A blood pressure detection device, method and preparation method based on bionic micro-nanostructure

Abstract

The present application relates to the field of detection equipment, and more particularly to a blood pressure detection device, method, and preparation method based on a bionic micro-nanostructure. The blood pressure detection device based on a bionic micro-nanostructure includes a first triboelectric pulse sensor and a second triboelectric pulse sensor. The first triboelectric pulse sensor is used to be placed at a first preset position on the patient's arterial tree to obtain first pulse wave data, and the second triboelectric pulse sensor is used to be placed at a second preset position on the arterial tree to obtain second pulse wave data, thereby achieving sleeveless, continuous, real-time dynamic detection of the patient's blood pressure. The pulse wave data output by the first and second triboelectric pulse sensors are input into a preset pulse wave-blood pressure model. The pulse wave-blood pressure model can adapt to the specific physiological characteristics of different patients to accurately deduce the patient's blood pressure value, thereby improving the adaptability of the blood pressure detection device and also improving the accuracy of the blood pressure detection device based on the bionic micro-nanostructure.

Description

Technical Field

[0001] The present application relates to the field of detection equipment, and in particular to a blood pressure detection device, method and preparation method based on bionic micro-nano structures. Background Art

[0002] Cardiovascular disease is the leading cause of death worldwide. Hypertension, a key risk factor, can lead to stroke, myocardial infarction, heart failure, dementia, renal failure, blindness, and other conditions. Monitoring blood pressure fluctuations is crucial for understanding the progression of cardiovascular disease and guiding clinical treatment.

[0003] In the relevant technology, blood pressure monitoring is mainly categorized into two main types: invasive and non-invasive. Most patients still rely on traditional cuff-based electronic non-invasive blood pressure measurement methods. Conventional cuff-based electronic non-invasive blood pressure measurement methods often employ an oscillometric (or oscillatory) method for indirect blood pressure measurement. These methods are bulky, inconvenient to carry, exhibit discrete blood pressure values, and require a fixed posture for measurement, making continuous daily blood pressure monitoring difficult. Furthermore, these methods require manual pressure application to the patient's measurement site, resulting in intermittent blood flow obstruction and severely impacting normal activities. Existing methods that indirectly measure blood pressure using parameters such as pulse and heart rate, however, cannot guarantee accuracy and consistency due to the diversity and variability of human physiological characteristics. Therefore, the development of continuous blood pressure monitoring sensor technology still faces numerous challenges, and the current state of the art lacks reliable and accurate wearable blood pressure monitoring devices. Summary of the Invention

[0004] The following is a summary of the subject matter described in detail herein. This summary is not intended to limit the scope of the claims.

[0005] The present application aims to solve at least one of the technical problems existing in the prior art. To this end, the embodiments of the present application provide a blood pressure detection device, method, and preparation method based on a bionic micro-nano structure, which is conducive to solving the problem that the cuff blood pressure detector cannot continuously and dynamically detect the patient's blood pressure in real time and has poor adaptability to individual differences. The present application places a triboelectric pulse sensor on the patient's arterial tree to achieve continuous and real-time dynamic detection of the patient's blood pressure, and combines the pulse wave-blood pressure model to accurately obtain the patient's blood pressure value, thereby improving the adaptability of the blood pressure detection device based on the bionic micro-nano structure.

[0006] In first aspect, an embodiment of the present application provides a blood pressure detection device based on a bionic micro-nano structure, comprising a first triboelectric pulse sensor and a second triboelectric pulse sensor, wherein the first triboelectric pulse sensor is used to be placed at a first preset position on the patient's arterial tree to obtain first pulse wave data, and the second triboelectric pulse sensor is used to be placed at a second preset position on the arterial tree to obtain second pulse wave data. The blood pressure detection device based on a bionic micro-nano structure is used to obtain blood pressure values ​​corresponding to the first pulse wave data and the second pulse wave data according to a preset pulse wave-blood pressure model.

[0007] The technical solution of the above-mentioned first aspect of the present application has at least one of the following advantages or beneficial effects: by setting the first triboelectric pulse sensor and the second triboelectric pulse sensor at the first preset position and the second preset position of the same arterial tree respectively, sleeveless continuous real-time dynamic detection of the patient's blood pressure is achieved, and by inputting the pulse wave data output by the first triboelectric pulse sensor and the second triboelectric pulse sensor into the preset pulse wave-blood pressure model, the pulse wave-blood pressure model can adapt to the specific physiological characteristics of different patients and accurately deduce the patient's blood pressure value, thereby improving the adaptability of the blood pressure detection device based on bionic micro-nano structure, and at the same time improving the accuracy of the blood pressure detection device based on bionic micro-nano structure.

[0008] Furthermore, the first triboelectric pulse sensor and the second triboelectric pulse sensor have the same structure. The first triboelectric pulse sensor includes a positive electrode friction layer, and the positive electrode friction layer is prepared from a flexible composite material with a micro-nano structure. The flexible composite material is a mixture of a nanoconductive material and a flexible material. The nanoconductive material includes one or more of CNTs, MXene, graphene, and nanofibers. The flexible material includes one or more of polyPDMS, silicone, and Ecoflex.

