OSAHS identification device

Abstract

The invention belongs to the technical field of wearable equipment, and particularly relates to an OSAHS recognition device. On one hand, the piezoelectric polyester elastomer film is excellent in flexibility and environment-friendly, and the piezoelectric acoustic device prepared from the piezoelectric polyester elastomer film is excellent in acoustic performance; on the other hand, the piezoelectric acoustic sensor adopts a highly integrated accessory product or a split type, so that the wearing part does not bring strong foreign body sensation to the target object, and the snore data acquisition accuracy of the target diagnosis object is improved; the snore data incorrectness caused by the fact that the sleep quality is influenced by too strong external interference in the sleep of the target object is avoided; and on the other hand, the data analysis and processing result is more accurate through a more powerful database for data processing arranged at the network end. Finally, the problems that an existing OSAHS diagnosis technology is complex in test operation and high in medical cost, and a test result may be inaccurate due to test conditions are effectively solved.

Description

Technical Field

[0001] The present invention belongs to the technical field of wearable devices, and in particular relates to an OSAHS recognition device. Background Art

[0002] Obstructive sleep apnea-hypopnea syndrome (OSAHS) is a common sleep breathing disorder caused by upper airway collapse or central nervous system regulation disorders, resulting in weak or even paused breathing during sleep at night. This can lead to decreased blood oxygen saturation and nighttime awakenings, thereby increasing the risk of a series of cardiovascular complications such as hypertension, ischemic heart disease, stroke, and neurocognitive dysfunction.

[0003] The current standard method for diagnosing OSAHS is the polysomnography (PSG) test. However, this method requires patients to attach a large number of electrode wires in a sleep laboratory to wear more than 20 sensors to record physiological signals, which will have a certain degree of impact on the patient's sleep quality, which may lead to an incorrect assessment of the severity of OSAHS. At the same time, the PSG test requires professional equipment and professionals to operate the instrument, which will make the disease difficult to detect and diagnose due to high health costs.

[0004] Snoring is an early symptom of OSAHS patients. Compared with the PSG test diagnostic criteria, the sensitivity and accuracy of snoring analysis in diagnosing OSAHS can reach about 90% of PSG test at the same time. However, the low cost and simplicity of snoring make it have obvious advantages in diagnosing OSAHS. However, there is a relative lack of wearable devices for diagnosing OSAHS through snoring analysis, and factors such as the accuracy of data collection and the reliability of the analysis algorithm will significantly affect the accuracy of the final diagnosis results.

[0005] With the advancement of science and technology, as well as the upgrade of device preparation materials and the improvement of integration, if highly integrated wearable high-precision equipment can be used to diagnose OSAHS, it will greatly benefit the diagnosis, treatment and monitoring of OSAHS. Summary of the invention

[0006] In view of the above-mentioned problems or deficiencies, in order to solve the problems of complicated test operation, high medical cost and inaccurate test results due to test conditions in the existing OSAHS diagnostic technology, the present invention provides an OSAHS identification device. The present invention is based on a piezoelectric elastomer material with a flexible segment, and uses its own material properties to make it into a piezoelectric acoustic sensor, and the piezoelectric acoustic sensor is made into a wearable OSAHS identification device for OSAHS identification; and further optimizes the accuracy of data collection to effectively improve the accuracy of the equipment analysis results. .

[0007] The specific technical solutions of the present invention are as follows:

[0008] An OSAHS recognition device comprises a piezoelectric acoustic sensor and a data processing module.

[0009] The piezoelectric acoustic sensor is prepared by using electrodes on both sides of a piezoelectric polyester elastomer film, which are led out with wires to collect the snoring sound of a target diagnostic object.

[0010] The data processing module compares and analyzes the snoring data collected by the piezoelectric acoustic sensor with its own database and gives the comparison and analysis results. The database is composed of prior disease diagnosis data.

[0011] Furthermore, the thickness of the OSAHS identification device does not exceed 2 mm, and when in use, it is attached to the snoring sound source in the form of a dressing (such as a plaster) within 10 cm to ensure the accuracy of the monitored snoring data collection.

