Sensor element for recording myographic signals, sensor with such sensor elements and measuring system with at least one such sensor

Abstract

The invention relates to a sensor element (100), a sensor (150) and a measuring system (170) for recording myographic signals.The sensor element (100) comprises: an electrically non-conductive substrate layer (101); at least two electrodes (102) arranged on a top surface of the substrate layer (101); an electrically conductive measuring layer (103) made of an elastic first material, wherein the underside of the measuring layer (103) facing the at least two electrodes (102) has a structure; a first mechanical coupling element (104) made of an elastic second material; and a second mechanical coupling element (105) made of an elastic third material, wherein the second coupling element (105) is arranged with its underside on the top surface of the substrate layer (101); wherein the at least two electrodes (102) can each be connected to an evaluation and control unit (113) via an electrical conductor arranged on and / or in the electrically non-conductive substrate layer (101).

Description

[0001] The invention relates to a sensor element for detecting myographic signals, a sensor with such sensor elements, and a measuring system with such a sensor. The disclosed sensor element and the measuring system are suitable for the diverse detection of biosignals evoked by the human body, which in particular provide information about the activity of muscles and nerves. Applications are aimed at the areas of telepresence and telemanipulation, i.e., for operating computer games or sports equipment, as well as for inputting and controlling machines or aircraft. Accordingly, the disclosed sensor element and the measuring system are also particularly suitable for industrial applications. Furthermore, the disclosed sensor element and the measuring system can be used in the medical technology sector for diagnostic purposes, stimulation, or for the intuitive control of mechatronic prostheses.

[0002] In the prior art, sensor elements for acquiring myographic signals are known as individual sensor elements distributed across an extremity. Systems or sensor elements are known in the prior art that can acquire either electromyographic signals (EMG: electrical signal-based myography), force signal-based myography (FMG), impedance signal-based myography (IMG), or light signal-based myography (LMG) to detect, for example, muscle activity. Such systems support only one of the aforementioned sensor technologies at a time and do not allow simultaneous measurements of the different signals at the same location.

[0003] The following documents are referenced regarding the state of the art: - JIANG, Shuo [et al.]: “A novel, co-located EMG-FMG-sensing wearable bracelet for hand gesture recognition” in: Sensors and Actuators A: physical, Vol. 301, 2020, Article-No. 111738, pp. 1-5. ISSN 0924-4247. https: / / doi. org / 10. 1016 / J. sna. 2019. 111738 - US 2023 / 0 210 403 A1 - WO 2023 / 220 775 A1 - CN 1 13616395A

[0004] The object of the invention is to provide a sensor element that is easy to manufacture, requires little energy to operate, and simultaneously captures EMG signals and FMG signals at the same location with high resolution.

[0005] The invention is defined by the features of the independent claims. Advantageous further developments and embodiments are the subject of the dependent claims. Further features, applications, and advantages of the invention will become apparent from the following description and the explanation of exemplary embodiments of the invention illustrated in the figures.

[0006] The problem is solved by a sensor element for detecting myographic signals, which according to the invention comprises: - an electrically non-conductive substrate layer; - at least two electrodes arranged on one upper side of the substrate layer; - a measuring layer made of an elastic first material arranged directly above the at least two electrodes, wherein the elastic first material has an electrical conductivity due to embedded (and advantageously homogeneously distributed) electrically conductive particles, wherein the underside of the measuring layer facing the at least two electrodes has a structure such that, compared to a mechanically relaxed state of the measuring layer, a larger contact area KF is created between the measuring layer and the at least two electrodes in a mechanically stressed state of the measuring layer, and thus an electrical contact resistance between the at least two electrodes decreases in the mechanically stressed state; and - a first mechanical coupling element made of an elastic second material, wherein the first coupling element is arranged with its underside on the top side of the substrate layer, and wherein the first mechanical coupling element has on its underside a recess for (advantageously enclosing) receiving the at least two electrodes and the measuring layer arranged above them.

