Oropharyngeal ventilation device and breath sound monitoring system

Abstract

The invention discloses an oropharynx ventilation device and a breath sound monitoring system, and relates to the technical field of medical instruments.The oropharynx ventilation device comprises a ventilation catheter, the ventilation catheter is made of a shape memory alloy skeleton and an elastic layer, the shape memory alloy skeleton is coated with the elastic layer, and a ventilation flow channel is formed in the ventilation catheter; the sound sensor is fixed to the ventilation catheter and used for being in communication connection with the monitoring host so as to transmit detected breathing sound information to the monitoring host. The sound sensor is fixed to the ventilation catheter, the sound sensor is used for detecting breathing sound information of a patient in real time, the sound sensor is used for being in communication connection with the monitoring host so as to transmit the detected breathing sound information to the monitoring host, the pharyngeal cavity breathing sound can be continuously collected in real time, and a blocked or abnormal breathing mode can be rapidly recognized in the early stage; in addition, the sound sensor is small in size and free of electromagnetic interference, the requirement of a disposable passive instrument is met, and the respiratory tract safety can be effectively improved.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and in particular to an oropharyngeal ventilation device and a respiratory sound monitoring system. Background Technology

[0002] In related technologies, oropharyngeal ventilation devices are commonly used disposable instruments in pre-hospital emergency care, anesthesia recovery, and intensive care to maintain upper airway patency and prevent tongue retraction. However, during use, patients may experience secretion blockage, coughing, partial airway obstruction, or tube displacement. Traditional monitoring mainly relies on visual observation of chest and abdominal movements or indirect indicators from electrocardiogram monitoring, making it difficult to detect airway abnormalities in a timely manner. Bedside auscultation is prone to distortion in noisy environments and cannot provide continuous monitoring. Existing electroacoustic microphones placed outside the oropharyngeal ventilation device are susceptible to environmental noise interference, while placing them inside the mouth presents significant risks of disinfection and electrical leakage. Furthermore, existing oropharyngeal ventilation devices are rigid and cannot automatically adjust their curvature according to different patients' oral structures, failing to meet the airway support needs of patients in different positions (e.g., supine, lateral, prone). Summary of the Invention

[0003] This invention aims to at least solve one of the technical problems existing in the prior art. Therefore, one objective of this invention is to provide an oropharyngeal ventilation device capable of continuously acquiring pharyngeal breath sounds in real time, rapidly identifying obstructed or abnormal breathing patterns in the early stages, reducing the risk of missed diagnoses by nursing staff, and featuring a small sound sensor that is free from electromagnetic interference, meeting the requirements for disposable passive devices, thereby effectively improving airway safety.

[0004] The present invention further proposes a respiratory sound monitoring system having the above-mentioned oropharyngeal ventilation device.

[0005] An oropharyngeal ventilation device according to an embodiment of the present invention includes: The ventilation tube is made of a shape memory alloy skeleton and an elastic layer. The elastic layer covers the shape memory alloy skeleton and forms an airway. The ventilation tube is used to be inserted into the patient's oral cavity. A sound sensor is fixed to the ventilation tube and is used to detect the patient's respiratory sounds in real time. The sound sensor is also used to communicate with the monitoring host to transmit the detected respiratory sound information to the monitoring host.

[0006] According to an embodiment of the present invention, the oropharyngeal ventilation device, by fixing a sound sensor to the ventilation tube, uses the sound sensor to detect the patient's respiratory sound information in real time and communicates with the monitoring host to transmit the detected respiratory sound information to the monitoring host. This allows for continuous real-time acquisition of pharyngeal respiratory sounds, enabling early and rapid identification of obstructed or abnormal breathing patterns, reducing the risk of missed diagnoses by nursing staff. Furthermore, the sound sensor is small in size, free from electromagnetic interference, and meets the requirements for disposable passive devices, thus effectively improving airway safety. In addition, the ventilation tube is made of a shape memory alloy skeleton and an elastic layer, allowing the ventilation tube to automatically adjust its curvature according to different patients' oral structures, thereby adapting to the airway support needs of patients in different positions (e.g., supine, lateral, prone, etc.).

[0007] According to some embodiments of the present invention, the ventilation tube includes: a tongue plate for inserting into the patient's oral cavity to press against the patient's tongue, and the tongue plate is provided with a sound sensor.

