductive threading to cover electrical conductor. Conductive thread can be arranged on electrical conductor by sewing or sewing conductive threading with sewing machine. Conductive threading can be formed by using zigzag stitching, so that zigzag pattern covers signal line and does not penetrate insulating layer. Conductive threading can be sewn through substrate (for example, fabric or clothing) in which signal line is arranged. When used in applications where substrate is in contact with user's skin, conductive threading is therefore engaged with user's skin and acts as skin electrode for grounding EMI.

[0071] In another embodiment, shielding can be achieved by using a coaxial yarn, which is basically a yarn with the structure of a coaxial cable. The internal signal line can be surrounded by an isolation layer and a grounding protective layer. The coaxial signal line can be very thin so that it can be sewn. The coaxial signal line can include two signal lines: one connected to the contact point 1104 and the other grounded (e.g., EMI shield 1200). In this way, shielding of the signal line can be achieved.

[0072] In yet another embodiment, two or more signal lines are drawn from one location to another, for example, in an embodiment employing a motion sensor at the location of an electrode, where a signal line is drawn from the electrode to the location of the measurement circuitry, the signal lines may be twisted relative to each other. Thus, a twisted pair signal line is formed, which provides protection against EMI.

[0073] In an embodiment, the signal lines may be covered by silicone or another protective material.

[0074] In an embodiment, a conductive paste coated on the signal line may be provided for EMI shielding of the signal line.

[0075] In an embodiment, the housing housing the electronics including the measurement circuit system 114 is detachable from the garment. The housing may be waterproof and mechanically attached to the garment, for example, by using snap fastenings. The snap fastenings may also align the housing relative to the garment so that signal lines in the garment will couple with corresponding interfaces in the housing. Fig.13 An example of such an embodiment is illustrated.

[0076] refer to Fig.13 , the measurement circuit system may include a housing 1322 that is integrated or attached to the garment 1112, for example, in a fixed or permanent manner. The housing can serve as a positioning member for the housing 1320 for housing the measurement circuit system. The housing 1322 may include a first set 1300, 1302 of signal connectors that are connected to electrodes in the garment (e.g., ECG electrodes and bioimpedance electrodes). The housing 1322 may include a second set 1304, 1306 of signal connectors that are configured to provide connections to corresponding connectors in the housing 1320. When the module 1320 is separated from the housing 1322, the connectors 1304, 1306 may be exposed. The connectors 1300, 1302 may be covered (e.g., in a housing) and connected in the housing to corresponding signal lines 1114 leading to corresponding electrodes. Internal wiring may be deployed in the housing 1322 to connect the connectors 1300, 1302 of the first set to appropriate connectors 1304, 1306 of the second set, such as Fig.13 as shown at the bottom of the .

[0077] The housing 1320 may include a set of connectors 1310, 1312 arranged so that when the housing 1320 is attached to the housing, the connectors connect to the appropriate connectors 1304, 1306 of the second set. Internal wiring may be provided in the module to connect the connectors to the corresponding components of the measurement circuit system, for example, to the differential amplifier 502, the voltmeter 500 and / or the current generator 202.

[0078] In an embodiment, the housing comprises a hole where the casing is to be attached. Fig.14This embodiment is illustrated. Hole 1400 is shown in the housing, and a sensor head 1410 is arranged in a corresponding position in the housing 1402. A sensor can be set in the sensor head 1410 on the surface of the housing, and the sensor is designed to enter the hole 1400 and contact the skin. The sensor head 1410 may include a photoelectric sensor, a photoelectric graph (PPG) sensor, an ECG sensor, and / or a temperature sensor. In this embodiment, depending on the position of the housing 1402 in the clothing, the sensor head 1410 in the housing can replace one or more of the above-mentioned electrodes. For example, if the position is above the heart level, the sensor head can replace one or more of sensors 120, 124, and 134. If the position is below the heart level, the sensor head can replace one or more of sensors 122, 126, 136. The sensor head can replace ECG sensors 130, 132. However, the switching mechanism 520 can still work in the above manner.

