Stretchable deformable electrode and biological sensing system

Abstract

A stretchable electrode and a biological sensing system, the stretchable electrode comprising a stretchable portion. The stretchable portion has a first stretchable range and a second stretchable range, wherein the stretchable portion has a first length variation and a first resistance variation in the first stretchable range, and the stretchable portion has a second length variation and a second resistance variation in the second stretchable range. The first resistance variation is substantially constant, and the second resistance variation changes with the change of the second length variation, wherein the second resistance variation is represented as R2, the second length variation is represented as L2, and R2=A*L2, wherein A is a positive number between 0.05 and 2. Since the stretchable electrode of the present disclosure has the ability to withstand a large degree of stretchable deformation, it can be well applied to a wearable biological sensing system without local cracks or complete rupture caused by the user's limb movements. In addition, by matching the stretchable electrode with a corrector, the biological sensing system of the present disclosure can have a wider application compared with traditional physiological sensing devices.

Description

Technical Field

[0001] This disclosure relates to a stretchable electrode and a biosensing system including said stretchable electrode. Background Technology

[0002] With the advancement of technology, many physiological sensing devices on the market are gradually evolving towards thinner, smaller, and wearable forms. However, the sensing electrodes in wearable physiological sensing devices are often unable to withstand the significant stretching and deformation caused by the user's limb movements, easily developing local cracks or breaking completely during use. This can lead to noise or signal loss, preventing the physiological sensing device from accurately collecting the physiological signals measured by the sensing electrodes. Therefore, providing a sensing electrode that can be reliably and stably applied in wearable physiological sensing devices is a worthy research direction in this field. Summary of the Invention

[0003] According to some embodiments disclosed herein, a tensile deformation electrode includes a tensile portion. The tensile portion has a first tensile range and a second tensile range, wherein the tensile portion has a first length change and a first resistance change in the first tensile range, and the tensile portion has a second length change and a second resistance change in the second tensile range. The first resistance change is substantially constant, and the second resistance change changes with the change in the second length, wherein the second resistance change is represented by R2, the second length change is represented by L2, and R2 = A × L2, where A is a positive number between 0.05 and 2.

[0004] In some embodiments disclosed herein, the tensile resistance recovery rate of the stretched portion is between 95% and 100%.

[0005] In some embodiments disclosed herein, the number of tensile recovery cycles of the stretched portion is between 1 and 3000.

[0006] In some embodiments disclosed herein, the determination coefficient (R) of the equation denoted by R² = A × L² is... 2 The value ranges from 0.95 to 1.00.

[0007] In some embodiments disclosed herein, the first length change is between 0% and 250%, and the second length change is between 250% and 450%.

[0008] In some embodiments disclosed herein, the ratio of the range of the first length change to the range of the second length change is greater than or equal to 1.25.

[0009] In some embodiments disclosed herein, the stretching portion includes a plurality of conductive particle structures, and the average particle size of the conductive particle structures is between 0.5 nm and 100 μm.

[0010] In some embodiments disclosed herein, the stretching portion includes a plurality of conductive wire structures, the average wire diameter of which is between 0.5 nm and 1 μm, and the average wire length of which is between 50 nm and 1000 μm.

[0011] According to other embodiments disclosed herein, a biosensing system includes a transmitter, a receiver, a controller, and a calibrator. The transmitter includes a working electrode layer, and the working electrode layer is the aforementioned tensile deformation electrode. The receiver is electrically connected to the transmitter and configured to receive a analyte and transmit a first signal value generated by the analyte to the transmitter, causing the transmitter to output a first signal value and a second signal value. The controller is electrically connected to the transmitter and configured to receive the first signal value and the second signal value, and determine whether the second signal value falls within a second tensile range of the tensile portion. The calibrator is electrically connected to the controller, wherein when the second signal value falls within the second tensile range of the tensile portion, the calibrator is configured to calibrate the first signal value to calculate the analyte parameter.

[0012] In some embodiments disclosed herein, when the second signal value does not fall within the second stretching range of the stretching portion, the corrector does not perform the correction function.

[0013] In some embodiments disclosed herein, the first signal value includes a current value, and the second signal value includes a resistance value.

[0014] In some embodiments disclosed herein, the stretching portion extends from the first endpoint to the second endpoint, wherein when the current value is between 0.0001 μA and 1000 μA, the change in the stretching length of the stretching portion is less than 450%, and the potential difference between the first endpoint and the second endpoint is between -1V and 1V, the area of ​​the stretching portion in the cyclic voltammogram is between 0.00015 μA × V and 1500 μA × V.

[0015] In some embodiments disclosed herein, the stretching portion extends from the first endpoint to the second endpoint, wherein when the current value is between 0.0001 μA and 835 μA, the change in the stretching length of the stretching portion is less than 450%, and the potential difference between the first endpoint and the second endpoint is between -1V and 1V, the area of ​​the stretching portion in the square wave voltammogram is between 0.00015 μA × V and 1245 μA × V.

[0016] In some embodiments disclosed herein, the stretching portion extends from the first endpoint to the second endpoint, wherein when the current value is between 0.0001 μA and 795 μA, the change in the stretching length of the stretching portion is less than 450%, and the potential difference between the first endpoint and the second endpoint is between -1V and 1V, the area of ​​the stretching portion in the differential pulse voltammogram is between 0.00015 μA × V and 1195 μA × V.

[0017] In some embodiments disclosed herein, the receiver may include a signal transmission layer, a signal generation layer, and a signal enhancement layer. The signal transmission layer is connected to the working electrode layer and configured to transmit a first signal value to the working electrode layer. The signal generation layer is configured to receive the analyte. The signal enhancement layer is sandwiched between the signal transmission layer and the signal generation layer.

[0018] In some embodiments disclosed herein, the oxidation potential of the signal transmission layer is higher than that of the signal enhancement layer.

[0019] In some embodiments disclosed herein, the working electrode layer has opposing first and second surfaces, and the biosensing system further includes a substrate and a waterproof layer. The substrate is disposed on the first surface of the working electrode layer. The waterproof layer is disposed on the second surface of the working electrode layer and has through-holes through which the receiver is exposed.

[0020] In some embodiments disclosed herein, the working electrode layer has opposing first and second sides, and the transmitter further includes a counter electrode layer and a reference electrode layer. The counter electrode layer is disposed on the first side of the working electrode layer and includes the aforementioned tensile deformation electrode. The reference electrode layer is disposed on the second side of the working electrode layer and includes the aforementioned tensile deformation electrode.

