AU2020101386A4 - A Biomimetic multifunctional flexible sensor based on skin collagen aggregate and its manufacturing method - Google Patents
A Biomimetic multifunctional flexible sensor based on skin collagen aggregate and its manufacturing method Download PDFInfo
- Publication number
- AU2020101386A4 AU2020101386A4 AU2020101386A AU2020101386A AU2020101386A4 AU 2020101386 A4 AU2020101386 A4 AU 2020101386A4 AU 2020101386 A AU2020101386 A AU 2020101386A AU 2020101386 A AU2020101386 A AU 2020101386A AU 2020101386 A4 AU2020101386 A4 AU 2020101386A4
- Authority
- AU
- Australia
- Prior art keywords
- collagen
- humidity
- sensor
- sensitive layer
- polyaniline
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Ceased
Links
Classifications
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
- C08L89/00—Compositions of proteins; Compositions of derivatives thereof
- C08L89/04—Products derived from waste materials, e.g. horn, hoof or hair
- C08L89/06—Products derived from waste materials, e.g. horn, hoof or hair derived from leather or skin, e.g. gelatin
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08K—Use of inorganic or non-macromolecular organic substances as compounding ingredients
- C08K3/00—Use of inorganic substances as compounding ingredients
- C08K3/02—Elements
- C08K3/04—Carbon
- C08K3/041—Carbon nanotubes
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08K—Use of inorganic or non-macromolecular organic substances as compounding ingredients
- C08K5/00—Use of organic ingredients
- C08K5/04—Oxygen-containing compounds
- C08K5/05—Alcohols; Metal alcoholates
- C08K5/053—Polyhydroxylic alcohols
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01L—MEASURING FORCE, STRESS, TORQUE, WORK, MECHANICAL POWER, MECHANICAL EFFICIENCY, OR FLUID PRESSURE
- G01L1/00—Measuring force or stress, in general
- G01L1/18—Measuring force or stress, in general using properties of piezo-resistive materials, i.e. materials of which the ohmic resistance varies according to changes in magnitude or direction of force applied to the material
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
- G01N27/60—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrostatic variables, e.g. electrographic flaw testing
- G01N27/605—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrostatic variables, e.g. electrographic flaw testing for determining moisture content, e.g. humidity
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08K—Use of inorganic or non-macromolecular organic substances as compounding ingredients
- C08K2201/00—Specific properties of additives
- C08K2201/001—Conductive additives
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08K—Use of inorganic or non-macromolecular organic substances as compounding ingredients
- C08K2201/00—Specific properties of additives
- C08K2201/011—Nanostructured additives
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08K—Use of inorganic or non-macromolecular organic substances as compounding ingredients
- C08K2201/00—Specific properties of additives
- C08K2201/013—Additives applied to the surface of polymers or polymer particles
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08K—Use of inorganic or non-macromolecular organic substances as compounding ingredients
- C08K3/00—Use of inorganic substances as compounding ingredients
- C08K3/02—Elements
- C08K3/04—Carbon
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
- C08L2203/00—Applications
- C08L2203/02—Applications for biomedical use
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
- C08L2203/00—Applications
- C08L2203/20—Applications use in electrical or conductive gadgets
Landscapes
- Chemical & Material Sciences (AREA)
- Health & Medical Sciences (AREA)
- Chemical Kinetics & Catalysis (AREA)
- Organic Chemistry (AREA)
- Polymers & Plastics (AREA)
- Medicinal Chemistry (AREA)
- General Physics & Mathematics (AREA)
- Physics & Mathematics (AREA)
- Life Sciences & Earth Sciences (AREA)
- General Health & Medical Sciences (AREA)
- Immunology (AREA)
- Pathology (AREA)
- Dermatology (AREA)
- Biochemistry (AREA)
- Analytical Chemistry (AREA)
- Electrochemistry (AREA)
- Engineering & Computer Science (AREA)
- Materials Engineering (AREA)
- Nanotechnology (AREA)
- Investigating Or Analyzing Materials By The Use Of Electric Means (AREA)
Abstract
The invention discloses a bio-mimetic multifunctional flexible sensor
based on collagen aggregate and a preparation method thereof, which is
different from the conventional sensor at present. It is characterized in that
natural collagen aggregation with superior bio-compatibility and three
dimensional network structure is organically doped with polyaniline-carbon
nanotube composite conductive material with excellent conductivity and
dispersibility, and by applying a specific processing method on such organically
doped material to manufacture respectively a sensor element material with high
sensitivity to both pressure and humidity and by assembling these two materials
to construct a piezoelectric layer multi-layer structure and an internal three
dimensional network structure, hence, manufacturing successfully a new
flexible multifunctional sensor sensitive to both pressure and humidity. The
multifunctional sensor has excellent biological characteristics and can be widely
used in the fields of intelligent prosthesis, high-end robot, virtual reality and
wearable sensor.
1/4
2
3
Fig. 1
/ 4
5
6
Fig. 2
Description
1/4
2
3
Fig. 1
/ 4
5
6
Fig. 2
PATENTS ACT 1990
A Biomimetic multifunctional flexible sensor based on skin collagen aggregate and its manufacturing method
The invention is described in the following statement:-
A Biomimetic multifunctional flexible sensor based on skin collagen aggregate and its manufacturing method
[0001] The invention relates to the field of leather industrial solid waste resource utilization and flexible sensor manufacturing technology, in particular to a bio-mimetic multifunctional flexible sensor based on skin collagen aggregate and a preparation method thereof.
[0002] Sensors will play the most fundamental and important role in the intellectual age of all things to mimic the perception of human skin of the external environment, including pressure, humidity and temperature, and will be reasonably analyzed by artificial intelligence. In that end, it is possible to continuously build large data on the intelligent Internet of things. It can be widely used in artificial intelligence and medical diagnosis, including intelligent prosthesis, high-end robot, wearable health monitor and virtual reality. Pressure sensors are key components of the sensor, which determine the characteristics and performance of the system. To date, pressure sensors with different working mechanisms, including capacitive, piezoelectric, frictional and piezoresistive, have attracted the most attention. Among them, piezoresistive sensors are more promising due to the simplicity, high sensitivity and operational stability of their manufacturing processes. The resistance change of the piezoresistive sensor is usually caused by a change in contact resistance or material structure. According to recent reports, melamine, polydimethylsiloxane, ionic liquids, polyvinylidene fluoride, silicone rubber, polyimide and the like have been widely used in the preparation of piezoelectric sensors, And the prepared product has excellent flexibility and sensing sensitivity. However, large scale manufacturing of pressure sensors still poses significant challenges due to the problems of biocompatibility, degradation, and raw material costs.