[0079] In the following embodiments, any of the above-described measurement configurations may be used to monitor a physical exercise performed by a user 100 . Fig.15 A process for providing training guidance related to physical exercise is illustrated. The process may be performed by a training computer. Fig.15 , the process includes: measuring (box 300) the user's cardiac activity during physical exercise by using a cardiac activity sensor; measuring (box 300) the user's bioimpedance during physical exercise by using a bioimpedance measurement sensor; calculating (box 302) the stroke volume based on the bioimpedance in synchronization with the user's cardiac cycle by using the measured cardiac activity; calculating (box 304) the training intensity of the physical exercise or a part of the physical exercise by the processing circuit system by at least using the calculated stroke volume; and comparing the training intensity with at least one threshold value by the processing circuit system (boxes 306 and 308), and outputting (box 310) at least one training guidance instruction based on the comparison.

[0080] Compared with conventional techniques that determine training intensity based on heart rate, there are several advantages to calculating training intensity using stroke volume. Heart rate does not show a complete picture of cardiac output and the user's effort level. For example, this can lead to inaccurate estimates of training load or energy expenditure. A typical example where heart rate is a suboptimal measurement is high-intensity interval training (HIIT) or strength training. After completing a high-intensity work period, the heart rate drops relatively quickly. This leads to an estimate of the light training effect of the exercise, although the user's muscles become exhausted. Stroke volume behaves differently and is better correlated with the tissue saturation index than heart rate. The tissue saturation index is a measure of oxygenated hemoglobin in the blood and can be considered to represent the true training intensity. After the heart rate reaches its maximum value, the stroke volume can also increase. This means that estimating training intensity using stroke volume enables quantifying training intensity when the heart rate is saturated. Thus, calculating training intensity using stroke volume provides better accuracy in estimating training intensity during and / or after exercise.

[0081] In an embodiment, training intensity is calculated based on stroke volume.

[0082] In an embodiment, the processing circuitry calculates the heart rate based on the measured heart activity and calculates the training intensity based on the cardiac output (CO) defined by the product of the calculated stroke volume (SV) and heart rate (HR):

[0083] CO(n)=SV(n)×HR(n)

[0084] Where n represents the time / sample index. As described above, bioimpedance and cardiac activity can be calculated synchronously. CO can therefore be calculated from samples or sets of samples having the same one or more time indices.

[0085] In an embodiment, the processing circuitry calculates the heart rate based on the measured heart activity and further calculates the training intensity based on the oxygen uptake (VO2) defined by the product of the calculated stroke volume, the heart rate, and a constant factor:

[0086] VO2(n)=SV(n)×HR(n)×avdiff

[0087] Where avdiff stands for arteriovenous oxygen difference. avdiff is an indication of how much oxygen is removed from the blood in the capillaries as the blood circulates through the body. In other words, it can be defined as the net difference in oxygen content between the aorta and the veins, expressed in liters of oxygen per liter of blood. For the processing circuitry, this factor can be considered a constant. It can be a predefined parameter specific to the user.

[0088] In an embodiment, the processing circuitry calculates the heart rate based on the measured heart activity and further calculates the training intensity based on an energy expenditure (EE) defined by the product of the calculated stroke volume, the heart rate, a factor avdiff and a predetermined parameter associated with the user:

[0089] EE(n)=SV(n)×HR(n)×avdiff×oec

[0090] Where oec is the oxygen energy coefficient, which represents the user's ability to convert oxygen into energy, for example 5 kilocalories per liter of oxygen. EE can be the instantaneous energy expenditure at time n.

[0091] Any one or combination of the above training intensity measurements may be used in block 304. They are all training intensity measures based on stroke volume.

[0092] In an embodiment, the processing circuit system may utilize training intensity zones mapped to different training intensity ranges by using stroke volume as a factor of the training intensity. In this embodiment, the processing circuit system may determine multiple training intensity zones based on stroke volume, wherein the range of each training intensity zone is mapped to a unique range of stroke volume values. Thereafter, the processing circuit system may perform the comparisons in blocks 306 and 308 by comparing the training intensity to at least one training intensity zone. In this embodiment, the at least one threshold may include at least one limit of at least one training intensity zone.