[0021] According to the embodiments disclosed above, since the tensile deformation electrode disclosed herein has the ability to withstand large-scale tensile deformation, it can be well applied to wearable biosensing systems without developing local cracks or breaking completely due to the user's limb movements. Furthermore, when the tensile deformation (e.g., length change) of the tensile deformation electrode exceeds a certain value, the resistance of the tensile deformation electrode begins to change, resulting in a weakening of the output signal value. At this time, the biosensing system can also perform a correction function through its calibrator to calculate the actual signal value (e.g., a first signal value), and then calculate the analyte parameters of the substance to be measured in the user's body. In other words, through the combination of the tensile deformation electrode and the calibrator, the biosensing system disclosed herein has a wider range of applications compared to traditional physiological sensing devices. Attached Figure Description

[0022] To make the above and other objects, features, advantages and embodiments disclosed herein more apparent and understandable, the accompanying drawings are described below:

[0023] Figure 1 A block diagram illustrating a biosensing system according to some embodiments of this disclosure;

[0024] Figure 2 Draw Figure 1 A three-dimensional schematic diagram of the working electrode layer of the transmitter;

[0025] Figure 3 Draw Figure 2A graph showing the relationship between the change in resistance of the stretched portion of the tensile deformation electrode and the change in tensile length.

[0026] Figure 4 Draw Figure 2 A graph showing the relationship between the resistance change of the stretched portion of the medium-stretched deformation electrode during stretching / recovery and time.

[0027] Figure 5 Draw Figure 1 An explosion diagram of a biosensing system, omitting the controller and calibrator;

[0028] Figure 6 A graph showing the relationship between the sensitivity of a biosensing system according to some embodiments of this disclosure and the change in the stretching length of the stretching portion is presented.

[0029] Figure 7 A graph showing the relationship between the first signal value and the analyte parameter of a biosensing system according to some embodiments of this disclosure is presented.

[0030] Figure 8 Cyclic voltammetry diagrams of the stretched portion of a stretched deformable electrode in a biosensing system according to some embodiments of this disclosure are shown.

[0031] Figure 9A A square wave voltammetry diagram of the stretched portion of a stretched deformation electrode in a biosensing system according to some embodiments of this disclosure is shown.

[0032] Figure 9B It is Figure 9A The test results are presented in detail through the relationship between the area of ​​the tensile portion in the square wave voltammetry and the test parameters of the test substance.

[0033] Figure 10A A differential pulse voltammetry diagram of the stretched portion of a stretched deformation electrode in a biosensing system according to some embodiments of this disclosure is shown.

[0034] Figure 10B It is Figure 10A The test results are presented in detail through the relationship between the area of ​​the tensile portion in the differential pulse voltammetry and the test parameters of the analyte.

[0035] Figure 11A A time-ampere curve is plotted of the stretched portion of a stretched deformation electrode in a biosensing system according to some embodiments of this disclosure; and

[0036] Figure 11B It is Figure 11A The test results are presented in detail through the relationship between the first signal value of the tensile part at 50 seconds in the chronoampere curve and the test parameters of the test substance.

[0037] [Symbol Explanation]

[0038] 100: Biosensor System

[0039] 110: Receiver

[0040] 112: Signal Transmission Layer

[0041] 114: Signal Enhancement Layer

[0042] 116: Signal Generation Layer

[0043] 120: Transmitter

[0044] 122: Tensile Deformation Electrode

[0045] 122A: Working electrode layer

[0046] 122B: Counter electrode layer

[0047] 122C: Reference electrode layer

[0048] 122S: Tensioning section

[0049] 123A: First side

[0050] 125A: Second side

[0051] 130: Controller

[0052] 140: Corrector

[0053] 150:Substrate

[0054] 160: Waterproof layer

[0055] 170: Protective layer

[0056] H: Through hole

[0057] P1: First endpoint

[0058] P2: Second endpoint

[0059] A1: First stretching range (non-correction zone)

[0060] A2: Second stretching range (correction zone)

[0061] Z1, Z2: Range Detailed Implementation

[0062] The following describes several embodiments of this disclosure with reference to the accompanying drawings. For clarity, many practical details will be described in the following description. However, it should be understood that these practical details should not be used to limit this disclosure. That is, in some embodiments of this disclosure, these practical details are not essential and therefore should not be used to limit this disclosure. Furthermore, for the sake of simplicity in the drawings, some known and conventional structures and components will be shown in a simplified schematic manner. In addition, for the reader's convenience, the dimensions of the components in the drawings are not drawn to scale.

[0063] It should be understood that relative terms such as “down” or “bottom” and “up” or “top” may be used herein to describe the relationship of one element to another, as illustrated in the accompanying drawings. It should be understood that relative terms are intended to include different orientations of the device beyond those shown in the figures. For example, if a device in one of the figures is flipped, an element described as being “down” to other elements will be oriented “up” to other elements. Thus, the exemplary term “down” can include both “down” and “up” orientations, depending on the specific orientation of the figure. Similarly, if a device in one of the figures is flipped, an element described as being “down” or “below” to other elements will be oriented “above” to other elements. Thus, the exemplary term “down” or “below” can include both “up” and “down” orientations.

[0064] This disclosure provides a stretchable electrode and a biosensing system including the stretchable electrode. Because the stretchable electrode of this disclosure can withstand significant stretching deformation, it can be well applied in wearable biosensing systems without developing localized cracks or breaking completely due to the user's limb movements. Furthermore, when the stretching deformation (e.g., length change) of the stretchable electrode exceeds a certain value, the resistance of the stretchable electrode begins to change, resulting in a weakening of the output signal value. At this point, the biosensing system can perform a correction function through its calibrator to calculate the actual signal value, and further calculate the analyte parameter (e.g., concentration) of the substance to be measured (e.g., glucose) in the user's body. In other words, through the combination of the stretchable electrode and the calibrator, the biosensing system of this disclosure has a wider range of applications compared to traditional physiological sensing devices.

[0065] Figure 1A block diagram illustrating a biosensing system 100 according to some embodiments of the present disclosure is shown. The biosensing system 100 disclosed herein may be a wearable biosensing system, such as a biosensing patch configurable on a user's body. The biosensing system 100 includes a receiver 110, a transmitter 120, a controller 130, and a calibrator 140, wherein the transmitter 120 is electrically connected to the receiver 110, the controller 130 is electrically connected to the transmitter 120, and the calibrator 140 is electrically connected to the controller 130. The receiver 110 is configured to contact the user's body to receive a analyte in the user's body and transmit the signal value generated by the analyte to the transmitter 120. The transmitter 120 is configured to transmit the signal value from the receiver 110 to the controller 130, whereby the controller 130 further determines whether the signal value needs to be calibrated. If, after evaluation, it is determined that no calibration is needed for the signal value, the controller 130 can calculate the analyte parameter using the signal value. If, after evaluation, it is determined that calibration is needed for the signal value, the calibrator 140 is configured to calibrate the signal value, and the controller 130 then calculates the analyte parameter using the calibrated signal value. Specific details regarding the operation of the biosensing system 100 will be further explained later.