[0003] Also, currently reported sensors generally have a single function, such as the high precision piezoresistive sensor provided by CN109443609A. These sensors are often unable to respond to a variety of external signals like human skin. Humidity sensing is also an essential function of the skin, and various types of humidity sensors, such as capacitive or resistive electrical sensors, and transmissive or reflective based optical sensors, are currently widely reported. However, there are few reports of multi-function humidity sensors, so that the integration and intelligent process of the sensors is hindered. In summary, it is necessary to develop a bionic multifunctional sensor with high sensitivity, low price and wide response range with pressure detection and humidity sensing functions.
[0004] Biomass materials, especially animal collagen aggregates, are receiving increasing attention due to their high bio-compatibility, excellent biodegradability, good sustainability and low antigenicity. China produces up to 1.4 million tons of leather solid wastes each year, of which 300,000 tons are chromium-containing high-risk wastes, more than 80% of which are made up of natural skin collagen. If that purify collagen aggregate in this part of waste is applied to the development of bio-mimetic material, not only the purpose of converting waste into treasure is realized. In particular to a novel biomimetic multifunctional flexible sensor base on skin collagen aggregate and a preparation method thereof.
[0005] Any discussion of the prior art throughout the specification should in no way be considered as an admission that such prior art is widely known or forms part of common general knowledge in the field.
[0006] The bionic multifunctional flexible sensor prepared by the invention is characterized in that a multifunctional flexible type having a "thousand-layer structure" and an inner "three-dimensional structure" is prepared in a simple manner while being sensitive to humidity and pressure sensor. The sensor can detect compression, bending and torsional strain with high sensitivity, large detection range and short response time. In addition, it has excellent performance as a humidity sensitive device, and has high sensitivity and extremely low short hysteresis. Due to the unique biological characteristics of collagen aggregates, the multifunctional flexible sensor has better water vapor permeability and comfort when worn as a device, and has degradability and durability. This is not the case with conventional flexible multi-functional flexible sensors. These special functions show that the multi-function flexible sensor can be widely used in intelligent robot by means of multi-analysis and statistical analysis to realize recognition and detection of complicated movement and manipulation of human body. Health monitor and human body movement monitoring.
[0007] It is an object of the present invention to overcome or ameliorate at least one of the disadvantages of the prior art, or to provide a useful alternative.
[0008] In order to achieve the above object, the technical solution adopted by the present invention is:
[0009] A biomimetic multifunctional flexible sensor based on skin collagen aggregate and a preparation method and a preparation method thereof, A natural skin collagen aggregate matrix including a three dimensional network structure, a polyaniline-acidified carbon nanotube composite conductive matrix dispersed in the matrix, and different treatment methods. A sensor element with high sensitivity to pressure and humidity was prepared respectively, and a multi-function sensor sensitive to pressure and humidity was successfully prepared by assembling the two materials.
[0010] Further, the natural skin collagen aggregate is prepared from a leather solid waste, and the structure is characterized by a typical light-dark cross-grain structure.
[0011] And further, that mas ratio of natural skin collagen aggregate: Polyaniline: Acidified carbon nanotube: Hydrophobic crosslinking agent is (0.1~30): (0.1~5): (0.1~5): (0.01-10). The treatment method is a freeze drying method.
[0012] And further, that natural skin collagen aggregate: Polyaniline: Acidified carbon nanotube: The mass ratio of glycerol is (0.1~30): (0.1~5): (0.1~5): (0.01~10). The treatment was dried at room temperature.
[0013] And further, the piezoresistive sensor material is attached above the moisture sensor material by the adsorption of proteins, and after a pressure of 1 to 10 MPa. The piezoelectric layer multilayer structure and the internal three-dimensional network structure are constructed. Preparation of multi-functional sensor.
[0014] The present invention also provides the bio-mimetic multifunctional flexible sensor based on collagen aggregate and a preparation method thereof, the preparation method comprising the steps of:
[0015] In that presence of aniline as monome and ammonium persulfate as oxidant. A polyaniline-acidified carbon nanotube composite conductive matrix material was prepared by reaction in a dispersion comprising sulfosalicylic acid and acidified carbon nanotubes; In a collagen solution, a dispersion liquid of a polyaniline-acidified carbon nanotube composite conductive matrix material and glycerin are added dropwise to that collagen solution, and the mixture is sufficiently stirred and dry at room temperature to obtain a high-precision moisture sensor material based on skin collagen aggregate. In that invention, a spray gun is use to spray conductive graphite to prepare a cross electrode, a dispersion liquid of a polyaniline-acidified carbon nanotube composite conductive matrix material is added dropwise to a collagen solution. The strain super-sensitive flexible multi-functional flexible sensor with the function of moisture sensitivity was prepared after freeze drying.
[0016] Further, in that dispersion for prepare the polyaniline-acidified carbon nanotube composite conductive matrix material, the mass ratio of the multi-wall carbon nanotube: Aniline is 1: (0.5 ~ 2); The molar ratio of aniline: Sulfosalicylic acid is 1: (1 ~ 5); The molar ratio of aniline: Ammonium persulfate is 1: (0.5 ~ 2).
[0017] Further, when the dispersion of the polyaniline-acidified carbon nanotube composite conductive matrix material is added dropwise to the collagen solution. Collagen: The mass ratio of polyaniline-acidified carbon nanotube composite conductive matrix material is 1: (0.03 ~ 1).
[0018] Further, the polyaniline-acidified carbon nanotube composite conductive matrix material is obtained by a method comprising the steps of:
[0019] (1) Placing a multi-walled carbon nanotube with a mass ratio of (0.1 ~ 1): (0.1 ~ 100): (0.1 ~ 100), concentrated sulfuric acid and concentrated nitric acid in a reactor. Heat and refluxing at 35~80°C for 2~20 h; and cooling to normal temperature; Diluting with 300-1000 mL of deionized water; Under the rotation speed of 5000 ~ 20000 x g, the supernatant was centrifuged several times to neutral; After filtration, the sediment was collected by freeze drying for 10 ~ 20 hours to obtain acidified carbon nanotubes.