[0093] Training intensity zones may be created for any of the above training intensity measures (e.g., SV, CO, VO2, or EE). They are all based on stroke volume and therefore better represent training intensity and training effect than, for example, heart rate zones. For example, another feature that distinguishes training intensity zones based on stroke volume from heart rate zones is that the processing circuit system may indicate these zones to the user by using a factor different from the factor on which these zones are based (e.g., stroke volume). The range of the zones may be mapped to values ​​for SV, CO, VO2, or EE, but the training intensity zones may be indicated to the user by using a verbal definition or by a percentage of a maximum value, such as Figure 4 As such, stroke volume or cardiac output may not be explained to the average user, and thus, the use of more descriptive zone definitions may serve the purpose of improving training guidance.

[0094] Heart rate can be a suboptimal metric for measuring training intensity and training load for strength training or HIIT workouts. In a typical HIIT workout, which is an example of interval training, the user exhibits high training intensity during the work period and rests or exhibits light training intensity during the rest period. The general trend of TSI is that TSI drops sharply shortly after the start of the high-intensity work period and recovers slowly during the rest period. This indicates that the user is exercising in the anaerobic zone during the work period, which is typical for HIIT workouts. During the work period, the heart rate increases, but during the rest period, the heart rate will drop rapidly depending on the user's heart rate recovery ability. However, the stroke volume rises during the work period and remains high during the work period. Eventually, SV begins to drop, but at a much slower rate than the heart rate, for example.

[0095] HIIT is a highly efficient exercise that maximizes the time at maximum SV. During the rest period, SV is shown to remain high, or even exceed the SV value measured during the work period, while during the rest period, VO2 and HR drop quite rapidly. Therefore, reducing the training intensity during the rest period of a HIIT exercise or even resting during the rest period can extend the time to exhaustion. It can also allow more time to accumulate in the high-intensity zone, extend the cumulative time spent at maximum SV, maximum CO, maximum VO2 and / or maximum EE, and lead to improved training benefits.

[0096] In an embodiment, the processing circuit system determines the training guidance so that the SV value is maximized. The processing circuit system can instruct the user to maintain the SV above a determined threshold level. In an embodiment, after detecting that the SV drops below the determined level, the processing circuit system can instruct the user to increase the intensity of the training. The accompanying drawings illustrate an embodiment in which the processing circuit system adapts the working period of the interval exercise to the observation of the measured stroke volume. In this embodiment, at least one threshold includes a threshold for triggering the next working interval after the rest period of the physical exercise.

[0097] refer to Fig.16, in box 950, the processing circuit system can trigger the start of the rest period. The trigger can be the end of the previous working period, and the end can be detected based on the measured time of the working period or the measured training intensity accumulation during the working period. During the rest period, the processing circuit system can execute box 302 and calculate SV. In box 952, the processing circuit system compares the calculated stroke volume with the threshold to trigger the next working interval. When it is detected in box 954 that the comparison indicates that the stroke volume has dropped below the determined level defined by the threshold ("yes" in box 954), the processing circuit system outputs a training guidance instruction that instructs the user to start the next working interval (box 956). Otherwise, the process can return to box 302 to calculate the next SV value. This embodiment makes it possible to maintain SV above the threshold level, thereby optimizing the training effect of interval training.

[0098] In an embodiment, the determined level defined by the threshold is a selected decrease in stroke volume from a reference stroke volume measured at the beginning of the recovery interval, for example, a value between 5% and 15%. In other words, when SV has decreased by an amount determined by the value from the beginning of the rest period, in block 956, the processing circuit system can trigger the next work period.

[0099] In an embodiment, a similar method is used by the processing circuit system to adjust the length of the working period, especially to adjust the end of the working period. In this embodiment, at least one threshold value includes a threshold value indicating the minimum training intensity of the working period of the interval exercise. The processing circuit system accumulates the time that the heart stroke volume remains above the threshold value during the working period, and outputs the training guidance instruction as an instruction to end the working period. The instruction is triggered by the processing circuit system after detecting that the heart stroke volume remains above the threshold value for a determined target time interval T. Fig.17 The process according to this embodiment is illustrated.

