CN220713907U - Sweat glucose concentration detecting system - Google Patents
Sweat glucose concentration detecting system Download PDFInfo
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- CN220713907U CN220713907U CN202320248764.7U CN202320248764U CN220713907U CN 220713907 U CN220713907 U CN 220713907U CN 202320248764 U CN202320248764 U CN 202320248764U CN 220713907 U CN220713907 U CN 220713907U
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- WQZGKKKJIJFFOK-GASJEMHNSA-N Glucose Natural products OC[C@H]1OC(O)[C@H](O)[C@@H](O)[C@@H]1O WQZGKKKJIJFFOK-GASJEMHNSA-N 0.000 title claims abstract description 117
- 239000008103 glucose Substances 0.000 title claims abstract description 117
- 210000004243 sweat Anatomy 0.000 title claims abstract description 76
- 238000001514 detection method Methods 0.000 claims abstract description 58
- 239000008280 blood Substances 0.000 claims abstract description 12
- 210000004369 blood Anatomy 0.000 claims abstract description 12
- 239000012790 adhesive layer Substances 0.000 claims description 27
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 20
- 238000010521 absorption reaction Methods 0.000 claims description 18
- 238000004891 communication Methods 0.000 claims description 12
- 230000002745 absorbent Effects 0.000 claims description 10
- 239000002250 absorbent Substances 0.000 claims description 10
- 239000010410 layer Substances 0.000 claims description 10
- 238000002955 isolation Methods 0.000 claims description 5
- 238000012545 processing Methods 0.000 claims description 5
- 230000005540 biological transmission Effects 0.000 claims description 3
- 238000012544 monitoring process Methods 0.000 abstract description 11
- 238000012360 testing method Methods 0.000 description 21
- 230000008859 change Effects 0.000 description 4
- 238000010586 diagram Methods 0.000 description 4
- 238000000970 chrono-amperometry Methods 0.000 description 3
- 230000000694 effects Effects 0.000 description 3
- 238000005259 measurement Methods 0.000 description 3
- 238000005516 engineering process Methods 0.000 description 2
- 230000005284 excitation Effects 0.000 description 2
- 230000003993 interaction Effects 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 239000000758 substrate Substances 0.000 description 2
- 206010061818 Disease progression Diseases 0.000 description 1
- 229910021607 Silver chloride Inorganic materials 0.000 description 1
- 238000012937 correction Methods 0.000 description 1
- 238000007405 data analysis Methods 0.000 description 1
- 206010012601 diabetes mellitus Diseases 0.000 description 1
- 238000003745 diagnosis Methods 0.000 description 1
- 230000005750 disease progression Effects 0.000 description 1
- 238000000835 electrochemical detection Methods 0.000 description 1
- 210000001061 forehead Anatomy 0.000 description 1
- 238000003780 insertion Methods 0.000 description 1
- 230000037431 insertion Effects 0.000 description 1
- 238000012417 linear regression Methods 0.000 description 1
- 235000012054 meals Nutrition 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 238000006479 redox reaction Methods 0.000 description 1
- 230000004044 response Effects 0.000 description 1
- HKZLPVFGJNLROG-UHFFFAOYSA-M silver monochloride Chemical compound [Cl-].[Ag+] HKZLPVFGJNLROG-UHFFFAOYSA-M 0.000 description 1
Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1468—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means
- A61B5/1477—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means non-invasive
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14507—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue specially adapted for measuring characteristics of body fluids other than blood
- A61B5/14517—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue specially adapted for measuring characteristics of body fluids other than blood for sweat
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02A—TECHNOLOGIES FOR ADAPTATION TO CLIMATE CHANGE
- Y02A90/00—Technologies having an indirect contribution to adaptation to climate change
- Y02A90/10—Information and communication technologies [ICT] supporting adaptation to climate change, e.g. for weather forecasting or climate simulation
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- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Physics & Mathematics (AREA)
- Biomedical Technology (AREA)
- Medical Informatics (AREA)
- Veterinary Medicine (AREA)
- Public Health (AREA)
- Biophysics (AREA)
- Pathology (AREA)
- Engineering & Computer Science (AREA)
- General Health & Medical Sciences (AREA)
- Heart & Thoracic Surgery (AREA)
- Optics & Photonics (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- Chemical & Material Sciences (AREA)
- Chemical Kinetics & Catalysis (AREA)
- General Chemical & Material Sciences (AREA)
- Emergency Medicine (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Abstract
The utility model discloses a sweat glucose concentration detection system, which comprises a sweat glucose concentration detection patch, a mobile terminal and a cloud server, wherein the sweat glucose concentration detection patch can be attached to the skin of a person to be detected so as to collect human sweat of the person to be detected and generate glucose concentration data; the mobile terminal is connected with the sweat glucose concentration detection patch, and is used for receiving glucose concentration data sent by the sweat glucose concentration detection patch and displaying the blood glucose condition of a person to be detected in real time; the cloud server is connected with the mobile terminal and is used for receiving the glucose concentration data sent by the mobile terminal and remotely storing the glucose concentration data so as to remotely monitor a person to be detected; therefore, real-time data acquisition is carried out through sweat glucose concentration detection paste, and remote storage monitoring is carried out through a cloud server, so that long-time noninvasive monitoring is realized.