[0009] Furthermore, the first triboelectric pulse sensor also includes a negative electrode friction layer, and the negative electrode friction layer is made of a negative electron affinity thin film material, and the negative electron affinity thin film material includes one or more of FEP, PET, and PTFE.

[0010] Furthermore, the preset pulse wave-blood pressure model is trained in the following manner:

[0011] collecting pulse wave data of patients for training;

[0012] Using an electronic blood pressure detector to obtain a voltage value corresponding to the pulse wave data and used to represent the patient's blood pressure, so as to construct a dual pulse wave-blood pressure training group data set;

[0013] Obtaining dual pulse wave features according to the dual pulse wave-blood pressure training group data set;

[0014] The dual pulse wave features are used as input and the voltage value is used as output to train the PLSR algorithm model, and the trained PLSR algorithm model is used as the pulse wave-blood pressure model.

[0015] In a second aspect, an embodiment of the present application provides a detection method for a blood pressure detection device based on a bionic micro-nanostructure, wherein the blood pressure detection device based on a bionic micro-nanostructure includes a first triboelectric pulse sensor and a second triboelectric pulse sensor, and the detection method includes:

[0016] receiving pulse wave data, the pulse wave data being acquired by the first triboelectric pulse sensor and the second triboelectric pulse sensor, which are respectively disposed at a first preset position and a second preset position of the same arterial tree of the patient, and performing collection for a preset period;

[0017] inputting the pulse wave data collected by the first triboelectric pulse sensor and the second triboelectric pulse sensor into a pulse wave-blood pressure model;

[0018] The pulse wave-blood pressure model is used to output a blood pressure value corresponding to the pulse wave data based on the pulse wave data.

[0019] The technical solution of the above-mentioned second aspect of the present application has at least one of the following advantages or beneficial effects: by receiving the first triboelectric pulse sensor and the second triboelectric pulse sensor arranged in the same arterial tree of the patient and collecting pulse wave data for a preset period, sleeveless, continuous and real-time dynamic detection of the patient's blood pressure can be achieved, and the pulse wave data can be directly input into the pulse wave-blood pressure model to directly obtain the blood pressure value corresponding to the pulse wave data, thereby improving the efficiency of blood pressure detection. At the same time, the pulse wave-blood pressure model can adapt to the specific physiological characteristics of different patients to accurately deduce the blood pressure value that is still unknown in the patient's subsequent detection, thereby improving the accuracy of the blood pressure detection method.

[0020] In a third aspect, an embodiment of the present application provides a method for preparing a blood pressure detection device based on a biomimetic micro-nanostructure, comprising: replicating a biomaterial having a micro-nanostructure on its surface as a biomimetic object by soft lithography technology to obtain a positive electrode friction layer;

[0021] The high negative ion affinity thin film material is treated by a plasma corona treater to obtain a negative electrode friction layer;

[0022] Leading out the positive electrode friction layer and the negative electrode friction layer through wires, assembling and splicing, and packaging to obtain the triboelectric pulse sensor in the blood pressure detection device based on the bionic micro-nano structure;

[0023] The two triboelectric pulse sensors are arranged at a first interval to form the blood pressure detection device based on the bionic micro-nano structure.

[0024] The technical solution of the third aspect of the present application has at least one of the following advantages or beneficial effects: using soft lithography technology to replicate biomaterials with micro-nano structures as biomimetic objects to obtain a positive friction layer, the biomimetic micro-nanostructure with flexible conductive characteristics effectively improves the efficiency and performance of the triboelectric pulse sensor in the process of sensing signals; using a plasma corona treatment machine to treat the negative electron affinity thin film material, the triboelectric pulse sensor can be highly responsive and sensitive to externally applied pressure in a self-powered manner, thereby effectively and sensitively detecting various weak signals and realizing sleeveless continuous real-time dynamic detection of the patient's blood pressure. Two identical triboelectric pulse sensors are arranged relative to each other to form a blood pressure detection device based on a biomimetic micro-nanostructure, which reduces the production cost and improves the efficiency of preparing the blood pressure detection device based on the biomimetic micro-nanostructure.

[0025] Furthermore, the biomaterial with micro-nanostructure on the surface is replicated as a biomimetic object by soft lithography technology to obtain a positive electrode friction layer, including:

[0026] Placing a biomaterial having a micro-nano structure on its surface in deionized water, and ultrasonically cleaning the biomaterial for a first preset time using an ultrasonic machine;

[0027] The biological material is taken out, washed again in deionized water, and dried in a vacuum at a first preset temperature;

[0028] The biomaterial is fixed on a clean glass substrate by using an adhesive to obtain a positive electrode friction layer sample;

[0029] The positive electrode friction layer sample is molded once, a PEGDA solution is dripped onto the positive electrode friction layer sample, and the sample is placed in a UV curing machine for curing, and the cured PEGDA mold is separated from the biomaterial to obtain a primary positive electrode friction layer;

[0030] The primary positive electrode friction layer is subjected to a secondary mold, a mixture of PDMS and CNTs is spin-coated on the primary positive electrode friction layer, and the mixture is placed in a thermostat at a second preset temperature for curing, and the cured PDMS and CNTs mold is separated from the primary positive electrode friction layer to obtain a secondary positive electrode friction layer;

[0031] The secondary positive electrode friction layer is subjected to double-sided gold spraying treatment using a magnetron sputtering apparatus to obtain a positive electrode friction layer.