[0100] refer to Fig.17 In block 1050, the processing circuit system triggers the start of a work period in the interval exercise. Fig.16or by using a preset timing for the duration and end of a previous rest period to trigger the start (box 1050). During the work period, in box 302, the processing circuit system can calculate the stroke volume in the manner described above. In box 1052, the calculated stroke volume can be compared with a threshold indicating a minimum training intensity for the work period. If the stroke volume indicates that the training intensity is above the threshold level, the processing circuit system can accumulate the time (not shown) that the training intensity is above the threshold level. In box 1054, the processing circuit system compares the accumulated time with the target time interval T. If it is determined in box 1054 that the training intensity indicated by the stroke volume remains above the threshold level for a target time interval or above the target time interval, then processing can proceed to box 1058, where the processing circuit system triggers the end of the work period, the start of a subsequent rest period, and outputs an instruction to the user to end the work period. Thereafter, for example, according to Fig. 9 In the embodiment of the present invention, in block 1060, the processing circuit system may begin monitoring for a trigger to start the next work period. After determining in block 1054 that the training intensity has not been above the threshold level for a sufficient period of time, the process may determine to maintain the instruction to continue the work period (block 1056) and then return to block 302.

[0101] Fig.18 An example of guidance during exercise is illustrated in the form of a curve illustrating training intensity based on stroke volume during exercise. Fig.18 The Y axis of the curve graph represents the training intensity based on the stroke volume, such as SV, CO, VO2 or EE. The two thresholds are mapped to the Y axis, according to Fig.17 Example, TH work For the accumulation of training intensity during the working period, and according to Fig.16 Example, TH rest Used to trigger the end of a rest period. Fig.18 The start of an interval workout can be triggered in any way, for example, the user starts a workout and sends a Fig.16 and Fig.17 The training computer of the process provides a start input. Thus, the first working period begins. The warm-up phase may precede the first working period, but for the sake of brevity, it is omitted in this specification. During the first working period, the processing circuit system executes Fig.17 The process of calculating the stroke volume and comparing the training intensity based on SV with the threshold TH work Whenever the training intensity is higher than the threshold, the time value is accumulated. When the time value reaches the target time interval T target When the processing circuit system triggers the start of the rest period, it starts comparing the stroke volume with the threshold value TH. rest When the stroke volume drops to the threshold THrest When the interval training is completed, the processing circuit system can trigger the start of the next working period. In this way, the process can continue until the interval training is completed.

[0102] In an embodiment, Fig.16 The SV-based training intensity monitored in the embodiment of Fig.17 For example, any of the SV-based training intensities (SV, CO, VO2, EE) may be suitable for Fig.17 However, in Fig.16 In embodiments of the invention, it may be advantageous to measure only SV. Let us remind you that the adjustment of HR for rest periods may be suboptimal due to the rapid decline. Thus, a metric involving HR may also not be as optimal as a metric with SV without HR.

[0103] In an embodiment, the processing circuit system is configured to detect fatigue of the user based on the calculated stroke volume during the work interval and output training guidance instructions for the user to end the interval exercise. Fig.19 An embodiment for canceling a workout after detecting user fatigue is illustrated. Fatigue can be detected by evaluating SV and heart rate during a work period. Fig.19 , the processing circuit system may perform blocks 1050, 302, 1052, 1054, 1056, 1058, and 1060 in the manner described above. After determining in block 1054 that the work period continues, the processing circuit system may then check the user's fatigue level. The check may include evaluating the development of SV. If the processing circuit system detects that the SV has dropped by at least a determined amount during the work period (e.g., by using a threshold comparison), the processing circuit system may treat it as an indicator of fatigue and then check the development of the user's performance (block 1250). If one or more other indicators indicate that the user is still performing at a high intensity, the processing circuit system may determine that the user is fatigued in block 1250 and proceed to block 1252, where the processing circuit system ends the exercise. Block 1252 may include outputting an indication to the user that the exercise is over. Block 1252 may include outputting an indication to the user that the user may be fatigued and should rest.

[0104] One or more other indicators indicating that the user is still performing at a high intensity may include heart rate or exercise intensity. Exercise intensity may be measured using a motion sensor, a force sensor, a cadence sensor, or a combination of these sensors. One or more thresholds may be employed in block 1250, for example, one for determining a sufficient decrease in SV and another for determining that the training intensity remains high enough to trigger the end of the workout.