[0020] (2) Placing 0.2 to 1.5 g of acidified carbon nanotubes in 50 to 200 mL deionized water, adding 0.5 to 2 times the mass of acidified carbon nanotubes and 1 to 5 times the amount of aniline monomer sulfosalicylic acid, Ultrasonically disperse for 20-90 min, transfer to a reactor, stir rapidly at room temperature; mix 0.5-2 times the amount of aniline monomer ammonium persulfate oxidizing agent into 20-100 mL deionized water, add into the reaction system dropwise. In that condition of 0 ~ 10°C, stir for 5 ~ hours, filter and washing with absolute ethanol and distilled water, freeze-drying for 10 ~ 20 hours, collect samples, and obtaining polyaniline acidified carbon nanotube composite conductive matrix material;
[0021] Further, the preparation method comprises the steps of: In that method, polyaniline-acidified carbon nanotube composite conductive matrix material and glycerin are adde to the collagen aggregate solution, and the mixture is uniformly mixed and dry to obtain a humidity-sensitive layer;
[0022] Spraying conductive graphite on the surface of the humidity sensitive layer to obtain an electrode layer.
[0023] (3) Adding polyaniline-acidified carbon nanotube composite conductive matrix material to the collagen aggregate solution to obtain a precursor solution of the mechanical sensitive material;
[0024] (4) the precursor solution of the mechanical sensitive material is constructed on the surface of the electrode layer, freeze-dried and press formed, and the mechanical sensitive layer with three-dimensional network structure is obtained.
[0025] Specific steps are as follows: (1) In that method, 0.1 to 30 g of natural skin collagen aggregate are taken and slowly stirred at 30 to 70°C for 5 to 60 minute to be dispersed in 10 to 100 mL of deionized water, Transfer to the reactor; take the polyaniline-acidified carbon nanotube composite conductive matrix material of 0.03 ~ 1 times the mass of collagen, disperse in 30 ~ 150 mL deionized water for 20 ~ 90 minutes with ultrasound, add into the collagen solution dropwise, Add 0.01 ~ 10 g glycerol, stir at room temperature for 2 ~ 10 h, collect mixed liquor, dry at room temperature in mold, obtain humidity sensing film, thickness is 0.1 ~1mm. Using a 1 cm x 2 cm humidity sensing film as the substrate, the conductive graphite was sprayed on the substrate using a spray gun to form a cross electrode, the spacing between adjacent electrodes was 1 ~ 5 mm, and the width of the interdigital electrodes was 1 ~ 2 mm. (2) And taking 0.1 to 30 g of natural dermal collagen aggregate, slowly stirring at 30 to 70 °C for 5 to 60 minutes to disperse it in 10 to 100 mL
deionized water, Transfer to the reactor; take the polyaniline-acidified carbon nanotube composite conductive matrix material of 0.03 ~ 1 times the mass of collagen, disperse in 30 ~ 150 mL deionized water for 20 ~
90 minutes with ultrasound, add into the collagen solution dropwise, Stirring at room temperature for 2 ~ 10 hours; collecting samples; uniformly spin coating 0.1 ~ 5 g of the prepared mixture on the base film, freeze drying, and forming under 1 ~ 10 MPa compression.
[0026] Further, the method comprises the steps of: (1) Acidification of multi-walled carbon nanotubes: Multi-walled carbon nanotubes with a mass ratio of 0.1 ~ 1: 0.1 ~ 100: 0.1 ~ 100, concentrated sulfuric acid and concentrated nitric acid were placed in a reactor and ultrasonically dispersed for 20 ~ 90 min. Then stirring and refluxing at 35 ~ °C for 2 ~ 20 h. Cool to normal temperature, dilute 300 ~ 1000 mL of deionized water, and centrifuge to supernatant to neutral at 5000 ~ 20000 x g. After filtration, freeze-dry for 10 ~ 20 hours to collect the lower layer precipitate, and prepare for use; (2) And placing the sample collected in step (1) of 0.2 to 1.5 g in 50 to 200 mL of deionized water, Aniline with a mass of 0.5 to 2 times that of multi-walled carbon nanotubes and sulfosalicylic acid with a mass of 1 to 5 times that of aniline monomer were added, and ultrasonic dispersion was carried out for 20 to 90 minutes, transferred to a reactor, and rapidly stirred at room temperature, The ammonium persulfate oxidizing agent containing 0.5 ~ 2 times the amount of aniline monomer was mixed into 20 ~ 100 mL deionized water, the reaction system was added dropwise, and the reaction was stirred at 0 ~ 10 °C for 5 ~ 20 hours. Filter and wash with absolute ethanol and distilled water respectively, freeze-dry for 10 ~ 20 hours, collect samples, and put them into use; (3) And take 0.1 ~ 30 g of natural dermal collagen aggregate, stir slowly at 30 ~ 70 °C for 5 ~ 60 min, disperse it in 10 ~ 100 mL deionized water, and transfer it to the reactor. Take the sample collected in step (2) having a mass of 0.03 to 1 times the mass of collagen, disperse in 30 to 150 mL deionized water for 20 to 90 minutes with ultrasound, and add into the collagen solution dropwise, In that invention, 0.01 to 10 g of glycerol is added, the mixture is stirred at normal temperature for 2 to 10 hour; the mixture is collected and dried at normal temperature in a mold; A new skin collagen aggregate-conductive polyaniline-carbon nanotube-glycerol humidity sensitive layer with a multi-layered structure and an internal three dimensional structure was obtained with a thickness of 0.1 ~ 1 mm. The conductive graphite was sprayed on the substrate using a spray gun with a humidity sensing film of 1.t imes.2 cm as the substrate to form a cross electrode. The spacing between adjacent electrodes is 1 ~ 5 mm, and the width of interdigital electrodes is 1 ~ 2 mm. (4) Taking 0.1 to 30 g of natural dermal collagen aggregate, slowly stirring at 30 to 70 °C for 5 to 60 minutes to disperse it in 10 to 100 mL deionized water, Transfer to the reactor; take the sample collected in the step (2) of 0.03 to 1 times the mass of collagen, disperse in 30 to 150 mL deionized water for 20 to 90 minutes with ultrasound, add into the collagen solution dropwise, Add 0.01 ~ 10 g of hydrophobic crosslinking agent, stir at room temperature for 2 ~ 10 h, and collect the sample. In that invention, 0.1 to 5 g of prepare mixture are uniformly spin coated on a base film, freeze dry, and formed under compression of 1 to 10 MPa, The pressure sensitive layer of a novel skin collagen aggregate - conductive polyaniline - carbon nanotube - hydrophobic crosslinking agent with multi-layered structure and internal three-dimensional structure was obtained.
[0027] Furthermore, natural skin collagen aggregates are derived from chromium-containing waste skin residues such as pigs, cattle and sheep in the leather industry.
