TWI746015B - Wearable measurement device and method of measuring a biological target using the same - Google Patents

Abstract

A wearable measurement device is provided. The wearable measurement device includes a wearable element, a liquid-transferring element, a bio-sensing electrode, a flow-sensing electrode and a meter. The wearable element has an opening. The liquid-transferring element is disposed in the opening of the wearable element and has a sampling portion exposed to outside through the opening. The bio-sensing electrode and the flow-sensing electrode are connected to a first position and a second position of the liquid-transferring element. The meter is disposed on/in the wearable element and electrically connected to the bio-sensing electrode and the flow-sensing electrode.

Description

Wearable measuring device and its biological target measuring method

The embodiment of the present invention relates to a measurement device and a method for measuring a biological target, and particularly relates to a wearable measurement device and a method for measuring a biological target.

Wearable and continuous measurement devices have been the goal pursued by current measurement devices. However, in the existing wearable and continuous measurement devices, whether it is optical or electrochemical measurement, it is through contact with the skin and miniaturized needles. Contact sampling and measurement methods such as subcutaneous implantation, etc., take sampling and measurement while minimizing user discomfort. Although these methods can improve the comfort of the user, they still cannot completely solve the discomfort of the user during activities.

Therefore, there is a great need for a novel wearable measurement device in the industry to solve the discomfort caused by the user when the measurement device touches the skin during activities.

The wearable measurement device of the embodiment of the present invention avoids the discomfort caused by the direct contact of the sensing electrode with the skin by arranging the pipetting element as a medium between the sensing electrode and the skin.

According to some embodiments of the present invention, a wearable measurement device is provided. The wearable measurement device includes a wearable element, a pipetting element, a biological sensing electrode, a flow sensing electrode, and a meter. The aforementioned wearing element has an opening. The aforementioned pipetting element is arranged in the wearing element and has a sample injection part exposed to the outside through the opening. The aforementioned biological sensing electrode and flow sensing electrode are respectively connected to the first position and the second position of the pipetting element. The aforementioned meter is arranged on or inside the wearable element and is electrically connected to the biological sensing electrode and the flow sensing electrode.

， 其中An代表該瞬時生物標的物濃度，Sn代表該瞬時生物液體量，t為量測時間且c為常數。According to some embodiments of the present invention, a method for measuring a biological target is provided. This method includes continuously measuring the instantaneous biological fluid concentration of the biological fluid with a biological sensing electrode; using the flow sensing electrode to continuously measure the instantaneous biological fluid volume of the biological fluid; and calibrating the biological target concentration by the following formula:

, Where An represents the instantaneous biological target concentration, Sn represents the instantaneous biological fluid volume, t is the measurement time and c is a constant.

Many different implementation methods or examples are disclosed below to implement different features of the embodiments of the present invention. The following describes specific elements and their arrangement embodiments to illustrate the embodiments of the present invention. Of course, these embodiments are only for illustration, and should not be used to limit the scope of the embodiments of the present invention. For example, in the specification, it is mentioned that the first feature is formed on the second feature, which includes the embodiment in which the first feature and the second feature are in direct contact, and it also includes the embodiments between the first feature and the second feature. The embodiment of the feature, that is, the first feature and the second feature are not in direct contact. In addition, repeated reference numerals or labels may be used in different embodiments. These repetitions are only used to describe the embodiments of the present invention simply and clearly, and do not represent a specific relationship between the different embodiments and/or structures discussed.

In addition, terms relative to space may be used, such as "below", "below", "lower", "above", "higher" and similar terms. These spatial relative terms are used for ease of description The relationship between one element or feature(s) and another element(s) or feature in the illustration. These spatial relative terms include the different orientations of the device in use or operation, as well as the orientation described in the drawings. When the device is turned in different directions (rotated by 90 degrees or other directions), the spatially relative adjectives used therein will also be interpreted according to the turned position.