[0066] Figure 2 Draw Figure 1 A perspective view of the working electrode layer 122A of the transmitter 120. The transmitter 120 disclosed herein may include a working electrode layer 122A, wherein the working electrode layer 122A may include a tensile deformation electrode 122. The tensile deformation electrode 122 may have the ability to withstand large-amplitude tensile deformation for stable application in a wearable biosensing system 100. In some embodiments, the tensile deformation electrode 122 has a tensile portion 122S extending from a first endpoint P1 to a second endpoint P2, and the tensile portion 122S may undergo tensile deformation in response to external stress (e.g., external force generated by user movement). In the following description, it will be understood that... Figure 3 and Figure 4 Content targeting Figure 2 The tensile portion 122S of the tensile deformation electrode 122 will be described in detail.

[0067] Figure 3 Draw Figure 2 A graph showing the relationship between the change in resistance of the tensile portion 122S of the tensile deformation electrode 122 and the change in tensile length. More specifically, Figure 3 This paper presents the relationship between the change in resistance and the change in stretching length of the tensile portion 122S of the tensile deformation electrode 122 when it undergoes tensile deformation under the action of an external force. Please also refer to... Figure 2 and Figure 3The stretched portion 122S of the stretch deformation electrode 122 has a first stretching range A1 and a second stretching range A2 in the relationship diagram of resistance change versus stretching length change. In the first stretching range A1, the stretched portion 122S has a first length change L1 (the horizontal axis coordinate position of any point on the curve in the first stretching range A1) and a first resistance change R1 (the vertical axis coordinate position of any point on the curve in the first stretching range A1); in the second stretching range A2, the stretched portion 122S has a second length change L2 (the horizontal axis coordinate position of any point on the curve in the second stretching range A2) and a second resistance change R2 (the vertical axis coordinate position of any point on the curve in the second stretching range A2). It should be noted that the "length change" in this document is defined as "the length L of the stretched portion 122S after stretching". f For the length L before stretching i (i.e., the original length L) i The ratio of (expressed as a percentage) to the resistance change is defined as "the change in resistance R of the stretched part 122S after stretching". f Subtract the resistance R before stretching i The value ΔR obtained after stretching is then compared with the resistance R before stretching. i The ratio (expressed as a percentage).

[0068] In some implementations, the first resistance change R1 remains substantially constant (i.e., the change in the first resistance R1 with respect to the first length change L1 is small, and the measurement deviation is acceptable, therefore no correction is required), while the second resistance change R2 changes with the change in the second length change L2. It should be noted that "substantially" as used herein means within 5% of a given value or range, and preferably within 3%. In other words, the aforementioned "first resistance change R1 remains substantially constant" means "the first resistance change R1 falls within 5%". In detail, since the resistance change of the stretching part 122S (i.e., the first resistance change R1) in the first stretching range A1 does not substantially change with the stretching length change (i.e., the first length change L1), when the stretching length change of the stretching part 122S falls within the range of the first stretching range A1, the signal value output by the stretching deformation electrode 122 will not substantially decrease accordingly. Therefore, the test parameters of the analyte can be accurately calculated through this signal value without further correction. Conversely, since the resistance change of the stretching part 122S (i.e., the second resistance change R2) in the second stretching range A2 changes with the stretching length change (i.e., the second length change L2), when the stretching length change of the stretching part 122S falls within the range of the second stretching range A2, the signal value output by the stretching deformation electrode 122 will decrease accordingly. Therefore, further correction of this signal value is required to accurately calculate the test parameters of the analyte through the corrected signal value. Based on the above, the first stretching range A1 can also be referred to as the "non-calibration area A1", and the second stretching range A2 can also be referred to as the "calibration area A2". Specific details regarding the calibration of the biosensing system 100 will be further explained later.

[0069] In some implementations, the relationship between the second resistance change R2 and the second length change L2 for the correction region A2 can be expressed by equation (1). Equation (1): R2 = A × L2, where A is a positive number between 0.05 and 2. In other words, in Figure 3In the calibration region A2, any R2 value and its corresponding L2 value can be found to satisfy the relationship of the above equation (1). Based on the above, the tensile portion 122S of the tensile deformation electrode 122 can have an appropriate amount of resistance change when it is stretched and deformed by external force, which is beneficial for its application in the biosensing system 100 that can be calibrated, and can ensure that the resistance change of the tensile portion 122S will not be too large instantaneously, thus increasing the difficulty of calibration. In detail, if A is less than 0.05 in equation (1), there will be no distinction between the uncorrected region A1 and the corrected region A2. That is, the tensile portion 122S of the tensile deformation electrode 122 will not have a corrected region A2, making the tensile deformation electrode 122 unusable in the biosensing system 100 that can be corrected. If A is greater than 2 in equation (1), the resistance change of the tensile portion 122S of the tensile deformation electrode 122 will spike instantly when deformed by external force, increasing the difficulty of correction or even making correction impossible. In a preferred embodiment, A is a positive number between 0.0500 and 0.5000 in the above equation (1), thereby better achieving the above-mentioned effect. On the other hand, the determination coefficient (R) of the equation expressed by equation (1) 2 The coefficient of determination (R) can be between 0.95 and 1.00 to ensure that the change in resistance of the stretching portion 122S and the change in stretching length have a sufficiently close linear relationship in the correction zone A2, thereby improving the accuracy and convenience of the correction. In a preferred embodiment, the coefficient of determination (R) of the equation expressed by formula (1) is... 2 It can further range between 0.95 and 1.00.

[0070] In some embodiments, the ratio of the range Z1 of the stretching length change (i.e., the first length change L1) of the stretching portion 122S in the non-correction region A1 to the range Z2 of the stretching length change (i.e., the second length change L2) of the stretching portion 122S in the correction region A2 can be greater than or equal to 1.25. In other words, the range Z2 of the stretching length change of the stretching portion 122S in the non-correction region A1 is relatively large, so that the stretching deformation electrode 122 can operate under a certain stretching length change without additional correction. In some embodiments, the range Z1 of the stretching length change (i.e., the first length change L1) of the stretching portion 122S in the non-correction region A1 can be between 0% and 250%, while the range Z2 of the stretching length change (i.e., the second length change L2) of the stretching portion 122S in the correction region A2 can be between 250% and 450%. In other words, when the change in the stretch length of the stretching portion 122S is less than 250%, the biosensing system 100 can directly calculate the test parameters of the substance to be tested through the signal value output by the stretching deformation electrode 122; and when the change in the stretch length of the stretching portion 122S is greater than 250%, the biosensing system 100 can further correct the signal value output by the stretching deformation electrode 122, so as to calculate the test parameters of the substance to be tested through the corrected signal value.