[0008] According to some embodiments of the present invention, the outer peripheral wall of the tongue plate is formed with a mounting groove that extends along the extension direction of the vent duct, and a sound sensor is mounted in the mounting groove.

[0009] In some embodiments of the present invention, the depth of the mounting groove is less than or equal to 0.3 mm; and / or The mounting slot contains medical-grade encapsulating adhesive to encapsulate the sound sensor within it.

[0010] According to some embodiments of the present invention, the outer peripheral wall of the tongue plate is provided with a pressure sensing strip and an inflatable flexible air bladder. The pressure sensing strip is used to detect the contact pressure between the air duct and the oral mucosa of the oral cavity, and the flexible air bladder is configured to adjust the inflation amount according to the detection information of the pressure sensing strip.

[0011] In some embodiments of the present invention, there are multiple sound sensors, which are arranged sequentially along the extension direction of the ventilation duct.

[0012] According to some embodiments of the present invention, the sound sensor is an optical fiber sensor and / or a MEMS sensor; and / or The inner wall of the air passage is formed with a spiral guide groove.

[0013] According to some embodiments of the present invention, the oropharyngeal ventilation device further includes: a pressure sensor, a temperature sensor, and a bioimpedance sensor, all of which are fixedly mounted on the ventilation tube. The pressure sensor is used to detect the patient's airway pressure in real time, the temperature sensor is used to detect the patient's expiratory temperature, and the bioimpedance sensor is used to detect secretions in real time. All three sensors are communicatively connected to a monitoring host. An adhesive layer is provided on the inner wall of the air passage.

[0014] A respiratory sound monitoring system according to an embodiment of the present invention includes: Oropharyngeal ventilation device, wherein the oropharyngeal ventilation device is the oropharyngeal ventilation device described in the above embodiment; The monitoring host and the sound sensor communicate with each other. The monitoring terminal is connected to the monitoring host, and the monitoring host is configured to transmit respiratory sound information to the monitoring terminal.

[0015] According to some embodiments of the present invention, the respiratory sound monitoring system further includes: an alarm device, which is communicatively connected to a monitoring host, and the monitoring host is configured to control the alarm device to issue an alarm message when abnormal respiratory sound information occurs.

[0016] Additional aspects and advantages of the invention will be set forth in part in the description which follows, and in part will be obvious from the description, or may be learned by practice of the invention. Attached Figure Description

[0017] The above and / or additional aspects and advantages of the present invention will become apparent and readily understood from the description of the embodiments taken in conjunction with the following drawings, in which: Figure 1 This is a schematic diagram of the oropharyngeal ventilation device according to an embodiment of the present invention; Figure 2 This is a cross-sectional view of the oropharyngeal ventilation device according to an embodiment of the present invention; Figure 3 This is a schematic diagram of the respiratory sound monitoring system according to an embodiment of the present invention.

[0018] Figure label: Oropharyngeal ventilation device 100; Ventilation duct 10; airflow channel 11; tongue plate 12; mounting groove 13; Sound sensor 20; Breathing sound monitoring system 200; monitoring host 201; monitoring terminal 202; alarm device 203. Detailed Implementation

[0019] Embodiments of the present invention are described in detail below. Examples of these embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals denote the same or similar elements or elements having the same or similar functions throughout. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain the present invention, and should not be construed as limiting the present invention.

[0020] The following is for reference. Figures 1-3 An oropharyngeal ventilation device 100 and a respiratory sound monitoring system 200 according to embodiments of the present invention are described.

[0021] An oropharyngeal ventilation device 100 according to an embodiment of the present invention includes: The ventilation tube 10 is made of a shape memory alloy skeleton and an elastic layer. The elastic layer covers the shape memory alloy skeleton. The ventilation tube 10 forms an airway 11. The ventilation tube 10 is used to be inserted into the patient's oral cavity. A sound sensor 20 is fixed to the ventilation tube 10. The sound sensor 20 is used to detect the patient's breathing sounds in real time, and the sound sensor 20 is used to communicate with the monitoring host 201 to transmit the detected breathing sound information to the monitoring host 201.

