Human Motion State Recognition Based on Flexible, Wearable Capacitive Pressure Sensors

Human motion state recognition technology based on flexible, wearable sensor devices has been widely applied in the fields of human–computer interaction and health monitoring. In this study, a new type of flexible capacitive pressure sensor is designed and applied to the recognition of human motion state. The electrode layers use multi-walled carbon nanotubes (MWCNTs) as conductive materials, and polydimethylsiloxane (PDMS) with microstructures is embedded in the surface as a flexible substrate. A composite film of barium titanate (BaTiO3) with a high dielectric constant and low dielectric loss and PDMS is used as the intermediate dielectric layer. The sensor has the advantages of high sensitivity (2.39 kPa−1), wide pressure range (0–120 kPa), low pressure resolution (6.8 Pa), fast response time (16 ms), fast recovery time (8 ms), lower hysteresis, and stability. The human body motion state recognition system is designed based on a multi-layer back propagation neural network, which can collect, process, and recognize the sensor signals of different motion states (sitting, standing, walking, and running). The results indicate that the overall recognition rate of the system for the human motion state reaches 94%. This proves the feasibility of the human motion state recognition system based on the flexible wearable sensor. Furthermore, the system has high application potential in the field of wearable motion detection.


Introduction
Human motion state recognition technology has been widely applied in different fields such as medical treatment [1,2], human-computer interaction [3,4], and home life [5,6]. The current research regarding human motion detection can typically be divided into two modes. The first mode is the human motion state recognition based on video and image processing technology. For example, Ma et al. [7] of Nanjing University of Posts and Telecommunications proposed an architecture of time-varying long short-term memory recurrent neural networks (TV-LSTMs) for human action recognition, which adopted convolutional neural networks (CNNs) as the feature generator, and obtained good recognition results. Bilen et al. [8] of the University of Edinburgh combined motion pictures and dynamic optical flow with CNNs and summarized the video as an image, which can realize end-to-end video action recognition. Although this vision-based recognition mode has the advantages of strong real-time performance, simple data acquisition, and good continuity, most of the studies focus on algorithm design with a long system development cycle. In addition, slight human movements are difficult to capture using hardware such as cameras. Natural factors such as ambient lighting and object occlusion can also affect the recognition effect to a certain extent. Moreover, the range of human movement is limited by the position of the camera, which can easily invade personal privacy. The second mode is the human motion state recognition based on wearable devices. For instance, Chamroukhi et al. [9] of the University of Toulon in France used an MTx-Xbus inertial where ε 0 is the vacuum dielectric constant, ε r is the relative dielectric constant of the dielectric layer, A is the relative area of the two electrode layers, and d is the distance between the two electrode layers. Among them, variable parameters A, d, and ε r affect the sensing performance such as sensitivity of the sensor. The sensitivity of a capacitive pressure sensor is as follows [25]: where S is the sensor sensitivity, C is the capacitance value output by the sensor after pressure is applied, C 0 is the initial capacitance value of the sensor, and P is the change in pressure received by the sensor. Substituting Equation (1) into Equation (2), we can obtain where ε r0 , A 0 , and d 0 , respectively, represent the relative dielectric constant of the dielectric layer, the relative area of the electrode plates, and the distance between the two electrodes in the initial state of the sensor; ε r , A, and d, respectively, represent the corresponding parameters when pressure, P, is applied to the sensor. As shown in Equation (3), to increase the sensitivity of the sensor, under the same pressure applied, ε r and A must be maximized as much as possible and d must be reduced. Currently, the main method to improve the performance of capacitive sensors is to construct microstructures in the dielectric layer and the electrode layer. For example, Bao et al. [26] from Stanford University proposed a dielectric layer integrated with a pyramid-shaped microstructure. The capacitive flexible pressure sensor composed of this dielectric layer had a sensitivity of 0.55 kPa −1 in a pressure range of 0-0.2 kPa. The pressure detection limit was as low as 3 Pa, and the response time was less than 1 s. Furthermore, Wei Li et al. [27] from Tiangong University proposed a flexible capacitive pressure sensor based on a polydimethylsiloxane (PDMS) dielectric layer with air gaps and high porosity. The sensor had an excellent sensitivity of 1.15 kPa −1 (<1 kPa) in a pressure detection range of 0-5 MPa. However, the volume of the sensor based on the foam structure was relatively large, and the wearability of the human motion detection was poor. Zian Zhang et al. [28] from Sun Yat-sen University reported a flexible, interlayered capacitive pressure sensor with micro-cone array electrodes and a porous medium layer. The sensor had high sensitivity (2.51 kPa −1 ), fast response time (84 ms), and a wide working range (>10 kPa). Clearly, further improvement of the performance of capacitive sensors can be realized by both constructing a microstructure in the electrode layer and improving the dielectric constant. Based on the above discussion, the following strategies are adopted in this study to improve the performance of sensors: using a low-cost sandpaper mold, the micro structure is fabricated on the surface of the sensor electrode. The BaTiO 3 with high dielectric constant and low dielectric loss is doped into PDMS as filler, and the dielectric constant of the dielectric layer is improved. On the other hand, because multi-layer back propagation neural network (BP neural network) training has strong nonlinear mapping ability and high self-learning and adaptive ability, the BP neural network is used to train and identify the collected samples.
In this paper, based on previous work [29], a human motion state recognition system based on wearable flexible capacitive pressure sensor was designed. Firstly, we designed a flexible pressure sensor consisting of MWCNTs/PDMS electrode layers with microstructures embedded on the surface and a BaTiO 3 /PDMS dielectric layer. The addition of BaTiO 3 effectively improved the dielectric constant of the dielectric layer and the sensitivity of the sensor. At the same time, the response characteristics and reliability of the sensor were explored using various mechanical deformations and a hot box test. Subsequently, the data acquisition, denoising, sample division, and feature extraction of the corresponding sensing signals (respiration signals and signals of elbow joint and knee joint bending) of volunteers in four motion states (sitting, standing, walking, and running) were completed. Finally, using BP neural network training, a data model of human motion state recognition was established, which realized the recognition of the motion states of sitting, standing, walking, and running. The sensor can effectively monitor human physiological activity information, such as breathing signals and the state of joint motion, and can significantly contribute to the field of wearable motion detection.

