Continuous gradient ion hydrogel as well as preparation method and application thereof

Abstract

The invention discloses continuous gradient ion hydrogel as well as a preparation method and application thereof. The preparation method comprises the following steps: respectively preparing a pre-polymerization solution A and a pre-polymerization solution B; measuring a certain volume of the pre-polymerization solution A, putting the pre-polymerization solution A into a mold, and carrying out free radical polymerization for 10-20 minutes under a preset condition; and slowly injecting an isometric pre-polymerization solution B, and synchronously polymerizing with the pre-polymerization solution A for 30-60 minutes under a preset condition to obtain the continuous gradient ionized water gel. The ionized water gel with the modulus gradient structure is constructed through a simple pre-polymerization liquid pouring method and different interactions between phytic acid and different high polymers, the ionized water gel has excellent mechanical performance and stability, the preparation method is simple, and operation is controllable.

Description

Technical Field

[0001] The invention belongs to the technical field of pressure sensing materials, and in particular relates to a continuous gradient ion hydrogel and a preparation method and application thereof. Background Art

[0002] As an important advanced sensor technology, flexible pressure sensors have broad application prospects. Due to their excellent flexibility and plasticity, they can adapt to various curved surfaces, especially playing a key role in wearable devices, which can monitor the user's physiological parameters in real time and promote the development of personalized health management.

[0003] Interfacial supercapacitor sensing or interfacial ion-electron sensing, as a new type of pressure sensing technology, has received widespread attention. This technology achieves ultra-high unit area capacitance (UAC) by constructing a special interfacial electric double layer (EDL) structure at the ion-electron interface. This significantly enhanced UAC not only improves the overall sensitivity of the device, but also reduces parasitic effects on the transmission line, minimizes electromagnetic interference, and fundamentally solves the main technical challenges faced by traditional parallel plate capacitance sensing methods. This breakthrough in sensing technology has greatly promoted the development of flexible pressure sensors.

[0004] In recent years, ionic hydrogels have become ideal materials for constructing the dielectric layer of EDL due to their high ionic conductivity, simple preparation method, high stability, and adjustable structural and mechanical properties. It is worth noting that the elastic modulus E (hardness) of ionic hydrogels plays a key role in regulating the pressure sensing performance. Hydrogels with lower E values ​​can show higher sensitivity in the low pressure range (<10kPa). However, the low E value also limits the response range because the softer hydrogels will quickly saturate and deform when under pressure. Therefore, the uniform structure of ionic hydrogels makes it difficult to achieve high sensing sensitivity and a wide sensing range at the same time, which greatly limits the development of hydrogel pressure sensors.

[0005] Therefore, there is an urgent need in the art for a simple and reliable method to construct hydrogel materials with continuous gradient structural changes to prepare pressure sensors with high sensitivity and a wide sensing range. Summary of the invention

[0006] The purpose of this section is to summarize some aspects of embodiments of the present invention and briefly introduce some preferred embodiments. Some simplifications or omissions may be made in this section and the specification abstract and the invention title of this application to avoid blurring the purpose of this section, the specification abstract and the invention title, and such simplifications or omissions cannot be used to limit the scope of the present invention.

[0007] In view of the above problems and / or the problems existing in the prior art, the present invention is proposed.

[0008] Therefore, the purpose of the present invention is to overcome the deficiencies in the prior art and provide a method for preparing a continuous gradient ion hydrogel.

[0009] In order to solve the above technical problems, the present invention provides the following technical solutions: a method for preparing a continuous gradient ion hydrogel, comprising:

[0010] Prepare prepolymer liquid A and prepolymer liquid B respectively;

[0011] Take a certain volume of prepolymer liquid A, put it in the mold, and perform free radical polymerization for 10-20 minutes under the preset conditions;

[0012] An equal volume of prepolymer solution B was slowly injected, and under preset conditions, it was polymerized synchronously with prepolymer solution A for 30-60 minutes to obtain a continuous gradient ion hydrogel.

[0013] As a preferred embodiment of the preparation method of the present invention, the prepolymer solution A comprises acrylic acid, phytic acid, an initiator, a cross-linking agent and water;

[0014] Wherein, the concentration of acrylic acid in the prepolymer solution A is 2.5 mol / L to 5 mol / L;

[0015] The concentration of the phytic acid in the prepolymer solution A is 0.3-0.4 mol / L;

[0016] The concentration of the initiator in the prepolymer solution A is 0.05-0.4 mol% of the molar amount of acrylic acid;

[0017] The concentration of the crosslinking agent in the prepolymer solution A is 0.05-0.2 mol % of the molar amount of acrylic acid.