[0012] Furthermore, the OSAHS identification device is attached to the flat area of ​​the pectoralis major epidermis of the target diagnosis object in the form of a dressing to ensure the accuracy of the collection of the monitored snoring data.

[0013] Furthermore, the OSAHS identification device is attached to the flat forehead area of ​​the target diagnosis object in the form of a dressing to ensure the accuracy of the monitored data collection.

[0014] Furthermore, the OSAHS identification device is worn on the wrists of the target diagnosis subject in the form of a wristband, and is worn on both wrists to ensure the accuracy of the collection of monitored snoring data.

[0015] Furthermore, the data processing module is a split device that is externally connected to reduce the size of the piezoelectric acoustic sensor of the wearable component, which is beneficial for not affecting the normal sleep of the target diagnostic subject during use, making the collected data more accurate.

[0016] Furthermore, the data processing module is arranged at the network end (by being arranged at a remote server or network cloud) to provide a more powerful and comprehensive database for post-processing of the snoring data, so that the analysis result is more accurate.

[0017] Furthermore, the external connectivity of the data processing module is wireless communication.

[0018] Furthermore, the preparation method of the piezoelectric polyester elastomer film is:

[0019] Step 1: Mix cis-1,4-butenediol, 1,3-propylene glycol, 1,4-butanediol, succinic acid and sebacic acid in a molar ratio of 0.05:0.225:0.225:0.35:0.15 to obtain a mixture A.

[0020] Step 2: Add 0.01 wt% of the antioxidant phosphorous acid and 0.04 wt% of the polymerization inhibitor hydroquinone to the mixture A, mix well in sequence, and then place in a 180° C. water bath and heat and stir for 2 h under a nitrogen atmosphere to obtain an oligomer.

[0021] Step 3: Add tetrabutyl titanate catalyst accounting for 0.1 wt% of mixture A to the oligomer obtained in step 2, and polymerize under reduced pressure at 220° C. and less than 300 Pa until the Weissenberg effect appears to obtain a piezoelectric polyester elastomer.

[0022] Step 4: Add 0.1 wt% of diisopropylbenzene peroxide crosslinking agent to the piezoelectric polyester elastomer obtained in step 3 at 80° C., keep the mixture in an internal mixer at 80° C. for 5 minutes, and then internally mix for 0.5 hours to obtain a preform.

[0023] Step 5: The preform obtained in step 4 is cross-linked and cured by a flat vulcanizer to obtain a piezoelectric polyester elastomer film.

[0024] On the one hand, the present invention utilizes the excellent flexibility of the piezoelectric polyester elastomer film: the elongation at break is 1300%, the elastic modulus is low, and it can be applied to the characteristics of the curvature change of human skin; the polyester elastomer is green and environmentally friendly, has good biocompatibility, and can be naturally degraded; and the piezoelectric acoustic device prepared by it has excellent acoustic performance (sound distance 2-100mm response or>63dB response), broadband response (20-12500Hz), and excellent self-healing performance (about 80%). On the other hand, by using a variety of ways (highly integrated dressing products or split data processing modules so that the wearable part does not give the target object a strong foreign body sensation) to set the piezoelectric acoustic sensor to improve the accuracy of snoring data collection of the target diagnosis object, considering that the sleep level of people is affected by excessive external interference during sleep (such as when the target object is disturbed by external foreign objects, sound interference, light interference, etc., it will cause the patient to have difficulty falling asleep or abnormal snoring or even stop), so that the snoring data is incorrect. On the other hand, the more powerful self-data processing database set by the network end makes the results of analyzing and processing data more accurate. Finally, the present invention effectively improves the problems of existing OSAHS diagnostic technology, such as complex test operation, high medical cost, and inaccurate test results due to test conditions. BRIEF DESCRIPTION OF THE DRAWINGS

[0025] Figure 1 This is the technical route and design idea diagram for polyester elastomer synthesis;

[0026] Figure 2 It is a schematic diagram of the structure of a piezoelectric acoustic sensor;

[0027] Figure 3 This is a schematic diagram of the OSAHS identification device;

[0028] Figure 4 This is a diagram of the output signal of the wristband monitoring the snoring of OSAHS patients. DETAILED DESCRIPTION

[0029] The present invention is further described in detail below in conjunction with the embodiments and drawings.