Preparation of Materials
The MWCNTs were purchased from Nanjing Xanano Materials Tech Co., Ltd., Nanjing, China with 95% purity, 10-30 m length, and 2.0 wt% carboxyl content. The MWCNTs were dispersed in anhydrous ethanol (AET) and stirred manually for 10 min. Subsequently, high-frequency ultrasound was used for 30 min to further disperse the MWCNTs to reduce the occurrence of agglomeration of the MWCNTs in the dispersion. Then, MWCNTs/AET dispersion with a mass fraction of 1 wt% was obtained. The dispersion solution was kept static for 12 h. Subsequently, the bottom precipitation was removed, and the supernatant was retained for further experiments. PDMS (Sylgard 184 model) was purchased from Dow Corning. The PDMS main agent and curing agent were mixed at a ratio of 15:1 and stirred for 30 min, and then they were processed under vacuum for 30 min to remove air bubbles in the mixed solution for later use. Eighty-mesh sandpaper (German Warrior brand) was purchased from a supermarket, cut, and affixed flat on a glass plate. BaTiO 3 with a particle diameter of 500 nm and content of 99.5% was purchased from Beijing Shenghe Haoyuan Technology Co., Ltd. BaTiO 3 /PDMS-mixed solutions with a mass percentage of 0%, 10%, 20%, and 30% were prepared. The solutions were stirred for 2 h to remove air bubbles. Adhesive polyimide (PI) tape (50 µm thickness) was purchased from 3M Company.

Fabrication of Microstructured Electrode Layer
Based on the previous work [29], the preparation method of the microstructured electrode is shown in Figure 1a. First, the MWCNTs solution was sprayed onto the surface of the 80-mesh sandpaper flatly attached to the glass plate. After heating and drying, a layer of dry MWCNTs was deposited on the surface of the sandpaper. The PDMS solution was poured on the surface, and the glue was homogenized by spin coating for 40 s at a speed of 300 rpm. The PDMS solution penetrated into the MWCNTs layer due to gravity. After heating and curing, the PDMS layer solidified to lock the MWCNTs layer firmly. Thereafter, the PDMS film was peeled off. Thus, the MWCNTs/PDMS electrode layer was obtained. Owing to the uneven microstructure on the surface of the sandpaper, the MWCNTs/PDMS electrode layer displayed a microstructure opposite to the unevenness of the sandpaper surface. Since the MWCNTs layer had a considerably lower thickness than the PDMS layer, this layer hardly affected the elastic properties of the PDMS layer, ensuring that the microstructured electrode had excellent stability, stretchability, and a low manufacturing cost. Figure 2a-c shows the surface morphology of the microstructured electrode layer. It can be seen that the MWCNTs layer is firmly embedded on the surface of the PDMS with microstructure. The close connection between MWCNTs and MWCNTs provides good conductivity for the sensor. In addition, we also characterized conductive MWCNTs layers at different positions of the electrode layer, as shown in Figure 2d-g. Figure 2d,e show that the thickness of the conductive MWCNTs layer at the bottom of the groove on the surface of the electrode layer is 1.094 µm-1.216 µm. Figure 2f,g show that the thickness of the conductive MWCNTs layer on the top of the bulge on the surface of the electrode layer is 3.054 µm-5 µm. ratio of 15:1 and stirred for 30 min, and then they were processed under vacuum for 3 min to remove air bubbles in the mixed solution for later use. Eighty-mesh sandpape (German Warrior brand) was purchased from a supermarket, cut, and affixed flat on glass plate. BaTiO3 with a particle diameter of 500 nm and content of 99.5% was purchase from Beijing Shenghe Haoyuan Technology Co., Ltd. BaTiO3/PDMS-mixed solutions wit a mass percentage of 0%, 10%, 20%, and 30% were prepared. The solutions were stirre for 2 h to remove air bubbles. Adhesive polyimide (PI) tape (50 µm thickness) was pur chased from 3M Company.

Fabrication of Microstructured Electrode Layer
Based on the previous work [29], the preparation method of the microstructured elec trode is shown in Figure 1a. First, the MWCNTs solution was sprayed onto the surface o the 80-mesh sandpaper flatly attached to the glass plate. After heating and drying, a laye of dry MWCNTs was deposited on the surface of the sandpaper. The PDMS solution wa poured on the surface, and the glue was homogenized by spin coating for 40 s at a spee of 300 rpm. The PDMS solution penetrated into the MWCNTs layer due to gravity. Afte heating and curing, the PDMS layer solidified to lock the MWCNTs layer firmly. Thereaf ter, the PDMS film was peeled off. Thus, the MWCNTs/PDMS electrode layer was ob tained. Owing to the uneven microstructure on the surface of the sandpaper, th MWCNTs/PDMS electrode layer displayed a microstructure opposite to the unevennes of the sandpaper surface. Since the MWCNTs layer had a considerably lower thicknes than the PDMS layer, this layer hardly affected the elastic properties of the PDMS laye ensuring that the microstructured electrode had excellent stability, stretchability, and low manufacturing cost.