[0018] As a preferred embodiment of the preparation method of the present invention, the prepolymer solution B comprises acrylamide, phytic acid, an initiator, a cross-linking agent and water;

[0019] The concentration of acrylamide in the prepolymer solution B is 2.5 mol / L to 5 mol / L;

[0020] The concentration of the phytic acid in the prepolymer solution B is 0.3-0.4 mol / L;

[0021] The concentration of the initiator in the prepolymer solution B is 0.05-0.4 mol% of the molar amount of acrylamide;

[0022] The concentration of the cross-linking agent in the prepolymer solution B is 0.05-0.2 mol % of the molar amount of acrylamide.

[0023] As a preferred embodiment of the preparation method of the present invention, the initiator comprises a free radical polymerization initiator selected from at least one of ammonium persulfate, potassium persulfate and 2-hydroxy-2-methyl-1-phenyl-1-propanone.

[0024] As a preferred embodiment of the preparation method of the present invention, the cross-linking agent comprises a cross-linking agent having a double bond at the terminal group, which is selected from at least one of polyethylene glycol diacrylate and N,N'-methylenebisacrylamide.

[0025] As a preferred embodiment of the preparation method of the present invention, the volume ratio of the prepolymer liquid A to the prepolymer liquid B is 1:1.

[0026] Another object of the present invention is to overcome the deficiencies in the prior art and provide a continuous gradient ion hydrogel prepared by a method for preparing a continuous gradient ion hydrogel.

[0027] Another object of the present invention is to overcome the deficiencies in the prior art and provide an application of a continuous gradient ion hydrogel in the preparation of a pressure sensor, wherein: the pressure sensor comprises a wire, a conductive cloth and a conductive medium fixed between two layers of conductive cloth;

[0028] The conductive medium is a continuous gradient ion hydrogel.

[0029] As a preferred solution of the application of the present invention, the sensitivity of the pressure sensor is 9.00 kPa. -1 (<15kPa), 2.32kPa -1 (15~150kPa), 1.12kPa -1 (150~400kPa) and 0.56kPa -1 (400~1200kPa);

[0030] The sensing range of the pressure sensor is 1Pa-1200kPa, and the response time is less than or equal to 12.5ms;

[0031] The pressure sensor senses sound waves in a frequency range of 100 to 6000 Hz and an intensity range of 70 to 100 dB;

[0032] The sensor can respond to airflows of different speeds and angles, and the lowest wind speed it can sense is 0.2m / s;

[0033] The sensor can realize high-pressure foot pressure pedaling, and has continuous and stable response to foot pedaling of different degrees and frequencies.

[0034] Beneficial effects of the present invention:

[0035] (1) The present invention uses a simple prepolymer casting method to construct an ionic hydrogel with a modulus gradient structure through different interactions between phytic acid and different polymers. The ionic hydrogel has excellent mechanical properties and stability, and the preparation method is simple and the operation is controllable.

[0036] (2) The gradient structure of the ion gel provided by the present invention is composed of the plasticizing effect and phase separation effect of phytic acid on polyacrylic acid and polyacrylamide hydrogels. The plasticizing effect weakens the mechanical properties of the hydrogel, and the phase separation effect enhances the mechanical properties of the hydrogel. During the preparation process, acrylamide penetrates from top to bottom, forming a gradual change from plasticizing to phase separation, and finally forming a gradient modulus structure.

[0037] (3) The gradient ion hydrogel pressure sensor provided by the present invention simultaneously achieves high sensitivity and a wide pressure detection range, as well as excellent low-pressure detection performance. It can successively realize extremely low-pressure vibrations caused by sound and airflow, pressure changes caused by pulse and muscle vibration, and high-pressure changes in the sole of the foot. Thanks to the addition of phytic acid, the sensor also has excellent antibacterial properties and biocompatibility, and has application potential in various flexible electronics fields. BRIEF DESCRIPTION OF THE DRAWINGS

[0038] In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the following briefly introduces the drawings required for describing the embodiments. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative labor. Among them:

[0039] Figure 1 Schematic diagram of the preparation of the hydrogel in the embodiment of the present invention.