Here, the terms "about", "approximately", and "approximately" usually mean within 20% of a given value or range, preferably within 10%, and more preferably within 5%, or 3 Within %, or within 2%, or within 1%, or within 0.5%. It should be noted that the quantity provided in the manual is an approximate quantity, that is, without specifying "about", "approximately", "approximately", "about", "approximately" and "approximately" can still be implied. The meaning of "probably".

It can be understood that although the terms "first", "second", "third", etc. may be used herein to describe various elements, components, regions, layers, parts, and/or sections, these elements and components , Regions, layers, parts and/or sections should not be limited by these terms, and these terms are only used to distinguish different elements, components, regions, layers, parts and/or sections. Therefore, a first element, component, region, layer, and/or portion discussed below may be referred to as a second element, component, region, layer, portion, and/or without departing from the teachings of the present disclosure. Or section.

Although the steps in some of the described embodiments are performed in a specific order, these steps can also be performed in other logical orders. In different embodiments, some of the steps described may be replaced or omitted, and some other operations may also be performed before, during, and/or after the steps described in the embodiments of the present invention.

Please refer to FIG. 1, which shows a plan view of a wearable measurement device 100 according to an embodiment of the present invention. The wearable measurement device 100 includes a wearable element 102, a pipetting element 104, a biological sensing electrode 106, and a flow sensor. Electrode 108 and meter 110.

The wearing element 102 has an opening. Specifically, the opening of the wearing element 102 faces the user's skin. In some embodiments, the wearable element 102 includes a hat, a headband, a wristband, clothing, or the foregoing similar elements. For example, the opening may be located on the body of the hat, the inner side of the headband, the cuffs or collar of the clothes, and so on.

The pipetting element 104 can be disposed in the wearing element 102 and has a sample injection part 1041. The sampling portion 1041 is exposed to the outside through the opening (cap opening) of the wearing element 102 to be in contact with the skin. The biological liquid penetrates the sampling portion 1041 and enters the pipetting element 104. The pipetting element 104 may have a single-layer or multi-layer structure, and its shape may include, but is not limited to, semicircular, circular, square, rectangular, L-shaped, T-shaped, and Y-shaped. The pipetting element 104 can be a pump or a water-absorbing material. Examples of water-absorbent materials include, but are not limited to, super-absorbent resin (SAP), hydrophilic fiber materials, or a combination thereof. Since the pipetting element 104 is a pump or a water-absorbent material, the biological liquid entering the pipetting element 104 can move in the pipetting element 104 by the active absorption of the pump or the capillary action of the water-absorbent material. In some embodiments, the biological fluid contains sweat, blood, or other similar fluids.

The biosensing electrode 106 is an electrode that can be used to measure the concentration of a biological target in a biological fluid, where the biological target (or can be regarded as a biochemical substance, metabolite, etc.) may include electrolyte, glucose, lactic acid or the like. The flow sensing electrode 108 is an electrode that can be used to measure the amount of biological fluid. The biological sensing electrode 106 and the flow sensing electrode 108 are respectively disposed in the wearable element 102 and connected to the pipetting element 104. By connecting with the pipetting element 104, the biological fluid can move to the biological sensing electrode 106 and the flow sensing electrode 108 without the biological sensing electrode 106 and the flow sensing electrode 108 contacting the skin, thereby reducing direct contact by the user Discomfort caused by the biological sensing electrode 106 and/or the flow sensing electrode 108. The biological sensing electrode 106 and the flow sensing electrode 108 can be connected to any position of the pipetting element 104. For example, as shown in Figure 1, when the pipetting element 104 has a Y-shape with three ends, the sample injection portion 1041 can be located at one end of the pipetting element 104, and the biosensing electrode 106 and The flow sensing electrodes 108 may be respectively located near the other two ends of the pipetting element 104 to be connected to the pipetting element 104. In this embodiment, the distance between the biological sensing electrode 106 and the sampling portion 1041 in the wearable measurement device 100 and the distance between the flow sensing electrode 108 and the sampling portion 1041 are approximately the same. Therefore, the biological The liquid moves to the biological sensing electrode 106 and the flow sensing electrode 108 at about the same time, but the present invention is not limited to this.