Fabrication and Analysis of Dielectric Layer
The preparation process is shown in Figure 1b. Four BaTiO3/PDMS mixed solutions with different contents were spin coated on the smooth glass sheet in sequence for 40 s at a speed of 400 rpm. After the spin coating was completed, the sample was heated at 70 °C for 3 h to cure the composite film. Finally, the composite film was peeled off from the surface of the smooth glass sheet. The surface of four dielectric layers was characterized using a scanning electron microscope (SEM). As shown in Figure 3a-d, the cross-section of the pure PDMS film was the smoothest, and the cross-section of the composite film with 10% BaTiO3 addition had sporadic BaTiO3 nanoparticles. Furthermore, there were more BaTiO3 nanoparticles in the cross-section of the composite film with 20% BaTiO3 addition, and BaTiO3 particles appeared as small agglomerates. The cross-section of the composite membrane with 30% BaTiO3 addition had more BaTiO3 particles distributed in the PDMS in the form of small agglomerates. Moreover, large BaTiO3 nanoparticle agglomerates were generated. We observed the presence of small aggregates in the cross-section of the composite film added with 30% barium titanate, as shown in Figure 3e. It can be observed that a large amount of barium titanate can accumulate and agglomerate together. If the BaTiO3 content was increased beyond 30%, a larger volume of BaTiO3 agglomerates appeared in the dielectric layer of the composite material. This considerably affected the stability of the sensor. Therefore, the maximum content of the dielectric layer composite material BaTiO3 in this study was set to 30%. We also characterized the surface of barium titanate film with the addition of 10%, 20%, and 30%, as shown in Figure 3f-h. It can be seen that there is no large-area barium titanate aggregation on the surface of the Ba-TiO3/PDMS film. This distribution of barium titanate is helpful to improve the dielectric constant of the dielectric layer.

Fabrication and Analysis of Dielectric Layer
The preparation process is shown in Figure 1b. Four BaTiO 3 /PDMS mixed solutions with different contents were spin coated on the smooth glass sheet in sequence for 40 s at a speed of 400 rpm. After the spin coating was completed, the sample was heated at 70 • C for 3 h to cure the composite film. Finally, the composite film was peeled off from the surface of the smooth glass sheet. The surface of four dielectric layers was characterized using a scanning electron microscope (SEM). As shown in Figure 3a-d, the cross-section of the pure PDMS film was the smoothest, and the cross-section of the composite film with 10% BaTiO 3 addition had sporadic BaTiO 3 nanoparticles. Furthermore, there were more BaTiO 3 nanoparticles in the cross-section of the composite film with 20% BaTiO 3 addition, and BaTiO 3 particles appeared as small agglomerates. The cross-section of the composite membrane with 30% BaTiO 3 addition had more BaTiO 3 particles distributed in the PDMS in the form of small agglomerates. Moreover, large BaTiO 3 nanoparticle agglomerates were generated. We observed the presence of small aggregates in the cross-section of the composite film added with 30% barium titanate, as shown in Figure 3e. It can be observed that a large amount of barium titanate can accumulate and agglomerate together. If the BaTiO 3 content was increased beyond 30%, a larger volume of BaTiO 3 agglomerates appeared in the dielectric layer of the composite material. This considerably affected the stability of the sensor. Therefore, the maximum content of the dielectric layer composite material BaTiO 3 in this study was set to 30%. We also characterized the surface of barium titanate film with the addition of 10%, 20%, and 30%, as shown in Figure 3f-h. It can be seen that there is no large-area barium titanate aggregation on the surface of the BaTiO 3 /PDMS film. This distribution of barium titanate is helpful to improve the dielectric constant of the dielectric layer. A three-electrode measurement system (Shanghai Anbiao Electronics Co., Ltd., Shanghai, China) was applied to measure the dielectric constant of the four dielectric layer samples. As shown in Figure 4a-b, the three-electrode measurement system mainly includes the protective electrode, the protected electrode, the common electrode and its accessories, the sample, and the shielding box. The equivalent diagram of a cross-section of the three-electrode measurement system is shown in Figure 4c. The three-electrode measurement system was made of stainless steel. The size parameters of the electrode are as follows: the diameter of the protected electrode was 50 mm, the diameter of the protective electrode was 74 mm, and the gap between the protected electrode and the protective electrode was 2 mm. The equivalent area of the electrode is calculated as follows: where 1 d is the diameter of the p r otected electrode, and g is the gap between the protected electrode and the protective electrode. The relative dielectric constant of the tested sample can be calculated as follows: Substituting Equation (4) into Equation (5), we can obtain: We connected the two test terminals of the LCR meter to the protected electrode and the common electrode, respectively, and measured the capacitance value ( C ) of the sam- A three-electrode measurement system (Shanghai Anbiao Electronics Co., Ltd., Shanghai, China) was applied to measure the dielectric constant of the four dielectric layer samples. As shown in Figure 4a,b, the three-electrode measurement system mainly includes the protective electrode, the protected electrode, the common electrode and its accessories, the sample, and the shielding box. The equivalent diagram of a cross-section of the three-electrode measurement system is shown in Figure 4c. The three-electrode measurement system was made of stainless steel. The size parameters of the electrode are as follows: the diameter of the protected electrode was 50 mm, the diameter of the protective electrode was 74 mm, and the gap between the protected electrode and the protective electrode was 2 mm.  A three-electrode measurement system (Shanghai Anbiao Electronics Co., Ltd., Shanghai, China) was applied to measure the dielectric constant of the four dielectric layer samples. As shown in Figure 4a-b, the three-electrode measurement system mainly includes the protective electrode, the protected electrode, the common electrode and its accessories, the sample, and the shielding box. The equivalent diagram of a cross-section of the three-electrode measurement system is shown in Figure 4c. The three-electrode measurement system was made of stainless steel. The size parameters of the electrode are as follows: the diameter of the protected electrode was 50 mm, the diameter of the protective electrode was 74 mm, and the gap between the protected electrode and the protective electrode was 2 mm. The equivalent area of the electrode is calculated as follows: where 1 d is the diameter of the p r otected electrode, and g is the gap between the protected electrode and the protective electrode. The relative dielectric constant of the tested sample can be calculated as follows: Substituting Equation (4) into Equation (5), we can obtain: We connected the two test terminals of the LCR meter to the protected electrode and the common electrode, respectively, and measured the capacitance value ( C ) of the sam- The equivalent area of the electrode is calculated as follows: where d 1 is the diameter of the protected electrode, and g is the gap between the protected electrode and the protective electrode. The relative dielectric constant of the tested sample can be calculated as follows: Substituting Equation (4) into Equation (5), we can obtain: We connected the two test terminals of the LCR meter to the protected electrode and the common electrode, respectively, and measured the capacitance value (C) of the sample. The relative dielectric constant (ε r ) of the tested sample could be calculated by Formula (6). The relative dielectric constants of the four samples with BaTiO 3 content of 0%, 10%, 20%, and 30% are shown in Figure 5. The test curve indicates that the dielectric constants of the four samples decreased slightly with the increase in the capacitance measurement frequency. This may be because, when the test frequency is further increased, the change of the dipole vector is slower than that of the applied electric field, resulting in the weakening of polarization and the reduction in dielectric constant of the composites [30]. With the increase in the BaTiO 3 content, the relative dielectric constant of the dielectric layer also increased. This may be because with the increase in the BaTiO 3 content, the crosslinking degree of the composite material increases and the polarization enhances. Thus, in this study, 30% (mass fraction) BaTiO 3 was added to PDMS to prepare composite dielectric layers.  (6). The relative dielectric constants of the four samples with BaTiO3 content of 0%, 10%, 20%, and 30% are shown in Figure 5. The test curve indicates that the dielectric constants of the four samples decreased slightly with the increase in the capacitance measurement frequency. This may be because, when the test frequency is further increased, the change of the dipole vector is slower than that of the applied electric field, resulting in the weakening of polarization and the reduction in dielectric constant of the composites [30].
With the increase in the BaTiO3 content, the relative dielectric constant of the dielectric layer also increased. This may be because with the increase in the BaTiO3 content, the crosslinking degree of the composite material increases and the polarization enhances. Thus, in this study, 30% (mass fraction) BaTiO3 was added to PDMS to prepare composite dielectric layers.