[0030] For polyester elastomers, the presence of permanent dipole C=O bonds in the material provides piezoelectric properties for the elastomer. Due to the multi-component copolymerization and the introduction of a long-chain structure, the main chain has a high degree of flexibility. At the same time, the multi-component random copolymerization reduces the crystallinity of the elastomer, resulting in a decrease in the elastic modulus. When the elastomer is subjected to external force, the deformation it produces is much greater than that of traditional piezoelectric polymers, and significant lattice distortion and asymmetry will occur, thereby improving the piezoelectric properties of the elastomer.

[0031] In this embodiment, the method for preparing the piezoelectric polyester elastomer film is as follows:

[0032] Step 1: Mix cis-1,4-butenediol, 1,3-propylene glycol, 1,4-butanediol, succinic acid and sebacic acid in a molar ratio of 0.05:0.225:0.225:0.35:0.15 to obtain a mixture A.

[0033] Step 2: Add 0.01 wt% of the antioxidant phosphorous acid and 0.04 wt% of the polymerization inhibitor hydroquinone to the mixture A, mix them in sequence, and then place them in a 180° C. water bath and heat and stir them under a nitrogen atmosphere for 2 hours to obtain an oligomer.

[0034] Step 3: Add tetrabutyl titanate catalyst accounting for 0.1 wt% of mixture A to the oligomer obtained in step 2, and polymerize under reduced pressure at 220° C. and less than 300 Pa until the Weissenberg effect appears to obtain a piezoelectric polyester elastomer.

[0035] Step 4: Add 0.1 wt% of diisopropylbenzene peroxide crosslinking agent to the piezoelectric polyester elastomer obtained in step 3 at 80° C., keep the mixture in an internal mixer at 80° C. for 5 minutes, and then internally mix for 0.5 hours to obtain a preform.

[0036] Step 5: Fill the preform obtained in step 4 into a 3×3×0.1 cm steel mold, set the temperature of the flat vulcanizer to 160°C and the pressure to 10 MPa, and keep the temperature for 5 minutes when the temperature rises to the preset temperature. Then put the mold into the vulcanizer for cross-linking for 10 minutes, so that the linear macromolecules in the elastomer are cross-linked into a three-dimensional network structure, and a piezoelectric polyester elastomer film is obtained.

[0037] Step 6: Evenly scrape silver paste on both sides of the piezoelectric polyester elastomer film obtained in step 5, and put it into an oven for drying to obtain a silver electrode; then use copper foil to stick the wire to the surface of the silver electrode to obtain a polyester-based piezoelectric acoustic sensor. The final product of this embodiment is worn on the wrist of the target diagnosis subject in the form of a wristband.

[0038] When the sound source vibrates, it will cause the air molecules to vibrate rhythmically, causing the surrounding air to change in density, forming alternating longitudinal waves, which will generate sound waves. Sound waves have a certain pressure. When this pressure acts on the wristband made of the acoustic sensor, the upper and lower layers of the piezoelectric material will form opposite positive and negative charges, and the sensor will be able to output a voltage signal, thus realizing the conversion of acoustic signals to electrical signals. When the snoring sound source is applied directly above the wristband, the wristband will be stimulated by the snoring signal to generate a voltage signal, which is output through the wires leading from the upper and lower electrodes of the device, and the output data is recorded and processed by a computer. Figure 4 This is a diagram showing the output signal of the wristband monitoring the snoring of OSAHS patients in this embodiment. Figure 4 In the figure, we can see that the flexible acoustic sensor records and identifies the patient's transition from normal snoring to weak or paused breathing. In the process of 0 to 39 seconds, the snoring is uniform and regular, which is a manifestation of normal snoring. Then it enters the irregular snoring state. After the snoring volume increases sharply, the patient has weak or paused breathing for about 3 seconds. After two snorings, the patient has weak or paused breathing for about 5 seconds. Finally, after a sudden increase in snoring, the patient has wheezing in 89.5 to 103.8 seconds. Irregular snoring, weak or paused breathing, and wheezing are all characteristics of sleep disorders. At the same time, these characteristics can be expressed by the time domain signals collected by the flexible acoustic sensor, which verifies the practical application of the wristband in the field of sleep disease monitoring.

