CN218922561U - Capacitive pulse condition sensor and wearable pulse condition detection equipment - Google Patents

Abstract

The utility model relates to a capacitive pulse condition sensor and wearable pulse condition detection equipment, which comprises a plurality of sensor units, wherein each sensor unit is provided with a flexible multifunctional layer, a curved elastic upper electrode is arranged in each multifunctional layer, a flexible supporting layer is arranged below the upper electrode, a lower electrode is arranged on the top surface of the flexible supporting layer, an insulating layer is arranged between the upper electrode and the lower electrode and forms different capacitances to reflect components of force in different directions, the flexible multifunctional layer is deformed by external force to drive the upper electrode to change the contact area with the insulating layer, and at least one of the upper electrode and the lower electrode is at least two; the flexible supporting layer is internally provided with a fiber artificial muscle actuator, the actuator has expansion capacity in the direction of the upper electrode, a circuit board is arranged below the actuator, the flexible supporting layer is fixed on the circuit board and is provided with an electric conduction path for electrically connecting the lower electrode and the circuit board, and the upper electrode is electrically connected with the circuit board.

Description

Capacitive pulse condition sensor and wearable pulse condition detection equipment

Technical Field

The utility model relates to a capacitive pulse condition sensor and wearable pulse condition detection equipment.

Background

The diagnosis of pulse condition is critical to the inheritance and development of traditional Chinese medicine. The pulse feeling of traditional Chinese medicine is to sense the pulse condition change of the arteries of the wrist, especially the arteries of the wrist, the cun and the chi of a patient by the fingers of traditional Chinese medicine, and the pulse condition change is divided into twenty eight pulse conditions, wherein the pulse condition change can be summarized into the blood pressure change information of the arteries of the wrist, especially the arteries of the wrist, the cun and the chi of the patient.

The technical development of pulse condition sensors can be divided into three phases: the single-point rigid surface pressure sensor single-head sensor appears in the period from 70 to 80 of the 1.20 century, but the single-probe pulse meter cannot collect pulse information of the cun, guan and chi parts at the same time, and the problem that the pulse information needs to be repeatedly tried to find the aiming pulse is solved, in addition, the single-point rigid surface pressure sensor is inconsistent with human body touch in bionics, and the collected pulse information is single; three-head type sensors capable of collecting pulse information of three parts of cun, guan and chi at the end of the 2.20 th century and collecting pulse information of a single part of cun, guan and chi independently are designed, and a manual vertical adjusting screw rod and a manual radial adjusting screw rod are designed to realize displacement of the sensors in radial direction and vertical direction of radial artery; since the 3.21 st century, pulse meters have been developed mainly around the following 3 points: (1) designing a common array type pressure sensor to perform multipoint acquisition on pulse information; (2) designing a flexible array type pressure sensor capable of simulating human body touch in the aspect of bionics; (3) a composite acquisition mode for cooperatively acquiring pulse information by a pressure sensor, a photoelectric sensor, a microphone and other non-contact sensors is constructed.

Two main defects of the existing pulse condition sensor technology are the accurate control capability of finger pressure of a traditional Chinese medicine expert and the detection sensitivity (expressed as the resolution capability of force) to pressure.

The pressure regulating device or actuator used for simulating finger pressure of the expert in traditional Chinese medicine is basically realized by a motor or a pneumatic device, for example, a fluid or air bag is used in CN107847164B, an air bag is used in CN201980023078, and the like. The motor or the pneumatic device is heavy, can't compare with dexterous human finger, has the shortcoming that pulse feeling operation efficiency is low, simultaneously hardly accomplish the accurate pressure variation with detecting data is cooperated, can't reach the accurate control ability that traditional chinese medical science expert's finger was exerted pressure.