[0032] Furthermore, the method of treating the high negative ion affinity thin film material with a plasma corona treater to obtain the negative electrode friction layer comprises:

[0033] Cutting the high negative ion affinity film material into a preset size;

[0034] The high negative ion affinity film material is washed and dried with deionized water and subjected to corona treatment with a plasma corona treater to obtain a primary negative electrode friction layer;

[0035] The primary negative electrode friction layer is subjected to double-sided gold spraying treatment using a magnetron sputtering apparatus to obtain a negative electrode friction layer.

[0036] Furthermore, the positive electrode friction layer and the negative electrode friction layer are led out through wires, assembled and spliced, and packaged to obtain the triboelectric pulse sensor in the blood pressure detection device based on the bionic micro-nano structure, including:

[0037] Adhere and fix the positive electrode friction layer using a flexible conductive tape;

[0038] A liquid crystal connecting wire is adhered to the back of the positive electrode friction layer as a lead wire of the positive electrode friction layer; a liquid crystal connecting wire is adhered to the back of the negative electrode friction layer as a lead wire of the negative electrode friction layer;

[0039] The back side of the positive electrode friction layer and the back side of the negative electrode friction layer are arranged opposite to each other;

[0040] Filling the gap between the positive electrode friction layer and the negative electrode friction layer with the cured PDMS to obtain a primary triboelectric pulse sensor;

[0041] The primary triboelectric pulse sensor is packaged and fixed by using liquid Ecoflex to obtain a triboelectric pulse sensor. BRIEF DESCRIPTION OF THE DRAWINGS

[0042] Figure 1 Schematic diagram of a blood pressure detection device based on a bionic micro-nano structure provided in an embodiment of the present application;

[0043] Figure 2 yes Figure 1 Schematic diagram of the structure of the first triboelectric pulse sensor;

[0044] Figure 3 yes Figure 1 Training flow chart of the pulse wave-blood pressure model;

[0045] Figure 4 This is a flowchart of the steps of a detection method of a blood pressure detection device based on a bionic micro-nano structure provided in an embodiment of the present application;

[0046] Figure 5 This is a flowchart of the steps of a method for preparing a blood pressure detection device based on a bionic micro-nano structure provided in an embodiment of the present application;

[0047] Figure 6 yes Figure 5 The step flow chart of S100;

[0048] Figure 7 yes Figure 5 The step flow chart of S200;

[0049] Figure 8 yes Figure 5 The step flow chart of S300;

[0050] Figure 9 This is a flowchart of the steps of another method for preparing a blood pressure detection device based on a bionic micro-nano structure provided in an embodiment of the present application. DETAILED DESCRIPTION

[0051] In order to make the purpose, technical solutions and advantages of this application more clear, the following further describes this application in detail with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are only used to explain this application and are not intended to limit this application.

[0052] In the description of this application, "a plurality" refers to more than two. The use of "first" or "second" is solely for the purpose of distinguishing technical features and should not be construed as indicating or implying relative importance, or implicitly indicating the number of technical features indicated, or implicitly indicating the order of the technical features indicated.

[0053] In the relevant technology, blood pressure monitoring is mainly categorized into two main types: invasive and non-invasive. Most patients still rely on traditional cuff-based electronic non-invasive blood pressure measurement methods. Conventional cuff-based electronic non-invasive blood pressure measurement methods often employ an oscillometric (or oscillatory) method for indirect blood pressure measurement. These methods are bulky, inconvenient to carry, exhibit discrete blood pressure values, and require a fixed posture for measurement, making continuous daily blood pressure monitoring difficult. Furthermore, these methods require manual pressure application to the patient's measurement site, resulting in intermittent blood flow obstruction and severely impacting normal activities. Existing methods that indirectly measure blood pressure using parameters such as pulse and heart rate, however, cannot guarantee accuracy and consistency due to the diversity and variability of human physiological characteristics. Therefore, the development of continuous blood pressure monitoring sensor technology still faces numerous challenges, and the current state of the art lacks reliable and accurate wearable blood pressure monitoring devices.

[0054] To this end, the embodiments of the present application provide a blood pressure detection device and preparation method based on bionic micro-nano structures, which are conducive to solving the problem that the cuff blood pressure detector cannot continuously and dynamically detect the patient's blood pressure in real time and has poor adaptability to individual differences. The present application arranges a friction electric pulse sensor and places it on the patient's arterial tree to achieve continuous and real-time dynamic detection of the patient's blood pressure, and combines the pulse wave-blood pressure model to accurately obtain the patient's blood pressure value, thereby improving the adaptability of the blood pressure detection device based on bionic micro-nano structures.

[0055] Reference Figure 1 , Figure 1 This is a structural schematic diagram of a blood pressure detection device based on a bionic micro-nano structure provided in an embodiment of the present application, including a first triboelectric pulse sensor 1000 and a second triboelectric pulse sensor 2000. The first triboelectric pulse sensor 1000 is used to be placed at a first preset position on the patient's arterial tree to obtain first pulse wave data, and the second triboelectric pulse sensor 2000 is used to be placed at a second preset position on the arterial tree to obtain second pulse wave data. The blood pressure detection device based on a bionic micro-nano structure is used to obtain blood pressure values ​​corresponding to the first pulse wave data and the second pulse wave data according to a preset pulse wave-blood pressure model 3000.

