Nasopharyngeal airway device with atomization administration function and application method thereof

Abstract

This invention discloses a nasopharyngeal airway device with nebulized drug delivery function and its application method. The device includes a nasopharyngeal airway tube with a sealed, pluggable airway body and a connecting end tube. A nebulization module is detachably connected between the airway body and the connecting end tube. The nebulization module includes a nebulizer body and a nebulizer core. The nebulizer body has a compressed air connection port, an installation port, and an aerosol outlet. The nebulizer core is detachably connected to the nebulizer body through the installation port. The nebulizer body is connected to an external compressed air source through the compressed air connection port. The aerosol outlet is a T-shaped three-way connector, with one port connecting to the inner cavity of the nebulizer body and the other two ports connecting to the airway body and the connecting end tube, respectively. This invention solves the problems of inconvenience in operation, drug waste, and poor treatment effect caused by separating the nasopharyngeal airway from the nebulization therapy device, achieving efficient and precise local drug delivery while maintaining airway patency.

Description

Technical Field

[0001] This invention relates to a nasopharyngeal airway device with nebulized drug delivery function and its application method, belonging to the field of medical device technology. Background Technology

[0002] In clinical practice, especially in emergency medicine, anesthesiology, and intensive care units (ICUs), maintaining a patient's airway patency and administering local drug therapy are two crucial and often simultaneous core operations. Currently, these two functions are typically performed by separate devices, which presents numerous technical limitations and operational inconveniences. The specific background and current technical status are as follows:

[0003] (1) Existing nasopharyngeal airways have a single function. The nasopharyngeal airway is a classic non-invasive airway management tool, inserted through the nasal cavity and positioned at the pharynx, mainly used to relieve upper airway obstruction. Its structure is simple, and it is only used as a physical ventilation tube, and cannot be used for local drug administration at the same time. When patients need nebulized drug administration (such as for laryngeal edema, pharyngeal inflammation or local anesthesia), medical staff must interrupt the ventilation operation and connect an external nebulizer, which is cumbersome and may delay treatment in emergency situations.

[0004] (2) The “splicing” mode of external nebulizers with nasopharyngeal airways has significant problems. The connection process may damage the airtightness and stability of the airway; the external tubing is long, and a large amount of drug is deposited on the tubing wall during delivery, resulting in drug waste and difficulty in accurately controlling the amount of drug reaching the target area; in emergency or anesthesia resuscitation scenarios, frequent disassembly and assembly operations increase the complexity of the work and the risk of contamination.

[0005] (3) Current nebulized drug delivery is a continuous mode, which cannot be synchronized with the patient's respiratory cycle. The drug aerosol generated during the expiratory phase cannot be effectively inhaled by the patient, resulting in a large amount of waste. Because drug aerosols are prone to condensation and adhere to the tube wall when passing through the long and cool nasopharyngeal airway, the proportion of drug that can actually reach the deep target areas (such as the glottis and larynx) is limited. In order to achieve the therapeutic effect, it is often necessary to increase the dosage, which increases the possibility of systemic drug absorption and may lead to unnecessary systemic side effects.

[0006] Therefore, how to achieve real-time nebulization of drugs near the target area and intelligently adjust the timing of nebulization according to the respiratory cycle in order to increase local drug concentration, enhance efficacy and reduce systemic effects is a key problem that existing technologies have not been able to effectively solve. Summary of the Invention

[0007] This invention aims to overcome the limitations of existing nasopharyngeal airways, which have a single function. Traditional nasopharyngeal airways can only maintain airway patency and cannot simultaneously administer nebulized drug delivery, resulting in cumbersome clinical operations and low treatment efficiency. At the same time, the connection between the nebulized drug delivery device and the nasopharyngeal airway is unstable. Traditional external nebulizers have problems such as complex connections, serious drug waste, low drug delivery accuracy, and the inability of the continuous nebulization mode to synchronize with the patient's respiratory cycle, resulting in significant drug waste during the expiratory phase.