[0028] Further, a novel skin collagen aggregate-conductive polyaniline-carbon nanotube-glycerol moisture sensitive layer having a multilayer structure and an internal three-dimensional structure, The optimum mass ratio is (0.1 ~ 30): (0.1 ~ 5): (0.1 ~ 5): (0.01 ~ 10).
[0029] Further, a pressure sensitive layer of a novel skin collagen aggregate-conductive polyaniline-carbon nanotube-hydrophobic crosslinking agent having a "thousand-layer structure" and an inner "three-dimensional structure," The optimum mass ratio is (0.1 ~ 30): (0.1 ~ 5): (0.1 ~ 5): (0.01 ~ ).
[0030] Compared with the prior art, the advantageous effects of the present invention are: (1) In comparison with the conventional synthetic materials, the present invention adopts collagen aggregates derived from chromium-containing waste skin slag to realize high-value resource reuse of wastes, The high precision piezoresistive sensor material based on collagen aggregate has more excellent biocompatibility and biodegradability than the synthetic material. (2) the present invention produces a novel multifunctional flexible sensor having a multilayer structure and an internal three-dimensional structure that is sensitive to humidity and pressure simultaneously. (3) The conductive matrix of the present invention is a polyaniline-acidified carbon nanotube composite material having a smaller electrical resistance, a higher mechanical strength and a greatly increased number of recyclable times compared to conventional conductive particles and conductive fibers. (4) the application fields of the present invention include artificial prostheses, intelligent robots, wearable sensors, and the like, and are more widely used.
[0031] FIG. 1 is a schematic structural diagram of a bionic multifunctional sensor according to the present invention.
[0032] FIG. 2 is an enlarged partial view of the bionic multifunction sensor of the present invention.
[0033] FIG. 3 shows the sensing mechanism of the multifunctional sensor according to the present invention after the force is applied.
[0034] FIG. 4 is a scanning electron microscope showing the cross sectional microstructure of the multifunction sensor of the present invention.
[0035] FIG. 5 is a deformation model of the multifunction sensor of the present invention under different stress conditions.
[0036] FIG. 6 is an output signal of the multifunction sensor of the present invention under different pressure conditions.
[0037] FIG. 7 is an output signal of the multifunction sensor of the present invention under different humidity conditions.
[0038] FIG. 8 is a schematic cross-sectional view of the bionic multifunction sensor of the present invention.
[0039] In the picture, A piezoelectric layer having a multi-layer structure, a 2-electrode, a 3-base layer, a conductive path having a higher potential in a 4-three-dimensional structure, a three-dimensional structure inside a 5-piezoelectric layer, Conductive paths with a lower potential in a 6 three-dimensional structure.
[0040] Preferred embodiments of the invention will now be described with reference to the accompanying drawings and non-limiting examples.
[0041] Referring to FIGS. 1-5 and FIG. 8, it is an object of the present invention to disclose a biomimetic multifunctional flexible sensor based on collagen aggregates. In contrast to that conventional sensor at present, it is characterized by dope natural dermal collagen aggregates with superior biocompatibility and three-dimensional network structure with excellent electrical conductivity. In addition, a sensor element material with high sensitivity to pressure and humidity is prepared by a specific processing method, and a piezoelectric layer multi-layer structure and an internal three dimensional network structure are constructed by assembling two materials, A new flexible multifunctional sensor sensitive to both pressure and humidity was successfully prepared. The multifunctional sensor has excellent biological characteristics and can be widely used in the fields of intelligent prosthesis, high-end robot, virtual reality and wearable sensor.
[0042] Referring to FIGS. 1, 2, and 8, the skin collagen aggregate based biomimetic multifunctional flexible sensor of the present invention includes three parts, namely, a piezoelectric layer 1, an electrode 2, and a base layer 3. Wherein the piezoelectric layer 1 is a mechanically sensitive layer having a multi-layer structure and an internal three-dimensional network structure. The piezoelectric layer 1 may be formed of a collagen aggregate having a resilient three-dimensional network structure as a matrix, and the collagen aggregate may be modified to have electrical conductivity.
[0043] Referring to FIGS. 2-4, the conductive paths in the piezoelectric layer 1 are mainly multi-layer contact and collagen fibers of an attached conductive substance in a three-dimensional network structure. In that normal state, the sheet contact in the piezoelectric lay 1 is small and the three-dimensional mesh structure 5 is in the natural extending state, and the numb of connection points of the conductive paths in the three-dimensional piezoelectric layer 1 is also stable, The conductive via 4 having a higher potential and the conductive via 6 having a lower potential are in a stable state, respectively.
[0044] When the piezoelectric layer 1 is subjected to the external force F, the multilayer contact (28 Pa < F < 20 KPa) and the three-dimensional network structure 5 are deformed (20 KPa < F < 100 KPa), so that the conductive paths in the structure contact each other, There are more connection points between the conductive paths. The contact between the conductive via 4 with a higher potential and the conductive via 6 with a lower potential results in a change in the potential of the mechanically sensitive layer, producing an electrical signal.
[0045] The mechanical sensitive material described in this embodiment may be a high-precision piezoresistive sensor material based on dermal collagen. This material can be prepared by adding the dispersion of polyaniline-acidified carbon nanotube composite conductive matrix material dropwise to the collagen solution, and then uniformly coating the surface of the humidity sensing material after stirring, and freeze drying.
[0046] The material is characterized in that natural collagen with three dimensional network structure is used as the matrix to improve the electrical conductivity of the material with polyaniline-acidified carbon nanotube composite conductive matrix dispersed in the matrix.
[0047] The base layer 3 is made of a humidity sensitive material. The requirement for the humidity sensitive material is that the material should have both electrical conductivity and hygroscopicity, and that when the humidity within the material changes, the electrical properties or potential within the humidity sensitive material changes to produce an electrical signal.
[0048] The humidity-sensitive material described in this embodiment differs from the mechanical-sensitive material mainly in that the humidity sensitive material should have a considerable hygroscopicity, and when the humidity changes, the moisture absorption in the material causes a change in electrical properties. And the mechanical sensitive material should change its electrical properties with the deformation of the material.
[0049] Therefore, the moisture sensitive material described in this example can be prepared by adding a dispersion of a polyaniline-acidified carbon nanotube composite conductive matrix material and a moisture absorbent (such as ethylene glycol, glycerin, etc.) dropwise to a collagen solution, After sufficient stirring, it was dried at room temperature to obtain a highly accurate humidity sensor material based on the collagen aggregate.
[0050] The obtained material is characterized in that natural skin collagen is used as the matrix to improve the electrical conductivity of the material with the polyaniline-acidified carbon nanotube composite conductive matrix dispersed in the matrix, And the hygroscopic properties of the product are influenced by the hygroscopicity of the hygroscopic agent incorporated in the conductive matrix.