[0022] The ventilation tube 10 can be made of medical-grade PE or silicone material. The ventilation tube 10 is a standard 80mm–100mm size and has an airflow channel 11. Inserted into the patient's mouth, the ventilation tube 10 effectively opens the base of the tongue and the posterior wall of the oropharynx, preventing upper airway obstruction caused by the tongue falling back. In out-of-hospital emergency care, the ventilation tube 10 can establish effective ventilation within seconds, buying crucial time for subsequent resuscitation. The airflow channel 11 formed by the ventilation tube 10 guides oxygen precisely to the lower respiratory tract, reducing interference from the nasal or oral cavity on gas exchange and significantly improving the patient's blood oxygen saturation.

[0023] The sound sensor 20 can be a fiber optic sensor or a MEMS sensor, or it can be a MEMS optical sensor combining a fiber optic sensor and a MEMS sensor. The MEMS sensor can function as a miniature capacitive microphone; sound waves cause a movable diaphragm to vibrate, changing the capacitance between the diaphragm and the backplate, thereby generating an electrical signal. The fiber optic sensor detects sound by modulating the optical signal through changes in the refractive index of the fiber optic cable caused by sound waves. It is entirely based on light transmission, has no electromagnetic induction, is radiation-resistant and corrosion-resistant, and is suitable for embedding in disposable airway devices. The sound sensor 20 is fixed to the ventilation tube 10. In some embodiments of the invention, the sound sensor 20 can be adhered to the ventilation tube 10 or clipped onto it. However, the invention is not limited to these methods; the sound sensor 20 can also be fixed to the ventilation tube 10 in other ways, as long as it is fixed to the ventilation tube 10. The sound sensor 20 is used to continuously detect the patient's respiratory sounds in real time, enabling early identification of airway obstruction or abnormal breathing patterns, meeting the clinical need for early screening of lung diseases (such as pneumonia, asthma, etc.). Furthermore, the sound sensor 20 is small in size and free from electromagnetic interference. The sound sensor 20 is fixed to the ventilation tube 10 and can be located inside the patient's mouth, which can effectively suppress environmental noise and ensure the purity of the respiratory sound signal.

[0024] Furthermore, the sound sensor 20 is used to communicate with the monitoring host 201. The sound sensor 20 can be used to communicate with the monitoring host 201 via a wire harness, or the sound sensor 20 can be used to communicate with the monitoring host 201 wirelessly. As long as the sound sensor 20 is used to communicate with the monitoring host 201, it is acceptable.

[0025] The sound sensor 20 is used to communicate with the monitoring host 201 to transmit the detected respiratory sound information to the monitoring host 201. It can instantly capture abnormalities such as apnea or worsening wheezing in patients, facilitating timely diagnosis and emergency treatment by medical staff. Furthermore, the continuous connection between the sound sensor 20 and the monitoring host 201 allows for 24-hour uninterrupted recording of the patient's respiratory changes, forming a dynamic data stream. Through time-frequency analysis, a respiratory sound intensity-time curve can be plotted to assist in assessing disease progression and effectively improve airway safety.

[0026] The shape memory alloy skeleton can be made of nickel-titanium alloy, and the elastic layer can be 0.5-1.0mm thick medical-grade liquid silicone, so that the ventilation tube 10 has both support rigidity and flexibility. The ventilation tube 10 can automatically adjust the curvature according to the patient's oral structure, so that the ventilation tube 10 can adapt to the airway support needs of the patient in different body positions, reducing the risk of mucosal damage and displacement of the ventilation tube 10.

[0027] According to an embodiment of the present invention, the oropharyngeal ventilation device 100 fixes a sound sensor 20 to the ventilation tube 10. The sound sensor 20 is used to detect the patient's respiratory sound information in real time and is used to communicate with the monitoring host 201 to transmit the detected respiratory sound information to the monitoring host 201. It can continuously collect pharyngeal respiratory sounds in real time, quickly identify obstruction or abnormal breathing patterns in the early stage, reduce the risk of missed diagnosis by nursing staff, and the sound sensor 20 is small in size, has no electromagnetic interference, meets the requirements of disposable passive devices, and can effectively improve airway safety.

[0028] According to some embodiments of the present invention, such as Figure 1 As shown, the ventilation tube 10 may include: a tongue plate 12, which is inserted into the patient's mouth to press down the patient's tongue, and the tongue plate 12 is equipped with a sound sensor 20.

