Wearable heart sound signal sensor, preparation method and application

Abstract

The invention discloses a wearable heart sound signal sensor, a preparation method and application, relates to the technical field of sensors, and aims to solve the problem of research and development of a product capable of monitoring human body acoustic physiological signals in real time and with high quality. Standing for 10 minutes in a vacuum environment; putting the mold into a forced air drying oven, curing for 25 minutes at the temperature of 90 DEG C, and taking out the polymer from the mold after curing to obtain a cured packaging layer; pasting a mask plate on the packaging layer, and evaporating a patterned electrode through a thermal evaporation method; a wire is led out from the electrode, the top packaging layer and the bottom packaging layer are folded, a gap is coated with polymer liquid, curing is carried out at a certain temperature, and a hollow sensor is obtained; and injecting the electrolyte solution into the sensor, coating an injection hole with a polymer liquid, and curing at a certain temperature to obtain the wearable acoustic physiological signal sensor.

Description

Technical Field

[0001] This invention relates to the technical field of flexible sensors, specifically to a wearable heart sound signal sensor, its fabrication method, and its application. Background Technology

[0002] Since the beginning of the 21st century, with the development of the economy and digitalization and informatization, the demand for precision medicine has risen sharply, giving rise to an urgent need for the deep integration of traditional medical technologies and the digital space. Traditional human body sensors, due to their rigid and inflexible nature, suffer from limitations such as size constraints, poor biocompatibility, and poor skin adhesion, making it difficult to maintain long-term stable monitoring in dynamic human environments. This demand has driven the development of flexible wearable electronic devices.

[0003] Since Laennec invented the stethoscope in 1816, the medical value of acoustic physiological signals has been increasingly recognized. Acoustic physiological signals such as heart sounds, breath sounds, and bowel sounds carry crucial pathological information about the cardiovascular, respiratory, and digestive systems. However, traditional stethoscopes have always faced many limitations, including excessive subjectivity, inability to track and detect in real time, and difficulties in quantitative analysis. This empirical approach to medicine cannot meet today's demands for precision medicine. While some solutions exist to address these issues, electronic stethoscopes are expensive and cannot provide real-time tracking and monitoring. Wearable sensors based on solid-state materials also suffer from acoustic impedance mismatch and poor signal quality. Therefore, there is an urgent need for a product that can achieve real-time, high-quality monitoring of human acoustic physiological signals. Summary of the Invention

[0004] This invention aims to solve the problem of developing a product capable of real-time, high-quality monitoring of human acoustic physiological signals. It proposes a wearable heart sound signal sensor, which includes, from top to bottom, a top encapsulation layer, a top electrode, an electrolyte solution, a bottom electrode, and a bottom encapsulation layer.

[0005] This invention also proposes a method for fabricating a wearable heart sound signal sensor as described above, which includes the following steps: S1: Pour the stirred polymer liquid into the encapsulation layer mold and let it stand in a vacuum environment for 10 minutes; S2: Place the mold from step S1 into a forced-air drying oven and cure it at 90°C for 25 minutes. After curing, remove the polymer from the mold to obtain the cured encapsulation layer. S3: A mask is pasted onto the encapsulation layer in step S2, and a patterned electrode is deposited by thermal evaporation. S4: Lead wires out from the electrodes in step S3, close the top encapsulation layer and the bottom encapsulation layer, apply polymer liquid to the gap, and cure at a certain temperature to obtain a hollow sensor; S5: Inject the electrolyte solution into the sensor from step S4, coat the injection hole with polymer liquid, and cure it at a certain temperature to obtain a wearable acoustic physiological signal sensor.

[0006] A further provision of the present invention is that the polymer liquid is selected from polydimethylsiloxane (PDMS) or Eco-flex.

[0007] A further setting of the present invention is that the vacuum degree of the vacuum environment in step S1 is 200 Pa.

[0008] A further provision of the present invention is that the electrode material thermally vapor-deposited in step S3 is one or more of gold, silver, and copper.

[0009] A further setting of the present invention is that the curing temperature in step S4 is 90°C and the curing time is 20 min.

[0010] A further provision of the present invention is that the electrolyte solution in step S5 is one of NaCl, LiCl, LiF, and H3PO4, with a concentration of 0.05-1 mol / L.

[0011] A further setting of the present invention is that the curing temperature in step S5 is 30°C and the curing time is 12h.

[0012] The present invention also proposes an application of the wearable heart sound signal sensor as described above, which is used in real-time monitoring of human acoustic physiological signals and in medical devices.

[0013] The beneficial effects of this invention are as follows:

[0014] 1. This invention uses flexible materials to prepare the PDMS-electrolyte solution composite system, and the acoustic impedance of the PDMS-electrolyte solution composite system is matched with the acoustic impedance of the human skin system. Compared with diaphragm solid material sensors, it can collect human acoustic physiological signals with high precision and low loss. In addition, it can adapt to complex skin surfaces and meet the needs of human physiological information collection.