[0039] It can be seen from the above embodiments that the present invention has three aspects: 1. It utilizes the excellent flexibility of the piezoelectric polyester elastomer film, which is green and environmentally friendly, and the piezoelectric acoustic device prepared therefrom has excellent acoustic performance; 2. By using the piezoelectric acoustic sensor as a highly integrated auxiliary material product, or a split type so that the wearable part does not give the target object a strong foreign body sensation, the accuracy of the snoring data collection of the target diagnosis object is improved to avoid the target object's sleep being affected by excessive external interference during sleep, resulting in incorrect snoring data; 3. The more powerful self-data processing database set up by the network end makes the results of analyzing and processing data more accurate. Finally, the present invention effectively improves the problems of the existing OSAHS diagnostic technology, such as complex test operation, high medical cost, and inaccurate test results due to test conditions.

Claims

1. An OSAHS identification device, characterized in that: It includes a piezoelectric acoustic sensor and a data processing module; The piezoelectric acoustic sensor is made of electrodes on both sides of a piezoelectric polyester elastomer film, which are led out with wires to collect the snoring sound of the target diagnostic object; The data processing module compares and analyzes the snoring data collected by the piezoelectric acoustic sensor with its own database and gives a comparison and analysis result, wherein the database is composed of prior disease diagnosis data.

2. The OSAHS identification device according to claim 1, characterized in that: The thickness of the OSAHS identification device does not exceed 2 mm. When in use, the device is attached to the snoring sound source in the form of a dressing within 10 cm to ensure the accuracy of the monitored data collection.

3. The OSAHS identification device according to claim 2, characterized in that: The OSAHS identification device is attached to the flat area of ​​the pectoralis major epidermis of the target diagnosis object in the form of a dressing to ensure the accuracy of the monitored data collection.

4. The OSAHS identification device according to claim 2, characterized in that: The OSAHS identification device is attached to the flat forehead area of ​​the target diagnosis object in the form of a dressing to ensure the accuracy of the monitored data collection.

5. The OSAHS identification device according to claim 1, characterized in that: The OSAHS identification device is worn on the wrists of the target diagnosis subject in the form of a wristband, and is worn on both wrists to ensure the accuracy of the monitored data collection.

6. The OSAHS identification device according to claim 1, characterized in that: The data processing module is a split device connected to the outside, so as to further reduce the volume of the piezoelectric acoustic sensor of the wearable component, which is beneficial for not affecting the normal sleep of the target diagnosis object during use, making the collected data more accurate.

7. The OSAHS identification device according to claim 6, characterized in that: The data processing module is arranged at the network end to provide a more powerful and comprehensive database for post-processing of the snoring data, so that the analysis result is more accurate.

8. The OSAHS identification device according to claim 1, characterized in that: The external connection mode of the data processing module is wireless communication.

9. The OSAHS identification device according to claim 1, characterized in that: The preparation method of the piezoelectric polyester elastomer film is as follows: Step 1, mixing cis-1,4-butenediol, 1,3-propylene glycol, 1,4-butanediol, succinic acid and sebacic acid at a molar ratio of 0.05:0.225:0.225:0.35:0.15 to obtain a mixture A; Step 2, adding 0.01 wt% of phosphorous acid as an antioxidant and 0.04 wt% of hydroquinone as a polymerization inhibitor to the mixture A, mixing them in sequence, and then placing them in a 180° C. water bath and heating and stirring them under a nitrogen atmosphere for 2 h to obtain an oligomer; Step 3, adding 0.1 wt% of tetrabutyl titanate catalyst to the oligomer obtained in step 2, and polymerizing under reduced pressure at 220° C. and less than 300 Pa until the Weissenberg effect appears to obtain a piezoelectric polyester elastomer; Step 4, adding 0.1 wt% of dicumyl peroxide crosslinking agent to the piezoelectric polyester elastomer obtained in step 3, and keeping the mixture in an internal mixer at 80° C. for 5 minutes; and then mixing the mixture for 0.5 hours to obtain a preform; Step 5: The preform obtained in step 4 is cross-linked and cured by a flat vulcanizer to obtain a piezoelectric polyester elastomer film.

Images