[0071] Figure 4 Draw Figure 2 A graph showing the resistance change of the tensile portion 122S of the tensile deformation electrode 122 during the tensile / recovery period versus time. Figure 4 The 275%, 300%, 375%, and 450% shown refer to the change in the tensile length of the tensile portion 122S of the tensile deformation electrode 122. For example... Figure 4As shown, the stretched portion 122S of the stretch deformation electrode 122, after being stretched to 275%, 300%, 375%, and 450% of its original length (i.e., the changes in stretch length are 275%, 300%, 375%, and 450%), still recovers well to its original resistance. Specifically, the stretched portion 122S of the stretch deformation electrode 122, after undergoing multiple consecutive stretching cycles over 600 seconds with gradually increasing changes in stretch length, still recovers well to its original resistance. Furthermore, the stretched portion 122S of the stretch deformation electrode 122 has a stretch resistance recovery rate between 95% and 100%, where the stretch resistance recovery rate is defined as "the ratio of the resistance of the stretched portion 122S after this stretching and recovery to the resistance of the stretched portion 122S after the previous stretching and recovery." In other words, the stretched portion 122S almost completely returns to its resistance before stretching after being stretched and recovered. In some embodiments, provided that the tensile resistance recovery rate of the tensile portion 122S falls within the aforementioned range, the tensile portion 122S may have a tensile recovery number between 1 and 3000, and preferably between 500 and 1500. Based on the above, the tensile deformation electrode 122 disclosed herein can have good tensile resistance recovery properties, making it more suitable for use in the biosensing system 100, thereby ensuring the reusability of the biosensing system 100 and extending its service life.

[0072] For example Figure 2 In some embodiments, the tensile portion 122S of the stretching electrode 122 may include multiple conductive structures, which may be, for example, conductive particle structures and / or conductive wire structures. In some embodiments, the average particle size of the conductive particle structures is between 0.5 nm and 100 μm. In some embodiments, the average wire diameter of the conductive wire structures is between 0.5 nm and 1 μm, and the average wire length of the conductive wire structures is between 50 nm and 1000 μm. By configuring the dimensions of the conductive structures (e.g., average particle size, average wire diameter, average wire length, etc.), the conductive structures can be densely distributed in the tensile portion 122S and in contact with each other to provide a continuous current path, thereby forming a conductive network. When the tensile portion 122S is stretched and deformed by external force, there are still buffer gaps between the conductive structures to avoid local cracks or overall breakage of the tensile portion 122S. In some embodiments, the material of the conductive structure is selected from a single metallic element (M1), a binary metal (M1-M2), a ternary metal (M1-M2-M3), or a single metal oxide (M1O). x ), binary metal oxides (M1O) x -M2O x ) and metal-metal oxides (M1-M1O) x) at least one of the groups composed of the composite, where 0 < x < 3, and M1, M2, and M3 are at least one selected from the group consisting of platinum, gold, palladium, silver, iridium, bismuth, lithium, iron, cobalt, nickel, copper, aluminum, chromium, titanium, manganese, antimony, zinc, zirconium, gallium, molybdenum, ruthenium, lawrencium, tin, indium, osmium, tantalum, tungsten, cerium, and yttrium. By selecting the material of the above conductive structure, the stretching part 122S of the stretching deformation electrode 122 can have good electrical conductivity and stretching resistance recovery, and thus has the various properties described in the above Figure 3 and Figure 4 content.

[0073] Figure 5 Illustrates Figure 1 An exploded view of the biosensing system 100, which omits the controller 130 and the corrector 140. More specifically, Figure 5 The biosensing system 100 of the present disclosure is presented in the form of a biosensing patch. Please also refer to Figure 1 and Figure 5 . Overall, the biosensing system 100 completes the physiological sensing of the user's body through the receiver 110, the transmitter 120, the controller 130, and the corrector 140. In the following description, reference will be made to Figure 1 and Figure 5 The biosensing system 100 will be described in detail in sequence for the structural configuration of the receiver 110, the transmitter 120, the controller 130, and the corrector 140 and their operation modes during physiological sensing.

[0074] In some embodiments, the receiver 110 includes a signal transmission layer 112, a signal enhancement layer 114, and a signal generation layer 116 stacked in sequence. In other words, the signal enhancement layer 114 is sandwiched between the signal transmission layer 112 and the signal generation layer 116. Among them, the signal generation layer 116 is configured to contact the user's body to receive the substance to be measured in the user's body, and then generate a signal value. In some embodiments, the signal generation layer 116 may include an oxidase (or enzyme) for reducing the activation energy required for the oxidation reaction of the substance to be measured, so that the substance to be measured undergoes an oxidation reaction quickly in the signal generation layer 116 to generate the signal value. That is to say, the signal value can be, for example, a signal value generated through a chemical reaction of an oxidation reaction. In some embodiments, the signal value may be a current value. For example, when the substance to be measured is glucose, the oxidase in the signal generation layer 116 may be glucose oxidase, so that glucose undergoes an oxidation reaction to generate hydrogen peroxide (H2O2), and the generated hydrogen peroxide can further generate a current value for subsequent interpretation.

[0075] In some embodiments, the oxidase in the signal generation layer 116 is selected from glucose oxidase, malate oxidase, hexose oxidase, cholesterol oxidase, aryl alcohol oxidase, L-gulonolactone oxidase, galactose oxidase, hexane oxidase, L-sorbose oxidase, pyridoxine-4-oxidase, methanol oxidase, ecdysone oxidase, (S)-2-hydroxy acid oxidase, choline oxidase, secondary alcohol oxidase, 4-hydroxymandelic acid oxidase, long-chain ethanol oxidase, glycerol-3-phosphate oxidase, vitamin B1 oxidase, zinc hydroxystannate oxidase, N-acyl Hexosamine oxidase, polyvinyl alcohol oxidase, lactone oxidase, vanillin oxidase, D-mannitol oxidase, nucleoside oxidase, xylitol oxidase, formate dehydrogenase, cellobiose dehydrogenase, aldehyde oxidase, pyruvate oxidase, oxalate oxidase, glyoxylate oxidase, aryl aldehyde oxidase, pyruvate oxidase (CoA-acetyl), retinaldehyde oxidase, ketoglutarate dehydrogenase (succinyl conversion), ABA aldehyde oxidase, coproporphyrinogen oxidase, dihydroorotic acid oxidase, aryl-CoA oxidase, dihydrouracil oxidase, tetrahydroberberine oxidase, tryptophan α,β-Oxidase, PQQ synthase, aryl-CoA dehydrogenase, dihydroorotate dehydrogenase, D-aspartate oxidase, L-galactonolactone oxidase, L-amino acid oxidase, D-amino acid oxidase, amino oxidase (containing flavonoids), doxalyl 5'-phosphate synthase, amino oxidase (containing copper), D-glutamate oxidase, ethanolamine oxidase, putrescine oxidase, L-glutamate oxidase, cyclohexylamine oxidase, D-glutamate (D-aspartate) oxidase, protein-lysine 6-oxidase Enzymes, L-isocyanate oxidase, L-aspartate oxidase, glycine oxidase, L-isocyanate 6-oxidase, amino dehydrogenase, FMN reductase, sarcosine oxidase, N-methyl-L-amino acid oxidase, N6-methyl-isocyanate oxidase, (S)-6-hydroxynicotinic acid oxidase, (R)-6-hydroxynicotinic acid oxidase, L-methylguanidine, dimethylglycine oxidase, polyamine oxidase, DHBP oxidase, trimethylamine dehydrogenase, L-hexahydropyridinecarboxylic acid dehydrogenase, cytokinin dehydrogenase Nitrite reductase, NAD(P)H oxidase, NAD(P)H dehydrogenase (p-phenylene ketone), nitroalkane oxidase, uric acid oxidase, methyl 3-nitropropionate oxidase, dihydrolipoyl dehydrogenase, sulfite oxidase, thiol oxidase, glutathione oxidase, methanethiol oxidase, alkylcysteine ​​oxidase, rafomycin-β oxidase, 3-hydroxy-2-aminobenzoic acid oxidase, NADH peroxidase, 2-nitropropane dioxygenase, lactate 2-monooxygenase, lysine 2-monooxygenase, luciferin 4 - At least one of the following groups: monooxygenase (ATP hydrolysis), phenylalanine 2-monooxygenase, clavaminate synthase, sodium anthracene benzoate 3-monooxygenase, xanthine dehydrogenase, phenylalanine 4-monooxygenase, naphtha 1,2-dioxygenase, alkanol monooxygenase, ethyl 4-aminobenzoate 1-monooxygenase, monophenol monooxygenase, 7-cholesterol oxidase, superoxide dismutase, superoxide reductase, xanthine oxidase, 6-hydroxynicotinic acid dehydrogenase, linalool alkalase, and ribulose diphosphate carboxylase. Based on the above, the oxidase in the signal generation layer 116 can be selected according to different analytes.