[0007] Advantageously, the first mechanical coupling element has a geometric design and the second material is selected such that, when an external mechanical force K acts on the first mechanical coupling element (e.g., through a muscle contraction), a predefined first force transmission (described as force transmission function KF1) to the elastic measuring layer results. Advantageously, the first force transmission function KF1 describes a predefined hysteresis and / or a predefined damping and / or a predefined vectorial force transmission. The geometric design of the first mechanical coupling element can, in particular, influence the direction of transmission of an externally applied force. The selection of the second material can, in particular, influence the damping and the temporal transmission behavior of an externally applied force.

[0008] The term "mechanically relaxed state of the measuring layer" here refers in particular to a state of rest characterized by the absence of any external force acting on the measuring layer. The term "mechanically stressed state of the measuring layer" here refers in particular to the presence of an external force F acting on the measuring layer, specifically a force acting perpendicularly to a surface of the measuring layer and compressing the measuring layer, thereby increasing the contact area KF between the measuring layer and the at least two electrodes and thus increasing the electrical conductivity between the at least two electrodes.

[0009] It is advantageous that the measuring layer is in the mechanically relaxed state in which no externally applied normal force F N acts on the measuring layer, a contact area K0 = KF(F N= 0) > 0 with at least two electrodes that move when a normal force F is applied N on the measuring layer depending on the normal force F N enlarged: KF(FN>0)>K0.

[0010] According to the invention, the sensor element further comprises: a second mechanical coupling element made of an elastic third material, wherein the second coupling element is arranged with its underside on the top side of the substrate layer, and has on its underside a recess for enclosing the first coupling element arranged on the top side of the substrate layer.

[0011] The at least two electrodes can each be connected to an evaluation and control unit via an electrical conductor that is arranged on and / or in the electrically non-conductive substrate layer.

[0012] Advantageously, the second mechanical coupling element has a geometric design and the third material is chosen such that when an external mechanical force acts on the second mechanical coupling element, a predetermined second force transmission (described as force transmission function KÜF2) to the first coupling element results.

[0013] Advantageously, the electrically non-conductive substrate layer consists of a substantially rigid material. Advantageously, the electrically non-conductive substrate layer is a printed circuit board (PCB). Advantageously, the PCB is made of a fiber-reinforced plastic. Alternatively, applications are conceivable in which the electrically non-conductive substrate layer consists of an elastic material.

[0014] Advantageously, at least two electrodes are made of aluminum or an aluminum alloy, or of copper or a copper alloy, or of silver or a silver alloy, or of gold or a gold alloy, or of platinum or a platinum alloy, or of graphite, or of graphene, or of one or more of the aforementioned materials.

[0015] Advantageously, the elastic first material of the measuring layer has an elastomer matrix in which the electrically conductive particles are homogeneously distributed. Advantageously, the electrically conductive particles of the first material consist of carbon, metal, graphite, graphene, aluminum, copper, gold, platinum, silver, or a mixture thereof.

[0016] Advantageously, the elastomer matrix of the first material consists of silicone, polyurethane or PVC, or a mixture thereof.

[0017] Advantageously, the electrically conductive particles of the first material have at least two distinct regions B1:= [D1... D2] and B2:= [D3... D4] of diameter D, whereby regions B1 and B2 do not overlap, and for D3: D3 ≥ 2 * D2. Advantageously, for B1: B1 = [D1 = 0.1 µm ... D2 = 1.0 µm].

[0018] Advantageously, the measuring layer has a thickness in the range of 5 µm to 100 µm.

[0019] Advantageously, the structuring of the underside of the measuring layer (103) facing the at least two electrodes exhibits a mean roughness R a in the range of 0.001 µm to 5 µm, especially from 0.1 µm to 2 µm.

[0020] The structuring of the underside of the measuring layer facing at least two electrodes is advantageous, as it is homogeneous across the surface.

[0021] Advantageously, the measuring layer is fixed in the recess of the first mechanical coupling element over at least two electrodes. It is also advantageous if the measuring layer is chemically fixed (e.g., bonded) to at least two electrodes.

[0022] The elastic second material is advantageous because it is electrically non-conductive.

[0023] Advantageously, the first mechanical coupling element consists of two or more first partial coupling elements joined together or nested within each other, wherein at least two of the first partial coupling elements have different geometries and / or are made of different second materials. The geometric design of the first mechanical partial coupling elements can, in particular, influence the transmission direction of an externally applied force. The selection of the different second materials can, in particular, influence the temporal transmission behavior of an externally applied force.