[0040] Figure 2 The compression performance curves of the hydrogels of Example 1 and Comparative Examples 1 and 2 of the present invention are shown.

[0041] Figure 3 Schematic diagram of the preparation of the pressure sensor in Example 1 of the present invention.

[0042] Figure 4 Graph showing relative capacitance change (ΔC / C0) and pressure sensitivity (S) of the hydrogel of Example 1 of the present invention under compressive stress of 0-1.2 MPa.

[0043] Figure 5 This is a cyclic sensing stability diagram of the hydrogel of Example 1 of the present invention under a compressive strain of 15%.

[0044] Figure 6 This is a diagram showing the response of the pressure sensor of Example 1 of the present invention to acoustic waves of different frequencies.

[0045] Figure 7 This is a diagram showing the response of the pressure sensor of Example 1 of the present invention to sound waves of different intensities.

[0046] Figure 8 This is a diagram showing the sound responses of the pressure sensor of Example 1 of the present invention to different English words.

[0047] Fig. 9 Graphs showing multiple responses of the pressure sensor of Example 1 of the present invention to continuous sound.

[0048] Fig.10 This is a diagram showing the response of the pressure sensor of Example 1 of the present invention to airflows of different speeds and directions.

[0049] Fig.11 This is a diagram showing the response of the pressure sensor of Example 1 of the present invention to pulse beats.

[0050] Fig.12 This is a pressure response diagram of the pressure sensor of Example 1 of the present invention to the vibration of the neck muscles during speaking, coughing and swallowing.

[0051] Fig.13 This is a pressure response diagram of the pressure sensor of Example 1 of the present invention to finger pressing with different pressures.

[0052] Fig.14 This is a pressure response diagram of the pressure sensor of Example 1 of the present invention to foot stepping at different degrees and frequencies. DETAILED DESCRIPTION

[0053] In order to make the above-mentioned objects, features and advantages of the present invention more obvious and easy to understand, the specific implementation methods of the present invention are described in detail below in conjunction with the embodiments of the specification.

[0054] In the following description, many specific details are set forth to facilitate a full understanding of the present invention, but the present invention may also be implemented in other ways different from those described herein, and those skilled in the art may make similar generalizations without violating the connotation of the present invention. Therefore, the present invention is not limited to the specific embodiments disclosed below.

[0055] Secondly, the term "one embodiment" or "embodiment" as used herein refers to a specific feature, structure, or characteristic that may be included in at least one implementation of the present invention. The term "in one embodiment" that appears in different places in this specification does not necessarily refer to the same embodiment, nor does it refer to a separate or selective embodiment that is mutually exclusive with other embodiments.

[0056] Example 1

[0057] (1) dissolving acrylic acid (5 mol / L) and phytic acid (0.4 mol / L) in deionized water and mixing well to obtain a precursor solution A;

[0058] (2) dissolving acrylamide (5 mol / L) and phytic acid (0.4 mol / L) in deionized water and mixing well to obtain a precursor solution B;

[0059] (3) treating the precursor solution with ultrasound for 10 min to remove bubbles;

[0060] (4) adding an initiator 2-hydroxy-2-methyl-1-phenyl-1-propanone (0.3 mol %) and a crosslinking agent polyethylene glycol diacrylate (0.1 mol %) to the above solution and stirring until completely dissolved to obtain prepolymer solutions A and B;

[0061] (5) 400 μL of prepolymer solution A was placed in a transparent cylindrical mold with an inner diameter of 13 mm and irradiated with an ultraviolet lamp with a wavelength of 365 nm for 20 min to increase the viscosity of the prepolymer solution.

[0062] (6) Then, 400 μL of prepolymer solution B was slowly injected and synchronously polymerized under ultraviolet light for 30 min to obtain a continuous modulus gradient ionic hydrogel.

[0063] The hydrogel preparation method is as follows Figure 1 shown.

[0064] The universal testing machine test shows that when the hydrogel of this embodiment reaches 80% compressive strain, the compressive stress is 1.20 MPa. Figure 2 shown.

[0065] The hydrogel was used as a cylindrical conductive medium with a diameter of 13 mm and a height of 4 mm, sandwiched between two pieces of commercial conductive carbon cloth produced by Taiwan Carbon Energy Technology Co., Ltd. to construct an interfacial dual-capacitive pressure sensor. Figure 3 .