[0076] In some embodiments, the signal enhancement layer 114 is connected to the signal generation layer 116 and configured to receive the signal value generated by the signal generation layer 116, and amplify the signal value to generate an enhanced signal value (also referred to as a first signal value). In other words, the first signal value is also a current value. In some embodiments, the signal enhancement layer 114 may include multiple conductive structures, and the conductive structures may be, for example, conductive particle structures and / or conductive wire structures. In some embodiments, the average particle size of the conductive particle structure is between 0.5 nm and 100 μm. In some embodiments, the average wire diameter of the conductive wire structure is between 0.5 nm and 1 μm, and the average wire length of the conductive wire structure is between 50 nm and 1000 μm. The material of the conductive structure can refer to the material of the conductive structure included in the stretching portion 122S mentioned above, and will not be repeated here. Through the above configuration of the conductive structure and the selection of its material, the signal enhancement layer 114 can preferably generate an enhanced first signal value.

[0077] In some embodiments, the signal transmission layer 116 connects the signal enhancement layer 114 and the working electrode layer 122A, and is sandwiched between the signal enhancement layer 114 and the working electrode layer 122A to receive a first signal value from the signal enhancement layer 114 and transmit the first signal value to the working electrode layer 122A. In some embodiments, the oxidation potential of the signal transmission layer 116 is higher than that of the signal enhancement layer 114 (i.e., the signal transmission layer 116 is relatively less prone to oxidation), to ensure that the signal transmission layer 116 does not undergo electrochemical reactions such as oxidation, thereby avoiding the generation of unnecessary signal values ​​by the signal transmission layer 116 and causing inaccurate physiological sensing. In some embodiments, the signal transmission layer 116 may include multiple conductive structures, and the material of the conductive structures is selected from at least one of the group consisting of platinum, gold, bismuth, palladium, silver, iridium, iron, carbon nanotubes, conductive carbon black, graphite, glassy carbon, nickel, cobalt, copper, osmium, tantalum, and tungsten. By selecting the materials for the conductive structure described above, the signal transmission layer 116 can ensure good conductivity without causing physiological sensing inaccuracies due to the generation of unnecessary signal values.

[0078] In some embodiments, the transmitter 120 may include a working electrode layer 122A, a counter electrode layer (also called an auxiliary electrode layer) 122B, and a reference electrode layer 122C. In some embodiments, the working electrode layer 122A has opposing first sides 123A and second sides 125A, and the counter electrode layer 122B and the reference electrode layer 122C are respectively disposed on the first side 123A and the second side 125A of the working electrode layer 122A. Based on the above, the working electrode layer 122A, the counter electrode 122B, and the reference electrode 122C together constitute the three-electrode system of the transmitter 120. As mentioned above, the working electrode layer 122A may include the aforementioned tensile deformation electrode 122. In some embodiments, the working electrode layer 122A is configured to receive a first signal value from the signal transmission layer 116, generate a second signal value, and transmit the first signal value and the second signal value to the controller 130. In some embodiments, the second signal value may be a resistance value of the tensile deformation electrode 122 in the current deformation state. In some embodiments, the counter electrode 122B and the reference electrode 122C may also include the aforementioned stretchable electrode 122, and the stretchable electrodes 122 of each of the working electrode layer 122A, the counter electrode 122B, and the reference electrode 122C may extend in the same direction (i.e., the long axes of the stretchable electrodes 122 of the working electrode layer 122A, the counter electrode 122B, and the reference electrode 122C extend in the same direction) to improve measurement accuracy and thus avoid physiological sensing inaccuracies. In some embodiments, the material of the conductive structure included in the stretchable electrode 122 of the reference electrode 122C is selected from at least one of the group consisting of silver, silver chloride, iridium oxide, ruthenium oxide, platinum oxide, palladium oxide, tin oxide, tantalum oxide, rhodium oxide, mercury, mercuric chloride, osmium oxide, titanium oxide, mercuric oxide, and antimony oxide.

[0079] Please also see Figure 1 , Figure 3 as well as Figure 5In some embodiments, the controller 130 is electrically connected to the working electrode layer 122A, the counter electrode layer 122B, and the reference electrode layer 122C of the transmitter 120, and is configured to receive a first signal value and a second signal value from the working electrode layer 122A, and determine whether the first signal value needs to be corrected based on the received second signal value. Specifically, taking the first signal value as a current value and the second signal value as a resistance value as an example, the controller 130 can calculate the current resistance change of the stretching section 122S based on the received resistance value, and determine whether the resistance change falls within the second stretching range A2 of the stretching section 122S, to further determine whether the received current value needs to be corrected. In detail, when the resistance change is determined to fall within the second stretching range A2 of the stretching section 122S, the controller 130 will decide that the current value needs to be corrected; and when the resistance change is determined not to fall within the second stretching range A2 of the stretching section 122S, the controller 130 will decide that the current value does not need to be corrected.