[0024] Advantageously, the second mechanical coupling element consists of two or more second sub-coupling elements joined together or nested within each other, wherein at least two of the second sub-coupling elements have different geometries and / or are made of different third materials. The geometric design of the second mechanical sub-coupling elements can, in particular, influence the direction of transmission of an externally applied force. The selection of different third materials can, in particular, influence the temporal transmission behavior of an externally applied force.

[0025] Advantageously, a distal surface of the second mechanical coupling element, relative to the substrate layer, consists of a biocompatible material suitable for direct contact with human skin. This distal surface is, in particular, the surface with which the sensor element is positioned directly against a person's skin.

[0026] Advantageously, the elastic third material of the second coupling element or the second partial coupling elements has an elastomer matrix in which electrically conductive particles are distributed. Advantageously, these electrically conductive particles consist of carbon, metal, graphite, graphene, aluminum, copper, gold, platinum, silver, silver chloride, or a mixture thereof.

[0027] Advantageously, the second mechanical coupling element has a higher density of electrically conductive particles on its distal surface than in the rest of the second mechanical coupling element. Advantageously, the second mechanical coupling element has an electrically conductive coating on its distal surface.

[0028] Advantageously, the second mechanical coupling element consists of an electrically conductive third material, which is electrically connected to at least one electrode arranged on the substrate layer.

[0029] Advantageously, the elastic third material of the second coupling element is optically transparent. Advantageously, the second coupling element is connected in a light-conducting manner to a light source and a light sensor located on the substrate layer. The elastic third material of the second coupling element is particularly optically transparent to light from the light source. Advantageously, the light source is an LED. Advantageously, the second coupling element has one or more light guides that connect a distal transparent surface of the sensor element to the light source, and one or more light guides that connect a distal transparent surface of the sensor element to the light sensor.

[0030] Another aspect of the invention relates to a sensor with several sensor elements arranged on a substrate layer, as described above.

[0031] An advantageous further development of the sensor is characterized by the fact that the several sensor elements are embedded in an elastic, electrically non-conductive material layer made of a fourth material in such a way that the respective distal surfaces of the individual sensor elements protrude above this material layer.

[0032] Advantageously, the substrate layer has a thickness of 0.1 mm to 2 mm.

[0033] Advantageously, the sensor has a flat dimension in the range of width: 5 mm to 70 mm and length 5 mm to 70 mm, in particular width 15 mm length 50 mm.

[0034] Advantageously, the sensor has a number N of sensor elements in the range of N = 10 to 50, in particular N = 16 to 32.

[0035] Another aspect of the invention relates to a measuring system for recording and evaluating force-based myographic signals, comprising: at least one sensor for recording the force-based myographic signals recorded by the individual sensor elements, as described above; an evaluation and control unit connected to the at least two electrodes of the individual sensor elements for evaluating the recorded myographic signals as evaluation results; and an interface for outputting the evaluation results.

[0036] Advantageously, the evaluation and control unit is designed and configured to perform impedance measurements between electrodes of different sensor elements and to provide the evaluation results at the interface.

[0037] Advantageously, the evaluation and control unit is designed and configured to control the light sources of the sensor elements and to evaluate the light signals detected by the light sensors of the sensor elements and to provide them as evaluation results at the interface.

[0038] An advantageous further development of the measuring system is characterized in that each of the sensors is designed as a link of a bracelet or is integrated into a link of a bracelet, wherein the sensors in the bracelet are arranged such that the distal surfaces of the individual sensor elements lie on the inside of the bracelet; the links of the bracelet are connected via a mechanical coupling element, which essentially consists of an auxetic material; and the coupling elements mechanically (advantageously directly) connect the substrate layers of two adjacent links.

[0039] Auxetic materials have the property of expanding perpendicular to the direction of stretching. They are therefore characterized by a negative Poisson's ratio.

[0040] Advantageously, the wristband includes a power source. Advantageously, the wristband includes an output unit for emitting visual and / or acoustic signals. The output unit is specifically designed to output data acquired by the measuring system and / or to emit warning signals if, for example, the acquired data does not meet predefined conditions, so that the wearer of the wristband can be warned immediately.