[0066] During the experiment, an LCR digital bridge (TH2830, Tonghui) was used to monitor the change in capacitance of the hydrogel during compression on a universal testing machine at a frequency of 1 kHz and a voltage of 1 V. The sensitivity S was calculated using the formula:

[0067] S=δ(ΔC / C0) / δP

[0068] Where: ΔC is the capacitance change, C0 is the initial capacitance when no pressure is applied, and P is the applied pressure.

[0069] After testing, the sensitivity of the pressure sensor is 9.00kPa -1 (<15kPa), 2.32kPa -1 (15~150kPa), 1.12kPa-1 (150~400kPa) and 0.56kPa -1 (400~1200kPa), pressure sensing range is 1Pa~1200kPa, response time is less than or equal to 12.5ms, see Figure 4 .

[0070] At the same time, 100 compression loading and unloading cycles with 20% strain were applied to the hydrogel. Through the LCR digital bridge, it was found that the hydrogel could maintain a continuous and stable capacitance change signal during the test, showing excellent strain sensing fatigue resistance. Figure 5 .

[0071] The pressure sensor exhibits excellent low-pressure sensitivity and can respond to sounds of different intensities and frequencies to varying degrees. The MAP sensor is suspended and fixed, and the PAM end is placed near the sound source or air source. For sound wave detection, a professional auditory signal processor (RZ6, TDT) emits various sound waves with determined frequencies and amplitudes, and the LCR digital bridge records the capacitance signal changes of the sensor.

[0072] It can be found that the frequency range of the MAP sensor's detection of sound waves is 100 to 6000 Hz, and the intensity range is 70 to 100 dB. Figure 6 , 7.

[0073] Furthermore, when the instrument emits different sounds, such as the English words "apple", "banana", "blueberry", "science and technology" and "pressure sensing", the sensor exhibits different response curves, see Figure 8 For continuous human voice, the sensor has good response specificity and repeatability, see Fig. 9 .

[0074] Furthermore, for airflow detection, air of different flow speeds and directions is applied to the sensor through a spray gun, and the LCR digital bridge records the capacitance signal changes caused thereby. The sensor can respond to airflows of different speeds and angles, and the lowest wind speed that can be sensed is 0.2m / s, see Fig.10 .

[0075] The sensor can also achieve sensitive response to moderate pressure changes. During the test, the hydrogel was adhered to the wrist, neck, and fingers of the volunteers, and an LCR meter was used to record the changes in the capacitance of the hydrogel sensor during body movement.

[0076] It can be found that the MAP sensor can realize the pulse of the human body ( Fig.11), neck muscle vibrations caused by talking, coughing, and swallowing ( Fig.12 ) and different degrees of finger pressure ( Fig.13 ) for accurate response.

[0077] Furthermore, the sensor can also respond to higher pressure. The hydrogel was attached to the sole of the volunteer's foot, and an LCR meter was used to record the change in the capacitance of the hydrogel sensor during continuous stepping. The sensor has a continuous response capability to different frequencies and degrees of continuous stepping on the sole of the human foot, see Fig.14 .

[0078] Example 2

[0079] (1) dissolving acrylic acid (5 mol / L) and phytic acid (0.4 mol / L) in deionized water and mixing well to obtain a precursor solution A;

[0080] (2) dissolving acrylamide (5 mol / L) and phytic acid (0.4 mol / L) in deionized water and mixing well to obtain a precursor solution B;

[0081] (3) treating the precursor solution with ultrasound for 10 min to remove bubbles;

[0082] (4) adding an initiator 2-hydroxy-2-methyl-1-phenyl-1-propanone (0.3 mol %) and a crosslinking agent polyethylene glycol diacrylate (0.1 mol %) to the above solution and stirring until completely dissolved to obtain prepolymer solutions A and B;

[0083] (5) 600 μL of prepolymer solution A was placed in a transparent cylindrical mold with an inner diameter of 13 mm and irradiated with an ultraviolet lamp with a wavelength of 365 nm for 20 min to increase the viscosity of the prepolymer solution.

[0084] (6) Then, 200 μL of prepolymer solution B was slowly injected and synchronously polymerized for 30 min under ultraviolet light to obtain a continuous modulus gradient ionic hydrogel.

[0085] According to the test of the universal testing machine, when the hydrogel of this embodiment reaches 80% compression strain, the compression stress is 4.72 MPa.