[0008] To address the aforementioned issues, this invention provides a nasopharyngeal airway device with nebulized drug delivery function and its application method. This solves the problems of inconvenience in operation, drug waste, and poor treatment effect caused by separating the nasopharyngeal airway from the nebulized treatment device, and achieves efficient and precise local drug delivery treatment while maintaining airway patency.

[0009] To achieve the above-mentioned technical objectives and effects, this application provides the following technical solution: In a first aspect, the present invention provides a nasopharyngeal airway device with nebulized drug delivery function, including a nasopharyngeal airway tube, wherein the nasopharyngeal airway tube has an airway body and a connecting end tube that are inserted and sealed together, and a nebulization module is detachably connected between the airway body and the connecting end tube, wherein the nebulization module is used to introduce nebulized drugs into the airway body.

[0010] Preferably, a plug groove is coaxially formed on the inner wall of the end of the connecting pipe that connects to the vent pipe body. The vent pipe body has a connecting part 1 with an outer diameter that is the same as the inner diameter of the plug groove. The plug groove and the connecting part 1 are plugged into and sealed together. A magnetic body 1 is embedded in the bottom wall of the plug groove. A magnetic body 2 that is magnetically attracted to the magnetic body 1 is embedded in the end of the connecting part 1.

[0011] Furthermore, the atomizing module includes an atomizer tube and an atomizing core. The atomizer tube has a compressed air connection port, an installation port, and an atomization outlet. The atomizing core is detachably connected to the atomizer tube through the installation port. The atomizer tube is connected to an external compressed air source through the compressed air connection port. The atomization outlet is a T-shaped three-way connector, with one port connecting to the inner cavity of the atomizer tube and the other two ports connecting to the air vent and the connecting end pipe, respectively.

[0012] Furthermore, the aerosol outlet has a second connecting part that is plugged into and sealed with the insertion slot, and a third magnetic body that is magnetically attracted to the first magnetic body is embedded at the end of the second connecting part.

[0013] Furthermore, the aerosol outlet also has an interface pipe section that is plugged into and sealed with the connecting part. The interface pipe section has a connecting groove whose inner diameter matches the outer diameter of the connecting part. A magnetic body four that is magnetically attracted to the magnetic body two is embedded in the bottom wall of the connecting groove.

[0014] Furthermore, a one-way valve is provided in one end of the interface where the aerosol outlet is connected to the connecting pipe, and the flow direction of the one-way valve is towards the vent pipe body.

[0015] Furthermore, a flow sensor can be detachably connected to one end of the aerosol outlet that connects to the ventilation pipe. The flow sensor is a flow sensor with bidirectional flow measurement capability, which distinguishes the airflow direction by the positive and negative directions of the output signal.

[0016] Furthermore, it also includes a controller, wherein the signal output terminal of the flow sensor is electrically connected to the signal input terminal of the controller, and the control output terminal of the controller is electrically connected to the control terminal of the external compressed air source; the controller is preset with a breathing phase recognition algorithm and configured to receive the breathing airflow signal collected by the flow sensor, identify the inspiratory and expiratory phases in the breathing cycle, control the external compressed air source to start during the inspiratory phase to drive the nebulization module to work, and control the external compressed air source to pause or reduce power during the expiratory phase.

[0017] Secondly, the present invention also provides an intelligent intermittent nebulization drug delivery method based on the respiratory cycle, using the aforementioned nasopharyngeal airway device with nebulization drug delivery function, comprising the following steps: S1, The patient's respiratory airflow flow signal is collected in real time through the flow sensor; S2, the flow signal is transmitted to the controller, and the controller identifies the inspiratory and expiratory phases in the respiratory cycle through a respiratory phase recognition algorithm; S3, within a set delay time after the start of the inhalation phase, the controller sends a start command to the external compressed air source to drive the nebulization module to work and generate drug aerosol; S4: Within a set delay time after the start of the exhalation phase, the controller sends a pause or power reduction command to the external compressed air source to reduce or stop nebulization.