Sensor Packaging
The fabricated MWCNTs/PDMS electrode layer was cut into a strip with a width of 1 cm and length of 4 cm, and the PDMS/BaTiO3 dielectric layer was cut into a square with a side length of 1.5 cm. The sensor thus adopted a "sandwich" structure, with the upper and lower layers being the electrode layers and the middle layer being a dielectric layer. The three-layer structure was sealed and bonded using a single-sided adhesive PI film. The schematic diagram of the sensor structure is shown in Figure 6a. A copper foil conductive tape was used to fix the wire on the surface of the electrode layer, making further testing and usage convenient. The actual image of the sensor is shown in Figure 6b. The thickness of the sensor was 1.05 mm, and the effective pressure sensing area was 1 cm × 1 cm. Images of the deformation states (such as bending and distortion) of the flexible sensor are shown in Figure 6c,d. It can be seen that the deformation type of sensor meets the demand of joint movement.

Sensor Packaging
The fabricated MWCNTs/PDMS electrode layer was cut into a strip with a width of 1 cm and length of 4 cm, and the PDMS/BaTiO 3 dielectric layer was cut into a square with a side length of 1.5 cm. The sensor thus adopted a "sandwich" structure, with the upper and lower layers being the electrode layers and the middle layer being a dielectric layer. The three-layer structure was sealed and bonded using a single-sided adhesive PI film. The schematic diagram of the sensor structure is shown in Figure 6a. A copper foil conductive tape was used to fix the wire on the surface of the electrode layer, making further testing and usage convenient. The actual image of the sensor is shown in Figure 6b. The thickness of the sensor was 1.05 mm, and the effective pressure sensing area was 1 cm × 1 cm. Images of the deformation states (such as bending and distortion) of the flexible sensor are shown in Figure 6c,d. It can be seen that the deformation type of sensor meets the demand of joint movement.  (6). The relative dielectric constants of the four samples with BaTiO3 content of 0%, 10%, 20%, and 30% are shown in Figure 5. The test curve indicates that the dielectric constants of the four samples decreased slightly with the increase in the capacitance measurement frequency. This may be because, when the test frequency is further increased, the change of the dipole vector is slower than that of the applied electric field, resulting in the weakening of polarization and the reduction in dielectric constant of the composites [30].
With the increase in the BaTiO3 content, the relative dielectric constant of the dielectric layer also increased. This may be because with the increase in the BaTiO3 content, the crosslinking degree of the composite material increases and the polarization enhances. Thus, in this study, 30% (mass fraction) BaTiO3 was added to PDMS to prepare composite dielectric layers.

Sensor Packaging
The fabricated MWCNTs/PDMS electrode layer was cut into a strip with a width of 1 cm and length of 4 cm, and the PDMS/BaTiO3 dielectric layer was cut into a square with a side length of 1.5 cm. The sensor thus adopted a "sandwich" structure, with the upper and lower layers being the electrode layers and the middle layer being a dielectric layer. The three-layer structure was sealed and bonded using a single-sided adhesive PI film. The schematic diagram of the sensor structure is shown in Figure 6a. A copper foil conductive tape was used to fix the wire on the surface of the electrode layer, making further testing and usage convenient. The actual image of the sensor is shown in Figure 6b. The thickness of the sensor was 1.05 mm, and the effective pressure sensing area was 1 cm × 1 cm. Images of the deformation states (such as bending and distortion) of the flexible sensor are shown in Figure 6c,d. It can be seen that the deformation type of sensor meets the demand of joint movement.

Characterization
The surface morphology of the dielectric layer was characterized using the Apreo SEM (Thermo Scientific, USA). A digital push-pull force gauge (Adburg) and an electric pushpull force gauge (ZQ-990A) (Dongguan Zhiqu Precision Instrument Co., Ltd., Dongguan, China) were used to provide pressure loading for the sensor. A flexible electronic tester (Shanghai Mifang Electronic Technology Co., Ltd., Shanghai, China) was used to provide bending loading for the sensor. An LCR meter (TH2826) (Changzhou Tonghui Electronics Co., Ltd., Changzhou, China) was used to record the changes in electrical signals output by the sensor. The performance test device of the sensor is shown in Figure 7.