[0086] The hydrogel was used as a conductive medium and sandwiched between two pieces of commercial conductive carbon cloth to construct an interfacial dual-capacitance pressure sensor.

[0087] Further experiments found that the sensitivity of the pressure sensor was 2.95 kPa. -1 (<150kPa), 1.72kPa -1 (150~1200kPa), 0.72kPa -1(120~4700kPa), the pressure sensing range is 1Pa~4700kPa.

[0088] Example 3

[0089] (1) dissolving acrylic acid (5 mol / L) and phytic acid (0.4 mol / L) in deionized water and mixing well to obtain a precursor solution A;

[0090] (2) dissolving acrylamide (5 mol / L) and phytic acid (0.4 mol / L) in deionized water and mixing well to obtain a precursor solution B;

[0091] (3) treating the precursor solution with ultrasound for 10 min to remove bubbles;

[0092] (4) adding an initiator 2-hydroxy-2-methyl-1-phenyl-1-propanone (0.3 mol %) and a crosslinking agent polyethylene glycol diacrylate (0.1 mol %) to the above solution and stirring until completely dissolved to obtain prepolymer solutions A and B;

[0093] (5) 200 μL of prepolymer solution A was placed in a transparent cylindrical mold with an inner diameter of 13 mm and irradiated with an ultraviolet lamp with a wavelength of 365 nm for 20 min to increase the viscosity of the prepolymer solution.

[0094] (6) Then, 400 μL of prepolymer solution B was slowly injected and synchronously polymerized under ultraviolet light for 30 min to obtain a continuous modulus gradient ionic hydrogel.

[0095] According to the test of the universal testing machine, when the hydrogel of this embodiment reaches 80% compression strain, the compression stress is 650 kPa.

[0096] The hydrogel was used as a conductive medium and sandwiched between two pieces of commercial conductive carbon cloth to construct an interfacial dual-capacitance pressure sensor.

[0097] Further experiments found that the sensitivity of the pressure sensor was 10.31 kPa. -1 (<50kPa), 8.42kPa -1 (50~250kPa), 5.22kPa -1 (250~650kPa), the pressure sensing range is 1Pa~650kPa.

[0098] Comparative Example 1

[0099] (1) dissolving acrylic acid (5 mol / L) and phytic acid (0.4 mol / L) in deionized water and mixing well to obtain a precursor solution A;

[0100] (2) treating the precursor solution with ultrasound for 10 min to remove bubbles;

[0101] (3) adding an initiator 2-hydroxy-2-methyl-1-phenyl-1-propanone (0.3 mol %) and a crosslinking agent polyethylene glycol diacrylate (0.1 mol %) to the above solution and stirring until completely dissolved to obtain a prepolymer solution A;

[0102] (4) 800 μL of prepolymer solution A was placed in a transparent cylindrical mold with an inner diameter of 13 mm and irradiated with a UV lamp with a wavelength of 365 nm for 50 min to obtain a homogeneous PAA / PA ion hydrogel.

[0103] Through the test of the universal testing machine, when the hydrogel of this comparative example reaches 80% compression strain, the compression stress is 7.21 MPa.

[0104] The hydrogel was used as a conductive medium and sandwiched between two pieces of commercial conductive carbon cloth to construct an interfacial dual-capacitance pressure sensor.

[0105] Further experiments found that the sensitivity of the pressure sensor was 2.52 kPa. -1 (<150kPa), 0.72kPa -1 (150~1200kPa), 0.22kPa -1 (120~4500kPa), 0.05(4500~7200kPa), the pressure sensing range is 1Pa~7200kPa.

[0106] Comparative Example 2

[0107] (1) dissolving acrylamide (5 mol / L) and phytic acid (0.4 mol / L) in deionized water and mixing well to obtain a precursor solution B;

[0108] (2) treating the precursor solution with ultrasound for 10 min to remove bubbles;

[0109] (3) adding an initiator 2-hydroxy-2-methyl-1-phenyl-1-propanone (0.3 mol %) and a crosslinking agent polyethylene glycol diacrylate (0.1 mol %) to the above solution and stirring until completely dissolved to obtain a prepolymer solution B;

[0110] (4) 800 μL of prepolymer solution A was placed in a transparent cylindrical mold with an inner diameter of 13 mm and irradiated with a UV lamp with a wavelength of 365 nm for 50 min to obtain a homogeneous PAM / PA ion hydrogel.