[0041] The disclosed invention enables the diverse acquisition of biosignals evoked by the human body, which in particular provide information about the activity of muscles and nerves. Potential applications of the invention target areas such as telepresence and telemanipulation, for example, for operating computer games or sports equipment, as well as for inputting and controlling machines or aircraft. Accordingly, the invention finds application in the consumer sector, but also in industry and research. Furthermore, the invention can be used in the medical technology sector for diagnostic purposes, stimulation, or for the intuitive control of mechatronic prostheses. For the first time, the invention enables the use of high-density, efficient pressure and electromyographic measurements at the same location and in the same device, something previously only possible with different, and especially spatially distributed, systems.Furthermore, the arrangement enables for the first time synchronous and uniformly localized stimulation with simultaneous measurement of the myographic response, thus enabling more efficient methods in diagnostics.

[0042] Further advantages, features, and details will become apparent from the following description, in which – possibly with reference to the drawing – at least one embodiment is described in detail. Identical, similar, and / or functionally equivalent parts are marked with the same reference numerals.

[0043] They show: Fig. 1 a basic operating principle of the proposed sensor element 100, in which the increase of the contact area when a force F acts on the measuring layer 103 leads to a reduction of the contact resistance between the at least two electrodes 102. Fig. 2 a sensor element 100 according to the invention in a vertical cross-section Fig. 3 a further sensor element 100 according to the invention in a vertical cross-section, which is designed and configured for measuring the impedance of the skin of a living being as well as for inputting and recording electrical signals and can thus be used for the simultaneous measurement of signals for FMG, EMG and IMG. Fig. 4 a further sensor element 100 according to the invention in a vertical cross-section, which is opposite the sensor element 100 of Fig. 3 is additionally designed and set up for the transmission and detection of light signals and can therefore be used for the simultaneous measurement of signals for FMG, EMG, IMG and LMG. Fig. 5a an example of a sensor 150 with several array-like arranged sensor elements 100. Fig. 5b of a representation of the substrate layer 101 with electrodes 102 and 110 of the sensor 150 arranged on it Fig. 5a. Fig. 6 three sensor elements 100 according to Fig. 3. Explanation of the measurement of the impedance of the skin of a living being Fig. 7 three sensor elements 100 according to Fig. 4. Explanation of light signal-based myography (LMG) measurement Fig. 8a Measuring system 170 with several sensors 150 designed as links 180 of a bracelet, which are connected to each other via coupling elements 181. Fig. 8b Detailed view of two sensors 150 connected via coupling elements 181 as links 180 of a bracelet. Fig. 9a,b Example of a coupling element made from an auxetic material or structure 181. Fig. 10 Measuring system 170 with several sensors 150 designed as links 180 of a bracelet, which are connected to each other via auxetic coupling elements 181.

[0044] Fig. Figures 1a and 1b show a basic operating principle of the proposed sensor element 100, in which the increase of the contact area when a force F acts on the measuring layer 103 leads to a reduction of the contact resistance between the at least two electrodes 102.

[0045] Both figures depict a sensor element 100 for detecting myographic signals in a vertical cross-section, comprising: an electrically non-conductive substrate layer 101; two electrodes 102 arranged on a top surface of the substrate layer 101; a measuring layer 103 arranged directly above the two electrodes 102, made of an elastic first material, wherein the elastic first material has electrical conductivity due to embedded electrically conductive particles, and the underside of the measuring layer 103 facing the two electrodes 102 has a structure such that, compared to a mechanically relaxed state of the measuring layer 103 (shown in Fig. 1a), in a mechanically stressed state of the measuring layer 103 by applying a force F acting perpendicularly on the measuring layer 103 (shown in Fig. 1b) a larger contact area KF is created between the measuring layer 103 and the two electrodes 102, and thus an electrical contact resistance R between the two electrodes 102 decreases in the mechanically stressed state.