[0015] 2. This invention, based on capacitive sensing technology, can be applied to the real-time monitoring of various human acoustic physiological signals, including heart sounds, respiratory sounds, and bowel sounds. It can accurately and reliably reflect the health status of the human cardiopulmonary and intestinal systems, thereby promoting its application in the fields of smart healthcare and precision medicine. The preparation method of this invention is simple and quick, making it easier for large-scale production and promotion. Attached Figure Description

[0016] Figure 1 The diagram shows the structure and equivalent circuit diagram of the wearable acoustic physical signal sensor proposed in Embodiment 1.

[0017] Figure 2The schematic diagram of the sensing process of the wearable acoustic physical signal sensor proposed in Example 1 is shown.

[0018] Figure 3 An image of the encapsulation layer of the vapor-deposited gold electrode prepared in Example 3 is shown.

[0019] Figure 4 An image of the wearable acoustic physiological signal sensor prepared in Example 3 is shown.

[0020] Figure 5 The image shows the human heart acoustic physiological signal collected by the wearable acoustic physiological signal sensor prepared in Example 3.

[0021] Figure 6 The spectral distribution of the human heart acoustic physiological signal collected by the wearable acoustic physiological signal sensor prepared in Example 3 is shown.

[0022] Figure 7 The diagram shows a pulse wave signal obtained by filtering the human heart acoustic physiological signal collected by the wearable acoustic physiological signal sensor prepared in Example 3.

[0023] Figure 8 The diagram shows a heart sound signal obtained by filtering the human heart acoustic physiological signal collected by the wearable acoustic physiological signal sensor prepared in Example 3.

[0024] Figure 9 The diagram shows the heart sound signal and its time-frequency plot obtained by filtering the human heart acoustic physiological signal collected by the wearable acoustic physiological signal sensor prepared in Example 3.

[0025] Figure 10 The image shows the human heart acoustic physiological signal collected by the wearable acoustic physiological signal sensor prepared in Example 4.

[0026] Figure 11 The diagram shows a heart sound signal obtained by filtering the human heart acoustic physiological signal collected by the wearable acoustic physiological signal sensor prepared in Example 4. Detailed Implementation

[0027] Those skilled in the art can refer to the content of this document and appropriately improve the process parameters to achieve the desired results. It should be particularly noted that all similar substitutions and modifications are obvious to those skilled in the art and are considered to be included in this invention. The methods and applications of this invention have been described through preferred embodiments. Those skilled in the art can make modifications or appropriate alterations and combinations to the methods and applications described herein without departing from the content, spirit, and scope of this invention to implement and apply the technology of this invention.

[0028] Example 1

[0029] This invention proposes a wearable acoustic physiological signal sensor, comprising, from top to bottom, a top encapsulation layer, a top electrode, an electrolyte solution, a bottom electrode, and a bottom encapsulation layer.

[0030] Example 2

[0031] A method for fabricating a wearable heart sound signal sensor as described in Example 1 includes the following steps:

[0032] S1: Pour the stirred polymer liquid into the encapsulation layer mold and let it stand in a vacuum environment for 10 minutes.

[0033] S2: Place the mold from step S1 into a forced-air drying oven and cure it at 90°C for 25 minutes. After curing, remove the polymer from the mold to obtain the cured encapsulation layer.

[0034] S3: A mask template is pasted onto the encapsulation layer in step S2, and a patterned electrode is deposited by thermal evaporation.

[0035] S4: Lead wires out from the electrodes in step S3, close the top and bottom encapsulation layers, apply polymer liquid to the gaps, and cure at a certain temperature to obtain a hollow sensor.

[0036] S5: Inject the electrolyte solution into the sensor from step S4, coat the injection hole with polymer liquid, and cure it at a certain temperature to obtain a wearable acoustic physiological signal sensor.

[0037] The polymer liquid is made of polydimethylsiloxane (PDMS) or Eco-flex.

[0038] In step S1, the vacuum level of the vacuum environment is 200 Pa.

[0039] In step S3, the electrode material for thermal evaporation is one or more of gold, silver, and copper.

[0040] The curing temperature in step S4 is 90°C and the curing time is 20 minutes.

[0041] The electrolyte solution in step S5 is one of NaCl, LiCl, LiF, and H3PO4, with a concentration of 0.05-1 mol / L.

[0042] The curing temperature in step S5 is 30℃, and the curing time is 12h.

[0043] Example 3

[0044] This embodiment uses the preparation method described in Example 2 to prepare a wearable heart sound signal sensor, including the following steps:

[0045] S1: Pour the stirred PDMS liquid into the encapsulation layer mold and let it stand for 10 minutes in a vacuum environment with a vacuum degree of 300Pa.

[0046] S2: Place the mold in which PDMS liquid was poured in step S1 into a forced-air drying oven and cure it at 90°C for 25 minutes. After curing, remove the polymer from the mold to obtain the cured encapsulation layer.

[0047] S3: A mask is pasted onto the encapsulation layer in step S2, and a patterned electrode made of gold is deposited by thermal evaporation.

[0048] S4: Lead wires out from the electrodes in step S3, join the top and bottom encapsulation layers, apply PDMS liquid to the gap, and cure at 90°C for 20 minutes to obtain a hollow sensor.