On the other hand, the university of Harbin industry, the professor group of Cold powerful pine finds that the 'Bipolar' (bipolarar) driving of artificial muscle intelligent materials can be converted into 'monopolar' (unipole) driving through a polyelectrolyte functionalization strategy, meanwhile, the abnormal phenomenon that the artificial muscle is reduced along with capacitance and the driving performance is enhanced (Scan Rate Enhanced Stroke, SRES) is found, further, the carbon nanotube fiber artificial muscle of a monopolar stroke and an electroosmotic pump is researched, and compared with the traditional artificial muscle, the artificial muscle has the characteristics of no toxicity, high driving frequency (up to 10 Hz), low driving voltage (1V), high specific energy (0.73-3.5J/g), high driving strain (3.85-18.6%), high energy density (up to 8.17W/g) and the like, and has great application potential in the fields of space development structures, bionic ornithopter, deformable aircraft, underwater robots, flexible robots, wearable exoskeletons, medical robots and the like.

In terms of pressure detection sensitivity, the detection capability of the hands of a traditional Chinese medical expert can reach the average normal pressure threshold value of a male fingertip of 0.055g, the corresponding value of a female is 0.019g, and a touch sensor in the electronic skin of a traditional pulse condition sensor is basically difficult to reach.

The flexible capacitive three-dimensional force vector sensor structure disclosed in patent CN201920633712.5 can realize the functional requirements of touch sensing (when a sensing system is about to or just touches an external object, the speed and distance of the external object about to or just touches should be roughly classified and judged), the sensing three-dimensional force size direction (XYZ), and the requirements of high sensitivity and wide detection range and flexible touch simultaneously through the upper electrode of the multifunctional layer and the lower electrode array arranged below. The sensor unit in the test can reach the resolution of 0.01 gram normal force (pressure direction and Z direction) and surpass the pressure resolution capability (0.019 gram) of the fingers of the traditional Chinese medical specialist, so that the sensor unit has the congenital advantage in the construction of the tactile sensor of the pulse condition sensor technology.

Therefore, how to organically mix two technologies in a very small space caused by the miniaturization trend of the pulse condition sensor to realize accurate control capability of finger pressure and detection sensitivity to pressure of a traditional Chinese medicine expert, and meanwhile, consider wiring difficulty caused by a plurality of electrodes is a problem to be solved by the patent proposal.

Disclosure of Invention

In order to overcome the defects in the prior art, a capacitive pulse condition sensor is provided, and comprises at least two sensor units, wherein each sensor unit is provided with a flexible multifunctional layer, an upper electrode electrically connected with the multifunctional layer is arranged in each multifunctional layer, and the upper electrode is a curved elastic electrode; a flexible supporting layer is arranged below the upper electrode, a lower electrode is arranged on the top surface of the flexible supporting layer, an insulating layer is arranged between the upper electrode and the lower electrode, the downward projection of the upper electrode at least covers part of the area of each lower electrode, the flexible multifunctional layer is deformed by external force to drive the upper electrode to change the contact area with the insulating layer, at least one of the upper electrode and the lower electrode is at least two, and different capacitances are formed between the upper electrode and the lower electrode to reflect the components of the force in different directions; the flexible supporting layer is internally provided with a fiber artificial muscle actuator, the actuator has expansion capacity in the direction of the upper electrode, a circuit board electrically connected with the actuator is arranged below the actuator, the flexible supporting layer is fixed on the circuit board and is provided with an electric conduction path for electrically connecting the lower electrode with the circuit board, and the upper electrode is electrically connected with the circuit board.

By adopting the structure of the utility model, the components of force in different directions can be reflected according to the deformation of the flexible multifunctional layer of the flexible sensor unit and the formation of different capacitances between the upper electrode and the lower electrode, so as to achieve or exceed the pressure resolution capability (normal direction and Z direction) of the human finger; the pressure control structure of the electric actuation fabric fiber artificial muscle lattice achieves low-voltage and low-power consumption pressure lattice control, is combined with a flexible sensor unit lattice, and when the artificial muscle is actuated in a telescopic way, the lower electrode can deform and conduct actuation, so that cooperative pressure control of pulse feeling floating, middle-sinking accurate alignment and accurate local pressure control of arterial blood vessels are realized, and accurate continuous blood pressure detection is achieved; the lightweight fabric fiber artificial muscle actuator is convenient for realizing the wearable pulse condition detection equipment; through the structural cooperation of upper electrode, flexible supporting layer, lower electrode, actuator and circuit board, when realizing that the actuator drives flexible multi-functional layer and accurate exerting pressure and pressure detection, the furthest optimizes required occupation space, solves the wiring difficult problem that the electrode quantity is numerous and brings, realizes satisfying pulse condition sensor miniaturization requirement.