[0051] Preferably, in order to avoid the influence of moisture absorption of the piezoelectric layer 1 on the accuracy of the humidity sensor of the base layer 3, the piezoelectric layer 1 can be subjected to a hydrophobic treatment. For example, hydrophobic segments, hydrophobic groups, and the like may be introduced into the mechanically sensitive material.
[0052] The electrode layer 2 is disposed between the mechanical sensitive layer and the humidity sensitive layer, and connects the mechanical sensitive layer and the humidity sensitive layer, respectively. The electrode selected for the electrode layer 2 is preferably an interdigital electrode.
[00531 Example 1 (1) Acidification of multi-walled carbon nanotubes: Multi-walled carbon nanotubes with mass of 0.2 g, 20 g and 0.02 g, concentrated sulfuric acid and concentrated nitric acid were placed in a reactor, ultrasonically dispersed for 20 min, The reflux was then stirred at 80°C for 2 h. Cool to normal temperature, dilute 300 mL of deionized water, centrifuge to supernatant liquid to neutral at 5000 x g rotation speed for several times. After filtration, freeze-dry for 10 hours to collect the lower precipitate, and prepare for use; (2) Placing 0.15 g of the sample collected in step (1) in 50 mL of deionized water, adding 0.3 g of aniline by mass and 4.44 g of sulfosalicylic acid by mass, ultrasonically dispersing for 20 min, transferring to the reactor.The reaction system was rapidly stirred at room temperature, and 1.58 g of ammonium persulfate oxidizing agent was mixed into 100 mL of deionized water, added dropwise to the reaction system, and the reaction was stirred at °C for 5 hours. Filter and wash with absolute ethanol and distilled water respectively, freeze-dry for 10 hours, collect samples, and put them into use; (3) Take 0.1 g of natural dermal collagen aggregate, slowly stir at 70°C. for min, disperse it in 1OmL of deionized water, and transfer to the reactor. The sample collected in step (2) having a mass of 0.1 g was dispersed in mL of deionized water by ultrasound for 20 min, and added dropwise to the collagen solution, Glycerol 0.01 g was added and stirred at room temperature for 2 h; the mixture was collected and dried at room temperature in a mold to obtain a humidity sensing film having a thickness of 0.1 mm. The conductive graphite was sprayed on the substrate using a spray gun with a humidity sensing film of 1.t imes.2 cm as the substrate to form a cross electrode. The spacing between adjacent electrodes was 1 mm, the width of the interdigital electrodes was 2 mm, (4) Taking 0.1 g of natural dermal collagen aggregate, slowly stirring at 70 °C for 5 min, and dispersing it in 10 mL of deionized water, Transfer to the reactor; take the sample collected in the step (2) of 0.03 to 1 times the mass of collagen, disperse the sample in 30 mL deionized water for 20 minutes, add into the collagen solution dropwise, Hydrophobic crosslink agent 0.01 g was added, stir at room temperature for 2 h, and sample was collected. The prepared mixture of 0.1 g was uniformly spin coated on the base film, freeze dried, and formed under 1 MPa compression.
[00541 Example 2 Acidification of multi-walled carbon nanotubes: Multi-walled carbon nanotubes with a mass of 1 g, 40 g and 10 g, concentrated sulfuric acid and concentrated nitric acid were placed in a reactor, ultrasonically dispersed for min, The reflux was then stirred at 65°C for 5 h. Cool to normal temperature, dilute 400 mL of deionized water, and centrifuge to supernatant liquid to neutral at a rotational speed of 9500 x g for several times. After filtration, freeze drying for 12 hours to collect the lower layer precipitate, and to be used; (2) Placing 0.5 g of the sample collected in step (1) in 80 mL of deionized water, adding 0.8 g of aniline by mass and 6.46 g of sulfosalicylic acid by mass, ultrasonically dispersing for 40 min, transferring to the reactor, The reaction system was rapidly stirred at room temperature, and 1.75 g of ammonium persulfate oxidizing agent was mixed into 80 mL of deionized water, added dropwise to the reaction system, and the reaction was stirred at 2.5 °C for 7 h. Filter and wash with absolute ethanol and distilled water respectively, freeze-dry for 12 hours, collect samples, and put them into use; (3) Taking 8 g of natural dermal collagen aggregate, slowly stirring at °C for 20 min, dispersing it in 30 mL deionized water, and transferring to the reactor. The sample collected in step (2) having a mass of 0.35 g was dispersed in 60 mL of deionized water by ultrasound for 40 min, and added dropwise to the collagen solution, Add 2 g of glycerol and stir at room temperature for 4 h; collect the mixed liquor and dry at room temperature in the mold to obtain a humidity sensing film with a thickness of 0.3 mm. The conductive graphite was sprayed on the substrate using a spray gun with a humidity sensing film of 1.t imes.2 cm as the substrate to form a cross electrode. The spacing between adjacent electrodes was 1.5 mm, the width of the interdigital electrode was 1.75 mm, (4) Taking 8 g of natural dermal collagen aggregate, slowly stirring at °C for 20 min, dispersing it in 30mL deionized water, transferring it to the reactor, taking the sample collected in step (2) of 0.5 times the mass of collagen, Ultrasonically dispersed in 60 mL deionized water for 40 min, added into collagen solution dropwise, added 2.5 g hydrophobic crosslinking agent, stirred at room temperature for 3.5 h, and collected samples. The 1.5 g prepared mixture was uniformly spin coated on the base film, freeze dried, and formed under 3 MPa compression.