[0080] In some embodiments, the calibrator 140 is electrically connected to the controller 130 and configured to receive instructions from the controller 130 to perform or not perform a calibration function. Specifically, when the controller 130 decides that the current value needs to be calibrated, the calibrator 140 is configured to calibrate the current value and transmit the calibrated current value data to the controller 130, so that the controller 130 can calculate the analyte parameters of the analyte using the calibrated current value data; when the controller 130 decides that the current value does not need to be calibrated, the calibrator 140 will not perform the calibration function, and the controller 130 will directly calculate the analyte parameters of the analyte using the current value it receives from the working electrode layer 122A.

[0081] Please refer to the following for specific calibration details. Figure 3 , Figure 5 , Figure 6 as well as Figure 7 ,in Figure 6 A graph showing the relationship between the sensitivity of the biosensing system 100 according to some embodiments of this disclosure and the change in the stretching length of the stretching portion 122S is presented. Figure 7 A graph showing the relationship between the first signal value (enhanced signal value) and the analyte parameter of the biosensing system 100 according to some embodiments of this disclosure is presented. When the controller 130 determines that the current value needs correction, the calibrator 140 can first... Figure 3 The presented relationship corresponds the resistance change of the stretching portion 122S received by the controller 130 to the stretching length change of the stretching portion 122S at the moment that resistance change occurs. Then, the calibrator 140 can... Figure 6The relationship presented is to correlate the obtained change in stretching length with the sensitivity of the stretching section 122S at the moment of the change in stretching length, where the sensitivity is defined as "formula: first signal value / (measured parameter of the analyte × area of ​​the stretching section 122S)", that is, the sensitivity is related to... Figure 7 The slope of the curve is proportional. Subsequently, the corrector 140 can be transmitted through... Figure 7 The relationship presented is to map the obtained sensitivity to the first signal value generated by the analyte (i.e., the signal value obtained after the actual signal value generated by the analyte is enhanced by the signal enhancement layer 114). Through the above correction steps, the corrector 140 can obtain the actual signal value generated by the analyte, and then calculate the test parameters of the analyte in the user's body.

[0082] Please return Figure 5 In some embodiments, the biosensing system 100 may further include a substrate 150 configured to carry a receiver 110 and a transmitter 120. The substrate 150 may be, for example, an insulating substrate, and the material of the substrate 150 is selected from at least one of the group consisting of polyurethane, polydimethylsiloxane, polyimide, polystyrene sulfonic acid, styrene-butadiene-styrene block copolymer, poly(3,4-ethylenedioxythiophene), and polybutylene adipate terephthalate. By selecting the material of the substrate 150, good tensile resilience can be ensured for its suitable application in the wearable biosensing system 100.

[0083] In some embodiments, the biosensing system 100 may further include a waterproof layer 160, which is disposed on the surface of the transmitter 120 relative to the substrate 150. In other words, the working electrode layer 122A, the counter electrode layer 122B, and the reference electrode layer 122C in the transmitter 120 share opposing first and second surfaces, and the substrate 150 and the waterproof layer 160 are respectively disposed on the first and second surfaces, such that the transmitter 120 is sandwiched between the substrate 150 and the waterproof layer 160. Based on the above, the substrate 150 and the waterproof layer 160 can jointly protect the transmitter 120 from damage caused by external factors (e.g., moisture), thereby ensuring the accuracy of physiological sensing. In some embodiments, the waterproof layer 160 has a through-hole H, through which the receiver 110 is exposed, thereby contacting the user's body to receive the analyte.

[0084] In some embodiments, the biosensing system 100 may further include two protective layers 170 corresponding to the counter electrode 122B and the reference electrode 122C, respectively. In some embodiments, the protective layer 160 may be made of an insulating material, and the two protective layers 170 may respectively cover the counter electrode 122B and the reference electrode 122C to provide appropriate protection. In some embodiments, the two protective layers 170 may also be exposed through the through-holes H of the waterproof layer 160, but this is not intended to limit the present disclosure.

[0085] The biosensing system 100 disclosed herein can be further defined in terms of its properties through various electrical testing methods. Specifically, these electrical testing methods may include cyclic voltammetry, square wave voltammetry, differential pulse voltammetry, and chronoamperometry. In the following description, [the methods will be described using...] Figures 8 to 11B Content and matching Figure 2 The properties of the biosensing system 100 under the above-mentioned electrical test methods will be explained one by one by the tensile deformation electrodes 122 in the working electrode layer 122A.

[0086] Figure 8 It illustrates a cyclic voltammogram of the stretched portion 122S of the stretched deformation electrode 122 in a biosensing system 100 according to some embodiments of the present disclosure, wherein... Figure 8The 0%, 250%, 325%, 400%, and 425% values ​​shown refer to the change in the stretch length of the stretch portion 122S of the stretch deformation electrode 122. In some embodiments, when the analyte is glucose, and the analyte parameter is the concentration of glucose, and the glucose concentration is between 0.005 mM and 1 mM (i.e., between 0.09 mg / dL and 18 mg / dL), the biosensor system 100 can generate a first signal value (e.g., a current value). When the first signal value passes through the stretch deformation electrode 122 of the working electrode layer 122A, a cyclic voltammogram of the stretch portion 122S of the stretch deformation electrode 122 can be obtained by cyclic voltammetry. Specifically, when the first signal value is between 0.0001 μA and 1000 μA (preferably between 0.0001 μA and 10 μA, more preferably between 0.0001 μA and 8 μA), and the change in the stretch length of the stretch portion 122S of the stretch deformable electrode 122 is less than 450%, and the potential difference between the two endpoints (i.e., the first endpoint P1 and the second endpoint P2) of the stretch portion 122S of the stretch deformable electrode 122 is between -1V and 1V (preferably between -0.8V and 0.8V, more preferably between -0.6V and 0.6V), the area of ​​the stretch portion 122S of the stretch deformable electrode 122 in the cyclic voltammetry is between 0.00015 μA × V and 1500 μA × V. In detail, if the area is less than 0.00015 μA × V, it means that the change in the stretching length of the stretching portion 122S of the stretching electrode 122 exceeds the correctable range, resulting in insufficient current and signal distortion. If the area is greater than 1500 μA × V, it means that the change in the stretching length of the stretching portion 122S of the stretching electrode 122 not only exceeds the correctable range, but also causes cracks in the electrode structure due to the excessive change in stretching length, resulting in a momentary surge in current and signal distortion. On the other hand, as the change in the stretching length of the stretching portion 122S gradually increases, the area of ​​the stretching portion 122S in the cyclic voltammogram gradually decreases. Please also refer to... Figure 3 More specifically, when the change in the tensile length of the stretching portion 122S is within the non-correction region A1 (i.e., when the stretching portion 122S has a first length change L1), the area of ​​the stretching portion 122S in the cyclic voltammogram is between 350 μA × V and 1500 μA × V; while when the change in the tensile length of the stretching portion 122S is within the correction region A2 (i.e., when the stretching portion 122S has a second length change L2), the area of ​​the stretching portion 122S in the cyclic voltammogram is between 0.00015 μA × V and 349 μA × V. It should be noted that... Figure 8 The cyclic voltammograms are merely exemplary embodiments, and the results were obtained at a glucose concentration of 0.5 mM.