[0029] The tongue plate 12 can be 2.1mm-2.3mm thick. The ventilation tube 10 may also include an occlusal block. The occlusal block and the tongue plate 12 are the core components of the airway assistive device. By inserting into the oral cavity and pressing against the tongue, they can effectively prevent the patient's tongue from falling back and obstructing the airway. The tongue plate 12 can be arc-shaped, allowing it to conform to the patient's oral cavity structure and ensure that the patient's airway remains open. For example, during anesthesia induction or epileptic seizures, the tongue plate 12 can quickly separate the patient's tongue from the posterior pharyngeal wall, restore ventilation function, and reduce the risk of suffocation.

[0030] Integrating the sound sensor 20 into the tongue plate 12 enables real-time monitoring of sound signals within the patient's airway (such as breathing sounds, snoring, and abnormal sounds caused by foreign body obstruction). When the tongue plate 12 shifts position due to patient movement or a vomiting reflex, the sound sensor 20 can trigger an alarm through sound changes (such as a decrease in airflow sound or the appearance of noise), prompting medical staff to adjust the position of the tongue plate 12 to avoid complete airway obstruction and effectively improve airway safety.

[0031] According to some embodiments of the present invention, such as Figure 1 As shown, the outer peripheral wall of the tongue plate 12 is formed with a mounting groove 13, which extends along the extension direction of the vent duct 10, and a sound sensor 20 is mounted in the mounting groove 13.

[0032] The mounting groove 13 and the outer peripheral wall of the tongue plate 12 can be integrally formed (e.g., by injection molding), or the mounting groove 13 can be engraved on the outer peripheral wall of the tongue plate 12, depending on the actual situation. The mounting groove 13 extends along the extension direction of the ventilation duct 10. The mounting groove 13 is equipped with a sound sensor 20, which can be firmly fixed by a mechanical interlocking structure (e.g., barbs, buckles) or adhesive bonding to prevent sensor displacement caused by patient chewing, swallowing, or medical staff operation, thus ensuring the stability of the patient's breath sound acquisition. The mounting groove 13 extends along the extension direction of the ventilation duct 10, which can disperse the vibration energy received by the sound sensor 20, reduce signal noise caused by mechanical vibration, effectively improve the information acquisition accuracy of the sound sensor 20, and thus improve airway safety.

[0033] According to some embodiments of the present invention, the depth of the mounting groove 13 may be less than or equal to 0.3 mm; and / or Medical encapsulating adhesive can be provided in the mounting slot 13 to encapsulate the sound sensor 20 in the mounting slot 13.

[0034] In one embodiment of the present invention, the depth of the mounting groove 13 can be less than or equal to 0.3 mm. In some embodiments of the present invention, the depth of the mounting groove 13 can be 0.3 mm, 0.25 mm, 0.24 mm, 0.1 mm, etc., but the present invention is not limited to these values. The depth of the mounting groove 13 can also be other values ​​less than 0.3 mm, as long as the depth of the mounting groove 13 is less than or equal to 0.3 mm.

[0035] The outer peripheral wall of the tongue plate 12 has a mounting groove 13. If the depth of the mounting groove 13 is too large, the outer peripheral wall of the tongue plate 12 will bend or break under the pressure of the patient's oral cavity due to local thinning. Setting the depth of the mounting groove 13 to less than or equal to 0.3 mm can reduce the amount of material removed, ensure the overall bending stiffness of the tongue plate 12, and make the deformation resistance of the tongue plate 12 close to that of a grooveless structure, thereby ensuring the support stability of the ventilation tube 10. Furthermore, the depth of the mounting groove 13 is less than or equal to 0.3 mm, which will not significantly reduce the surface flatness of the outer peripheral wall of the tongue plate 12, thereby reducing the frictional stimulation of the tongue plate 12 on the patient's oral cavity structure and reducing patient discomfort.

[0036] It can be noted that the lower limit of the depth of the mounting groove 13 can be reasonably set according to the actual situation. As a specific embodiment of the present invention, the depth of the mounting groove 13 can be 0.25mm and the width of the mounting groove 13 can be 0.3mm. This setting can not only meet the installation requirements of the sound sensor 20, but also ensure the support stability of the ventilation duct 10.