[0111] Through the test of the universal testing machine, when the hydrogel of this comparative example reaches 80% compression strain, the compression stress is 301.47 kPa.

[0112] The hydrogel was used as a conductive medium and sandwiched between two pieces of commercial conductive carbon cloth to construct an interfacial dual-capacitance pressure sensor.

[0113] Further experiments found that the sensitivity of the pressure sensor was 11.15 kPa. -1 (<150kPa), 9.64kPa -1 (150~300kPa), the pressure sensing range is 1Pa~300kPa.

[0114] It should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention rather than to limit it. Although the present invention has been described in detail with reference to the preferred embodiments, those skilled in the art should understand that the technical solutions of the present invention can be modified or replaced by equivalents without departing from the spirit and scope of the technical solutions of the present invention, which should all be included in the scope of the present invention.

Claims

1. A method for preparing a continuous gradient ion hydrogel, characterized in that: include, Prepare prepolymer liquid A and prepolymer liquid B respectively; Take a certain volume of prepolymer liquid A, put it in the mold, and perform free radical polymerization for 10-20 minutes under the preset conditions; An equal volume of prepolymer solution B was slowly injected, and under preset conditions, it was polymerized synchronously with prepolymer solution A for 30-60 minutes to obtain a continuous gradient ion hydrogel.

2. The preparation method according to claim 1, characterized in that: The prepolymer solution A comprises acrylic acid, phytic acid, an initiator, a crosslinking agent and water; Wherein, the concentration of acrylic acid in the prepolymer solution A is 2.5 mol / L to 5 mol / L; The concentration of the phytic acid in the prepolymer solution A is 0.3-0.4 mol / L; The concentration of the initiator in the prepolymer solution A is 0.05-0.4 mol% of the molar amount of acrylic acid; The concentration of the crosslinking agent in the prepolymer solution A is 0.05-0.2 mol % of the molar amount of acrylic acid.

3. The preparation method according to claim 1 or 2, characterized in that: The prepolymer solution B comprises acrylamide, phytic acid, an initiator, a cross-linking agent and water; The concentration of acrylamide in the prepolymer solution B is 2.5 mol / L to 5 mol / L; The concentration of the phytic acid in the prepolymer solution B is 0.3-0.4 mol / L; The concentration of the initiator in the prepolymer solution B is 0.05-0.4 mol% of the molar amount of acrylamide; The concentration of the cross-linking agent in the prepolymer solution B is 0.05-0.2 mol % of the molar amount of acrylamide.

4. The preparation method according to claim 3, characterized in that: The initiator comprises a free radical polymerization initiator selected from at least one of ammonium persulfate, potassium persulfate and 2-hydroxy-2-methyl-1-phenyl-1-propanone.

5. The preparation method according to claim 4, characterized in that: The cross-linking agent includes a cross-linking agent with a double bond at the terminal group, and is selected from at least one of polyethylene glycol diacrylate and N,N'-methylenebisacrylamide.

6. The preparation method according to any one of claims 1, 2, 4 or 5, characterized in that: The volume ratio of the prepolymer liquid A to the prepolymer liquid B is 1:

1.

7. The continuous gradient ion hydrogel prepared by the preparation method according to any one of claims 1 to 6.

8. Use of the continuous gradient ion hydrogel as claimed in claim 7 in preparing a pressure sensor.

9. The use according to claim 8, characterized in that: The pressure sensor comprises a wire, a conductive cloth and a conductive medium fixed between two layers of conductive cloth; The conductive medium is a continuous gradient ion hydrogel.

10. The use according to claim 8 or 9, characterized in that: The sensitivity of the pressure sensor is 9.00 kPa. -1 (<15kPa), 2.32kPa -1 (15~150kPa), 1.12kPa -1 (150~400kPa) and 0.56kPa -1 (400~1200kPa); The sensing range of the pressure sensor is 1Pa-1200kPa, and the response time is less than or equal to 12.5ms; The pressure sensor senses sound waves in a frequency range of 100 to 6000 Hz and an intensity range of 70 to 100 dB; The sensor can respond to airflows of different speeds and angles, and the lowest wind speed it can sense is 0.2m / s; The sensor can realize high-pressure foot pressure pedaling, and has continuous and stable response to foot pedaling of different degrees and frequencies.

Images