[0087] Figure 9AThis diagram illustrates a square-wave voltammetry plot of the stretched portion 122S of the tensile deformation electrode 122 in a biosensing system 100 according to some embodiments of this disclosure. Figure 9A The values ​​of 0 mM, 0.05 mM, 0.1 mM, 0.2 mM, 0.3 mM, 0.5 mM, and 1 mM shown refer to the analyte parameters, which in this embodiment refer to the glucose concentration. In some embodiments, when the analyte is glucose, and the analyte parameter is the glucose concentration, and the glucose concentration is between 0.005 mM and 1 mM (i.e., between 0.09 mg / dL and 18 mg / dL), the biosensor system 100 can generate a first signal value (e.g., a current value). When the first signal value passes through the tensile deformation electrode 122 of the working electrode layer 122A, a square wave voltammetry diagram of the tensile portion 122S of the tensile deformation electrode 122 can be obtained using the square wave voltammetry method. Specifically, when the first signal value is between 0.00015μA and 835μA (preferably between 0.00015μA and 6μA, more preferably between 0.00015μA and 5μA), and the change in the stretch length of the stretch portion 122S of the stretch deformation electrode 122 is less than 450%, and the potential difference between the two endpoints (i.e., the first endpoint P1 and the second endpoint P2) of the stretch portion 122S of the stretch deformation electrode 122 is between -1V and 1V (preferably between -0.05V and 0.50V, more preferably between -0.05V and 0.45V), the area of ​​the stretch portion 122S of the stretch deformation electrode 122 in the square wave voltammetry is between 0.00015μA×V and 1245μA×V. In detail, if the area is less than 0.00015 μA × V, it means that the change in the stretching length of the stretching portion 122S of the stretching electrode 122 exceeds the correctable range, resulting in insufficient current and signal distortion. If the area is greater than 1245 μA × V, it means that the change in the stretching length of the stretching portion 122S of the stretching electrode 122 not only exceeds the correctable range, but also causes cracks in the electrode structure due to the excessive change in stretching length, resulting in an instantaneous excessive current and signal distortion. On the other hand, as the change in the stretching length of the stretching portion 122S gradually increases, the area of ​​the stretching portion 122S in the square wave voltammogram gradually decreases. Please also refer to... Figure 3 More specifically, when the change in the stretching length of the stretching portion 122S is within the non-correction region A1 (i.e., when the stretching portion 122S has a first length change L1), the area of ​​the stretching portion 122S in the square wave voltammogram is between 250 μA × V and 1245 μA × V; when the change in the stretching length of the stretching portion 122S is within the correction region A2 (i.e., when the stretching portion 122S has a second length change L2), the area of ​​the stretching portion 122S in the square wave voltammogram is between 0.00015 μA × V and 249 μA × V. It should be noted that... Figure 9AThe square wave voltammetry plot is merely an exemplary embodiment, and it is the result measured when the change in tensile resistance of the stretched portion 122S is 5%. Furthermore, for clarity, please refer to... Figure 9B It is to Figure 9A The test results are presented in detail through the relationship between the area of ​​the tensile portion 122S in the square wave voltammetry and the test parameter (concentration of glucose) of the test substance.

[0088] Figure 10A The diagram illustrates a differential pulse voltammogram of the stretched portion 122S of the tensile deformation electrode 122 in a biosensing system 100 according to some embodiments of the present disclosure, wherein... Figure 10A The indicated values ​​of 0 mM, 0.05 mM, 0.1 mM, 0.2 mM, 0.3 mM, 0.5 mM, and 1 mM refer to the analyte parameters, which in this embodiment refer to the glucose concentration. In some embodiments, when the analyte is glucose, and the analyte parameter is the glucose concentration, and the glucose concentration is between 0.005 mM and 1 mM (i.e., between 0.09 mg / dL and 18 mg / dL), the biosensor system 100 can generate a first signal value (e.g., a current value). When the first signal value passes through the tensile deformation electrode 122 of the working electrode layer 122A, a differential pulse voltammetry diagram of the tensile portion 122S of the tensile deformation electrode 122 can be obtained using differential pulse voltammetry. Specifically, when the first signal value is between 0.00015 μA and 795 μA (preferably between 0.00015 μA and 6 μA, more preferably between 0.00015 μA and 5 μA), and the change in the stretching length of the stretching portion 122S of the stretching electrode 122 is less than 450%, and the potential difference between the two endpoints (i.e., the first endpoint P1 and the second endpoint P2) of the stretching portion 122S of the stretching electrode 122 is between -1V and 1V (preferably between -0.05V and 0.50V, more preferably between -0.05V and 0.45V), the area of ​​the stretching portion 122S of the stretching electrode 122 in the differential pulse voltammogram is between 0.00015 μA × V and 1195 μA × V. For an explanation of the critical significance of the upper and lower limits of the above area, please refer to the previous paragraph; it will not be repeated here. On the other hand, as the change in the stretching length of the stretching portion 122S gradually increases, the area of ​​the stretching portion 122S in the differential pulse voltammogram gradually decreases. Please also refer to... Figure 3More specifically, when the change in the stretching length of the stretching portion 122S is within the non-correction region A1 (i.e., when the stretching portion 122S has a first length change L1), the area of ​​the stretching portion 122S in the differential pulse voltammogram is between 215 μA × V and 1195 μA × V; while when the change in the stretching length of the stretching portion 122S is within the correction region A2 (i.e., when the stretching portion 122S has a second length change L2), the area of ​​the stretching portion 122S in the differential pulse voltammogram is between 0.00015 μA × V and 214 μA × V. It should be noted that... Figure 10A The differential pulse voltammogram is merely an exemplary embodiment, and it was measured when the change in tensile resistance of the stretched portion 122S was 5%. Furthermore, for clarity, please refer to... Figure 10B It is to Figure 10A The test results are presented in detail through the relationship between the area of ​​the tensile portion 122S in the differential pulse voltammogram and the analyte parameter (concentration of glucose).