2A-2C are schematic diagrams of the biosensing electrode 106 according to some embodiments of the present invention. The biosensing electrode 106 includes a conductive element 106A. The conductive element 106A can be an electrode or a conductive webbing. The electrodes contain conductive materials, and the conductive webbing is woven from conductive materials (conductive woven threads) and man-made fibers or natural fibers. In an embodiment, the conductive element 106A can directly contact the pipetting element 104 to react with the biological target of the biological liquid flowing therein, as shown in FIG. 2C. In such an embodiment, the conductive element 106A may include, but is not limited to, cobalt, nickel, selenium, cobalt oxide, nickel oxide, selenium oxide, silver carbon, graphene carbon nanotube (carbon nanotube) or Any combination or conductive material of carbon nanotubes, the above-mentioned materials are used as the conductive woven wire in the electrode or conductive webbing. In another embodiment, the biosensing electrode 106 may further include a reaction component 106B. The reaction member 106B includes a reactant 10 and a fixed layer 106B'. The reaction part 106B is located between the conductive element 106A and the pipetting element 104. The reaction part XX can directly contact the pipetting element 104 to react with the biological target of the biological liquid flowing therein, and the conductive element 106A then generates an electrical signal according to the change of the reaction, as shown in Figs. 2A and 2B. In such an embodiment, the conductive element 106A may include aluminum (Al), molybdenum (Mo), tungsten (W), titanium (Ti), tantalum (Ta), platinum (Pt), hafnium (Hf), nickel (Ni) ), cobalt (Co), zinc (Zb), graphite or similar conductive materials mentioned above, but the present invention is not limited thereto. The reactant 10 may include immobilized enzymes, enzymes, antibodies, proteins, nucleic acids, chemical reaction reagents, or a combination of the foregoing, but the present invention is not limited thereto. For example, the reactant 10 may include glucose oxidase, glucose dehydrogenase, lactate oxidase, lactate dehydrogenase, and 3-hydroxybutyrate dehydrogenase. Enzyme (3-hydroxybutyrate dehydrogenase), urease (urease), cholesterol esterase (cholesterol esterase), cholesterol oxidase (cholesterol oxidase) or any combination thereof, but the present invention is not limited thereto. Those with ordinary knowledge in the technical field of the present invention understand that the type of reactant depends on the type of biological target to be measured.

The reactant 10 can be fixed on the conductive element 106A in various ways. In one embodiment, as shown in FIG. 2A, the reaction member 106B may further include a fixing layer 106B' for fixing the reactant 10. The material of the fixing layer 106B' includes poly vinyl pyrrolidone (PVP), polyethylene glycol (PEG), polyethylene imine (PEI), polyvinyl alcohol (PVA) ) Or carboxymethyl cellulose (Carboxymethyl cellulose, CMC). The fixed layer 106B' may be located on the reactant 10. The fixed layer 106B' can also be located between the reactant 10 and the conductive element 106A. The reactant 10 can also be located between two fixed layers 106B'.

In another embodiment, for example, when the reactant 10 is an immobilized enzyme, the reactant 10 can utilize 1-ethyl-3-(3-dimethylaminopropyl) (EDC)/N- Hydroxysuccinimidyl (NHS), EDC/sulfo-NHS, glutaraldehyde (GA), Nafion or electrochemical methods are directly fixed to the conductive element 106A without a fixing layer, as shown in Figure 2B.

The biosensing electrode 106 can use general current and voltage, differential pulse voltammetry (DPV) or square wave voltammetry (SWV) and other electrochemical methods to measure the biological target of the biological liquid.