[0105] In an embodiment, the fatigue check of block 1250 may be performed at another instance of the process or at a later time relative to the Fig.10 and / or Fig. 9 The process is executed in parallel with the process.

[0106] Fig. 20 An embodiment of a training computer is illustrated, which includes a method for performing a computer-implemented process Fig.15 or the processing circuit system of any embodiment thereof. The training computer may be a smart phone, a tablet computer, a wrist computer, or even a server computer. The training computer may include a measurement circuit system 10 configured to perform calculations and interfaces when monitoring a physical exercise performed by a user, such as during or after an exercise. The measurement circuit system 10 includes the processing circuit system 14 described above. The measurement circuit system may also include a sensor interface 12 configured to provide a communication connection with one or more sensors 25 inside the training computer. For example, the wrist computer may include an ECG sensor or a PPG sensor for measuring cardiac activity. In some embodiments, the sensor interface and the internal sensor are omitted. The measurement circuit system may also include a communication interface 16 that provides a wireless communication connection with an external sensor 28 (e.g., a measurement circuit system 114 included in clothing). The communication interface 16 may support Bluetooth protocols, such as Bluetooth Low Energy or Bluetooth Smart.

[0107] The training computer may also include a user interface 26 including a display screen and input components, such as buttons or a touch-sensitive display. The processing circuitry 14 may output instructions regarding the exercise to the user interface 26.

[0108] The training computer may also include or have access to at least one memory 20. The memory 20 may store computer program code 24, which includes instructions that can be read and executed by the processing circuit system 14 and configure the above-mentioned operations of the processing circuit system 14. The memory 20 may also store a configuration database 22, which defines parameters for the processing circuit system, such as Fig.16 Thresholds and / or mapping tables of embodiments.

[0109] Some embodiments described herein may be implemented in the form of a computer process defined by a computer program or a portion thereof. Figure 6 , Figure 7 , Fig. 9 , Figures 15 to 17 and Fig.19Embodiments of the described methods may be performed by executing at least a portion of a computer program including corresponding instructions. The computer program may be in source code form, object code form, or some intermediate form, and may be stored in some carrier, which may be any entity or device capable of carrying the program. For example, the computer program may be stored on a computer program distribution medium readable by a computer or processor. The computer program medium may be, for example, but not limited to, a recording medium, a computer memory, a read-only memory, an electrical carrier signal, a telecommunications signal, and a software distribution package. The computer program medium may be a non-transient medium. The coding of the software for executing the illustrated and described embodiments is well within the scope of those of ordinary skill in the art.

[0110] Fig.21 Another embodiment for realizing the electrodes and in particular improving the electrical coupling between the skin and the electrodes is shown. Fig.21 124 and 127. For example, when clothing including multiple electrodes becomes wet during exercise, electrical coupling between the electrodes through the clothing may be formed. This coupling may degrade the performance of the measurement. In order to isolate this form of electrical coupling, the electrical path between the electrodes through the clothing may be isolated. Fig.21 An embodiment is illustrated in which isolation is achieved by isolating the electrodes from the clothing by isolation elements 125, 129. The isolation elements may be made of, for example, TPU or another electrically isolating material. The isolation elements may be disposed between the respective electrodes and the clothing, for example surrounding the respective electrodes. In this way, the electrical coupling between the electrodes 124, 127 through the clothing is isolated, thereby improving the measurement accuracy.

[0111] It will be clear to a person skilled in the art that, as technology advances, the inventive concept can be implemented in various ways.The invention and its embodiments are not limited to the examples described above but may vary within the scope of the claims.