[0046] Fig. Figure 2 shows a sensor element 100 according to the invention in a vertical cross-section. The sensor element 100 for detecting myographic signals comprises: an electrically non-conductive substrate layer 101; two electrodes 102 arranged on a top side of the substrate layer 101, wherein one electrode 102 is designed as a circular area and the other electrode 102 is designed as a ring enclosing the circular area;A measuring layer 103 made of an elastic first material is arranged directly above the two electrodes 102, wherein the elastic first material has an electrical conductivity due to embedded and electrically conductive particles, and the underside of the measuring layer 103 facing the two electrodes 102 has a structure such that, compared to a mechanically relaxed state of the measuring layer 103, a larger contact area KF is created between the measuring layer 103 and the two electrodes 102 in a mechanically stressed state of the measuring layer 103, and thus an electrical contact resistance R between the at least two electrodes 102 decreases in the mechanically stressed state.

[0047] Furthermore, the sensor element 100 comprises a first mechanical coupling element 104 made of an elastic second material, wherein the first coupling element 104 is arranged with its underside on the top side of the substrate layer 101, and has a recess on its underside for (enclosing) receiving the two electrodes 102 and the measuring layer 103 arranged above them. The two electrodes 102 and the measuring layer 103 arranged above them are thus arranged in the recess.

[0048] Furthermore, the sensor element 100 comprises a second mechanical coupling element 105 made of an elastic third material, wherein the second coupling element 105 is arranged with its underside on the top side of the substrate layer 101, and has a recess on its underside for (enclosing) receiving the first coupling element 104 arranged on the top side of the substrate layer 101. The second mechanical coupling element 105 thus receives the first mechanical coupling element 104 in its recess, preferably in a form-fit or material-fit manner. The two electrodes 102 can each be connected to an evaluation and control unit 113 (not shown) via an electrical conductor arranged on and / or in the electrically non-conductive substrate layer 101 (not shown). The sensor element 100 is particularly suitable for acquiring signals for FMG.

[0049] Fig. Figure 3 shows a further sensor element 100 according to the invention in a vertical cross-section, which is designed and configured for measuring the impedance of the skin of a living being as well as for tapping and inputting electrical signals and for detecting electrical signals and can thus be used for the simultaneous measurement of signals for FMG, EMG and IMG.

[0050] Sensor element 100 differs from sensor element 100 of Fig. 2. The second mechanical coupling element 105 has an electrically conductive coating 130 on its distal surface, the third material is electrically conductive, and the second coupling element 105 is electrically connected to an electrode 110 arranged on the substrate layer 101. Electrical signals can be introduced via the electrode 110 into a living organism in contact with the coating 130 through the third material and the coating 130, or electrical signals can be picked up via the skin of the living organism. The electrode 130 is connected to a control and evaluation unit (not shown).

[0051] Fig. Figure 4 shows another sensor element 100 according to the invention in a vertical cross-section, which differs from the sensor element 100 of Fig. 3 is additionally designed and set up for the transmission and detection of light signals and can therefore be used for the simultaneous measurement of signals for FMG, EMG, IMG and LMG.

[0052] Sensor element 100 differs from sensor element 100 of Fig. 3. The elastic third material is optically transparent, and the second coupling element 105 is connected in a light-conducting manner to a light source 111 (e.g., LED) and a light sensor 112 (photocell) arranged on the substrate layer 101. The light source 111 and the light sensor 112 are connected to a control and evaluation unit (not shown).

[0053] Fig. Figure 5a shows an example of a sensor 150 with several array-like arranged sensor elements 100.

[0054] Fig. Figure 5b shows a representation of the substrate layer 101 with electrodes 102 and 110 of the sensor 150 arranged on it. Fig. 5a.

[0055] Fig. Figure 6 shows three sensor elements 100 according to Fig. 3. To explain impedance measurement with at least two sensor elements 100. A known electrical signal (current I) is applied via the middle sensor element 100. S ) is emitted into a living being in contact with surface 130, which is detected by the other two sensor elements 100. Impedance values ​​can be determined from the measurements.

[0056] Fig. Figure 7 shows three sensor elements 100 according to Fig. 4. To explain light signal-based myography (LMG) measurement. A known light signal (hv1) is emitted into the skin of a living being via the light source 111 of the middle sensor element 100; the backscattered light is detected by the light sensors 112 of the other two sensor elements 100 as hv2 and hv3.