Characterization
The surface morphology of the dielectric layer was characterized using the Apreo SEM (Thermo Scientific, USA). A digital push-pull force gauge (Adburg) and an electric push-pull force gauge (ZQ-990A) (Dongguan Zhiqu Precision Instrument Co., Ltd., Dongguan, China) were used to provide pressure loading for the sensor. A flexible electronic tester (Shanghai Mifang Electronic Technology Co., Ltd., Shanghai, China) was used to provide bending loading for the sensor. An LCR meter (TH2826) (Changzhou Tonghui Electronics Co., Ltd., Changzhou, China) was used to record the changes in electrical signals output by the sensor. The performance test device of the sensor is shown in Figure 7.

Performance of the Pressure Sensor
The sensor was fixed on the base of the digital push-pull force gauge. As pressure was applied, the LCR meter recorded the capacitance changes corresponding to different levels of pressure. Then, the pressure-capacitance change curve was obtained, as shown in Figure 8a. The piecewise linear fitting analysis shows that the sensitivity of the sensor was 2.39 kPa −1 in the pressure range 0-0.12 kPa, 0.23 kPa −1 in 0.27-2.68 kPa, 0.08 kPa −1 in 3.25-9.45 kPa, and 0.02 kPa −1 in 10.73-28.73 kPa. Thus, the sensitivity of the sensor gradually decreased as the pressure increased. This may be because the microstructure of the electrode surface is constantly compressed under the action of external forces, approaching the deformation limit. The air groove formed between the electrode layer and the dielectric layer almost disappeared due to compression. When the sensor was under high pressure, the microstructure of the electrode layer was close to the deformation limit and contributed little to the sensitivity. At this time, the dielectric layer was still within its elastic range, and could produce elastic deformation under high pressure, further reducing the distance between the upper and lower electrodes, resulting in a small output response of the sensor. To measure the response time and recovery time of the sensor more efficiently, a 200 mg weight piece was lightly thrown on the surface of the sensor to simulate transient pressure loading. Subsequently, tweezers were used to quickly move the weight piece away from the sensor to simulate pressure unloading. Figure 8b indicates that the response time (Tr) of the sensor was 16 ms when the weight piece was loaded, and the recovery time (Tf) of the sensor was 8 ms when the weight piece was unloaded. It was also found through experiments that, when a 50 mg weight piece was loaded on the sensor (with pressure approximately 6.8 Pa), the capacitance output of the sensor had a recognizable increase change, and the sensor could effectively maintain the change in the capacitance value. The response curve of the sensor pressure limit detection is shown in Figure 7. Performance test device of sensor.