Claims

1. A garment made of a flexible material, comprising: a first measuring electrode integrated into the garment at a first location; a second measuring electrode integrated into the garment at a second location different from the first location; a measurement circuit system configured to measure bioimpedance by using a first measurement electrode and a second measurement electrode and transmit the measured bioimpedance, and to measure an electrocardiogram by using at least one or the other of the first measurement electrode and the second measurement electrode, wherein the measurement is performed using a plurality of bioimpedance sample sets, wherein samples having the same index in the respective sample sets are averaged to calculate a stroke volume; as well as at least one motion sensor configured to measure the motion of a first measuring electrode or a second measuring electrode of the clothing at a first position and / or a second position, wherein the measurement circuit system is configured to perform motion compensation on the measured bioimpedance signal based on the motion of the first measuring electrode or the second measuring electrode measured at the first position and / or the second position, and calculate the stroke volume by using a processor based on a mapping table that maps training intensity or heart rate to stroke volume when the measured motion is above a predetermined threshold or when the signal quality of the measured bioimpedance is below another predetermined threshold, The garment is an upper body garment, wherein the first measuring electrode is arranged above the heart level and the second measuring electrode is arranged below the heart level.

2. The garment of claim 1 , wherein the measurement circuitry is configured to trigger the start of a new bioimpedance sample set upon detection of an R-peak in the measured electrocardiogram, and to calculate stroke volume from one or more bioimpedance sample sets including the new bioimpedance sample set.

3. The garment of claim 1 or 2, wherein the measurement circuit system comprises at least one switch which switches the function of at least one of the measurement electrodes between electrocardiogram measurement and bioimpedance measurement.

4. The garment of claim 3 , wherein the at least one switch switches the functionality of the measuring electrodes between at least two of the following measuring modes: a full electrocardiogram mode, in which all measuring electrodes are used to measure an electrocardiogram; a full bioimpedance measurement mode, in which all measuring electrodes are used to measure bioimpedance; and a mixed measurement mode, in which a first subset of the measuring electrodes are used to measure an electrocardiogram and a second subset of the measuring electrodes are used to measure bioimpedance.

5. A garment as claimed in claim 1 or 2, wherein the garment has a back side arranged to face the back of a user wearing the garment, and also has a front side arranged to face the front of the user, wherein the first measuring electrode is deployed on at least the back side of the garment in the neck or shoulder area of ​​the garment.

6. A garment as claimed in claim 5, wherein the second measuring electrode is arranged in a chest area of ​​the garment, wherein the garment is arranged to fit next to the body at the location of the second measuring electrode.

7. The garment of claim 5, wherein the first measuring electrode is elongated and extends from the back side of the garment to the front side of the garment over the shoulders of the user.

8. The garment according to claim 1 or 2, further comprising: a third electrode integrated into the garment at a third location; a fourth electrode integrated into the garment at a fourth position, wherein a line drawn from the first measuring electrode to the second measuring electrode intersects a line drawn from the third electrode to the fourth electrode, and Wherein the measurement circuit system is configured to form a current feeding circuit system by using the third electrode and the fourth electrode, and to form a voltage measurement circuit system by using the first measurement electrode and the second measurement electrode.

9. The garment of claim 1 , wherein the measurement circuitry is configured to detect a cadence from the measured motion, and upon detecting the cadence, perform motion compensation by adjusting a length of an averaging window for the bioimpedance measurements based on the measured motion, wherein the length of the averaging window is adjusted such that a larger window is selected for higher cadences.

10. The garment of claim 1 , wherein the measurement circuitry is configured to detect a rhythm from the measured motion, and upon detecting the rhythm, perform interference suppression by detecting a signal component having a frequency of the determined rhythm in the bioimpedance measurement and removing the signal component from the measured bioimpedance.

11. A garment as claimed in claim 1 or 2, wherein the measurement circuit system is included in a housing that can be separated from the garment, and wherein the garment further comprises a shell configured to receive and position the shell and connect the measurement circuit system to the first measurement electrode and the second measurement electrode.

12. The garment of claim 11, wherein the housing includes a sensor head coupled to the measurement circuitry, wherein the housing includes an aperture for receiving the sensor head, and wherein the sensor head is arranged to contact the user's skin when the housing is connected to the housing and the user wears the garment.

13. The garment of claim 12, wherein the sensor head comprises at least one of a first measurement electrode and a second measurement electrode.

14. The garment of claim 12, wherein the sensor head comprises at least one of a photoplethysmographic sensor head and a temperature sensor head.

15. The garment as claimed in claim 1 or 2, wherein the garment is a shirt, a vest or a suspenders.

Images