Differential pulse voltammetry is a method of superimposing a pulse voltage of a certain amplitude (for example, 10-100 mV) on a DC voltage for measurement. Square wave voltammetry (SWV) is to give a square wave potential of a large amplitude differential pulse to the electrode, and collect two reaction currents through the square wave cycle. They are the end current of the forward pulse and the reverse pulse ( The last point current of Reverse pulse), the net current can be obtained by subtracting the two points, which has the effect of amplifying the signal and has better sensitivity than the differential pulse voltammetry. In addition, the main advantages of square wave voltammetry include fast scanning. The effective scanning rate is the square wave frequency multiplied by the potential change, so the scanning time can be reduced to complete the analysis quickly.

FIG. 3 is a graph showing the change of the response current signal of the biological target object measured by the amperometric method using the biological sensing electrode 106 of the wearable measurement device 100 for 10 minutes. Figure 3 is an example of a biosensing electrode 106 with a water-absorbing material as the pipetting element 104, glucose as a biomarker, and a biosensing electrode 106 with glucose oxidase (equivalent to reactant 10) directly immobilized on the conductive element 106A. Figure 2B illustrates the feasibility of the wearable measurement device 100 according to the embodiment of the present invention. First, one side of the pipetting element 104 is used as the sampling portion 1041, and the side of the pipetting element 104 opposite to the sampling portion 1041 is connected to the biosensing electrode 106, as shown in FIG. Glucose solution is added to the sampling part 1041 several times. With the water absorption and pipetting function of the pipetting element 104, the glucose solution can move in the pipetting element 104 and flow through the reaction zone of the biological sensing electrode 106, and finally from the biological sensor. The sensing electrode 106 collects the reaction current signal, and the result is shown in FIG. 3. It can be seen from Figure 3 that every time the glucose solution is added, the peak can be detected (as shown by the arrow). The current value of the peak can be converted to the glucose concentration, which means that the reaction current will rise rapidly after the glucose solution is added. Then return to a higher stable reaction current. By recording the stable reaction current value and matching it with a table established with standard products, the glucose concentration in the sample can be calculated. This example proves that the biological liquid can be continuously sent to the reaction area of the biological sensing electrode 106 for electrochemical reaction by using the pipetting function of the water-absorbing material, and the wearable measurement device 100 of this case can continuously and repeatedly measure the content of the sample. The concentration of the biological target.

4A-4F are schematic diagrams showing the configuration of the flow sensing electrode 108 and the pipetting element 104 according to some embodiments of the present invention. The above-mentioned conductive component can be an electrode or a conductive webbing and can measure small changes in the amount of biological fluid in detail. The electrodes contain conductive materials, and the conductive webbing is woven from conductive materials and man-made fibers or natural fibers. Examples of conductive materials may include, but are not limited to, aluminum (Al), molybdenum (Mo), tungsten (W), titanium (Ti), tantalum (Ta), platinum (Pt), hafnium (Hf), nickel (Ni), Cobalt (Co), zinc (Zb), graphite or the aforementioned similar materials.

In an embodiment, the flow sensing electrode 108 may include more than two conductive components. As shown in Figure 4A, the flow sensing electrode 108 connected to the pipetting element 104 may include a first conductive element 108A, a second conductive element 108B, a third conductive element 108C, a fourth conductive element 108D, and a fifth conductive element 108E , Wherein the distance between the first conductive component 108A and the sampling portion is greater than the distance between the second conductive component 108B and the sampling portion, and the distance between the second conductive component 108B and the sampling portion is greater than the distance between the third conductive component 108C and the third conductive component 108C. The distance between the sample injection part, the distance between the third conductive component 108C and the sample injection part is greater than the distance between the fourth conductive component 108D and the sample injection part, and the distance between the fourth conductive component 108D and the sample injection part It is greater than the distance between the fifth conductive component 108E and the sample injection part. Each conductive component has a double-wire electrode to measure the potential difference, and there is a fixed distance between each conductive component. The moving direction of the biological fluid is shown by the arrow in Figure 4A. Therefore, the biological fluid will first move to the fifth conductive element 108E, and then sequentially move to the fourth conductive element 108D, the third conductive element 108C, and the second conductive element 108E. The component 108B finally moves to the first conductive component 108A. In this embodiment, the fifth conductive element 108E first measures the current and voltage changes, and then the fourth conductive element 108D to the first conductive element 108A sequentially measure the current and voltage changes. The flow sensing electrode 108 with the above configuration can measure large biological fluid changes, and can obtain accurate biological fluid total or water content through the biological fluid volume changes measured by the first conductive element 108A to the fifth conductive element 108E, respectively (Also known as moisture content, moisture content).