As an exemplary illustration, on the basis of the above-mentioned tactile sensor structure, when the capacitance value of each electrode is collected by matching with a high-conversion rate chip with a chip conversion rate of 0.5ms or more, the human blood flow velocity is less than 20mm/s, in other words, 20/2000=0.01 mm/ms, in other words, the normal force resolution of 0.01 gram can be achieved, which exceeds the pressure resolution capability (0.02 gram) of the fingers of the expert of traditional Chinese medicine. The high conversion rate chip can be an R-SpiNNaker chip, achieves 24-bit high-speed CDC, has an effective resolution of 21.9 bits and a conversion time of 0.5ms, and can support high-precision touch signal acquisition and encoding; the function core and SNN core architecture supports complex quasi-neural state calculation by using small-scale neurons, and can realize real-time single-chip pulse classification; the quasi-neural state sensing, calculating and executing integrated structure can support high-precision pulse diagnosis pressure control and pulse classification data processing by a single chip, and the details can be referred to patent data CN202110956246.6.

In the utility model, the upper electrode can be used as a common electrode, the lower electrodes are provided with at least two mutually insulated electrodes, and the common electrode forms different capacitances for the lower electrodes to reflect the components of the force in different directions; alternatively, the lower electrode is used as a common electrode, and the upper electrodes are at least two and insulated from each other, and the common electrode forms different capacitances for the respective upper electrodes to reflect components of force in different directions.

Furthermore, the circuit board can be a PCB hard board or an FPCB board, wherein the FPCB board is preferably adopted to enable the pulse condition sensor of the wearable pulse condition detection device such as a wristwatch to have better performance in terms of bionics. The top surface of the flexible supporting layer is an arc surface or a plane.

As an improvement scheme, the circuit board can be arranged as two layers of upper and lower layers of mutually electric connection, wherein the lower layer circuit board is positioned below the actuator, the upper layer circuit board is arranged below the flexible multifunctional layer, the position of the upper layer circuit board aligned with the flexible supporting layer is provided with an avoidance hole through which the flexible supporting layer can pass, and the upper layer electrode is electrically connected with the upper layer circuit board through the flexible multifunctional layer. In this improvement scheme, the lower floor electrode passes through flexible supporting layer and connects the lower floor circuit board, and upper electrode passes through flexible multi-functional layer and connects the upper circuit board, connects upper and lower floor circuit board electricity again, can maximize the optimization wiring structure, reduces the wiring degree of difficulty, reaches the reliable connection of multiple electrode under the miniaturized condition, reduces the detection interference that the circuit brought. More preferably, the capacitive pulse condition sensor can be further provided with an artificial muscle positioning block, the artificial muscle positioning block is provided with a containing groove, the flexible supporting layer and the actuator are arranged in the containing groove for positioning and supporting, at the moment, the lower circuit board is fixed on the bottom surface of the artificial muscle positioning block, and the upper circuit board is fixed on the top surface of the artificial muscle positioning block, so that the overall stability of the structure is improved.

Further, the flexible support layer and the lower electrode are integrally formed by bicolor molding of a flexible insulator and a flexible conductor, wherein the insulator separates the conductor into the lower electrode, and the bottom of the lower electrode extends downwards to be electrically connected with a circuit board below the actuator.