[0018] Preferably, the respiratory phase recognition algorithm in step S2 includes taking the airflow rate signal as input, determining the start of the inspiratory phase when the airflow rate changes from negative to positive and continues to rise, and determining the start of the expiratory phase when the airflow rate changes from positive to negative.

[0019] The nasopharyngeal airway device with nebulized drug delivery function and its application method provided by the present invention have the following advantages: 1. This invention achieves a perfect combination of nasopharyngeal airway and nebulization function, integrating the nebulization module between the airway body and the connecting end tube, eliminating the need for external tubing and greatly simplifying the clinical operation process.

[0020] 2. The nasopharyngeal airway device with nebulized drug delivery function of the present invention is stable and reliable through magnetic sealing connection. The sealing and plugging of the insertion groove and the connection part one, combined with the magnetic positioning of magnetic body one to magnetic body four, ensures the stability and airtightness of each connection end.

[0021] 3. The nasopharyngeal airway device of the present invention with nebulized drug delivery function has proximal nebulization to reduce condensation loss: the nebulization module is set at the proximal end of the airway body, and the aerosol formation position is close to the airway inlet, which greatly shortens the drug delivery path and reduces condensation deposition on the tube wall.

[0022] 4. The nasopharyngeal airway device of the present invention, equipped with nebulized drug delivery function, significantly improves drug utilization through intelligent intermittent nebulization. A flow sensor monitors respiratory airflow in real time, and the controller initiates nebulization during the inspiratory phase and pauses it during the expiratory phase, avoiding drug waste during expiration. Comparative experiments show that the drug utilization rate of the intelligent intermittent nebulization mode is 82.5%, significantly higher than the 54.2% of the continuous nebulization mode, and the drug waste rate is reduced from 31.6% to 8.3%. Attached Figure Description

[0023] Figure 1 A cantilever diagram of a nasopharyngeal airway device with nebulized drug delivery function provided in an embodiment of the present invention. Figure 1 ; Figure 2 A cantilever diagram of a nasopharyngeal airway device with nebulized drug delivery function provided in an embodiment of the present invention. Figure 2 ; Figure 3 This is a cross-sectional structural diagram illustrating the connection relationship between the nasopharyngeal airway tube and the nebulization module, which is the main feature of this invention. Figure 4 for Figure 3 Enlarged schematic diagram of part A in the middle.

[0024] In the picture: 1-Nasopharyngeal airway tube; 11-Airway body; 111-Connector 1; 12-Connecting end tube; 121-Plug-in slot; 2-Atomizing module; 21-Atomizer tube body; 211-Compressed air connection port; 212-Installation port; 213-Aerosol outlet; 2131-Connector 2; 2132-Interface tube section; 213A-Connecting groove; 22-Atomizing core; 3-Magnetic body 1; 4-Magnetic body 2; 5-Magnetic body 3; 6-Magnetic body 4; 7-One-way valve; 8-Flow sensor; 9-Controller. Detailed Implementation

[0025] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0026] Reference Figure 1 and Figure 2 This invention provides a nasopharyngeal airway device with nebulized drug delivery function, comprising a nasopharyngeal airway tube 1. The nasopharyngeal airway tube 1 is made of medical-grade polyvinyl chloride (PVC) or antibacterial coated silicone and has a plug-in sealing fit between the airway body 11 and the connecting end tube 12, realizing the basic function of establishing a nasopharyngeal airway. The connecting end tube 12 is used to connect to an oxygen inhalation tube. A nebulization module 2 can also be detachably connected between the airway body 11 and the connecting end tube 12, which can be installed as needed, such as in advance when nebulized drug delivery is required. In emergency, anesthesia, and intensive care scenarios, it can maintain airway patency and achieve timely, efficient, high-utilization, and well-sealed nebulized drug delivery.

[0027] Reference Figures 1-4 A insertion groove 121 is coaxially provided on the inner wall of the end of the connecting tube 12 that connects to the vent tube 11. The vent tube 11 has a connecting part 111 with an outer diameter that is the same as the inner diameter of the insertion groove 121. The connecting part 111 and the insertion groove 121 are inserted and sealed to establish a preliminary and stable connection. A magnetic body 3 is embedded in the bottom wall of the insertion groove 121. A magnetic body 4 that is attracted to the magnetic body 3 is embedded in the end of the connecting part 111. The magnetic attraction structure further ensures the stability of the connection between the connecting tube 12 and the vent tube 11.