[0089] Figure 11A A time-ampere curve is plotted for the stretched portion 122S of the tensile deformation electrode 122 in a biosensing system 100 according to some embodiments of this disclosure, and Figure 11A The indicated values ​​of 0.05 mM to 0.1 mM, 3 mM, 5 mM, 10 mM, 20 mM, and 50 mM refer to the analyte parameters, which in this embodiment refer to the glucose concentration. In some embodiments, when the analyte is glucose, and the analyte parameter is the glucose concentration, and the glucose concentration is between 0.005 mM and 50 mM (i.e., between 0.09 mg / dL and 900 mg / dL), the biosensor system 100 can generate a first signal value (e.g., a current value). When the first signal value passes through the tensile deformation electrode 122 of the working electrode layer 122A, a chronoamperometric curve of the tensile portion 122S of the tensile deformation electrode 122 can be obtained using chronoamperometry. It should be noted that... Figure 11A The timing-ampere curve is merely an exemplary embodiment, and it is the result measured when the change in tensile resistance of the stretched portion 122S is 5%. Figure 11A As shown by the dashed line, after 50 seconds of applying a driving voltage to the biosensing system 100, the measured current value ranged from 0.0001 μA to 35 μA. Furthermore, for clarity, please refer to... Figure 11B It is to Figure 11A The test results are presented in detail through the relationship between the first signal value (current value) of the tensile part 122S at the 50th second of the chronoampere curve and the test parameter (concentration of glucose) of the test substance.

[0090] According to the embodiments disclosed above, since the tensile deformation electrode disclosed herein has the ability to withstand large-scale tensile deformation, it can be well applied to wearable biosensing systems without developing local cracks or breaking completely due to the user's limb movements. Furthermore, when the tensile deformation (e.g., length change) of the tensile deformation electrode exceeds a certain value, the resistance of the tensile deformation electrode begins to change, resulting in a weakening of the output signal value. At this time, the biosensing system can also perform a correction function through its calibrator to calculate the actual signal value (e.g., a first signal value), and then calculate the analyte parameters of the substance to be measured in the user's body. In other words, through the combination of the tensile deformation electrode and the calibrator, the biosensing system disclosed herein has a wider range of applications compared to traditional physiological sensing devices. On the other hand, since the biosensing system disclosed herein exhibits specific properties in various electrical test patterns under various electrical testing methods, it can effectively realize the function of physiological sensing.

[0091] Although the present disclosure has been described above with reference to embodiments, it is not intended to limit the present disclosure. Any person skilled in the art may make various modifications and alterations without departing from the spirit and scope of the present disclosure. Therefore, the scope of protection of the present disclosure shall be determined by the scope defined in the appended claims.

Claims

1. A stretch-deformed electrode characterized by, The stretchable portion has a first length variation and a first resistance variation in a first stretchable range, and has a second length variation and a second resistance variation in a second stretchable range, the first resistance variation is constant, and the second resistance variation changes with the second length variation, wherein the second resistance variation is represented by R2, the second length variation is represented by L2, and R2=A*L2, A is a positive number between 0.05 and 2, the first length variation is between 0% and 250%, and the second length variation is between 250% and 450%. The stretchable portion has a stretchable resistance recovery rate between 95% and 100%.

2. The stretchable deformable electrode of claim 1, wherein, The stretchable portion has a stretchable recovery number between 1 and 3000.

3. The stretch-textured electrode of claim 2, wherein, The equation of R2=A*L2 has a determination coefficient between 0.95 and 1.

00.

4. The stretchable deformable electrode of claim 1, wherein, The ratio of the range of the first length variation to the range of the second length variation is greater than or equal to 1.

25.

5. The stretchable deformable electrode of claim 1, wherein, The stretchable portion includes a plurality of conductive particle structures, and the average particle size of the plurality of conductive particle structures is between 0.5 nm and 100 μm.

6. The stretchable deformable electrode of claim 1, wherein, The stretchable portion includes a plurality of conductive linear structures, the average linear size of the plurality of conductive linear structures is between 0.5 nm and 1 μm, and the average linear length of the plurality of conductive linear structures is between 50 nm and 1000 μm.

7. The stretchable deformable electrode of claim 1, wherein, The transmitter includes a working electrode layer, wherein the working electrode layer includes the stretchable deformation electrode of claim 1.

8. A biosensing system characterized by, The receiver is electrically connected to the transmitter and is configured to receive a to-be-measured substance and transmit a first signal value generated by the to-be-measured substance to the transmitter, so that the transmitter outputs the first signal value and a second signal value. The controller is electrically connected to the transmitter and is configured to receive the first signal value and the second signal value and determine whether the second signal value falls within the second stretchable range of the stretchable portion. The corrector is electrically connected to the controller, wherein when the second signal value falls within the second stretchable range of the stretchable portion, the corrector is configured to correct the first signal value to calculate a to-be-measured parameter of the to-be-measured substance. When the second signal value does not fall within the second stretchable range of the stretchable portion, the corrector does not perform the correction function. The first signal value includes a current value, and the second signal value includes a resistance value. The stretchable portion extends from a first end point to a second end point, when the current value is between 0.0001 μA and 1000 μA, a stretchable length variation of the stretchable portion is less than 450%, and a potential difference between the first end point and the second end point is between -1 V and 1 V, an area of the stretchable portion in a cyclic voltammogram is between 0.00015 μA*V and 1500 μA*V.

9. The biological sensing system of claim 8, wherein, ​ 10. The biological sensing system of claim 8, wherein, ​ 11. The biological sensing system of claim 10, wherein, ​ 12. The biological sensing system of claim 10, wherein, The stretch portion extends from a first end point to a second end point, and when the current value is between 0.0001 μA and 835 μA, a stretch length variation of the stretch portion is less than 450%, and a potential difference between the first end point and the second end point is between -1 V and 1 V, an area of the stretch portion in a square wave voltammogram is between 0.00015 μA×V and 1245 μA×V.

13. The biological sensing system of claim 10, wherein, The stretch portion extends from a first end point to a second end point, and when the current value is between 0.0001 μA and 795 μA, a stretch length variation of the stretch portion is less than 450%, and a potential difference between the first end point and the second end point is between -1 V and 1 V, an area of the stretch portion in a differential pulse voltammogram is between 0.00015 μA×V and 1195 μA×V.

14. The biological sensing system of claim 8, wherein, The receiver comprises: a signal transfer layer connected to the working electrode layer and configured to transfer the first signal value to the working electrode layer; a signal generation layer configured to receive the analyte; and a signal enhancement layer interposed between the signal transfer layer and the signal generation layer.

15. The biological sensing system of claim 14, wherein, An oxidation potential of the signal transfer layer is higher than an oxidation potential of the signal enhancement layer.

16. The biological sensing system of claim 8, wherein, The working electrode layer has opposite first and second surfaces, and the biosensing system further comprises: a substrate disposed on the first surface of the working electrode layer; and a waterproof layer disposed on the second surface of the working electrode layer and having a through hole, wherein the receiver is exposed by the through hole.

17. The biological sensing system of claim 8, wherein, The working electrode layer has opposite first and second sides, and the transmitter further comprises: a pair of electrode layers disposed on the first side of the working electrode layer and comprising the stretchable deformation electrode of claim 1; and a reference electrode layer disposed on the second side of the working electrode layer and comprising the stretchable deformation electrode of claim 1.

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