[0056] By setting the first triboelectric pulse sensor 1000 and the second triboelectric pulse sensor 2000 at the first preset position and the second preset position of the same arterial tree respectively, sleeveless continuous real-time dynamic detection of the patient's blood pressure is achieved. By inputting the pulse wave data output by the first triboelectric pulse sensor 1000 and the second triboelectric pulse sensor 2000 into the preset pulse wave-blood pressure model 3000, the pulse wave-blood pressure model 3000 can adapt to the specific physiological characteristics of different patients and accurately deduce the patient's blood pressure value, thereby improving the adaptability of the blood pressure detection device based on bionic micro-nano structure, and at the same time improving the accuracy of the blood pressure detection device based on bionic micro-nano structure.

[0057] It should be noted that, in the embodiment of the present application, the first preset position is the radial artery position of the patient's arm, and the second preset position is a position greater than 8 cm and less than 12 cm away from the radial artery position.

[0058] Reference Figure 2 , Figure 2 yes Figure 1Figure 1 shows the schematic structure of the first triboelectric pulse sensor 1000. The first triboelectric pulse sensor 1000 comprises a positive friction layer 100 and a negative friction layer 200. The positive friction layer 100 is made of a flexible composite material with micro-nano structures. This composite material is obtained by replicating the uniform and regular surface micro-nanostructures of biomaterials using soft lithography. These biomimetic micro-nanostructures with flexible conductive properties effectively improve the efficiency and performance of the first triboelectric pulse sensor 1000 in sensing signals. The negative friction layer 200 is made of a negative electron affinity thin film material. This material is treated with a plasma corona treatment process, enabling the first triboelectric pulse sensor 1000 to be highly responsive and sensitive to external pressure in a self-powered manner. This allows for the effective and sensitive detection of various weak signals and the acquisition of the rhythmic pulse waveform and pulse wave propagation velocity required by the pulse wave-blood pressure model 3000. Through the cooperation between the positive friction layer 100 and the negative friction layer 200, the first triboelectric pulse sensor 1000 can collect rhythmic pulse waveform signals in a portable, accurate and low-energy manner, and use them to extract various pulse wave features to achieve non-invasive real-time dynamic monitoring of blood pressure.

[0059] The first triboelectric pulse sensor 1000 also includes a flexible conductive tape 300 and a liquid crystal connecting wire 400. The flexible conductive tape 300 is used to adhere and fix the positive friction layer 100 and the negative friction layer 200. The liquid crystal connecting wire 400 is used to adhere to the back side of the positive friction layer 100 as a lead-out wire of the positive friction layer 100; it is also used to adhere to the back side of the negative friction layer 200 as a lead-out wire of the negative friction layer 200; the positive friction layer 100 and the negative friction layer 200 are encapsulated and fixed using liquid Ecoflex (copolyester) 500 to form the first triboelectric pulse sensor 1000, realizing sleeveless continuous real-time dynamic detection of the patient's blood pressure.

[0060] It should be noted that the flexible composite material in the embodiments of this application is a mixture of a nanoconductive material and a flexible material. The nanoconductive material includes one or more of CNTs (carbon nanotubes), MXene (two-dimensional materials), graphene, and nanofibers; and the flexible material includes one or more of polydimethylsiloxane (PDMS), silicone, and Ecoflex (copolyester). The embodiments of this application do not limit the types of nanoconductive materials and flexible materials.

[0061] It should be noted that the biological materials in the embodiments of the present application include one or more of cicada wings, lotus leaves, rose petals, and vase flowers.

[0062] It should be noted that the negative electron affinity film material in the embodiment of the present application includes FEP (fluorinated ethylene propylene copolymer), and can also be one or more of PET (polyethylene terephthalate) and PTFE (polytetrafluoroethylene).

[0063] It should be noted that the second triboelectric pulse sensor 2000 and the first triboelectric pulse sensor 1000 in the present embodiment have the same structure. The two identical triboelectric pulse sensors are arranged relative to each other to form a blood pressure detection device based on a biomimetic micro-nanostructure, which reduces manufacturing costs and improves the efficiency of manufacturing blood pressure detection devices based on biomimetic micro-nanostructures. By arranging the first triboelectric pulse sensor 1000 and the second triboelectric pulse sensor 2000 relative to each other, sleeveless, continuous, real-time dynamic monitoring of a patient's blood pressure is achieved.

[0064] Reference Figure 3 , Figure 3 yes Figure 1 The training flow chart of the pulse wave-blood pressure model 300 includes steps S10 to S40. Specifically,

[0065] S10: collecting pulse wave data of the patient for training;

[0066] S20: using an electronic blood pressure detector to obtain a voltage value corresponding to the pulse wave data and used to represent the patient's blood pressure, so as to construct a dual pulse wave-blood pressure training group data set;

[0067] S30: obtaining dual pulse wave features according to the dual pulse wave-blood pressure training group data set;

[0068] S40: Using the dual pulse wave features as input and the voltage value as output, the PLSR algorithm model is trained, and the trained PLSR algorithm model is used as the pulse wave-blood pressure model.