In another embodiment, as shown in FIG. 4B, the flow sensing electrode 108 connected to the pipetting element 104 may include a first conductive component 108A (single-wire electrode) and a second conductive component 108B (two-wire electrode). The measurement accuracy of the biological liquid change can be improved by increasing the length of the exposed sensing area of the first conductive element 108A and the second conductive element 108B for contact with the biological liquid. In the embodiment shown in Figure 4B, the amount of biological liquid enters from the arrow. When the amount of biological liquid becomes larger and larger, the current and voltage changes measured by the second conductive element 108B will also become larger. When the amount of the biological liquid reaches a certain level, the biological liquid will move to the first conductive component 108A, and at this time, the first conductive component 108A also starts to measure changes in current and voltage. With the above configuration, the flow sensing electrode 108 can measure large biological fluid changes, and can obtain accurate biological fluid total or content through the changes in the biological fluid measured by the first conductive element 108A and the second conductive element 108B, respectively. The amount of water.

The configuration of the conductive components in the flow sensing electrode 108 can be adjusted as needed. For example, the conductive components of the flow sensing electrode 108 can be geometrically configured as shown in Figure 4C (4 linear electrodes facing each other), as shown in Figure 4D (2 toe electrodes interlaced with each other) and Figure 4E. A ground gate configuration or an S-shaped cross configuration as shown in Fig. 4F (overlapping in space but no contact), but the present invention is not limited to this. In addition to capturing current and/or voltage changes, the measurement method can also be performed using electrochemical methods such as DVP and SWV.

The measurement principle of the flow sensing electrode 108 is described in further detail below. FIG. 5A is a schematic diagram showing the configuration of the flow sensing electrode 108 according to another embodiment of the present invention. As shown in Figure 5A, the flow sensing electrode 108 connected to the pipetting element 104 includes a first conductive element 108A, a second conductive element 108B, a third conductive element 108C, and a fourth conductive element 108D (for simplicity of description, 5A In the figure, only two points are used to indicate the exposed sensing area of each conductive component or dot electrodes are used). The arrow direction in Figure 5A indicates the moving direction of the biological liquid. The first conductive component 108A is far away from the sample injection part, the third conductive component 108C is closest to the sample injection part, and the second and fourth conductive components 108B and 108D are located between the first conductive component. Between the component 108A and the third conductive component 108C.

FIG. 5B is a diagram of electrical signal changes of the flow sensing electrode 108 with the conductive element arranged as shown in FIG. 5A. Add phosphate buffer solution (PBS) to the injection part every three minutes. Since the third conductive element 108C is closest to the sample injection part, the third conductive element 108C responds first. As shown in Figure 5B, when the cumulative injection volume of PBS reaches 50 mL, the voltage of the third conductive component 108C drops earliest, and the voltage drop represents the measured potential of the PBS. The second and fourth conductive components 108B and 108D are slightly farther away from the injection port than the third conductive component 108C, so the second and fourth conductive components 108B and 108D respond after the third conductive component 108C. As shown in Figure 5B, next, when the cumulative injection volume of PBS reaches 100 mL and 150 mL, the voltage of the second and fourth conductive components 108B and 108D drops after the third conductive component 108C. Then, since the first conductive element 108A is the farthest away from the sample injection part, the first conductive element 108A will respond at the end. As shown in Figure 5B, when the cumulative injection volume of PBS reaches 550 mL, the voltage of the first conductive component 108A drops. Therefore, the configuration of the electrode assembly can be used to calculate the water content of the biological fluid.