The artery of the human body is of a tubular structure, the flow of blood in the artery is periodic, the flow direction of the blood is taken as X direction, the pressure change is reflected as Z direction (normal direction) bulge information caused by the blood in the wall of the artery when the heart pumps blood, the X direction can reflect the direction type information of the flow of the blood, and the Y direction can reflect the thickness of the blood vessel. For blood pressure detection, information on pressure change is more important, and the flow direction and the thickness of blood vessels are used as auxiliary information.

As a further development, the flexible multifunctional layer may be provided with the following structure:

(1) The device comprises a spherical or ellipsoidal first flexible multifunctional layer, wherein at least one of an upper electrode and a lower electrode below the first flexible multifunctional layer is at least three in number, for example, the upper electrode is used as a common electrode, and the lower electrode forms a matrix, so that the XYZ directional resolution of force can be obtained;

(2) The touch sensor comprises a strip-shaped second flexible multifunctional layer, at least one of an upper electrode and a lower electrode below the second flexible multifunctional layer is at least two, each electrode of the at least two electrodes is distributed on two sides of the strip of the second flexible multifunctional layer, the second flexible multifunctional layer can drive the upper electrode to change the contact area with an insulating layer due to stress deformation in the radial direction of the strip of the second flexible multifunctional layer, for example, the upper electrode is used as a public electrode, the lower electrode is two and distributed on two sides of a broken line A, the broken line A is distributed along the X direction, at the moment, the touch sensor can obtain Y-direction resolution in addition to Z-direction resolution of the obtained force, and meanwhile, due to the advantages of channel distribution pressure and cost reduction caused by the reduction of the number of the electrodes, the broken line A can be distributed along the Y direction so as to obtain X-direction resolution; the above-mentioned is the situation that the long strip extending direction of the second flexible multi-functional layer is the same, for the situation that the long strip extending direction is different, for example, the upper electrode is regarded as the public electrode, the lower electrode of every sensor unit is two, the lower electrode of some sensor units is distributed on both sides of the broken line A, the lower electrode of some sensor units is distributed on both sides of the broken line B, one of the broken line A, broken line B is set up along X direction of the coordinate axis, another one inclines or perpendicular to X direction, can reach the high resolution in XYZ direction, every node in the array has Z direction resolving power at the same time, and the quantity of electrode matrix is reduced to the quantity of the required channel of two whole arrays from four to the lowest, the cost is reached and controlled optimally, furthermore, can set up one of broken line A, broken line B along X direction of the coordinate axis, another one along Y direction, make two perpendicular, except all possess Z direction detecting capability, one is used for obtaining X direction one and is used for obtaining Y direction and not interfering each other;

(3) The sensor array may further comprise the sum of the schemes (1) and (2), for example, the sensor array comprises at least one first sensor unit and at least one second sensor unit; each first sensor unit is provided with a spherical or ellipsoidal first flexible multifunctional layer, each second sensor unit is provided with a second flexible multifunctional layer, in the first sensor unit, at least one of an upper electrode and a lower electrode of the first sensor unit is at least three, in the second sensor unit, at least one of the upper electrode and the lower electrode of the second sensor unit is at least two, at the moment, the first sensor unit can achieve high resolution in the XYZ direction, the second sensor unit at least has high resolution in the Z direction, an array formed by the two sensor units is convenient for aligning a size and detecting pressure, meanwhile, the number of electrode matrixes of the second sensor units is reduced from four to two at least, the number of channels required by the whole array is greatly reduced, and the cost is controllable. In the scheme (3), the first sensor units and the second sensor units in each row and each column in the array can be alternately arranged, and as the blood vessels are in a strip shape, the alternating arrangement mode can ensure that at least one of the adjacent second sensor units is also contacted with the blood vessels under the condition that the first sensor units are contacted with the blood vessels.