Performance of the Pressure Sensor
The sensor was fixed on the base of the digital push-pull force gauge. As pressure was applied, the LCR meter recorded the capacitance changes corresponding to different levels of pressure. Then, the pressure-capacitance change curve was obtained, as shown in Figure 8a. The piecewise linear fitting analysis shows that the sensitivity of the sensor was 2.39 kPa −1 in the pressure range 0-0.12 kPa, 0.23 kPa −1 in 0.27-2.68 kPa, 0.08 kPa −1 in 3.25-9.45 kPa, and 0.02 kPa −1 in 10.73-28.73 kPa. Thus, the sensitivity of the sensor gradually decreased as the pressure increased. This may be because the microstructure of the electrode surface is constantly compressed under the action of external forces, approaching the deformation limit. The air groove formed between the electrode layer and the dielectric layer almost disappeared due to compression. When the sensor was under high pressure, the microstructure of the electrode layer was close to the deformation limit and contributed little to the sensitivity. At this time, the dielectric layer was still within its elastic range, and could produce elastic deformation under high pressure, further reducing the distance between the upper and lower electrodes, resulting in a small output response of the sensor. To measure the response time and recovery time of the sensor more efficiently, a 200 mg weight piece was lightly thrown on the surface of the sensor to simulate transient pressure loading. Subsequently, tweezers were used to quickly move the weight piece away from the sensor to simulate pressure unloading. Figure 8b indicates that the response time (Tr) of the sensor was 16 ms when the weight piece was loaded, and the recovery time (Tf) of the sensor was 8 ms when the weight piece was unloaded. It was also found through experiments that, when a 50 mg weight piece was loaded on the sensor (with pressure approximately 6.8 Pa), the capacitance output of the sensor had a recognizable increase change, and the sensor could effectively maintain the change in the capacitance value. The response curve of the sensor pressure limit detection is shown in Figure 8c. The ratio of the capacitance change to the sensor's initial value was approximately 0.015. Unfortunately, when the mass of the weight was less than 50 mg, the capacitance value change of the sensor was difficult to recognize owing to noise interference. Therefore, 6.8 Pa can be regarded as the minimum pressure resolution that the sensor can recognize. This also proves that the sensor has certain advantages in detecting extremely low pressure. To prove that the flexible pressure sensor can adapt to complex non-planar environments by virtue of its own flexibility, the sensor was fixed on the two splints of the flexible electronic tester. One of the splints was moved inward to make the sensor bend and arch, forming different angles. The test results are shown in Figure 8d. As the bending angle increased, the capacitance of the sensor gradually increased and the speed gradually increased. When the sensor was bent, the dielectric layer and the microstructure of the electrode surface were squeezed, thereby changing the initial capacitance value. To demonstrate the capability of the sensor responding to the pressure changes even in the bent state, the sensor was attached to the outer wall of 100 mL, 50 mL, and 10 mL graduated cylinders. At this time, the bending angles of the sensor were approximately 38 • , 45 • , and 76 • , respectively. The sensitivity tests were performed on the sensors in the three bending states (Figure 8e). The results indicate that, compared with the sensitivity curve of the sensor in the flat state, the sensitivity of the sensor in the bent state is obviously lower. This is because the sensor was compressed when the sensor was bent, which increased the initial capacitance value of the sensor; that is, C 0 in ∆C/C 0 increased, resulting in a decreased slope of the pressure-capacitance curve and a decrease in sensitivity. In the sensor bending test, the pressure response curve when the sensor was bent at 36 • was the steepest, followed by the pressure response curve at 45 • , and the pressure response curve at 76 • was the flattest. This indicates that the larger the sensor bending angle, the higher is the initial capacitance value and the lower is the sensitivity of the sensor. To explore the sensor's ability to detect different pressure loading signals, sharp pulse pressure and square wave pressure of signal values 0.3, 0.8, and 1.5 kPa were repeatedly applied to the sensor twice. As shown in Figure 8f,g, under the same applied pressure, irrespective of whether square wave pressure or sharp pulse pressure was applied, the corresponding capacitance output response value was almost the same. This indicates that the sensor has a stable response to different types of pressure signals. To analyze whether the sensor could work normally for a long period while generating heat or in a high-temperature environment, the sensor was placed in a vacuum drying oven and the temperature increased from 20 • C to 80 • C. Then, the capacitance change curve of the sensor during the heating process was measured, and the results are as shown in Figure 8h. It can be seen that the capacitance change of the sensor from 20 • C to 80 • C was only 3.1% of the initial capacitance value. Thus, the impact on the electrical performance of the sensor is small and the sensor meets the working requirements under high temperature. To show the durability and service life of the sensor, a cyclic pressurization-unloading test was performed on the sensor. The test pressure was 200 and 400 Pa, and the number of repetitions was approximately 2000 (Figure 9). As shown in Figure 9a  To show the durability and service life of the sensor, a cyclic pressurization-unloading test was performed on the sensor. The test pressure was 200 and 400 Pa, and the number of repetitions was approximately 2000 ( Figure 9). As shown in Figure 9a,d, the capacitance response curves can maintain good stability at 200 and 400 Pa, indicating that the sensor has good repeatability under different pressure. As shown in Figure 9b,c and Figure 9e,f, at different time periods of 1000-1040 s and 4000-4040 s, the capacitance response curves are very close, and there is no consistent increase or decrease in the capacitance change. This proves that the sensor has good durability and creep resistance. To show the durability and service life of the sensor, a cyclic pressurization-unloading test was performed on the sensor. The test pressure was 200 and 400 Pa, and the number of repetitions was approximately 2000 ( Figure 9). As shown in Figure 9a,d, the capacitance response curves can maintain good stability at 200 and 400 Pa, indicating that the sensor has good repeatability under different pressure. As shown in Figure 9b,c and Figure 9e,f, at different time periods of 1000-1040 s and 4000-4040 s, the capacitance response curves are very close, and there is no consistent increase or decrease in the capacitance change. This proves that the sensor has good durability and creep resistance. In the repeatability test with pressure 200 and 400 Pa, a loading-unloading process was carried out to explore the hysteresis of the sensor under dynamic pressure. As shown in Figure 10a,b, the hysteresis of the sensor under a dynamic pressure of 200 Pa was approximately 5.9% and that under a dynamic pressure of 400 Pa was approximately 9%. In the repeatability test with pressure 200 and 400 Pa, a loading-unloading process was carried out to explore the hysteresis of the sensor under dynamic pressure. As shown in Figure 10a,b, the hysteresis of the sensor under a dynamic pressure of 200 Pa was approximately 5.9% and that under a dynamic pressure of 400 Pa was approximately 9%. The sensor has suitably low hysteresis. To explore the sensitivity change of the sensor after a long-term operation, the sensitivity of the sensors under repeated loading-unloading cycles for a total of more than 10,000 times was tested and compared with the initial sensitivity ( Figure 10c). The test results show that, after more than 10,000 pressure loading-unloading cycles, the sensitivity curve of the sensor basically fit the initial sensitivity curve, and the maximum error was approximately 8%. However, the sensitivity of the sensor after 10,000 repetitions was slightly higher than the initial sensitivity. This may be due to the performance abnormality caused by fatigue damage to the flexible material of the sensor under long-term loading.
The performance of the proposed sensor is compared with that of some reported sensors ( Table 1). The proposed sensor evidently has certain advantages in terms of sensitivity, minimum resolution, response time, and stability.
cycles for a total of more than 10,000 times was tested and compared with the initial sensitivity (Figure 10c). The test results show that, after more than 10,000 pressure loadingunloading cycles, the sensitivity curve of the sensor basically fit the initial sensitivity curve, and the maximum error was approximately 8%. However, the sensitivity of the sensor after 10,000 repetitions was slightly higher than the initial sensitivity. This may be due to the performance abnormality caused by fatigue damage to the flexible material of the sensor under long-term loading. The performance of the proposed sensor is compared with that of some reported sensors ( Table 1). The proposed sensor evidently has certain advantages in terms of sensitivity, minimum resolution, response time, and stability.