[0057] The substrate layer 101 can, for example, be a printed, rigid printed circuit board made of glass fiber epoxy resin laminate, with copper conductors and preferably gold-plated electrodes 102, 110. The use of flexible printed circuit boards as the substrate layer 101 is also possible. Furthermore, elastic, i.e., stretchable, substrate layers 101 are possible, which preferably have a greater hardness than the coupling elements 104, 105. The electrodes 102, 110 and the conductors are preferably made of conductive elastomers. Rigid conductors, on the other hand, have geometric compensating elements (e.g., bonded copper traces with meander structures for strain compensation). It is preferred to use simple geometries for the electrodes 102, 110, e.g., concentric rings, with the innermost ring preferably being a via. Alternatively, C-shaped structures are preferred.It can be provided that the areas around the electrodes 102, 110 have a slight depression of 5 µm to 30 µm, depending on the thickness of the measuring layer 103, so that the measuring layer 103 does not expand significantly radially when compressed. This allows for high areal densities of individual sensor elements in sensor matrices without the measuring layer 103 being compressed towards an adjacent electrode 102, 110.

[0058] The measuring layer 103 advantageously has a one-sided structured underside. The measuring layer 103 consists, for example, of an elastomer matrix which is impregnated with electrically conductive particles, wherein the particle size is advantageously not homogeneous and thus forms an underside with a structured roughness during vulcanization. When a force F is applied to the measuring layer 103, the structured underside is compressed, whereby the contact area KF between the structured underside and the electrodes 102 advantageously increases proportionally to the normal force F.

[0059] The first mechanical coupling element 104 is referred to as the "intermediate." It advantageously serves to adapt the force transmission function KÜF1 and thus to scale a sensor signal generated by the sensor element 100. In the simplest case, the transmission function KÜF1 is set via the hardness of the coupling element. More complex transmission functions can be achieved via geometric properties as well as the integration of fillers and filler structures (e.g., hysteresis, damping, etc.). The first coupling element 104 can also serve for mechanical fixation on the substrate layer 101.

[0060] Electrodes 102 and 110 are used to detect electrical resistance R, impedance, current, or voltage. When printed circuit boards are used, electrodes 102 and 110 are simple conductive traces with a defined geometry. They are advantageously made of copper and may preferably be gold-plated to minimize their potential contact resistance relative to the contact resistance of the measuring layer 103. The size of electrodes 102 and 110 depends on the application and the associated size and geometry of the measuring layer 103.

[0061] The second mechanical coupling element 105 advantageously serves to adapt the sensor element 100 to a desired application. This second coupling element is particularly useful for adapting the combination of the first coupling element 104, the measuring layer 103, and the substrate layer 101 with electrodes 102, 110 to the requirements of an application. For force measurement, the intended form of force application and transmission is crucial. If, for example, the sensor element 100 is used to measure contact forces on human skin, the distal surface of the second coupling element is advantageously made of a biocompatible material. At the same time, small forces F must be optimally transmitted to the measuring layer 103.

[0062] The second coupling element 105 can advantageously consist of an elastomer containing conductive fillers, which is connected to the mass (GND, Ground) of a measuring electronics in order to shield the sensor element 100 and at the same time enable a structural adaptation to the application.

[0063] The second electrically conductive coupling element 105 establishes the connection between the measuring or stimulation electrodes 102, 110 on the substrate layer 101 and the skin of a test subject. The coupling element 105 is advantageously made from an elastomer matrix containing conductive particles. When measurements are used for the LMG method, the second coupling element 105 is advantageously vertically segmented such that electrically conductive segments are arranged next to optically transparent segments, allowing electrical and optical signals to be transmitted in parallel.

[0064] The conductive second coupling element 105 can be segmented for the emission and acquisition of light-based myographic signals (LMG) such that optically transparent segments are created which guide light emitted from the light source 111 at the substrate layer 101 to the distal surface of the second coupling element. This segmented, light-transparent second coupling element can be manufactured, for example, by injection molding. In the simplest case, light-guiding channels are recessed during the production of the electrically conductive second coupling element. After vulcanization of the conductive part, these channels are filled with a suitable elastomer that is transparent to light from the light source 111.