Description
Technical Field
The utility model relates to the technical field of sweat detection, in particular to a sweat glucose concentration detection system.
Background
In the related art, at present, diagnosis of diabetes requires monitoring blood glucose in blood of a patient so as to confirm the condition of disease progression in time; the existing clinical test comprises invasive and non-invasive modes for monitoring blood sugar of a patient, wherein the invasive mode needs to take blood by needle insertion for a certain time before and after daily meal of the patient, physiological and psychological burden is easily brought to the patient, real-time measurement cannot be carried out, and the non-invasive mode can only monitor real-time short sweat information and cannot detect and analyze blood sugar changes in a period of time.
Disclosure of Invention
The present utility model aims to solve at least to some extent one of the technical problems in the above-described technology. Therefore, an object of the present utility model is to provide a sweat glucose concentration detection system, which performs real-time data acquisition through sweat glucose concentration detection paste and performs remote storage monitoring through a cloud server, so as to realize long-time noninvasive monitoring.
In order to achieve the above-mentioned objective, an embodiment of the present utility model provides a sweat glucose concentration detection system, including a sweat glucose concentration detection patch, where the sweat glucose concentration detection patch can be attached to skin of a person to be detected, so as to collect sweat of a human body of the person to be detected and generate glucose concentration data; the mobile terminal is connected with the sweat glucose concentration detection patch and is used for receiving glucose concentration data sent by the sweat glucose concentration detection patch and displaying the blood glucose condition of the person to be detected in real time; the cloud server is connected with the mobile terminal and is used for receiving the glucose concentration data sent by the mobile terminal and remotely storing the glucose concentration data so as to remotely monitor the person to be detected.
The sweat glucose concentration detection system comprises a sweat glucose concentration detection patch, a mobile terminal and a cloud server, wherein the sweat glucose concentration detection patch can be attached to the skin of a person to be detected so as to collect human sweat of the person to be detected and generate glucose concentration data; the mobile terminal is connected with the sweat glucose concentration detection patch, and is used for receiving glucose concentration data sent by the sweat glucose concentration detection patch and displaying the blood glucose condition of a person to be detected in real time; the cloud server is connected with the mobile terminal and is used for receiving the glucose concentration data sent by the mobile terminal and remotely storing the glucose concentration data so as to remotely monitor a person to be detected; therefore, real-time data acquisition is carried out through sweat glucose concentration detection paste, and remote storage monitoring is carried out through a cloud server, so that long-time noninvasive monitoring is realized.
In addition, the sweat glucose concentration detection system according to the above embodiment of the present utility model may further have the following additional technical features:
optionally, the sweat glucose concentration detection patch includes: the sweat collecting device comprises a first adhesive layer, a second adhesive layer and a first detection layer, wherein a plurality of sweat collecting holes are formed in the first adhesive layer, and the first adhesive layer can be adhered to the skin of a person to be detected; the first water absorption pad and the second water absorption pad are arranged on the first adhesive layer; a three-electrode glucose concentration sensor lining between the first absorbent pad and the second absorbent pad; the first water absorption pad, the three-electrode glucose concentration sensor and the second water absorption pad are glued together through the isolation layer and the first adhesive layer; the flexible micro-current collecting plate is connected with the three-electrode glucose concentration sensor, and the flexible micro-current collecting plate is fixed on the isolation layer through the second adhesive layer.
The sweat glucose concentration detection patch is convenient to wear, small in size and light in weight.