As another improvement, the sensor can be further provided with a correlation organization, the correlation organization is made of flexible materials and is connected with the flexible multifunctional layers of the sensor units, and the correlation organization is used for correlating the stress of any area on the surface of the pulse condition sensor to the flexible multifunctional layers of at least two sensor units closest to the stress point. Through the association organization arranged on the flexible multifunctional layer of each sensor unit, stress in any area on the surface of the association organization is associated to the peripheral unit package, and the position of a stress point can be calculated through the data of the peripheral unit package, so that the detection blind area is solved. More preferably, the associated tissue can be set to be a flexible tectorial membrane, in the scheme, the outer surface of the flexible multifunctional layer of each sensor unit is covered by the flexible tectorial membrane, when the surface of the associated tissue is stressed, the peripheral unit bags are pulled by the flexible tectorial membrane to realize stress association, so that the problems of motion interference and noise removal can be improved; alternatively, the association tissue can be provided as a flexible filling and filled between flexible multifunctional layers of any sensor unit, and at this time, the association tissue surface is stressed to push the peripheral unit package to realize stress association through the flexible filling. The two schemes can be combined, and meanwhile, the flexible coating and flexible filling are arranged, so that association and restraint are realized through push-pull combination. Further, the associated tissue may be provided to be insulating or conductive. In one case, the associated tissue is arranged in an insulating manner, and at this time, the flexible multifunctional layers of each sensor unit can be insulated, and the touch sense detection function is realized by taking the flexible multifunctional layers as electrodes and combining the electrodes of each flexible multifunctional layer; alternatively, the flexible multifunctional layers of the sensor units are mutually conductive, and the associated organization is used for protecting the flexible multifunctional layers. In another case, the associated tissue is electrically conductive, and is arranged in an insulating manner between the associated tissue and the flexible multifunctional layer of each sensor unit, and the associated tissue is used as a shielding electrode; alternatively, the associated tissue is provided in electrical connection with the flexible multifunctional layer of each sensor unit, in which case the associated tissue may be integrally formed with each flexible multifunctional layer or may be electrically connected to the multifunctional layer by means of a conductive member such as a conductive adhesive.

As another improvement, the flexible multifunctional layer and the upper electrode are integrally provided. The flexible multifunctional layer can be arranged in a sphere, an ellipsoid or a bar shape on the basis of forming the capacitive combinations in different vector directions. The flexible multifunctional layer is arranged in a spherical shape or an ellipsoidal shape, so that a good deformation effect of stress in the XYZ direction can be achieved, and the strip shape of the flexible multifunctional layer influences the stress deformation in the strip-shaped extending direction. The optimal choice of the upper electrode is to form the same shape with the flexible multifunctional layer, for example, when the flexible multifunctional layer is arranged in a spherical shape or an ellipsoidal shape, the upper electrode is also arranged in the spherical shape or the ellipsoidal shape to achieve the optimal resolution effect, or when the flexible multifunctional layer is in a strip shape, the upper electrode is arranged in a strip shape parallel to the flexible multifunctional layer.

The wearable pulse condition detection device comprises the capacitive pulse condition sensor.

Drawings

FIG. 1 is a schematic diagram of a capacitive pulse condition sensor and a wearable pulse condition detection device.

Fig. 2 is a schematic wearing diagram of the capacitive pulse condition sensor and the wearable pulse condition detection device.

FIG. 3 is a schematic diagram of a capacitive pulse condition sensor and a wearable pulse condition detection device in a flattened state.

FIG. 4 is an exploded schematic view of a capacitive pulse condition sensor and a wearable pulse condition detection device.

FIG. 5 is a schematic diagram of the lower electrode unit of the capacitive pulse condition sensor.

FIG. 6 is a schematic diagram showing the distribution of the upper and lower electrodes of the capacitive pulse condition sensor unit.

FIG. 7 is a schematic illustration of a cross-sectional structure of a capacitive pulse condition sensor.

FIG. 8 is a schematic diagram illustrating the operation of the artificial muscle of the capacitive pulse condition sensor.

Detailed Description

The technical solutions in the embodiments of the present utility model will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present utility model.