Acquisition and Denoising of Sensor Signals
Under the premise of not affecting normal human activities, a portable and wearable hardware circuit board was designed to flexibly collect three-channel capacitive sensing signals in real time. Using the built-in Bluetooth system of the microcontroller module, the collected signals were transmitted to the PC by wireless transmission to complete the storage and analysis of the sensor data. The actual image and installation position of the hardware circuit board are shown in Figure 11. The hardware circuit includes the capacitance acquisition module (PCap02, German ACAM company, Stutensee, Germany), microcontroller module (CC2541, TI company, Dallas, TA, USA), switch module (ADG711, Analog Devices Inc., Norwood, MA, USA), and power module (TLV75733PDBVR, TI company). The power supply voltage of the circuit board was 3.3 V. the collected signals were transmitted to the PC by wireless transmission to complete the storage and analysis of the sensor data. The actual image and installation position of the hardware circuit board are shown in Figure 11. The hardware circuit includes the capacitance acquisition module (PCap02, German ACAM company, Stutensee, Germany), microcontroller module (CC2541, TI company, Texas, USA), switch module (ADG711, Analog Devices Inc, Massachusetts, USA), and power module (TLV75733PDBVR, TI company). The power supply voltage of the circuit board was 3.3 V. The multi-channel sensor signal acquisition system was used to realize the data acquisition of respiratory signals, elbow joint bending signals, and knee joint bending signals. The acquisition results are shown in Figure 12. Figure 12a shows that the sensor responds more accurately to the three breathing states, namely normal breathing, deep breathing, and rapid breathing. The intensity of deep breathing is greater than that of normal breathing, while the frequency of rapid breathing is higher. In addition, the intensity of inhalation during rapid breathing is similar to that of deep breathing, but the exhalation is not thorough enough. The real-time acquisition of the change in the sensor capacitance has a better mapping ability with the actual breathing situation. Figure 12b,c, respectively, show the capacitance response of the sensor to the bending state of the elbow joint and the knee joint. Between them, the elbow joint is a smaller joint, and the sensor has a larger bend when the elbow joint is bent, and thus can produce a larger change in capacitance. Because the knee joint is a larger joint, even if the knee joint is bent at a larger angle, owing to the small size of the sensor, its capacitance response is slightly lower than that when the elbow joint is bent. The test curve results also prove that the sensor can generate effective responses to different joint motion signals. The multi-channel sensor signal acquisition system was used to realize the data acquisition of respiratory signals, elbow joint bending signals, and knee joint bending signals. The acquisition results are shown in Figure 12. Figure 12a shows that the sensor responds more accurately to the three breathing states, namely normal breathing, deep breathing, and rapid breathing. The intensity of deep breathing is greater than that of normal breathing, while the frequency of rapid breathing is higher. In addition, the intensity of inhalation during rapid breathing is similar to that of deep breathing, but the exhalation is not thorough enough. The real-time acquisition of the change in the sensor capacitance has a better mapping ability with the actual breathing situation. Figure 12b,c, respectively, show the capacitance response of the sensor to the bending state of the elbow joint and the knee joint. Between them, the elbow joint is a smaller joint, and the sensor has a larger bend when the elbow joint is bent, and thus can produce a larger change in capacitance. Because the knee joint is a larger joint, even if the knee joint is bent at a larger angle, owing to the small size of the sensor, its capacitance response is slightly lower than that when the elbow joint is bent. The test curve results also prove that the sensor can generate effective responses to different joint motion signals. Therefore, in this study, three sensors to collect breathing signals, elbow joint bending signals, and knee joint bending signals were installed to distinguish the four typical motion states of the human body, namely sitting, standing, walking, and running. The process is as follows. First, the three flexible sensors were attached to the volunteer's chest, elbow, and knee joints and attached to a hardware circuit board. The volunteer maintained the four states for 1 min each and repeated them 15 times. Considering a breathing frequency range of 0.15-0.4 Hz and taking into account the movement frequency of the elbow and knee joints, a sensor signal acquisition frequency of 5 Hz was set in this study to avoid introducing excessive noise. The acquired sensor data are shown in Figure 13ad. Therefore, in this study, three sensors to collect breathing signals, elbow joint bending signals, and knee joint bending signals were installed to distinguish the four typical motion states of the human body, namely sitting, standing, walking, and running. The process is as follows. First, the three flexible sensors were attached to the volunteer's chest, elbow, and knee joints and attached to a hardware circuit board. The volunteer maintained the four states for 1 min each and repeated them 15 times. Considering a breathing frequency range of 0.15-0.4 Hz and taking into account the movement frequency of the elbow and knee joints, a sensor signal acquisition frequency of 5 Hz was set in this study to avoid introducing excessive noise. The acquired sensor data are shown in Figure 13a-d.
process is as follows. First, the three flexible sensors were attached to the volunteer's chest, elbow, and knee joints and attached to a hardware circuit board. The volunteer maintained the four states for 1 min each and repeated them 15 times. Considering a breathing frequency range of 0.15-0.4 Hz and taking into account the movement frequency of the elbow and knee joints, a sensor signal acquisition frequency of 5 Hz was set in this study to avoid introducing excessive noise. The acquired sensor data are shown in Figure 13ad.  As indicated by the black curve in Figure 14, the acquired signals inevitably comprise various noise signals because of the limitations of environment and experimental conditions during the signal acquisition process. Herein, to denoise the collected sensor signals, the wavelet threshold denoising method was adopted. The parameter setting rules of the wavelet threshold denoising method are as follows: the wavelet basis function is coif4, the number of wavelet decomposition layers is 5, the rigrsure threshold rule is used as the threshold method, and the soft threshold function is used as the threshold function. The data of different motion states collected by the sensor were transmitted to PC through Bluetooth for storage and denoising. The red curve in Figure 14 shows the denoising effect of partial breathing signals collected in the state of standing still. Clearly, the noise in the signals was successfully removed, and the signals after denoising had better smoothness and better retained the original change trend and characteristics of the signals.

Construction of BP Neural Model and Testing of Human Motion State Recognition System
In this study, windowing processing was conducted on the collected signals; that is, the relatively long data were divided into fixed-length data fragments as samples. The window length was set to 10 s, and the signals were divided into a series of analysis samples with a sliding window in 5 s increments, thereby generating a 5 s overlap. The signal overlap method was used to maximize the use of continuous data flow. The signal sampling frequency of the sensor was 5 Hz; that is, every 50 data points were regarded as a sample. A sample was collected every 25 data points, thus resulting in a total of 716 sets of samples in the four motion states. Each set of samples includes respiration signals, elbow joint bending signals, and knee joint bending signals with a 10 s length. The sample features were extracted using a time-domain feature extraction method. Five common time-domain features were selected, namely the maximum value, minimum value, average value, root mean square, and variance. A set of samples included three sets of data collected by the sensor-breathing signals, elbow joint bending signals, and knee joint bending signals, denoted as A, B, and C, respectively. Through calculation, the eigenvalues of the five time-domain features of the three sets of data were obtained. A sample with 15 characteristic parameters was formed as the input for the neural network training. Subsequently, a three-layer forward BP network was established, including an input layer, a hidden layer, and an output layer. The input layer of the BP network had 15 nodes. The 15-dimensional input vectors formed sequentially corresponded to the 15 eigenvalues in a set of samples. The output layer had a node which represented the motion states of sitting, standing still, walking, and running with outputs 1, 2, 3, and 4, respectively. The number of neurons in the hidden layer was seven. From the obtained 716 groups of sample sets for distinguishing the four motion states, 70% of the samples were randomly selected as the training set, 15% of the samples as the validation set, and 15% of the samples as the test set. The Levenberg-Marguardt algorithm was adopted as the training algorithm. As indicated by the black curve in Figure 14, the acquired signals inevitably comprise various noise signals because of the limitations of environment and experimental condi tions during the signal acquisition process. Herein, to denoise the collected sensor signals the wavelet threshold denoising method was adopted. The parameter setting rules of the wavelet threshold denoising method are as follows: the wavelet basis function is coif4, the number of wavelet decomposition layers is 5, the rigrsure threshold rule is used as the threshold method, and the soft threshold function is used as the threshold function. The data of different motion states collected by the sensor were transmitted to PC through Bluetooth for storage and denoising. The red curve in Figure 14 shows the denoising effec of partial breathing signals collected in the state of standing still. Clearly, the noise in the signals was successfully removed, and the signals after denoising had better smoothnes and better retained the original change trend and characteristics of the signals.