In addition, according to the technical means, the first adhesive layer can prevent sweat on the first water absorption pad and the second water absorption pad from volatilizing, so that the sweat concentration in the first water absorption pad and the second water absorption pad can be kept stable for a certain time.
Optionally, the three-electrode glucose concentration sensor includes a first working electrode, a first reference electrode, and a first counter electrode.
Optionally, the flexible micro-current acquisition board comprises a constant potential three-electrode circuit, a micro-current detection circuit, a high-precision voltage reference circuit and a communication module circuit, wherein a first input end of the constant potential three-electrode circuit is connected with the high-precision voltage reference circuit, a second input end of the constant potential three-electrode circuit is connected with the three-electrode glucose concentration sensor, an output end of the constant potential three-electrode circuit is connected with an input end of the micro-current detection circuit, and an output end of the micro-current detection circuit is connected with the communication module circuit.
Optionally, the potentiostatic three-electrode circuit includes a second working electrode, a second reference electrode and a second counter electrode, which are respectively connected with the first working electrode, the first reference electrode and the first counter electrode of the three-electrode glucose concentration sensor in a one-to-one manner.
Optionally, the communication module circuit comprises a bluetooth MCU chip, so that data processing and sending can be performed through the bluetooth MCU chip.
Drawings
FIG. 1 is a schematic diagram of a sweat glucose concentration detection system according to an embodiment of the present utility model;
FIG. 2 is a schematic diagram of the connection structure of a flexible microcurrent collecting plate and a three-electrode glucose concentration sensor according to one embodiment of the present utility model;
FIG. 3 is an equivalent circuit diagram according to one embodiment of the present utility model;
FIG. 4 is a diagram of an equivalent circuit test effect according to one embodiment of the present utility model;
FIG. 5 is a graph of simulated sweat testing effects according to one embodiment of the utility model;
FIG. 6 is a graph of glucose concentration variation for an actual wear test according to one embodiment of the present utility model.
Detailed Description
Embodiments of the present utility model are described in detail below, examples of which are illustrated in the accompanying drawings, wherein like or similar reference numerals refer to like or similar elements or elements having like or similar functions throughout. The embodiments described below by referring to the drawings are illustrative and intended to explain the present utility model and should not be construed as limiting the utility model.
In order that the above-described aspects may be better understood, exemplary embodiments of the present utility model will be described in more detail below with reference to the accompanying drawings. While exemplary embodiments of the present utility model are shown in the drawings, it should be understood that the present utility model may be embodied in various forms and should not be limited to the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the utility model to those skilled in the art.
In order to better understand the above technical solutions, the following detailed description will refer to the accompanying drawings and specific embodiments.
As shown in fig. 1-2, the sweat glucose concentration detection system according to an embodiment of the present utility model includes: sweat glucose concentration detection patch 10, mobile terminal 8 and cloud server 9.
The sweat glucose concentration detection patch 10 may be applied to the skin of the person to be detected, such as the forehead or the arm, so as to collect sweat of the person to be detected and generate glucose concentration data.
As an embodiment, the sweat glucose concentration detection patch comprises a first adhesive layer 1, a first water absorption pad 2, a second water absorption pad 4, a three-electrode glucose concentration sensor 3, an isolation layer 5, a flexible micro-current collecting plate 6 and a second adhesive layer 7, wherein a plurality of sweat collecting holes 11 are arranged on the first adhesive layer 1, and the first adhesive layer 1 can be stuck on the skin of a person to be detected; the first water absorbing pad 2 and the second water absorbing pad 4 are arranged on the first adhesive layer 1; the three-electrode glucose concentration sensor 3 is lined between the first water absorption pad 2 and the second water absorption pad 4; the first water absorption pad 2, the three-electrode glucose concentration sensor 3 and the second water absorption pad 4 are glued together through the isolating layer 5 and the first adhesive layer 1; the flexible microcurrent collecting plate 6 is connected with the three-electrode glucose concentration sensor 3, and the flexible microcurrent collecting plate 6 is glued and fixed on the isolating layer 5 through the second adhesive layer 7.