As shown in fig. 1, in this embodiment, a capacitive pulse condition sensor and a wearable pulse condition detection device are provided. The present detection device includes a capacitive pulse condition sensor 10, and a wearable wrist 20 with a display. When the device is worn on the wrist as in fig. 2, the sensing area of the pulse condition sensor can completely cover and cling to the pulse area of the cunguan ruler of the wrist.

As shown in FIG. 3, the capacitive pulse condition sensor is entirely of a flexible material and can be placed flat when the pulse condition detection apparatus is not being worn. As shown in fig. 4, the capacitive pulse condition sensor includes: the upper electrode multifunctional layer 100 is made of conductive silica gel by molding; the lower electrode group 200 is made of insulating silica gel and conductive silica gel by molding with a double-color mold; an FPC flexible circuit board 400; the flexible positioning block 500 is made of conductive silica gel by molding a mold; CDC and control chip 600; a flexible wrist 700.

As shown in fig. 5, the electrode unit 201 in the lower electrode group is formed by molding an insulating silicone and a conductive silicone two-color mold. And the surface is sprayed with insulating paint. Wherein the 201-5 insulating cross divides the conductive silicone into 4 electrodes 201-1, 201-2, 20-3, 201-4. As shown in fig. 6, one sensing cell 101 of the upper common electrode layer is a round pack, which forms capacitances C1-1, C1-2, C1-3, C1-4 with electrode cell arrays 201-1, 201-2, 201-3, 201-4 in the lower electrode group, respectively. The outer hemispherical convex surface receives external forces in different directions. The inner hemisphere is tangent to the surface of the lower electrode unit, and theoretically the hemisphere of the upper electrode is in point contact with the insulating paint on the surface of the lower electrode unit, and the contact point is just in the center of the electrode 201 group. When the outer surface is acted by wrist pulse beating pressure 800, the flexible upper electrode deforms, and the hemisphere of the upper electrode and the insulating ink on the surface of the PCB can be easily converted into small-area contact from the previous point contact, so that the C1 capacitance group is changed to sense wrist pulse beating.

As shown in the schematic cross-sectional view of fig. 7, the artificial muscle units 301 are placed inside the lower electrode unit 201, and they are fixed in the through holes of the positioning block 500. The lower electrode passes through the through hole of the positioning block and the flexible circuit board and is contacted with the upper electrode. As shown in fig. 8, when the artificial muscle unit is applied with voltage, the artificial muscle is deformed and stretched to push the lower electrode unit and the upper electrode to locally stretch and protrude to press the wrist, so as to simulate the pressing of the traditional Chinese medicine fingers on the pulse with different degrees, achieve the aim of controlling the floating, middle and sinking pressure, and further realize the measurement of complex pulse condition changes.

As shown in fig. 4, since four upper electrodes 201-1, 201-2, 20-3, and 201-4 are added to the single sensor unit to be electrically connected, in order to solve the wiring problem, the FPC flexible circuit board 400 is disposed as an upper layer and a lower layer and then electrically connected sideways, wherein the lower circuit board is located below the artificial muscle unit 301, the upper circuit board is located below the flexible multifunctional layer 100, the upper circuit board is provided with a relief hole aligned to the flexible supporting layer, and electrically connected to the upper circuit board through the flexible multifunctional layer, and the artificial muscle unit 301 and the lower electrodes 201-1, 201-2, 20-3, and 201-4 are connected to the lower circuit board through the bottoms thereof.

Finally, it should be noted that the above embodiments are only for illustrating the technical solution of the present utility model, and not for limiting the scope of the present utility model, and although the present utility model has been described in detail with reference to the preferred embodiments, it should be understood by those skilled in the art that modifications or equivalent substitutions can be made to the technical solution of the present utility model without departing from the spirit and scope of the technical solution of the present utility model.