[0037] Alternatively, as another embodiment of the present invention, a medical encapsulating adhesive can be provided in the mounting groove 13. Specifically, the sound sensor 20 can be encapsulated with a medical sterilizable epoxy adhesive. The medical sterilizable epoxy adhesive can withstand high-pressure steam sterilization at 121℃-134℃ for no less than 20 minutes, ensuring that no byproducts (peroxide residues) are generated during the curing process of the medical sterilizable epoxy adhesive, thereby reducing the risk of byproducts irritating the patient's oral mucosa. Furthermore, the medical encapsulating adhesive forms a three-dimensional elastic network through chemical cross-linking, integrating the sound sensor 20 with the wall of the mounting groove 13 through "adhesion-encapsulation". This not only improves the fixation stability of the sound sensor 20 but also extends the vibration fatigue life of the sound sensor 20, ensuring signal stability for the patient during long-term monitoring. Furthermore, encapsulating the sound sensor 20 with medical encapsulating adhesive will not significantly increase the size of the ventilation tube 10. The increase in the size (outer diameter) of the ventilation tube 10 after encapsulating the sound sensor 20 is less than or equal to 0.15 mm, which can ensure the compatibility of the ventilation tube 10, avoid damage to the patient's oral mucosa due to the excessive size of the ventilation tube 10, and also avoid changing the sound wave transmission path, which would cause the signal of the sound sensor 20 to attenuate.

[0038] As another embodiment of the present invention, the depth of the mounting groove 13 can be less than or equal to 0.3 mm, and medical encapsulating adhesive can be provided in the mounting groove 13 to encapsulate the sound sensor 20 in the mounting groove 13 (the present invention will be described using this embodiment as an example).

[0039] According to some embodiments of the present invention, such as Figure 1 As shown, there can be multiple sound sensors 20, which are located at different positions in the ventilation duct 10.

[0040] The sound sensor 20 can be multiple. In some embodiments of the present invention, there can be two, three, four, or other numbers of sound sensors 20. However, the present invention is not limited to this, and other numbers of sound sensors 20 can also be used, as long as there are multiple sound sensors 20. Breath sounds (such as wheezing and moist rales) have directional and attenuation characteristics in the airway. Sound sensors 20 can be set at the distal end, middle section, and curved section of the ventilator 10 to perform multi-point breath sound monitoring. Compared with a single sound sensor 20, this can further ensure the complete preservation of the time-frequency characteristics of breath sounds (such as the "two-tone structure" of wheezing).

[0041] As a specific embodiment of the present invention, there can be two sound sensors 20. One sound sensor 20 is located at the bend of the lingual plate 12 at the distal end of the ventilation tube 10 (near the posterior pharyngeal wall), and the other sound sensor 20 is located in the middle section of the ventilation tube 10 (above the soft palate). The two sound sensors 20 are connected in series. The signal-to-noise ratio of the series sound sensors 20 can be effectively improved, thereby effectively suppressing background noise. The distal sound sensor 20 is close to the posterior pharyngeal wall and can mainly collect high-frequency respiratory sounds (such as wheezing). The middle sound sensor 20 is located above the soft palate and can more easily capture low-frequency respiratory sounds (such as moist rales). The high-frequency and low-frequency signals are "separated and collected" by the two sound sensors 20 and then superimposed, which can improve the integrity of the full-frequency signal and enable early identification of obstruction or abnormal breathing patterns, thereby further improving airway safety.

[0042] According to some embodiments of the present invention, such as Figure 1 As shown, multiple sound sensors 20 can be arranged sequentially along the extension direction of the ventilation duct 10 to form a sensor network. These multiple sound sensors 20 can receive sound signals from different locations, and by analyzing information such as time delay and phase difference between these signals, the specific location of the sound source can be determined. Compared to a single sound sensor 20, an array of multiple sound sensors 20 can provide richer spatial information. This not only helps to more accurately locate the sound source but also provides more dimensions for subsequent signal processing and analysis.

[0043] According to some embodiments of the present invention, the sound sensor 20 may be an optical fiber sensor and / or a MEMS sensor; and / or The inner wall of the air passage 11 is formed with a spiral guide groove.