[0055] Example 3 Acidification of multi-walled carbon nanotubes: Multi-walled carbon nanotubes with mass of 1.5 g, 75 g and 75 g, concentrated sulfuric acid and concentrated nitric acid were placed in a reactor, ultrasonically dispersed for min, The reflux was then stirred at 50°C. for 10 h. Cool to room temperature, dilute 500 mL of demonized water, and centrifuge to supernatant to neutral at 13500 x g for several times. After filtration, freeze drying for 15 hours to collect the lower layer precipitate, and prepare for use; (2) placing 1 g of the sample collected in step (1) in 120 mL of deionized water, adding 1 g of aniline by mass and 8.87 g of sulfosalicylic acid by mass, ultrasonically dispersing for 60 min, and transferring to a reactor, The reaction system was added dropwise to 60 mL of deionized water by rapid stirring at room temperature, and the reaction was stirred at 5
°C for 10 hours. Filter and wash with absolute ethanol and distilled water respectively, freeze-dry for 15 hours, collect samples, and put them into use; (3) 15 g of natural dermal collagen aggregates were slowly stirred at °C for 30 min, dispersed in 50 mL of deionized water, and transferred to the reactor. The sample collected in step (2) having a mass of 0.75 g was dispersed in 90 mL of deionized water by ultrasound for 60 min, and added dropwise to the collagen solution, The mixture was collected and dried at normal temperature in a mold to obtain a humidity sensing film with a thickness of 0.5 mm. The conductive graphite was sprayed on the substrate using a spray gun with a humidity sensing film of1.t imes.2cm as the substrate to form a cross electrode. The spacing between adjacent electrodes was 2.5 mm and the width of the interdigital electrodes was 1.5 mm. (4) Take 15 g of natural dermal collagen aggregates, slowly stirred at °C for 30 min, dispersed in 50 mL of deionized water and transferred to the reactor, and samples collected in step (2) of 0.75 times the mass of collagen were taken, Ultrasonically dispersed in 90 mL deionized water for min, added into collagen solution dropwise, added 5 g of hydrophobic crosslinking agent, stirred at room temperature for 5 h, and collected the sample. The 2.5 g prepared mixture was uniformly spin coated on the base film, freeze dried, and formed under 5 MPa compression.
[0056] It is necessary to note here that this embodiment is dedicated to the further description of the invention and is not to be construed as limiting the scope of the invention, Non-essential improvements and adjustments may be made by those skilled in the art in accordance with the above invention.
[0057] Although the invention has been described with reference to specific examples, it will be appreciated by those skilled in the art that the invention may be embodied in many other forms, in keeping with the broad principles and the spirit of the invention described herein.
[0058] The present invention and the described preferred embodiments specifically include at least one feature that is industrial applicable.
Claims (10)
1. A bio-mimetic multifunctional flexible sensor based on collagen aggregates comprising: a mechanically sensitive layer having a multi-layered structure and an internal three-dimensional network structure; a collagen aggregate having a three-dimensional network structure of resilience is used as a matrix, and the collagen aggregate is modified to have electrical conductivity, and when the mechanical sensitive layer is deformed, the sheet structure contact and the three dimensional network structure are deformed, thereby causing a change in the potential of the mechanical sensitive layer and generating an electric signal; wherein in a humidity-sensitive layer, the collagen aggregate is used as a matrix, and the collagen aggregate is modified to obtain both electrical conductivity and hygroscopicity; moisture absorption of the humidity-sensitive layer causes a change in electrical performance or potential of the humidity sensitive layer to generate an electrical signal; an electrode layer disposed between the mechanical sensitive layer and the humidity sensitive layer to connect the mechanical sensitive layer and the humidity sensitive layer, respectively.
2. The sensor according to claim 1 wherein the mechanically sensitive layer is a high precision piezoresistive sensor material based on dermal collagen.
3. The sensor according to claim 2, wherein the high-precision piezoresistive sensor material based on dermal collagen is subjected to hydrophobic treatment.
4. The sensor according to claim 1, wherein the moisture sensitive layer is based on a collagen aggregate, wherein the conductivity is obtained by dispersing polyaniline-acidified carbon nanotube composite conductive matrix in the matrix and modifying and enhancing the hygroscopicity of the composite conductive matrix.
5. The sensor according to claim 4, wherein the humidity-sensitive material used in the humidity-sensitive layer is obtained by adding polyaniline acidified carbon nanotube composite conductive matrix material and glycerin to the collagen aggregate solution, stirring sufficiently and drying, to obtain a highly accurate humidity sensor material based on collagen aggregates.
6. A high precision moisture sensor material based on collagen aggregate for use in the sensor according to any one of claims 1 to 5, wherein the moisture sensitive layer is based on the collagen aggregate; the conductivity is obtained by dispersing polyaniline-acidified carbon nanotube composite conductive matrix in the matrix and modifying and enhancing the hygroscopicity of the composite conductive matrix.
7. The humidity sensor material according to claim 6, wherein the sensor material is obtained by a method comprising the steps of adding polyaniline acidified carbon nanotube composite conductive matrix material and glycerin to a collagen aggregate solution; after sufficient stirring and drying, obtaining a high-precision humidity sensor material based on collagen aggregate; Collagen aggregate: Polyaniline: Acidified carbon nanotubes: the mass ratio of glycerol is (0.1 ~ 30): (0.1 ~ 5): (0.1 ~ 5): (0.01 ~ 10).
8. A method of preparing a biomimetic multifunctional flexible sensor based on collagen aggregate, comprising the steps of: collagen aggregate solution, polyaniline-acidified carbon nanotube composite conductive matrix material and glycerin are added, mixed uniformly and then dry to obtain a humidity sensitive layer; spraying conductive graphite on the surface of the humidity sensitive layer to obtain an electrode layer; adding polyaniline-acidified carbon nanotube composite conductive matrix material to the collagen aggregate solution to obtain a precursor solution of the mechanical sensitive material; the precursor solution of the mechanical sensitive material is constructed on the surface of the electrode layer, freeze-dried and press-formed, and the mechanical sensitive layer with three-dimensional network structure is obtained.
9. The preparation method, according to claim 8, wherein a hydrophobic cross-linking agent is also added to the precursor solution of the mechanically sensitive material, Collagen aggregate: Polyaniline: acidified carbon nanotubes: the mass ratio of hydrophobic crosslinking agent (KH570) is (0.1 ~ 30): (0.1 ~ ): (0.1 ~ 5): (0.01 ~ 10).