[0069] It should be noted that in the embodiments of the present application, the voltage value corresponding to the pulse wave data obtained by the electronic blood pressure monitor to represent the patient's blood pressure includes the patient's systolic pressure, diastolic pressure, and mean arterial pressure; the dual pulse wave features include the systolic peak transmission time, the predicted period peak transmission time, the predicted period peak transmission frequency, the time difference between the systolic peak and the predicted period peak, and the peak-to-peak ratio between the systolic peak and the predicted period peak. By inputting the dual pulse wave features and blood pressure values ​​into the PLSR algorithm model for training, iteration, and optimization, the PLSR algorithm model is used as a pulse wave-blood pressure model that can adapt to each patient's individual physiological characteristics, such as vascular wall elasticity, blood viscosity, and skin tissue properties. The patient only needs to use the first and second triboelectric pulse sensors to collect dual pulse data from the patient and use this as input to the model. The model can then derive the dual pulse data into the corresponding blood pressure value through the internally trained relationship matrix, thereby realizing non-invasive dynamic blood pressure monitoring and deriving the patient's individual blood pressure value that remains unknown during subsequent monitoring. This enables continuous dynamic detection of the patient's blood pressure value and realizes non-invasive, wearable dynamic blood pressure monitoring.

[0070] It should be noted that the blood pressure detection device based on the bionic micro-nano structure and the pulse wave-blood pressure model in the embodiment of the present application can be combined with smart medical care and the Internet of Things to form a communicative platform for real-time dynamic monitoring and treatment management of blood pressure, which helps to improve the health management and quality of life of patients with cardiovascular diseases.

[0071] Reference Figure 4 , Figure 4 The embodiment of the present application provides a detection method for a blood pressure detection device based on a bionic micro-nano structure, comprising steps S50 to S60. Specifically,

[0072] S50: receiving pulse wave data, the pulse wave data being acquired by a first triboelectric pulse sensor and a second triboelectric pulse sensor respectively disposed at a first preset position and a second preset position on the same arterial tree of the patient for a preset period;

[0073] S60: Inputting the pulse wave data collected by the first triboelectric pulse sensor and the second triboelectric pulse sensor into the pulse wave-blood pressure model;

[0074] The pulse wave-blood pressure model is used to output a blood pressure value corresponding to the pulse wave data based on the pulse wave data.

[0075] By receiving the first triboelectric pulse sensor and the second triboelectric pulse sensor arranged in the same arterial tree of the patient and collecting pulse wave data at a preset period, sleeveless, continuous and real-time dynamic detection of the patient's blood pressure can be achieved. By directly inputting the pulse wave data into the pulse wave-blood pressure model, the blood pressure value corresponding to the pulse wave data can be directly obtained, thereby improving the efficiency of blood pressure detection. At the same time, the pulse wave-blood pressure model can adapt to the specific physiological characteristics of different patients and accurately deduce the blood pressure value that is still unknown in the patient's subsequent detection, thereby improving the accuracy of the blood pressure detection method.

[0076] It should be noted that the first preset position is the radial artery position of the arterial tree, and the second preset position is a position 8 cm to 12 cm away from the radial artery.

[0077] It should be noted that the collection of preset period data by the first triboelectric pulse sensor and the second triboelectric pulse sensor includes: using the first triboelectric pulse sensor and the second triboelectric pulse sensor to collect pulse wave data of the individual patient for 2 to 5 days, with the collection time being 1 to 2 hours per day, and collecting 10 to 20 sets of pulse wave data per day.

[0078] Reference Figure 5 , Figure 5 This is a flowchart of a method for preparing a blood pressure detection device based on a bionic micro-nano structure provided in an embodiment of the present application, including steps S100 to S400. Specifically,

[0079] S100: Using soft lithography technology, a biomaterial with a micro-nanostructured surface is replicated as a biomimetic object to obtain a positive electrode friction layer;

[0080] S200: using a plasma corona treater to treat the high negative ion affinity thin film material to obtain a negative electrode friction layer;

[0081] S300: Leading out the positive electrode friction layer and the negative electrode friction layer through wires, assembling and splicing them, and packaging them to obtain the triboelectric pulse sensor in the blood pressure detection device based on the bionic micro-nano structure;

[0082] S400: Arrange two triboelectric pulse sensors at a first interval to form the blood pressure detection device based on the bionic micro-nano structure.

[0083] Using soft lithography, a biomaterial with a micro-nanostructure is replicated as a biomimetic object to create a positive friction layer. This biomimetic micro-nanostructure with flexible conductive characteristics effectively improves the efficiency and performance of the triboelectric pulse sensor in sensing signals. Using a plasma corona treatment machine to treat the negative electron affinity thin film material, the triboelectric pulse sensor is highly responsive and sensitive to externally applied pressure in a self-powered manner, effectively and sensitively detecting various weak signals and enabling sleeveless, continuous, real-time dynamic monitoring of a patient's blood pressure. Two identical triboelectric pulse sensors are positioned relative to each other to form a blood pressure detection device based on a biomimetic micro-nanostructure, reducing production costs and improving the efficiency of the device's fabrication.