[0044] In one specific embodiment of the present invention, the sound sensor 20 can be an optical fiber sensor or a MEMS sensor, or it can be a MEMS optical sensor combining an optical fiber sensor and a MEMS sensor. The MEMS sensor can function as a miniature capacitive microphone; sound waves cause a movable diaphragm to vibrate, changing the capacitance between the diaphragm and the backplate, thereby generating an electrical signal. The optical fiber sensor detects sound by modulating the optical signal through changes in the refractive index of the optical fiber caused by sound waves. It is entirely based on optical transmission, has no electromagnetic induction, is radiation-resistant and corrosion-resistant, and is suitable for embedding in disposable airway devices. Further, in another specific embodiment of the present invention, the sound sensor 20 can employ an optical fiber FabryPerot (FP) microcavity with the following parameters: cavity length 25µm, acoustic bandwidth 20Hz–5kHz, diaphragm made of 1µm Si3N4, and sensitivity 200mV / Pa.

[0045] When the sound sensor 20 employs fiber optic sensor technology, it achieves high-sensitivity sound wave detection, wide bandwidth response, electromagnetic interference resistance, long-distance transmission, and resistance to harsh environments. The fiber optic sensor utilizes the minute deformation of the optical fiber under the influence of a sound field (such as bending or length change) to modulate the optical signal, thereby achieving sound wave detection. This gives the fiber optic sensor extremely high sensitivity, enabling it to detect very weak sound signals. The fiber optic sensor has a wide operating bandwidth, covering a broad range of sound waves from low to high frequencies. Because the fiber optic sensor uses optical signals for transmission and detection, it is unaffected by electromagnetic interference. The fiber optic sensor employs a passive design with no semiconductor components at the front end, thus exhibiting high reliability and long lifespan.

[0046] It can be noted that multiple sound sensors 20 can be connected in series via a 125µm diameter single-mode optical fiber. Fiber optic sensors utilize optical fibers for signal transmission, offering advantages such as long transmission distance and low signal attenuation. This allows fiber optic sensors to easily acquire and transmit sound signals over long distances without the need for repeater amplification equipment. The very low loss in fiber optic transmission ensures the quality of the sound signal during transmission. The fabrication process of the sound sensor 20 can be as follows: a microcavity with a length of 25µm is formed by fused tapering at the end face of a single-mode optical fiber; a Si3N4 diaphragm is fabricated and bonded using MEMS technology; after vacuum oil injection, pre-stress calibration, and encapsulation with Parylene C (poly(p-xylene) type) to enhance the biological barrier, followed by moisture-heat sterilization at 134℃ for 30 minutes.

[0047] Alternatively, as another embodiment of the present invention, the spiral guide groove extends along the extension direction of the air passage 11. By providing the spiral guide groove, the airflow turbulence and resistance in the air passage 11 can be reduced, which is beneficial to improving the ventilation efficiency.

[0048] Alternatively, as another embodiment of the present invention, the sound sensor 20 can be a MEMS optical sensor that combines an optical fiber sensor and a MEMS sensor. Furthermore, the spiral guide groove extends along the extension direction of the air passage 11. By providing the spiral guide groove, the airflow turbulence and resistance in the air passage 11 can be reduced, which is beneficial to improving the ventilation efficiency (the present invention will be described using this embodiment as an example).

[0049] According to some embodiments of the present invention, the outer peripheral wall of the tongue plate 12 is provided with a pressure sensing strip and an inflatable flexible airbag. The pressure sensing strip is used to detect the contact pressure between the ventilation tube 10 and the oral mucosa of the oral cavity, and the flexible airbag is configured to adjust the inflation amount according to the detection information of the pressure sensing strip.

[0050] The pressure sensing strip is a strip-shaped sensor used to measure pressure changes, and it is fixed to the ventilation tube 10. The pressure sensing strip can communicate with the monitoring host 201, transmitting the detected pressure information to the host. The flexible airbag can be connected to a miniature air pump, which in turn communicates with the monitoring host 201. When the pressure detected by the pressure sensing strip exceeds a preset value, the monitoring host 201 controls the flexible airbag to deflate; when the pressure detected by the pressure sensing strip is less than the preset value, the monitoring host 201 controls the miniature air pump to inflate the flexible airbag. This allows for automatic adjustment of the flexible airbag inflation volume according to the patient's tongue size, achieving personalized tongue fixation and avoiding the discomfort and damage caused by traditional rigid fixation. Furthermore, it improves the versatility of the oropharyngeal ventilation device 100.