[0065] The electrode 110 serves to contact the electrically conductive second coupling element 105. The electrode 110 is located on the side of the substrate layer facing the second coupling element 105, wherein the conductive coupling element 105 is advantageously either joined or bonded to the electrode 110 after its manufacture, or is manufactured directly onto the electrode 110 during the injection molding process. The electrode 110 is then advantageously connected via electrical conductors (e.g., a printed circuit board) to a control and evaluation unit, which enables connection to drivers or amplifiers for the stimulation or measurement of evoked signals.

[0066] To produce an optimal contact resistance to the skin of a test subject, the distal end of the electrically conductive second coupling element 105 is advantageously provided with an electrically conductive coating 130 made of an elastomer mixture which contains particles, preferably of silver, silver / silver chloride or gold.

[0067] Optoelectronic transmitters / light sources 111 are used to emit light-based myographic signals (LMG), which are advantageously attached to the base of the segmented, conductive second coupling element 105 in such a way that they can couple optical signals into at least one optically transparent segment of the second coupling element 105, and the optical signals thus reach the distal surface of the second coupling element 105.

[0068] To capture and evaluate the optical signals reflected from a subject's tissue when using LMG technology, an optoelectronic receiver 112 is advantageously arranged on the substrate layer 101 at the base of the optically transparent second coupling element 105. Depending on the wavelength used, different optical information can be determined from the optical signals reflected from the tissue.

[0069] Fig. Figure 8a shows a measuring system 170 with several sensors 150 designed as links 180 of a wristband, which are connected to each other via coupling elements 181. The measuring system 170 further comprises an evaluation and control unit 113 (not shown) connected to the respective electrodes 102, 110 of the individual sensor elements 100 for evaluating the recorded myographic signals as evaluation results, as well as an interface (not shown) for outputting and / or providing the evaluation results. The interface can, for example, be a Bluetooth interface. The evaluation results can advantageously be transmitted to a smartphone.

[0070] Fig. Figure 8b shows a detailed view of two sensors 150 connected via coupling elements 181 as links 180 of a bracelet.

[0071] Fig. Figures 9a and 9b show an example of a coupling element 181 made from an auxetic material or structure.

[0072] Fig. Figure 10 shows a measuring system 170 with several sensors 150 designed as links 180 of a bracelet, which are connected to each other via auxetic coupling elements 181. Advantageously, the measuring system has its own power source.

[0073] Although the invention has been further illustrated and explained in detail by means of preferred embodiments, the invention is not limited by the disclosed examples, and other variations can be derived from them by a person skilled in the art without departing from the scope of protection of the invention. It is therefore clear that a multitude of possible variations exist. It is also clear that the embodiments mentioned as examples are truly only examples and are not to be understood in any way as limiting, for example, the scope of protection, the possible applications, or the configuration of the invention.Rather, the preceding description and the description of the figures enable the person skilled in the art to implement the exemplary embodiments in concrete terms, whereby the person skilled in the art, with knowledge of the disclosed inventive concept, can make various changes, for example with regard to the function or the arrangement of individual elements mentioned in an exemplary embodiment, without leaving the scope of protection defined by the claims and their legal equivalents, such as a further explanation in the description. Reference symbol list 100 sensor elements 101 Substrate layer 102 electrodes 103 Measuring layer 104 first mechanical coupling element 105 second mechanical coupling element 111 Light source e.g. LED 112 Light sensor 113 Evaluation and control unit 114 Interface 130 coating 150 sensors with multiple sensor elements 100 170 measuring system 180 links of a bracelet 181 Coupling element 190 skin 191 auxetic material