That is, the sweat glucose concentration detection patch is attached to the skin of a human body through the first adhesive layer 1, the first absorbent pad 2 and the second absorbent pad 4 are disposed on the first adhesive layer 1, and the first adhesive layer 1 is provided with a plurality of sweat collecting holes 11, whereby the first absorbent pad 2 and the second absorbent pad 4 collect sweat through the plurality of sweat collecting holes 11 of the first adhesive layer 1, and furthermore, the three-electrode glucose concentration sensor 3 is lined between the first absorbent pad 2 and the second absorbent pad 4, so that sweat data of a person to be detected can be stably collected for a long time.
The flexible microcurrent collecting plate 6 is connected with the three-electrode glucose concentration sensor 3 through a flexible connector.
In addition, the flexible microcurrent collecting plate can be reused, and other parts of the sweat glucose concentration detecting patch can be degraded after the actual detection of one stage is completed.
Furthermore, the devices and high density batteries on the flexible microcurrent collecting plate 6 ensure that the whole flexible microcurrent collecting plate 6 has a small weight and is easy to fix to the isolating layer 5.
As one example, the three-electrode glucose concentration sensor 3 includes a first working electrode, a first reference electrode, and a first counter electrode.
The three-electrode glucose concentration sensor 3 is composed of a flexible substrate, and an Ag/AgCl reference electrode and a Pt counter electrode which are formed on the flexible substrate, wherein the three-electrode glucose concentration sensor 3 leads out three electrodes through the first adhesive layer 1.
As an embodiment, the flexible micro-current collecting board 6 includes a constant potential three-electrode circuit 61, a micro-current detecting circuit 62, a high precision voltage reference circuit 63 and a communication module circuit 64, a first input end of the constant potential three-electrode circuit 61 is connected with the high precision voltage reference circuit 63, a second input end of the constant potential three-electrode circuit 61 is connected with the three-electrode glucose concentration sensor 3, an output end of the constant potential three-electrode circuit 61 is connected with an input end of the micro-current detecting circuit 62, and an output end of the micro-current detecting circuit 62 is connected with the communication module circuit 64.
As one example, the potentiostatic three-electrode circuit 61 includes a second working electrode WE, a second reference electrode RE, and a second counter electrode CE, which are connected one-to-one with the first working electrode, the first reference electrode, and the first counter electrode of the three-electrode glucose concentration sensor 3, respectively.
That is, the second working electrode WE is connected to the first working electrode, the second reference electrode RE is connected to the first reference electrode, and the second counter electrode CE is connected to the first counter electrode.
As one example, the communication module circuit 64 includes a bluetooth MCU chip for data processing and transmission through the bluetooth MCU chip.
That is, the flexible micro-current collecting board 6 has a flexible antenna, and communicates by means of bluetooth communication.
The high-precision voltage reference circuit 63 generates a high-precision reference voltage, and a high-precision reference voltage with high stability is added between the working electrode and the reference electrode of the potentiostatic three-electrode circuit 61 to maintain the electrochemical stability of the sensor, and the glucose solution in sweat generates oxidation-reduction reaction by excitation of the high-precision reference voltage and generates weak current with a certain relation with the glucose concentration in human sweat on the surface of the working electrode; the working electrode surface of the constant potential three-electrode circuit 61 generates weak current signals, the weak current signals are converted into voltage signals through the micro-current detection circuit 62, the voltage signals are corrected through linear regression and other correction algorithms to obtain glucose concentration, and the glucose concentration information is sent into a Bluetooth MCU chip for data processing and transmission; the Bluetooth MCU chip is in a dormant state most of the time, and current measurement is carried out through timing awakening so as to reduce power consumption.
In addition, the specific circuits of the potentiostatic three-electrode circuit 61, the microcurrent detection circuit 62, the high-precision voltage reference circuit 63 and the communication module circuit 64 may be conventional widely used circuits, and will not be described herein.
The mobile terminal 8 is connected with the sweat glucose concentration detection patch 10, and the mobile terminal 8 is used for receiving glucose concentration data sent by the sweat glucose concentration detection patch and displaying the blood glucose condition of a person to be detected in real time; the cloud server 9 is connected with the mobile terminal 8, and the cloud server 9 is used for receiving the glucose concentration data sent by the mobile terminal 8 and remotely storing the glucose concentration data so as to remotely monitor a person to be detected.