[0051] According to some embodiments of the present invention, the oropharyngeal ventilation device 100 may further include: a pressure sensor, a temperature sensor, and a bioimpedance sensor, all of which are fixed to the ventilation tube. The pressure sensor is used to detect the patient's airway pressure in real time, the temperature sensor is used to detect the patient's expiratory temperature, and the bioimpedance sensor is used to detect secretions in real time. All three sensors are communicatively connected to a monitoring host. An adhesive layer is provided on the inner wall of the air passage 11.

[0052] In one embodiment of the present invention, the pressure sensor, temperature sensor, and bioimpedance sensor can all transmit the detected data to the monitoring host, enabling the simultaneous acquisition of respiratory sounds, airway pressure, expiratory temperature, and bioimpedance. Combined with the algorithm within the monitoring host, the monitoring host can determine whether the airway is abnormal, achieving early identification and accurate judgment of airway abnormalities, thereby improving the accuracy and timeliness of airway abnormality identification.

[0053] As another embodiment of the present invention, the adhesive layer can be an adhesive layer, and the particles entering the air passage 11 can be adhered by the adhesive layer, reducing the risk of particles entering the air passage.

[0054] As another embodiment of the present invention, the oropharyngeal ventilation device 100 may further include: a pressure sensor, a temperature sensor, and a bioimpedance sensor. The pressure sensor, temperature sensor, and bioimpedance sensor are all fixed to the ventilation tube. The pressure sensor is used to detect the airway pressure of the patient in real time, the temperature sensor is used to detect the patient's expiratory temperature, and the bioimpedance sensor is used to detect secretions in real time. The pressure sensor, temperature sensor, and bioimpedance sensor are all communicatively connected to the monitoring host. Furthermore, the inner sidewall of the ventilation channel 11 is provided with an adhesive layer (the present invention will be described using this embodiment as an example).

[0055] like Figure 3 As shown, the respiratory sound monitoring system 200 according to an embodiment of the present invention includes: The oropharyngeal ventilation device 100 is the oropharyngeal ventilation device 100 described in the above embodiment. Monitoring host 201, and the sound sensor 20 are connected in communication; The monitoring terminal 202 is communicatively connected to the monitoring host 201, and the monitoring host 201 is configured to transmit respiratory sound information to the monitoring terminal 202.

[0056] The monitoring host 201 may include: an external optical demodulation host, a signal processing unit, and a wireless communication module. The external optical demodulation host includes an ASE broadband light source and a high-speed interferometric demodulation module (1 pm resolution, >20 kS / s). The signal processing unit separates the inspiratory and expiratory phase energies in real time, detects the peak values ​​of continuous high-resistance noises, high-frequency whistling sounds, and wet rales, and determines airway obstruction, secretions, and coughing.

[0057] The monitoring host 201 and the sound sensor 20 are communicatively connected. In some embodiments of the present invention, the monitoring host 201 and the sound sensor 20 can be connected via a wire harness, or they can be connected wirelessly, as long as they are communicatively connected. In a specific embodiment of the present invention, the sound sensor 20 is connected to an optical fiber lead. The optical fiber lead extends 25cm from an external connector and is connected to the monitoring host 201 via a multi-core LC / APC quick-connect. The optical fiber lead is covered with a medical protective sleeve to prevent biting.

[0058] The monitoring terminal 202 can be a mobile APP, a nurse station monitor, etc. The monitoring terminal 202 and the monitoring host 201 can communicate and connect via BLE 5.3 / WiFi 6, etc. The monitoring host 201 is configured to transmit respiratory sound information to the monitoring terminal 202 so that medical staff can monitor the patient's breathing in real time, thereby enabling them to quickly identify obstructed or abnormal breathing patterns in the early stages and provide timely diagnosis and treatment for the patient.

[0059] According to some embodiments of the present invention, such as Figure 3 As shown, the respiratory sound monitoring system 200 may further include: an alarm device 203, which is communicatively connected to the monitoring host 201, and the monitoring host 201 is configured to control the alarm device 203 to issue an alarm message when the respiratory sound information is abnormal.