Returning to Figure 1, the meter 110 can be installed on or inside the wearable device 102, and is electrically connected to the biosensing electrode 106 and the flow sensing electrode 108 to receive electrical signals from the biosensing electrode 106 and the flow sensing electrode 108 . Depending on where the biosensing electrode 106 and the flow sensing electrode 108 are connected to the pipetting element 104, electrical signals from the biosensing electrode 106 and the flow sensing electrode 108 can reach the meter 110 at the same time or sequentially. The meter 110 may include an arithmetic module to obtain and record the concentration of the biological target of the biological fluid, the total amount of the biological fluid, and the corrected concentration of the biological target. In another embodiment, the meter 110 may further include a power supply module to provide power to the biosensing electrode 106 and the flow sensing electrode 108. In another embodiment, the meter 110 may further include a display module to display the concentration of the biological target of the biological fluid, the total amount of the biological fluid, and/or the corrected concentration of the biological target.

FIG. 6 shows a plan view of a wearable measurement device 200 according to another embodiment of the present invention. As shown in FIG. 6, the pipetting element 204 has an L-shaped shape, the L-shaped pipetting element 204 is disposed inside the wearing element 202, and the sampling portion 2041 is located at one end of the L-shaped pipetting element 204. The biological sensing electrode 206 and the flow sensing electrode 208 are respectively disposed in the wearable element 202 and connected to the pipetting element 204. As shown in Figure 6, the biosensing electrode 206 and the flow sensing electrode 208 are respectively connected to the first position 204A and the second position 204B of the pipetting element 204, wherein the distance between the second position 204B and the sampling portion 2041 is greater than the first position 204A and the second position 204B of the pipetting element 204. The distance between a position 204A and the sampling portion 2041. . In the wearable measurement device 200, since the biosensing electrode 206 is closer to the sample injection portion 2041 than the flow sensing electrode 208, the biological fluid will first reach the biosensing electrode 206 and then the flow sensing electrode 206 The electrode 208, the biological sensing electrode 206 continuously measures the instantaneous (real time) biological target concentration or the instant biological target concentration of the biological fluid, and the flow sensing electrode 208 is used to continuously measure the instantaneous biological fluid volume of the biological fluid. The invention is not limited to this. In one embodiment, the flow sensing electrode may be closer to the sample injection part than the biological sensing electrode, so that the biological fluid will first reach the flow sensing electrode and then the biological sensing electrode. The wearable element 202, the meter 210, the biosensing electrode 206, and the flow sensing electrode 208 in the wearable measurement device 200 are the same as the wearable element 102, the meter 110, the biological sensing electrode 106, and the flow rate in the wearable measurement device 100. The sensing electrode 108 has a similar structure, so it will not be repeated here. In the following, the wearable measurement device 200 is taken as an example to further explain the specific operation mode of the wearable measurement device of the present application.