That is, the sweat glucose concentration detection patch 10 communicates with the mobile terminal 8 through the flexible micro-current acquisition board 6 in a bluetooth communication manner, the mobile terminal 8 periodically collects concentration data sent by the flexible micro-current acquisition board 6, provides a user interaction interface, displays glucose concentration in real time, draws a concentration change curve, and can obtain blood glucose condition in real time after the concentration data is corrected by a certain algorithm; the cloud server 9 stores the data received by the mobile terminal 8 remotely, analyzes the data by combining big data, and realizes remote medical monitoring.
It should be noted that specific signal processing and data analysis may use existing techniques.
As an example, the mobile terminal 8 may be a mobile phone.
As a specific example, to verify the effect of the flexible microcurrent acquisition board, a chronoamperometry and actual wear were used for testing, respectively.
The chronoamperometry is an electrochemical detection technology which is widely applied, and the working principle is as follows: applying a high-precision step voltage signal between a working electrode and a reference electrode of a constant potential three-electrode circuit as excitation; the high precision, high stability voltage maintains the stability of the sensor redox chemistry, the response current of the chemistry in solution flows through the working electrode and counter electrode, and the small current changes reflect the concentration changes.
In order to verify the measurement accuracy and performance of the flexible micro-current acquisition board, an equivalent circuit test and simulated sweat are used as test objects respectively, and a timing current method is adopted to test the whole system.
Test 1 is an equivalent circuit test, and the test is performed by using a traditional electrochemical workstation and a system designed by the utility model and using an equivalent circuit as shown in fig. 3 to simulate the change of glucose concentration and performing a chronoamperometry, and the test result is shown in fig. 4.
Test 2 is a simulated sweat test, wherein a traditional electrochemical workstation and a system designed by the utility model are respectively adopted, a fixed voltage of 0.5V is applied to the simulated sweat, and a standard glucose solution is sequentially added for testing, and the test result is shown in figure 5.
In the actual wearing test, the change curve of the glucose concentration shown in fig. 6 is a test result of wearing the test circuit for a long time; the testing circuit is worn on the arm of the person to be detected, and the mobile phone is used for receiving the glucose concentration data in real time; the system can be used for measuring for a long time and reflecting the change of the concentration of glucose in human sweat by wearing the test for a long time.
In summary, the sweat glucose concentration detection system according to the embodiment of the present utility model includes a sweat glucose concentration detection patch, a mobile terminal and a cloud server, where the sweat glucose concentration detection patch may be attached to the skin of a person to be detected, so as to collect sweat of a human body of the person to be detected and generate glucose concentration data; the mobile terminal is connected with the sweat glucose concentration detection patch, and is used for receiving glucose concentration data sent by the sweat glucose concentration detection patch and displaying the blood glucose condition of a person to be detected in real time; the cloud server is connected with the mobile terminal and is used for receiving the glucose concentration data sent by the mobile terminal and remotely storing the glucose concentration data so as to remotely monitor a person to be detected; therefore, real-time data acquisition is carried out through sweat glucose concentration detection paste, and remote storage monitoring is carried out through a cloud server, so that long-time noninvasive monitoring is realized.
In the description of the present utility model, it should be understood that the terms "center", "longitudinal", "lateral", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", etc. indicate orientations or positional relationships based on the orientations or positional relationships shown in the drawings are merely for convenience in describing the present utility model and simplifying the description, and do not indicate or imply that the devices or elements referred to must have a specific orientation, be configured and operated in a specific orientation, and thus should not be construed as limiting the present utility model.
Furthermore, the terms "first," "second," and the like, are used for descriptive purposes only and are not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include one or more such feature. In the description of the present utility model, the meaning of "a plurality" is two or more, unless explicitly defined otherwise.
In the present utility model, unless explicitly specified and limited otherwise, the terms "mounted," "connected," "secured," and the like are to be construed broadly, and may be, for example, fixedly connected, detachably connected, or integrally formed; can be mechanically or electrically connected; can be directly connected or indirectly connected through an intermediate medium, and can be communicated with the inside of two elements or the interaction relationship of the two elements. The specific meaning of the above terms in the present utility model can be understood by those of ordinary skill in the art according to the specific circumstances.
In the present utility model, unless expressly stated or limited otherwise, a first feature "above" or "below" a second feature may include both the first and second features being in direct contact, as well as the first and second features not being in direct contact but being in contact with each other through additional features therebetween. Moreover, a first feature being "above," "over" and "on" a second feature includes the first feature being directly above and obliquely above the second feature, or simply indicating that the first feature is higher in level than the second feature. The first feature being "under", "below" and "beneath" the second feature includes the first feature being directly under and obliquely below the second feature, or simply means that the first feature is less level than the second feature.