[0084] Reference Figure 6 , Figure 6 yes Figure 5 The step flow chart of step S100 includes steps S110 to S160. Specifically,

[0085] S110: placing a biomaterial having a micro-nano structure on its surface in deionized water, and ultrasonically cleaning the biomaterial for a first preset time using an ultrasonic machine;

[0086] S120: taking out the biological material, washing it again in deionized water, and drying it in a vacuum at a first preset temperature;

[0087] S130: fixing the biomaterial on a clean glass substrate using an adhesive to obtain a positive electrode friction layer sample;

[0088] S140: performing a mold on the positive electrode friction layer sample, dripping a PEGDA solution onto the positive electrode friction layer sample, and placing the sample in a UV curing machine for curing, separating the cured PEGDA mold from the biomaterial to obtain a primary positive electrode friction layer;

[0089] S150: performing a secondary mold on the primary positive electrode friction layer, spin-coating a mixture of PDMS and CNTs on the primary positive electrode friction layer, and placing the mixture in a thermostat at a second preset temperature for curing, and separating the cured PDMS and CNTs mold from the primary positive electrode friction layer to obtain a secondary positive electrode friction layer;

[0090] S160: The secondary positive electrode friction layer is subjected to double-sided gold spraying treatment using a magnetron sputtering apparatus to obtain a positive electrode friction layer.

[0091] In one embodiment of the present application, a biomaterial with micro-nanostructured surfaces is replicated as a biomimetic object using soft lithography to produce a positive electrode friction layer. Specifically, the steps include placing the biomaterial with micro-nanostructured surfaces in deionized water, ultrasonically cleaning the biomaterial for a predetermined time, removing the biomaterial sample, and washing it again with deionized water. The sample is then dried in a vacuum environment at a predetermined temperature for 1 to 2 hours. The biomaterial is then affixed to a clean glass substrate using an adhesive to produce a positive electrode friction layer sample. The biomaterial is then molded using PEGDA. PEGDA (polyethylene glycol diacrylate) and a photoinitiator (2-hydroxy-2-methylpropiophenone) were mixed at a volume ratio of 100:1 to 100:5. After stirring and centrifuging to remove bubbles, the PEGDA solution was dripped onto the biomaterial sample under vacuum and placed in a UV curing machine. The sample was irradiated at 50-80% power for 120 to 300 seconds. The cured PEGDA mold was separated from the biomaterial sample, ultrasonically cleaned for 10 minutes, and dried in a 40-60°C oven for 1 to 2 hours to obtain the primary positive electrode friction layer. A CNTs / PDMS flexible composite was prepared and a second mold was performed. PDMS (dimethylsiloxane) and a curing agent were mixed at a volume ratio of 8:1 or 12:1. After stirring, vacuumization and centrifugation were performed to remove bubbles. Carbon nanotube powder (CNTs) was then added to the mixture at a mass ratio of 6:1 or 12:1. After thorough stirring, vacuumization and centrifugation were performed again to remove bubbles. This resulted in a PDMS / CNTs mixture. A CNTs / PDMS mixture was spin-coated onto the PEGDA inverted structure using spin coating parameters of 1500 to 5000 rpm for 90 to 200 seconds, with an acceleration of 200 to 500 rpm / s. After spin coating, the sample was cured in a constant temperature oven at 40-80°C for 3-8 hours. After peeling, a secondary positive friction layer with the biomaterial surface micro-nanostructure was obtained. The resulting secondary positive friction layer was then gold-sputtered on both sides using a magnetron sputtering instrument. Under vacuum conditions of less than 3 Pa and a current of 15 to 45 mA, magnetron sputtering was performed for 3 to 8 minutes to obtain the positive friction layer.

[0092] Through soft lithography technology, biomaterials with micro-nano structures are replicated as bionic objects to obtain a positive electrode friction layer. The bionic micro-nano structure with flexible conductive characteristics effectively improves the efficiency and performance of the triboelectric pulse sensor in the signal sensing process, and at the same time improves the detection accuracy of the blood pressure detection device based on the bionic micro-nano structure.

[0093] It should be noted that the biomaterial in the embodiment of the present application can be one or more of the animal and plant biomaterials with micro-nano structures on the surface of cicada wings, lotus leaves, rose petals, and the inner wall of bottle flowers. The embodiment of the present invention does not limit the type of biomaterial.

[0094] It should be noted that, in the embodiment of the present application, the first preset time is 5 to 15 minutes. The first preset time can be set according to different biological materials, and the present application does not limit the first preset time.

[0095] It should be noted that, in the embodiment of the present application, the first preset temperature is 40° C. to 80° C. The first preset temperature can be set according to different biological materials, and the present application does not limit the first preset temperature.

[0096] Reference Figure 7 , Figure 7 yes Figure 5 The step flow chart of step S200 includes steps S210 to S230. Specifically,

[0097] S210: cutting the high negative ion affinity film material into a preset size;

[0098] S220: washing and drying the high negative ion affinity thin film material with deionized water and performing corona treatment with a plasma corona treater to obtain a primary negative electrode friction layer;

[0099] S230: performing double-sided gold spraying treatment on the primary negative electrode friction layer using a magnetron sputtering apparatus to obtain a negative electrode friction layer.

[0100] In one embodiment of the present application, a high-negative electron affinity thin film material is cut into predetermined dimensions, cleaned with deionized water, dried, and then corona treated using a plasma corona treater to form a primary negative electrode friction layer. Gold is then sprayed onto both the non-friction contact surface and the non-corona treated surface of the high-negative electron affinity thin film material using magnetron sputtering. Magnetron sputtering is performed for 3 to 8 minutes at a vacuum of less than 3 Pa and a current of 15 to 14 mA to form the negative electrode friction layer.