Construction of BP Neural Model and Testing of Human Motion State Recognition System
In this study, windowing processing was conducted on the collected signals; that is the relatively long data were divided into fixed-length data fragments as samples. The window length was set to 10 s, and the signals were divided into a series of analysis sam ples with a sliding window in 5 s increments, thereby generating a 5 s overlap. The signa overlap method was used to maximize the use of continuous data flow. The signal sam pling frequency of the sensor was 5 Hz; that is, every 50 data points were regarded as a sample. A sample was collected every 25 data points, thus resulting in a total of 716 set of samples in the four motion states. Each set of samples includes respiration signals, el bow joint bending signals, and knee joint bending signals with a 10 s length. The sample features were extracted using a time-domain feature extraction method. Five common time-domain features were selected, namely the maximum value, minimum value, aver age value, root mean square, and variance. A set of samples included three sets of data collected by the sensor-breathing signals, elbow joint bending signals, and knee join bending signals, denoted as A , B , and C , respectively. Through calculation, the eigen values of the five time-domain features of the three sets of data were obtained. A sample with 15 characteristic parameters was formed as the input for the neural network training Subsequently, a three-layer forward BP network was established, including an inpu layer, a hidden layer, and an output layer. The input layer of the BP network had 15 nodes The 15-dimensional input vectors formed sequentially corresponded to the 15 eigenvalue in a set of samples. The output layer had a node which represented the motion states o sitting, standing still, walking, and running with outputs 1, 2, 3, and 4, respectively. The The mean square errors of the three sample sets after 26 training iterations are shown in Figure 15. The verification set reached the optimal mean square error of 0.13724 at the 20th iteration. At this time, the mean square errors of the training set and the test set were 0.10342 and 0.11179, respectively. The lower the mean square error, the better is the effect of the neural network. Finally, the human body motion state recognition system was established (Figure 16). A new type of flexible capacitive sensor was applied for sensing human physiological signals. The data were transmitted to the PC through the signal acquisition system. After denoising, sample partition, and feature extraction, the processed data were used for neural network training, and the trained neural network model was used to perform human motion state recognition. Through the application of the signal acquisition system, a total of 100 test samples were obtained, including 25 each of sitting, standing, walking, and running samples. These samples were used to test the reliability of the trained human motion state recognition network. The test results obtained are shown in Table 2. quisition system. After denoising, sample partition, and feature extraction, the processed data were used for neural network training, and the trained neural network model was used to perform human motion state recognition. Through the application of the signal acquisition system, a total of 100 test samples were obtained, including 25 each of sitting, standing, walking, and running samples. These samples were used to test the reliability of the trained human motion state recognition network. The test results obtained are shown in Table 2.    quisition system. After denoising, sample partition, and feature extraction, the processed data were used for neural network training, and the trained neural network model was used to perform human motion state recognition. Through the application of the signal acquisition system, a total of 100 test samples were obtained, including 25 each of sitting, standing, walking, and running samples. These samples were used to test the reliability of the trained human motion state recognition network. The test results obtained are shown in Table 2.     As shown in Table 2, the overall correct recognition rate of the test was 94%. In detail, the highest recognition rate was obtained for sitting and standing still, reaching 96%, followed by walking and running, which were both 92%. The first two states have extremely low motion amplitudes with only slight unconscious motion of the joints. Hence, the data collected by the sensor were relatively stable. By contrast, because the motion amplitudes of walking and running are large, the signals collected by the sensor changed drastically. The training samples are not sufficiently comprehensive to cover all possible samples.

Discussion and Conclusions
In summary, this paper presented a method for human body motion state recognition based on a flexible, wearable capacitive pressure sensor. The sensor used sandpaper as a template, MWCNTs as a conductive material, and PDMS as a flexible substrate to obtain a MWCNTs/PDMS electrode layer with microstructure embedded on the surface. To reduce the interference of parasitic capacitance, the dielectric layer was made of a BaTiO 3 /PDMS composite film with a mass ratio of 30%, which effectively improved the dielectric constant of the sensor. The designed flexible pressure sensor showed a sensitivity up to 2.39 kPa −1 in a pressure measurement range of 0-120 kPa, a minimum pressure resolution of 6.8 Pa, fast response time (16 ms), and fast recovery time (8 ms). In the dynamic response, the designed sensor had a low hysteresis and could remain stable after repeated loading over 10,000 times. The hardware circuit board was used to collect the breathing signals, the elbow joint bending signals, and the knee joint bending signals of the human body in different motion states. The collected sensor signals were denoised by the wavelet threshold denoising method. Subsequently, the denoised data were divided into samples. The time-domain feature values were extracted to form feature samples. The BP neural network was used to train and learn the samples to obtain a motion state analysis model. Finally, the human motion state recognition system was constructed, which realized the recognition of four motion states, namely sitting, standing, walking, and running. After testing, the comprehensive correct recognition rate of the system was approximately 94%. This method provides a new concept for the field of human motion recognition and has great application potential in human-computer interaction and health monitoring.