Claims (11)

1. A capacitive pulse condition sensor, characterized by:

the sensor comprises at least two sensor units, wherein each sensor unit is provided with a flexible multifunctional layer, an upper electrode electrically connected with the multifunctional layer is arranged in each multifunctional layer, and the upper electrode is a curved elastic electrode;

a flexible supporting layer is arranged below the upper electrode, a lower electrode is arranged on the top surface of the flexible supporting layer, an insulating layer is arranged between the upper electrode and the lower electrode, the downward projection of the upper electrode at least covers part of the area of each lower electrode, the flexible multifunctional layer is deformed by external force to drive the upper electrode to change the contact area with the insulating layer, at least one of the upper electrode and the lower electrode is at least two, and different capacitances are formed between the upper electrode and the lower electrode to reflect the components of the force in different directions;

the flexible support layer is internally provided with a fiber artificial muscle actuator, the actuator has expansion capacity in the direction of the upper electrode, a circuit board electrically connected with the actuator is arranged below the actuator, the flexible support layer is fixed on the circuit board and is provided with an electric conduction path for electrically connecting the lower electrode and the circuit board, and the upper electrode is electrically connected with the circuit board.

2. The capacitive pulse condition sensor of claim 1, wherein: the circuit board is a PCB hard board or an FPCB board.

3. The capacitive pulse condition sensor of claim 1, wherein the upper electrode is electrically connected to the circuit board in a manner that further comprises:

the circuit board is provided with an upper layer and a lower layer which are electrically connected with each other;

the lower circuit board is positioned below the actuator, the upper circuit board is arranged below the flexible multifunctional layer, the position of the upper circuit board aligned with the flexible supporting layer is provided with an avoidance hole through which the flexible supporting layer can pass, and the upper electrode is electrically connected with the upper circuit board through the flexible multifunctional layer.

4. A capacitive pulse condition sensor according to claim 3, characterized in that: the flexible support layer and the actuator are arranged in the accommodating groove, the lower circuit board is fixed on the bottom surface of the artificial muscle positioning block, and the upper circuit board is fixed on the top surface of the artificial muscle positioning block.

5. The capacitive pulse condition sensor of claim 1, wherein: the top surface of the flexible supporting layer is an arc surface or a plane.

6. A capacitive pulse condition sensor according to claim 1 or 3, characterized in that: the flexible supporting layer and the lower electrode are integrally formed through double-color forming of a flexible insulator and a flexible conductor, wherein the insulator separates the conductor into the lower electrode, and the bottom of the lower electrode extends downwards to be electrically connected with a circuit board below the actuator.

7. The capacitive pulse condition sensor of claim 1, wherein:

the flexible multifunctional layer comprises a spherical or ellipsoidal first flexible multifunctional layer, and the number of at least one of an upper electrode and a lower electrode below the first flexible multifunctional layer is at least three; and/or

The flexible multifunctional layer comprises a strip-shaped second flexible multifunctional layer, at least one of an upper electrode and a lower electrode below the second flexible multifunctional layer is at least two, each electrode of the at least two electrodes is distributed on two sides of the strip of the second flexible multifunctional layer, and the second flexible multifunctional layer can drive the upper electrode to change the contact area with the insulating layer under the stress deformation of the strip-shaped second flexible multifunctional layer in the radial direction.

8. The capacitive pulse condition sensor of claim 7, wherein: the elongated strips of each second flexible multifunctional layer extend in the same or different directions.

9. The capacitive pulse condition sensor of claim 1, wherein: the capacitive pulse condition sensor further comprises a correlation organization which is made of flexible materials and is connected with the flexible multifunctional layers of the sensor units, and the correlation organization is used for correlating the stress of any area on the surface of the capacitive pulse condition sensor to the flexible multifunctional layers of at least two sensor units closest to the stress point.

10. The capacitive pulse condition sensor of claim 9, wherein:

the related tissue is a flexible tectorial membrane, and the outer surface of the flexible multifunctional layer of each sensor unit is covered by the flexible tectorial membrane; and/or

The associated organization is a flexible filling and fills in between the flexible multifunctional layers of any of the sensor units.

11. A wearable pulse condition detection device is characterized in that: comprising a capacitive pulse condition sensor as defined in any one of claims 1-10.

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