[0060] The alarm device 203 can be a sound alarm, a light alarm, or a combination of sound and light alarms, which can be selected and configured appropriately according to actual conditions. The alarm device 203 and the monitoring host 201 can be connected via a wire harness or wirelessly. The monitoring host 201 is configured to control the alarm device 203 to issue an alarm when abnormal respiratory sound information occurs (abnormality lasting ≥3 cycles), which can reduce the risk of missed diagnoses by nursing staff and thus effectively improve patient safety. The usage procedure of the respiratory sound monitoring system 200 is as follows: insert the oropharyngeal ventilation device 100 into the patient's mouth → connect the oropharyngeal ventilation device 100 to the monitoring host 201 → the sound sensor 20 collects respiratory sounds in real time → the monitoring host 201 analyzes the respiratory sounds in real time → if an abnormal pattern is detected, the alarm device 203 will sound an alarm and prompt nursing intervention.

[0061] In the description of this specification, the references to terms such as "one embodiment," "some embodiments," "illustrative embodiment," "example," "specific example," or "some examples," etc., indicate that a specific feature, structure, material, or characteristic described in connection with that embodiment or example is included in at least one embodiment or example of the invention. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples.

[0062] Although embodiments of the invention have been shown and described, those skilled in the art will understand that various changes, modifications, substitutions and alterations can be made to these embodiments without departing from the principles and spirit of the invention, the scope of which is defined by the claims and their equivalents.

Claims

1. An oropharyngeal ventilation device, characterized in that, include: A ventilation tube, the ventilation tube being made of a shape memory alloy skeleton and an elastic layer, the elastic layer covering the shape memory alloy skeleton, the ventilation tube forming an airflow channel, the ventilation tube being inserted into the patient's oral cavity; A sound sensor is fixed to the ventilation tube. The sound sensor is used to detect the patient's respiratory sounds in real time and is used to communicate with the monitoring host to transmit the detected respiratory sounds to the monitoring host.

2. The oropharyngeal ventilation device according to claim 1, characterized in that, The ventilation tube includes a tongue plate, which is inserted into the patient's mouth to press down the patient's tongue, and the tongue plate is equipped with the sound sensor.

3. The oropharyngeal ventilation device according to claim 2, characterized in that, The outer peripheral wall of the tongue plate is formed with a mounting groove, which extends along the extension direction of the air duct, and the sound sensor is mounted in the mounting groove.

4. The oropharyngeal ventilation device according to claim 3, characterized in that, The depth of the mounting groove is less than or equal to 0.3 mm; and / or The mounting slot is provided with medical encapsulating adhesive to encapsulate the sound sensor within the mounting slot.

5. The oropharyngeal ventilation device according to claim 2, characterized in that, The outer peripheral wall of the tongue plate is provided with a pressure sensing strip and an inflatable flexible air bladder. The pressure sensing strip is used to detect the contact pressure between the air duct and the oral mucosa of the oral cavity. The flexible air bladder is configured to adjust the inflation volume according to the detection information of the pressure sensing strip.

6. The oropharyngeal ventilation device according to claim 1, characterized in that, The sound sensors are multiple, and the multiple sound sensors are arranged sequentially along the extension direction of the ventilation duct.

7. The oropharyngeal ventilation device according to any one of claims 1-6, characterized in that, The sound sensor is a fiber optic sensor and / or a MEMS sensor; and / or The inner wall of the air passage is formed with a spiral guide groove.

8. The oropharyngeal ventilation device according to any one of claims 1-6, characterized in that, The oropharyngeal ventilation device further includes: a pressure sensor, a temperature sensor, and a bioimpedance sensor. The pressure sensor, temperature sensor, and bioimpedance sensor are all fixed to the ventilation tube. The pressure sensor is used to detect the patient's airway pressure in real time. The temperature sensor is used to detect the patient's expiratory temperature. The bioimpedance sensor is used to detect secretions in real time. The pressure sensor, temperature sensor, and bioimpedance sensor are all communicatively connected to the monitoring host; and / or The inner wall of the air passage is provided with an adhesive layer.

9. A respiratory sound monitoring system, characterized in that, include: An oropharyngeal ventilation device, wherein the oropharyngeal ventilation device is the oropharyngeal ventilation device according to any one of claims 1-8; A monitoring host, which is communicatively connected to the sound sensor; A monitoring terminal is communicatively connected to the monitoring host, and the monitoring host is configured to transmit the respiratory sound information to the monitoring terminal.

10. The respiratory sound monitoring system according to claim 9, characterized in that, The respiratory sound monitoring system further includes an alarm device, which is communicatively connected to the monitoring host. The monitoring host is configured to control the alarm device to issue an alarm message when the respiratory sound information is abnormal.

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