[0101] By treating the negative electron affinity thin film material with a plasma corona treater, the triboelectric pulse sensor can be highly responsive and sensitive to external pressure in a self-powered manner, thereby effectively and sensitively detecting various weak signals and realizing sleeveless continuous real-time dynamic detection of patients' blood pressure.

[0102] It should be noted that the high electron-affinity film material in the embodiment of the present application is FEP (fluorinated ethylene propylene copolymer), and can also be one or more of PET (polyethylene terephthalate) and PTFE (polytetrafluoroethylene). The present application does not limit the high electron-affinity film material.

[0103] Reference Figure 8 and Figure 98 is a flowchart of step S300 in step 5, including steps S310 to S350. Specifically,

[0104] S310: Using a flexible conductive tape to adhere and fix the positive electrode friction layer;

[0105] S320: Using a liquid crystal connecting wire to adhere to the back of the positive electrode friction layer as a lead wire of the positive electrode friction layer; Using a liquid crystal connecting wire to adhere to the back of the negative electrode friction layer as a lead wire of the negative electrode friction layer;

[0106] S330: placing the back surface of the positive electrode friction layer and the back surface of the negative electrode friction layer opposite to each other;

[0107] S340: Filling the gap between the positive electrode friction layer and the negative electrode friction layer with the cured PDMS to obtain a primary triboelectric pulse sensor;

[0108] S350: Encapsulating and fixing the primary triboelectric pulse sensor using liquid Ecoflex to obtain the triboelectric pulse sensor.

[0109] Liquid crystal connecting wires are respectively adhered to the back of the positive friction layer and the negative friction layer as the lead-out wires of the positive friction layer and the negative friction layer. The friction surfaces of the positive friction layer and the negative friction layer are placed opposite to each other, and then the cured PDMS is placed between the positive and negative friction layers to create a gap during the friction process to obtain a primary triboelectric pulse sensor; Ecoflex's A and B glues are mixed and stirred in a 1:1 ratio to defoam to form liquid Ecoflex, and the liquid Ecoflex is used to encapsulate and fix the sensor.

[0110] A triboelectric pulse sensor is obtained by arranging the positive electrode friction layer 100 and the negative electrode friction layer 200 relative to each other and using liquid Ecoflex for packaging and fixing. Since the positive electrode friction layer has a bionic micro-nano structure with flexible conductive characteristics, it effectively improves the efficiency and performance of the triboelectric pulse sensor in the process of sensing signals. The self-powered mode of the negative electrode friction layer is highly responsive and sensitive to external pressure, and can effectively and sensitively detect various weak signals, thereby improving the detection accuracy of the blood pressure detection device based on the bionic micro-nano structure, and at the same time realizing sleeveless, portable, accurate continuous real-time dynamic detection of patients' blood pressure.

[0111] It should be noted that the flexible conductive tape in the embodiment of the present application is a copper conductive tape, and may also be a platinum conductive tape. The present application does not limit the type of the flexible conductive tape.

[0112] It should be noted that the lead wires of the positive electrode friction layer and the negative electrode friction layer in the embodiment of the present application are liquid crystal connecting wires, and can also be one or more of copper wires and platinum wires. The embodiment of the present application does not limit the types of the lead wires of the positive electrode friction layer and the negative electrode friction layer.

[0113] The embodiments of the present application are described in detail above in conjunction with the accompanying drawings, but the present application is not limited to the above embodiments. Various changes can be made within the scope of knowledge possessed by ordinary technicians in the technical field without departing from the purpose of the present application.

Claims

1. A method for preparing a blood pressure detection device based on a bionic micro-nano structure, characterized in that: include: The biomaterial with micro-nanostructure on the surface is replicated as a biomimetic object through soft lithography technology to obtain the positive electrode friction layer; The high negative ion affinity thin film material is treated by a plasma corona treater to obtain a negative electrode friction layer; Leading out the positive electrode friction layer and the negative electrode friction layer through wires, assembling and splicing, and packaging to obtain the triboelectric pulse sensor in the blood pressure detection device based on the bionic micro-nano structure; The two triboelectric pulse sensors are arranged at a first interval to form the blood pressure detection device based on the bionic micro-nano structure.

2. The method for preparing a blood pressure detection device based on a bionic micro-nano structure according to claim 1, characterized in that: The method of replicating a biomaterial having a micro-nano structure on its surface as a biomimetic object by soft lithography technology to obtain a positive electrode friction layer comprises: Placing a biomaterial having a micro-nano structure on its surface in deionized water, and ultrasonically cleaning the biomaterial for a first preset time using an ultrasonic machine; The biological material is taken out, washed again in deionized water, and dried in a vacuum at a first preset temperature; The biomaterial is fixed on a clean glass substrate by using an adhesive to obtain a positive electrode friction layer sample; The positive electrode friction layer sample is molded once, a PEGDA solution is dripped onto the positive electrode friction layer sample, and the sample is placed in a UV curing machine for curing, and the cured PEGDA mold is separated from the biomaterial to obtain a primary positive electrode friction layer; The primary positive electrode friction layer is subjected to a secondary mold, a mixture of PDMS and CNTs is spin-coated on the primary positive electrode friction layer, and the mixture is placed in a thermostat at a second preset temperature for curing, and the cured PDMS and CNTs mold is separated from the primary positive electrode friction layer to obtain a secondary positive electrode friction layer; The secondary positive electrode friction layer is subjected to double-sided gold spraying treatment using a magnetron sputtering apparatus to obtain a positive electrode friction layer.