10. The preparation method according to claim 8, further comprising the steps of: (1) multi-wall carbon nanotube having a mas ratio of (0.1 ~ 1): (0.1 ~ 100): (0.1 ~ 100), concentrated sulfuric acid and concentrated nitric acid are placed in a reactor, Heat and refluxing at 35~80 DEG C for 2~20 h; cool to normal temperature; diluting with 300~1000 mL of demonized water; rotate speed of 5000 ~ 20000 x g, the upper layer liquid is centrifuge to neutral for several times; after filtration, the lower layer precipitate is collect by freeze drying for ~ 20 hours to obtain acidified carbon nanotubes;
(2) Placing 0.2 ~ 1.5 g of acidified carbon nanotubes in 50 ~ 200 mL demonized water, and 0.5 ~ 2 times the mass of aniline and 1 ~ 5 times the amount of aniline monomer were added to the acidified carbon nanotubes; ultrasonically disperse for 20-90 min, transfer to a reactor, stir rapidly at room temperature; mix 0.5~2 times the amount of aniline monomer ammonium persulfate oxidizing agent into 20~100 mL demonized water, add into the reaction system dropwise at 0 ~ 10 C, stir for 5 ~ 20 hours, filter and washing with absolute ethanol and
distilled water, freeze-drying for 10 ~ 20 hours, collect samples, and obtaining polyaniline-acidified carbon nanotube composite conductive matrix material; (3) Taking 0.1 ~ 30 g of natural dermal collagen aggregate, stir slowly at 30 ~ 70 °C for 5 ~ 60 min to disperse it in 10 ~ 100 mL demonized water, Transfer to the reactor; take the polyaniline-acidified carbon nanotube composite conductive matrix material of 0.03 ~ 1 times the mass of collagen, disperse in 30 ~ 150 mL demonized water for 20 ~ 90 minutes with ultrasound, add into the collagen solution dropwise, Add 0.01 ~ 10 g glycerol, stir at room temperature for 2 ~ 10 h, collect mixed liquor, dry at room temperature in mold, obtain humidity sensing film, thickness is 0.1 ~1mm; using a 1 cm x2 cm humidity sensing film as the substrate, the conductive graphite was sprayed on the substrate using a spray gun to form a cross electrode, the spacing between adjacent electrodes was 1 ~ 5 mm, and the width of the interdigital electrodes was 1 ~ 2 mm; (4) Take 0.1~30 g of natural dermal collagen aggregate, stir slowly at 30~70 °C for 5~60 min and disperse it in 10~100 mL demonized water; Transfer to the
reactor; take the polyaniline-acidified carbon nanotube composite conductive matrix material of 0.03 ~ 1 times the mass of collagen, disperse in 30 ~ 150 mL demonized water for 20 ~ 90 minutes with ultrasound, add into the collagen solution dropwise; add 0.01 ~ 10 g of hydrophobic crosslinking agent, stir at room temperature for 2 ~ 10 h; collect sample; spin coat 0.1 ~ 5 g of prepared mixture on base film uniformly, freeze dry, and form under 1 ~ 10 MPa compression.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| AU2020101386A AU2020101386A4 (en) | 2020-07-16 | 2020-07-16 | A Biomimetic multifunctional flexible sensor based on skin collagen aggregate and its manufacturing method |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| AU2020101386A AU2020101386A4 (en) | 2020-07-16 | 2020-07-16 | A Biomimetic multifunctional flexible sensor based on skin collagen aggregate and its manufacturing method |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| AU2020101386A4 true AU2020101386A4 (en) | 2020-08-20 |
Family
ID=72039806
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| AU2020101386A Ceased AU2020101386A4 (en) | 2020-07-16 | 2020-07-16 | A Biomimetic multifunctional flexible sensor based on skin collagen aggregate and its manufacturing method |
Country Status (1)
| Country | Link |
|---|---|
| AU (1) | AU2020101386A4 (en) |
Cited By (15)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112212898A (en) * | 2020-09-09 | 2021-01-12 | 山东科技大学 | Intelligent skin based on small-size distributed optical fiber sensing array |
| CN112812332A (en) * | 2021-02-07 | 2021-05-18 | 陕西科技大学 | Collagen fiber-based flexible pressure sensing material and preparation method thereof |
| CN113189171A (en) * | 2021-04-16 | 2021-07-30 | 哈尔滨理工大学 | Preparation method of gas sensor made of organic-inorganic hybrid composite material |
| CN113503914A (en) * | 2021-06-29 | 2021-10-15 | 西北工业大学 | Preparation method of flexible sensor |
| CN113896942A (en) * | 2021-10-28 | 2022-01-07 | 福州大学 | Air-permeable surface electrode and preparation method thereof |
| CN114002276A (en) * | 2021-08-25 | 2022-02-01 | 常州大学 | Resistance type humidity sensor based on carbon nano tube/titanium dioxide/polyethyleneimine composite membrane and preparation method thereof |
| CN114062443A (en) * | 2021-11-10 | 2022-02-18 | 北京印刷学院 | Flexible sensor for monitoring humidity of package headspace |
| CN114396868A (en) * | 2022-01-18 | 2022-04-26 | 陕西科技大学 | alpha-MWCNTs/MgAl-LDH/leather flexible wearable strain sensing material and preparation method thereof |
| CN114479468A (en) * | 2022-01-20 | 2022-05-13 | 苏州大学 | Preparation method of CNT/PDMS flexible composite material and capacitive pressure sensor |
| CN114754906A (en) * | 2022-03-18 | 2022-07-15 | 复旦大学 | Ultra-sensitive flexible pressure sensor inspired by biology and preparation method thereof |
| CN114810827A (en) * | 2022-04-18 | 2022-07-29 | 重庆邮电大学 | Magnetorheological rubber intelligent sliding bearing structure and manufacturing and control method thereof |
| CN114848909A (en) * | 2022-04-22 | 2022-08-05 | 四川大学 | Collagen aggregate scaffold material and preparation method thereof |
| CN115449101A (en) * | 2022-09-30 | 2022-12-09 | 广西大学 | High-conductivity and high-environmental-stability strain sensing film and preparation method thereof |
| CN116653372A (en) * | 2023-05-29 | 2023-08-29 | 东北电力大学 | Biopolymer artificial muscle and preparation method and application thereof |
| CN113465665B (en) * | 2021-06-29 | 2023-11-17 | 西北工业大学 | Preparation method of flexible integrated sensor |
-
2020
- 2020-07-16 AU AU2020101386A patent/AU2020101386A4/en not_active Ceased
Cited By (24)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112212898A (en) * | 2020-09-09 | 2021-01-12 | 山东科技大学 | Intelligent skin based on small-size distributed optical fiber sensing array |
| CN112812332A (en) * | 2021-02-07 | 2021-05-18 | 陕西科技大学 | Collagen fiber-based flexible pressure sensing material and preparation method thereof |
| CN113189171A (en) * | 2021-04-16 | 2021-07-30 | 哈尔滨理工大学 | Preparation method of gas sensor made of organic-inorganic hybrid composite material |
| CN113189171B (en) * | 2021-04-16 | 2023-09-08 | 哈尔滨理工大学 | Preparation method of gas sensor of organic-inorganic hybrid composite material |