[0049] S5: Inject 0.1 mol / L NaCl into the hollow sensor from step S4, coat the injection hole with PDMS liquid, and cure at 30°C for 12 hours to obtain a wearable acoustic physiological signal sensor.

[0050] It should be noted that the acoustic physiological signals mentioned in this invention include signals such as heart sounds, respiratory sounds, and bowel sounds.

[0051] Example 4

[0052] This embodiment uses the preparation method described in Example 2 to prepare a wearable heart sound signal sensor, including the following steps:

[0053] S1: Pour the stirred PDMS liquid into the encapsulation layer mold and let it stand for 10 minutes in a vacuum environment with a vacuum degree of 300Pa.

[0054] S2: Place the mold in which PDMS liquid was poured in step S1 into a forced-air drying oven and cure it at 90°C for 25 minutes. After curing, remove the polymer from the mold to obtain the cured encapsulation layer.

[0055] S3: A mask is pasted onto the encapsulation layer in step S2, and a patterned electrode made of gold is deposited by thermal evaporation.

[0056] S4: Lead wires out from the electrodes in step S3, join the top and bottom encapsulation layers, apply PDMS liquid to the gap, and cure at 90°C for 20 minutes to obtain a hollow sensor.

[0057] S5: Inject 0.05mol / L H3PO4 solution into the hollow sensor from step S4, coat the injection hole with PDMS liquid, and cure at 30°C for 12 hours to obtain a wearable acoustic physiological signal sensor.

[0058] It should be noted that the acoustic physiological signals mentioned in this invention include signals such as heart sounds, respiratory sounds, and bowel sounds.

[0059] Example 5

[0060] This embodiment discloses an application of the wearable acoustic physiological signal sensor as described in Embodiment 1, which is applied to the real-time monitoring of human acoustic physiological signals and the field of smart healthcare. The acoustic physiological signals include heart sounds, respiratory sounds, and bowel sounds. (Reference) Figure 9 This demonstrates the ability of wearable acoustic physiological signal sensors to collect human heart sounds and perform time-frequency analysis, thereby enabling the assessment of heart health and showcasing its application in the fields of smart healthcare and precision medicine.

[0061] In summary, this invention designs an impedance matching structure, enabling the sensor to acquire human acoustic physiological signals with high precision and low loss. Furthermore, this invention can also be applied to the real-time monitoring of various human acoustic physiological signals, including heart sounds, respiratory sounds, and bowel sounds, accurately and reliably reflecting the health status of the cardiopulmonary and intestinal systems, thereby promoting its application in smart healthcare and precision medicine. The preparation method of this invention is simple and rapid, making it easier for large-scale production and promotion.

[0062] The above description is only a preferred embodiment of the present invention. It should be noted that for those skilled in the art, several improvements and modifications can be made without departing from the principle of the present invention, and these improvements and modifications should also be within the scope of protection of the present invention.

Claims

1. A wearable heart sound signal sensor, characterized in that, It includes, from top to bottom, a top encapsulation layer, a top electrode, an electrolyte solution, a bottom electrode, and a bottom encapsulation layer.

2. A method for fabricating a wearable heart sound signal sensor as described in claim 1, characterized in that, It includes the following steps: S1: Pour the stirred polymer liquid into the encapsulation layer mold and let it stand in a vacuum environment for 10 minutes; S2: Place the mold from step S1 into a forced-air drying oven and cure it at 90°C for 25 minutes. After curing, remove the polymer from the mold to obtain the cured encapsulation layer. S3: A mask is pasted onto the encapsulation layer in step S2, and a patterned electrode is deposited by thermal evaporation. S4: Lead wires out from the electrodes in step S3, close the top encapsulation layer and the bottom encapsulation layer, apply polymer liquid to the gap, and cure at a certain temperature to obtain a hollow sensor; S5: Inject the electrolyte solution into the sensor from step S4, coat the injection hole with polymer liquid, and cure it at a certain temperature to obtain a wearable acoustic physiological signal sensor.

3. The method for fabricating a wearable heart sound signal sensor according to claim 2, characterized in that, The polymer liquid is made of polydimethylsiloxane (PDMS) or Eco-flex.

4. The method for fabricating a wearable heart sound signal sensor according to claim 2, characterized in that, The vacuum level of the vacuum environment in step S1 is 200 Pa.

5. The method for fabricating a wearable heart sound signal sensor according to claim 2, characterized in that, The electrode material thermally vapor-deposited in step S3 is one or more of gold, silver, and copper.

6. The method for fabricating a wearable heart sound signal sensor according to claim 2, characterized in that, The curing temperature in step S4 is 90°C and the curing time is 20 min.

7. The method for fabricating a wearable heart sound signal sensor according to claim 2, characterized in that, The electrolyte solution in step S5 is one of NaCl, LiCl, LiF, and H3PO4, with a concentration of 0.05-1 mol / L.

8. The method for fabricating a wearable heart sound signal sensor according to claim 2, characterized in that, The curing temperature in step S5 is 30°C and the curing time is 12 hours.

9. An application of the wearable heart sound signal sensor as described in claim 1, characterized in that, It is applied to the real-time monitoring of human acoustic physiological signals and in medical equipment.

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