FIG. 7 is a flowchart of the operation of the wearable measurement device 200 according to an embodiment of the present invention. As shown in Fig. 7, the operation flow chart of the wearable measurement device 200 includes a sampling step S701, a first electrical signal generation step S703, a second electrical signal generation step S704, a signal processing step S705, and output and/or Step S707 of recording the result. Referring to FIGS. 6 and 7 at the same time, first, in the sampling step S701, the biological liquid is sucked and enters the L-shaped pipetting element 204 through the sampling portion 2041. In the embodiment shown in FIG. 6, the biological fluid will first move to the biological sensing electrode 206 and then to the flow sensing electrode 208. In step S703, the biological fluid will move to the biological sensing electrode 206. At this time, the biological sensing electrode 206 will measure the reaction current value when the biological fluid flows through the flow sensing electrode 206 and generate a first electrical signal accordingly. In step S704, the biological fluid moves to the flow sensing electrode 208. At this time, the flow sensing electrode 208 measures the current change and voltage change when the biological fluid flows through the flow sensing electrode 208, and generates a second telecommunication accordingly. No. The execution order of step S703 and step S704 is not particularly limited, and they can be performed simultaneously or sequentially. In the signal processing step S705, the meter 210 receives the first electric signal and the second electric signal and then calculates to obtain the concentration of the biological target and the total amount of biological liquid, and further obtains the corrected biological target according to the following correction formula concentration. In the calibration formula, An represents the instantaneous biomarker concentration measured by the biosensing electrode 206, Sn represents the instantaneous biological liquid content or water content measured by the flow sensing electrode 208, t is the measurement time and c is a constant. After multiplying the instantaneous biomarker concentration An by the instantaneous biological fluid amount Sn, the time t is integrated, and after adding the constant c, the corrected biomarker concentration or average monitoring amount can be obtained.

Finally, in step S707 of outputting and/or recording the result, outputting and/or recording the concentration of the biological target, the total amount of biological fluid and/or the corrected biological fluid calculated based on the first electrical signal and the second electrical signal The concentration of the target substance provides continuous cumulative measurement data.

Compared with the wearable measurement device of the prior art, the wearable measurement device provided by the embodiment of the present invention has one or more of the following advantages, but is not limited thereto: (1) Since the wearable measurement device of the embodiment of the present invention arranges the pipetting element in the opening of the wearable element, it can prevent the sensing electrode from directly contacting the skin, thereby preventing the sensing electrode from contacting the skin. Of discomfort. (2) Since the biological fluid can be continuously transported by the pipetting element to the biological sensing electrode and the flow sensing electrode, the wearable measurement device of the embodiment of the present invention can continuously measure the biological target substance and the amount of biological fluid. . (3) In addition, the pipetting element, biosensing electrode and flow sensing electrode are disposable modules. You only need to replace the pipetting element, biological sensing electrode and flow sensing electrode to measure different biological targets. . (4) In addition, the embodiment of the present invention also corrects the concentration of the biological target substance in the biological liquid through the water content, which can more accurately reflect the physiological condition of the user.

Although the embodiments of the present invention and its advantages have been disclosed as above, it should be understood that any person with ordinary knowledge in the relevant technical field can make changes, substitutions and modifications without departing from the spirit and scope of the present disclosure. In addition, the scope of protection of this disclosure is not limited to the manufacturing process, machinery, manufacturing, material composition, device, method, and steps in the specific embodiments described in the specification. Anyone with ordinary knowledge in the technical field can disclose the content from this disclosure. It is understood that the current or future developed processes, machines, manufacturing, material composition, devices, methods, and steps can be used according to the present disclosure as long as they can implement substantially the same functions or obtain substantially the same results in the embodiments described herein. Therefore, the protection scope of the present disclosure includes the above-mentioned manufacturing processes, machines, manufacturing, material composition, devices, methods, and steps. In addition, each patent application scope constitutes an individual embodiment, and the protection scope of the present disclosure also includes each patent application scope and a combination of embodiments.