| CN113503914A (en) * | 2021-06-29 | 2021-10-15 | 西北工业大学 | Preparation method of flexible sensor |
| CN113465665B (en) * | 2021-06-29 | 2023-11-17 | 西北工业大学 | Preparation method of flexible integrated sensor |
| CN113503914B (en) * | 2021-06-29 | 2023-11-17 | 西北工业大学 | Preparation method of flexible sensor |
| CN114002276A (en) * | 2021-08-25 | 2022-02-01 | 常州大学 | Resistance type humidity sensor based on carbon nano tube/titanium dioxide/polyethyleneimine composite membrane and preparation method thereof |
| CN113896942B (en) * | 2021-10-28 | 2023-01-03 | 福州大学 | Air-permeable surface electrode and preparation method thereof |
| CN113896942A (en) * | 2021-10-28 | 2022-01-07 | 福州大学 | Air-permeable surface electrode and preparation method thereof |
| CN114062443B (en) * | 2021-11-10 | 2023-10-03 | 北京印刷学院 | Flexible sensor for monitoring humidity of package headspace |
| CN114062443A (en) * | 2021-11-10 | 2022-02-18 | 北京印刷学院 | Flexible sensor for monitoring humidity of package headspace |
| CN114396868A (en) * | 2022-01-18 | 2022-04-26 | 陕西科技大学 | alpha-MWCNTs/MgAl-LDH/leather flexible wearable strain sensing material and preparation method thereof |
| CN114396868B (en) * | 2022-01-18 | 2023-06-16 | 陕西科技大学 | Flexible wearable strain sensing material of a-MWCNTs/MgAl-LDH/leather and preparation method thereof |
| CN114479468A (en) * | 2022-01-20 | 2022-05-13 | 苏州大学 | Preparation method of CNT/PDMS flexible composite material and capacitive pressure sensor |
| CN114754906B (en) * | 2022-03-18 | 2023-09-22 | 复旦大学 | Biosensing flexible pressure sensor and preparation method thereof |
| CN114754906A (en) * | 2022-03-18 | 2022-07-15 | 复旦大学 | Ultra-sensitive flexible pressure sensor inspired by biology and preparation method thereof |
| CN114810827B (en) * | 2022-04-18 | 2023-11-14 | 重庆邮电大学 | Magnetorheological rubber intelligent sliding bearing structure and manufacturing and control method thereof |
| CN114810827A (en) * | 2022-04-18 | 2022-07-29 | 重庆邮电大学 | Magnetorheological rubber intelligent sliding bearing structure and manufacturing and control method thereof |
| CN114848909A (en) * | 2022-04-22 | 2022-08-05 | 四川大学 | Collagen aggregate scaffold material and preparation method thereof |
| CN115449101B (en) * | 2022-09-30 | 2023-11-14 | 广西大学 | Strain sensing film with high conductivity and high environmental stability and preparation method thereof |
| CN115449101A (en) * | 2022-09-30 | 2022-12-09 | 广西大学 | High-conductivity and high-environmental-stability strain sensing film and preparation method thereof |
| CN116653372A (en) * | 2023-05-29 | 2023-08-29 | 东北电力大学 | Biopolymer artificial muscle and preparation method and application thereof |
| CN116653372B (en) * | 2023-05-29 | 2024-02-23 | 东北电力大学 | Biopolymer artificial muscle and preparation method and application thereof |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| AU2020101386A4 (en) | A Biomimetic multifunctional flexible sensor based on skin collagen aggregate and its manufacturing method | |
| CN111121870B (en) | Preparation method of bionic multifunctional flexible sensor based on collagen aggregate | |
| Fu et al. | Controlled assembly of MXene nanosheets as an electrode and active layer for high‐performance electronic skin | |
| Ren et al. | Flexible sensors based on organic–inorganic hybrid materials | |
| Li et al. | Superhydrophobic electrically conductive paper for ultrasensitive strain sensor with excellent anticorrosion and self-cleaning property | |
| Wang et al. | A novel bio-inspired multi-functional collagen aggregate based flexible sensor with multi-layer and internal 3D network structure | |
| Tan et al. | Flexible pressure sensors based on bionic microstructures: from plants to animals | |
| Duan et al. | Inspiration from daily goods: a low-cost, facilely fabricated, and environment-friendly strain sensor based on common carbon ink and elastic core-spun yarn | |
| Zhu et al. | Highly-stretchable porous thermoplastic polyurethane/carbon nanotubes composites as a multimodal sensor | |
| Xu et al. | Two-birds-one-stone: Flexible PANI film with bionic microstructures for multifunctional sensing of physical and chemical stimuli | |
| Pan et al. | Recent progress in development of wearable pressure sensors derived from biological materials | |
| Huang et al. | Recent advances in functional bacterial cellulose for wearable physical sensing applications | |
| CN110207866A (en) | A kind of highly sensitive pliable pressure sensor and preparation method thereof based on modified paper base | |
| CN108797099A (en) | A kind of composite and flexible conductive fabric, conductive fabric preparation method and its flexible sensor | |
| Du et al. | Electrospun elastic films containing AgNW-bridged MXene networks as capacitive electronic skins | |
| Liu et al. | High-performance piezoresistive flexible pressure sensor based on wrinkled microstructures prepared from discarded vinyl records and ultra-thin, transparent polyaniline films for human health monitoring | |
| Yu et al. | Multilayer Perceptron Algorithm-Assisted Flexible Piezoresistive PDMS/Chitosan/cMWCNT Sponge Pressure Sensor for Sedentary Healthcare Monitoring | |
| Luo et al. | Highly sensitive, wide-pressure and low-frequency characterized pressure sensor based on piezoresistive-piezoelectric coupling effects in porous wood | |
| Xu et al. | Skin-friendly corrugated multilayer microspherical sensor fabricated with silk fibroin, poly (lactic-co-glycolic acid), polyaniline, and kappa-carrageenan for wide range pressure detection | |
| Li et al. | Macromolecule relaxation directed 3D nanofiber architecture in stretchable fibrous mats for wearable multifunctional sensors | |
| Ge et al. | Intrinsically conductive bifunctional nanocellulose-reinforced robust and self-healable electronic skin: deep insights into multiple bonding network, property reinforcement, and sensing mechanism | |
| Wang et al. | Development of high-sensitivity piezoresistive sensors based on highly breathable spacer fabric with TPU/PPy/PDA coating | |
| Guo et al. | AP (VDF-TrFE) nanofiber composites based multilayer structured dual-functional flexible sensor for advanced pressure-humidity sensing | |
| Guo et al. | Recent advances in electronic skins with multiple-stimuli-responsive and self-healing abilities | |
| Seesaard et al. | Fabric-based piezoresistive Ti3AlC2/PEDOT: PSS force sensor for wearable E-textile applications |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| FGI | Letters patent sealed or granted (innovation patent) | ||
| MK22 | Patent ceased section 143a(d), or expired - non payment of renewal fee or expiry |