Claims

[1] Sensor element (100) for detecting myographic signals, comprising: - an electrically non-conductive substrate layer (101); - at least two electrodes (102) arranged on a top side of the substrate layer (101); - a measuring layer (103) made of an elastic first material arranged directly above the at least two electrodes (102), wherein ◯ the elastic first material exhibits electrical conductivity due to embedded and electrically conductive particles, and ◯ the underside of the measuring layer (103) facing the at least two electrodes (102) has a structure such that, compared to a mechanically relaxed state of the measuring layer (103), a larger contact area is created between the measuring layer (103) and the at least two electrodes (102) in a mechanically stressed state of the measuring layer (103), and thus an electrical contact resistance between the at least two electrodes (102) decreases in the mechanically stressed state; - a first mechanical coupling element (104) made of an elastic second material, wherein the first coupling element (104) ◯ with its underside on the top side of the substrate layer (101), and ◯ has a recess on its underside for receiving at least two electrodes (102) and the measuring layer (103) arranged above them, and - a second mechanical coupling element (105) made of an elastic third material, wherein the second coupling element (105) ◯ with its underside on the top side of the substrate layer (101), and ◯ has on its underside a recess for enclosing the first coupling element (104) arranged on the top side of the substrate layer (101), wherein the at least two electrodes (102) can be connected to an evaluation and control unit (113) via an electrical line arranged on and / or in the electrically non-conductive substrate layer (101). [2] Sensor element (100) according to claim 1, wherein the electrically conductive particles have at least two different regions B1:= [D1... D2] and B2:= [D3... D4] of diameters D, wherein the regions B1 and B2 do not overlap, and for D3: D3 ≥ 2 * D2. [3] Sensor element (100) according to one of claims 1 or 2, wherein the first mechanical coupling element (104) consists of two or more first partial coupling elements joined together, wherein at least two of the first partial coupling elements have a different geometry and / or consist of different second materials. [4] Sensor element (100) according to one of claims 1 to 3, wherein the second mechanical coupling element (105) consists of two or more second part coupling elements joined together, wherein at least two of the second part coupling elements have a different geometry and / or are made of different third materials. [5] Sensor element (100) according to one of claims 1 to 4, wherein the elastic third material of the second coupling element (105) has an elastomer matrix in which electrically conductive particles are distributed. [6] Sensor element (100) according to one of claims 1 to 5, wherein the second mechanical coupling element (105) has an electrically conductive coating (130) on its distal surface. [7] Sensor element (100) according to claim 6, wherein the electrically conductive coating (130) is optically transparent. [8] Sensor element (100) according to one of claims 1 to 7, wherein the second mechanical coupling element (105) is electrically connected to at least one electrode (110) arranged on the substrate layer (101). [9] Sensor element (100) according to one of claims 1 to 8, wherein the elastic third material of the second coupling element (105) is optically transparent or the second coupling element (105) comprises at least one optical conductor. [10] Sensor element (100) according to one of claims 1 to 9, wherein a distal surface of the second coupling element (105) is connected in a light-conducting manner to a light source (111) arranged on the substrate layer (101) and a light sensor (112) arranged on the substrate layer (101). [11] Sensor (150) with several sensor elements (100) arranged on a substrate layer (101) according to one of claims 1 to 10. [12] Sensor (150) according to claim 11, wherein the multiple sensor elements (100) are embedded in an elastic, electrically non-conductive material layer (118) made of a fourth material such that the respective distal surfaces of the individual sensor elements (100) extend beyond this material layer (118). [13] Measuring system (170) for recording and evaluating myographic signals, comprising: - at least one sensor (150) for detecting the myographic signals detected by the individual sensor elements (100) according to one of claims 11 or 12, - an evaluation and control unit (113) connected to at least two electrodes (102) of the individual sensor elements (100) for evaluating the recorded myographic signals as evaluation results, and - an interface (114) for outputting the evaluation results. [14] Measuring system (170) according to claim 13, wherein the evaluation and control unit (113) is designed and configured to control the light sources (111) of the sensor elements (100) and to evaluate the light signals detected by light sensors (112) of the sensor elements (100) and to provide them as evaluation results at the interface (114). [15] Measuring system (170) according to one of claims 13 or 14, wherein - each of the sensors (150) is designed as a link (180) of a bracelet, wherein the sensors (150) are arranged in the bracelet such that the distal surfaces of the individual sensor elements (100) are located on the inside of the bracelet, - the links (180) of the bracelet are each connected via a mechanical coupling element (181) which consists essentially of an auxetic material (191), and - the coupling elements (181) mechanically connect the substrate layers (101) of two adjacent members (180).

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