In the description of the present specification, a description referring to terms "one embodiment," "some embodiments," "examples," "specific examples," or "some examples," etc., means that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the present utility model. In this specification, schematic representations of the above terms should not be understood as necessarily being directed to the same embodiment or example. Furthermore, the particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples. Further, one skilled in the art can engage and combine the different embodiments or examples described in this specification.
While embodiments of the present utility model have been shown and described above, it will be understood that the above embodiments are illustrative and not to be construed as limiting the utility model, and that variations, modifications, alternatives and variations may be made to the above embodiments by one of ordinary skill in the art within the scope of the utility model.
Claims (5)
1. A sweat glucose concentration detection system, comprising:
the sweat glucose concentration detection patch can be attached to the skin of a person to be detected so as to collect sweat of the person to be detected and generate glucose concentration data;
the mobile terminal is connected with the sweat glucose concentration detection patch and is used for receiving glucose concentration data sent by the sweat glucose concentration detection patch and displaying the blood glucose condition of the person to be detected in real time;
the cloud server is connected with the mobile terminal and is used for receiving the glucose concentration data sent by the mobile terminal and remotely storing the glucose concentration data so as to remotely monitor the person to be detected;
wherein, sweat glucose concentration detects subsides includes:
the sweat collecting device comprises a first adhesive layer, a second adhesive layer and a first detection layer, wherein a plurality of sweat collecting holes are formed in the first adhesive layer, and the first adhesive layer can be adhered to the skin of a person to be detected;
the first water absorption pad and the second water absorption pad are arranged on the first adhesive layer;
a three-electrode glucose concentration sensor lining between the first absorbent pad and the second absorbent pad;
the first water absorption pad, the three-electrode glucose concentration sensor and the second water absorption pad are glued together through the isolation layer and the first adhesive layer;
the flexible micro-current collecting plate is connected with the three-electrode glucose concentration sensor, and the flexible micro-current collecting plate is fixed on the isolation layer through the second adhesive layer.
2. The sweat glucose concentration detection system of claim 1 wherein the three electrode glucose concentration sensor comprises a first working electrode, a first reference electrode, and a first counter electrode.
3. The sweat glucose concentration detection system according to claim 2, wherein the flexible microcurrent acquisition board comprises a potentiostatic three-electrode circuit, a microcurrent detection circuit, a high-precision voltage reference circuit and a communication module circuit, a first input end of the potentiostatic three-electrode circuit is connected with the high-precision voltage reference circuit, a second input end of the potentiostatic three-electrode circuit is connected with the three-electrode glucose concentration sensor, an output end of the potentiostatic three-electrode circuit is connected with an input end of the microcurrent detection circuit, and an output end of the microcurrent detection circuit is connected with the communication module circuit.
4. The sweat glucose concentration detection system of claim 3 wherein the potentiostatic three electrode circuit comprises a second working electrode, a second reference electrode and a second counter electrode in one-to-one connection with the first working electrode, the first reference electrode and the first counter electrode, respectively, of the three electrode glucose concentration sensor.
5. The sweat glucose concentration detection system of claim 4 wherein the communication module circuit comprises a bluetooth MCU chip for data processing and transmission through the bluetooth MCU chip.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202223110272 | 2022-11-22 | ||
| CN2022231102726 | 2022-11-22 |
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| Publication Number | Publication Date |
|---|---|
| CN220713907U true CN220713907U (en) | 2024-04-05 |
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| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202320248764.7U Active CN220713907U (en) | 2022-11-22 | 2023-02-07 | Sweat glucose concentration detecting system |
| CN202310122367.XA Pending CN116195997A (en) | 2022-11-22 | 2023-02-07 | Sweat glucose concentration detecting system |
Family Applications After (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202310122367.XA Pending CN116195997A (en) | 2022-11-22 | 2023-02-07 | Sweat glucose concentration detecting system |
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| CN (2) | CN220713907U (en) |
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- 2023-02-07 CN CN202320248764.7U patent/CN220713907U/en active Active
- 2023-02-07 CN CN202310122367.XA patent/CN116195997A/en active Pending
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|---|---|
| CN116195997A (en) | 2023-06-02 |
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