10: Reactant

100,200: Wearable measuring device

102, 202: wearable components

104, 204: Pipetting elements

106,206: Biosensing electrodes

106A: conductive element

106B: Reaction parts

106B’: Fixed layer

108,208: Flow sensing electrode

108A, 108B, 108C, 108D, 108E: conductive components

110,210: instrument

1041, 2041: injection part

S701, S703, S704, S705, S707: steps

The embodiments of the present invention will be described in detail below in conjunction with the accompanying drawings. It should be noted that, according to standard practices in the industry, various features are not drawn to scale and are only used for illustration and illustration. In fact, it is possible to arbitrarily enlarge or reduce the size of the element to clearly show the characteristics of the embodiment of the present invention. FIG. 1 is a plan view of a wearable measurement device according to an embodiment of the present invention. 2A-2C are schematic diagrams of biosensing electrodes according to some embodiments of the present invention. FIG. 3 is a graph showing changes in electrical signals of the biosensing electrode according to some embodiments of the present invention measured by the amperometric method using an electrochemical instrument. Figures 4A-4F are schematic diagrams showing the configuration of flow sensing electrodes according to some embodiments of the present invention. FIG. 5A is a schematic diagram showing the configuration of flow sensing electrodes according to another embodiment of the present invention. FIG. 5B is a diagram of electrical signal changes of the flow sensing electrode having the configuration shown in FIG. 5A. FIG. 6 is a plan view of a wearable measurement device according to another embodiment of the present invention. Fig. 7 is a flowchart of the operation of the wearable measurement device shown in Fig. 6.

100: Wearable measuring device

102: Wearable components

104: Pipetting element

1041: Sampling part

106: Biological sensing electrode

108: Flow sensor electrode

110: Meter

Claims (10)

A wearable measurement device includes: a wearable element having an opening; a water-absorbent material arranged in the wearable element and having a sample injection part exposed to the outside through the opening; and a biosensing electrode connected to A first position of the water-absorbent material, the biosensing electrode continuously measures the concentration of an instantaneous biomarker of a biological fluid; a flow sensor electrode connected to a second position of the water-absorbent material, the flow rate The sensing electrode continuously measures an instantaneous amount of biological fluid of the biological fluid; and a meter is arranged on or inside the wearable element and is electrically connected to the biological sensing electrode and the flow sensing electrode to receive the instantaneous biological fluid The concentration of the target substance and the instantaneous biological fluid volume, and the concentration of the biological target substance is corrected by the instantaneous biological target concentration and the instant biological fluid volume. The wearable measurement device according to claim 1, wherein the distance between the second position and the sample injection part is greater than the distance between the first position and the sample injection part. The wearable measurement device according to claim 1, wherein the flow sensing electrode includes a first conductive element and a second conductive element. The wearable measurement device according to claim 3, wherein the distance between the first conductive component and the sampling portion is greater than the distance between the second conductive component and the sampling portion. The wearable measurement device of claim 1, wherein the biosensing electrode includes a conductive element, and the conductive element includes cobalt, nickel, selenium, cobalt oxide, Nickel oxide, selenium oxide, silver carbon, graphene, carbon nanotube, or any combination thereof. The wearable measurement device according to claim 1, wherein the biosensing electrode includes a conductive element and a reaction member, the reaction member is located between the conductive element and the water-absorbing material, and the reaction member includes a reactant , The reactant contains immobilized enzymes, enzymes, antibodies, proteins, nucleic acids, chemical reaction reagents or a combination of the foregoing. The wearable measurement device according to claim 6, wherein the biological sensing electrode further comprises a fixing layer for fixing the reactant, the reactant comprising enzymes, antibodies, proteins, nucleic acids, chemical reaction reagents or the foregoing combination. A method for measuring a biological target, comprising: using a biological sensing electrode connected to a first position of a pipetting element to continuously measure the concentration of an instantaneous biological target of a biological fluid; using the pipetting element connected to the A flow sensing electrode at a second position continuously measures an instantaneous amount of the biological fluid; and the concentration of the biological target is corrected by the following formula:

Wherein An represents the instantaneous biomarker concentration, Sn represents the instantaneous amount of biological fluid, t is the measurement time and c is a constant, wherein the pipetting element is arranged in a wearable element having an opening and is exposed to through the opening An external injection part. The method for measuring a biological target according to claim 8, wherein the step of measuring the instantaneous concentration of the biological target includes measuring the reaction current value when the biological liquid flows through the biological sensing electrode. The method for measuring a biological target object according to claim 8, wherein the step of measuring the instantaneous amount of biological liquid includes using voltage change, current change, amperometry, square wave voltammetry, and/or differential pulse voltammetry Take measurements.

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