3. The method for preparing a blood pressure detection device based on a bionic micro-nano structure according to claim 1, characterized in that: The method of treating the high negative ion affinity thin film material with a plasma corona treater to obtain the negative electrode friction layer comprises: Cutting the high negative ion affinity film material into a preset size; The high negative ion affinity film material is washed and dried with deionized water and subjected to corona treatment with a plasma corona treater to obtain a primary negative electrode friction layer; The primary negative electrode friction layer is subjected to double-sided gold spraying treatment using a magnetron sputtering apparatus to obtain a negative electrode friction layer.

4. The method for preparing a blood pressure detection device based on a biomimetic micro-nano structure according to claim 1, characterized in that: The positive electrode friction layer and the negative electrode friction layer are led out through wires, assembled and spliced, and packaged to obtain the triboelectric pulse sensor in the blood pressure detection device based on the bionic micro-nano structure, including: Adhere and fix the positive electrode friction layer using a flexible conductive tape; A liquid crystal connecting wire is adhered to the back of the positive electrode friction layer as a lead wire of the positive electrode friction layer; a liquid crystal connecting wire is adhered to the back of the negative electrode friction layer as a lead wire of the negative electrode friction layer; The back side of the positive electrode friction layer and the back side of the negative electrode friction layer are arranged opposite to each other; Filling the gap between the positive electrode friction layer and the negative electrode friction layer with the cured PDMS to obtain a primary triboelectric pulse sensor; The primary triboelectric pulse sensor is packaged and fixed by using liquid Ecoflex to obtain a triboelectric pulse sensor.

5. A blood pressure detection device based on bionic micro-nanostructure, characterized in that: The blood pressure detection device is manufactured by the manufacturing method according to any one of claims 1 to 4, and includes a first triboelectric pulse sensor and a second triboelectric pulse sensor, wherein the first triboelectric pulse sensor is used to be placed at a first preset position on the patient's arterial tree to obtain first pulse wave data, and the second triboelectric pulse sensor is used to be placed at a second preset position on the arterial tree to obtain second pulse wave data, and the blood pressure detection device based on the biomimetic micro-nanostructure is used to obtain blood pressure values ​​corresponding to the first pulse wave data and the second pulse wave data according to a preset pulse wave-blood pressure model; The first triboelectric pulse sensor and the second triboelectric pulse sensor have the same structure. The first triboelectric pulse sensor includes a positive electrode friction layer, and the positive electrode friction layer is made of a flexible composite material with a micro-nano structure. The first triboelectric pulse sensor further includes a negative electrode friction layer, which is made of a negative electron affinity thin film material.

6. The blood pressure detection device based on bionic micro-nanostructure according to claim 5, characterized in that: The flexible composite material is formed by mixing a nano-conductive material and a flexible material. The nano-conductive material includes one or more of CNTs, MXene, graphene, and nanofibers. The flexible material includes one or more of poly-PDMS, silica gel, and Ecoflex.

7. The blood pressure detection device based on biomimetic micro-nanostructure according to claim 6, characterized in that: The negative electron affinity thin film material includes one or more of FEP, PET, and PTFE.

8. The blood pressure detection device based on bionic micro-nano structure according to claim 5, characterized in that: The preset pulse wave-blood pressure model is trained in the following manner: collecting pulse wave data of patients for training; Using an electronic blood pressure detector to obtain a voltage value corresponding to the pulse wave data and used to represent the patient's blood pressure, so as to construct a dual pulse wave-blood pressure training group data set; Obtaining dual pulse wave features according to the dual pulse wave-blood pressure training group data set; The dual pulse wave features are used as input and the voltage value is used as output to train the PLSR algorithm model, and the trained PLSR algorithm model is used as the pulse wave-blood pressure model.

9. The blood pressure detection device based on bionic micro-nanostructure according to claim 8, characterized in that: The dual pulse wave features include systolic peak transmission time, predicted period peak transmission time, predicted period peak transmission frequency, time difference between systolic peak and predicted period peak, and peak height ratio between systolic peak and predicted period peak.

10. A detection method for a blood pressure detection device based on a bionic micro-nano structure, characterized in that: The blood pressure detection device is prepared by the preparation method according to any one of claims 1 to 4. The blood pressure detection device based on the bionic micro-nano structure includes a first triboelectric pulse sensor and a second triboelectric pulse sensor. The detection method includes: receiving pulse wave data, the pulse wave data being acquired by the first triboelectric pulse sensor and the second triboelectric pulse sensor, which are respectively disposed at a first preset position and a second preset position of the same arterial tree of the patient, and performing collection for a preset period; inputting the pulse wave data collected by the first triboelectric pulse sensor and the second triboelectric pulse sensor into a pulse wave-blood pressure model; The pulse wave-blood pressure model is used to output a blood pressure value corresponding to the pulse wave data based on the pulse wave data.

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