[0028] Reference Figures 1-4 The atomizing module 2 includes an atomizer tube 21 and an atomizing core 22. The atomizer tube 21 has an integrally formed compressed air connection port 211, an installation port 212, and an atomization outlet 213. The atomizing core 22 is detachably connected to the atomizer tube 21 through the installation port 212. The atomizer tube 21 is connected to an external compressed air source, such as a medical compressor or a central oxygen supply system with a jet atomization interface, through the compressed air connection port 211.

[0029] In a further embodiment, the aerosol outlet 213 is a T-shaped three-way connector, with one port connecting to the inner cavity of the atomizer tube 21, and the other two ports connecting to the ventilation tube 11 and the connecting end tube 12, respectively. Specifically, the aerosol outlet 213 has a connecting part 2131 that is fitted into the insertion slot 121 for a sealing fit, and a magnetic body 5 that is magnetically attracted to the magnetic body 3 is embedded at the end of the connecting part 2131. The aerosol outlet 213 also has an interface tube section 2132 that is fitted into the connecting part 111 for a sealing fit, and the interface tube section 2132 has a connecting groove 213A with an inner diameter matching the outer diameter of the connecting part 111, and a magnetic body 6 that is magnetically attracted to the magnetic body 4 is embedded on the inner bottom wall of the connecting groove 213A. Through the structural design of the aerosol outlet 213, the existing connection structure between the connecting end tube 12 and the ventilation tube 11 is fully utilized, while ensuring the stability and airtightness of the connection between the atomizing module 2 and the connecting end tube 12 and the ventilation tube 11.

[0030] Reference Figure 4 A one-way valve 7 is installed in the interface at the end where the aerosol outlet 213 connects to the connecting tube 12. The flow direction of the one-way valve 7 is towards the ventilation tube 11. This avoids the possibility of nebulized medication flowing out from the end where the aerosol outlet 213 connects to the connecting tube 12, thus improving medication utilization, without affecting the normal oxygen supply requirements of the nasopharyngeal airway tube 1. When the nebulization module is in use, compressed air enters the inner cavity of the nebulizer tube 21 through the compressed air connection port 211. The high-speed airflow creates negative pressure (Venturi effect) at the nebulizer core 22, drawing the liquid medication from the liquid medication storage chamber and pulverizing it into an aerosol. The aerosol is guided through the T-shaped three-way interface of the aerosol outlet 213, with one end leading to the ventilation tube 11 (facing the patient), and the other end connected to the connecting tube 12 via the one-way valve 7.

[0031] In a further embodiment, a flow sensor 8 can be detachably connected to one end of the aerosol outlet 213 that connects to the ventilation tube 11. The flow sensor 8 is a flow sensor with bidirectional flow measurement capability, which distinguishes the airflow direction by the positive and negative directions of the output signal. In feasible embodiments, the flow sensor 8 can be a disposable proximal flow sensor, such as the SFM3300-D model, which is designed for non-invasive ventilation interfaces such as nasopharyngeal airways and masks. It can be inserted later with the aerosol outlet 213 or integrated into the design. It is used to monitor the patient's respiratory airflow in real time, and then realize intelligent intermittent nebulization control by monitoring the respiratory airflow. It can automatically adjust the nebulization timing according to the patient's respiratory cycle, which significantly improves the drug utilization rate.

[0032] Reference Figure 1In a further embodiment, a controller 9 is also embedded on the outer wall of the nebulizer tube 21. The signal output terminal of the flow sensor 8 is electrically connected to the signal input terminal of the controller, and the control output terminal of the controller 9 is electrically connected to the control terminal of the external compressed air source. The controller 9 is preset with a breathing phase recognition algorithm and configured to receive the breathing airflow signal collected by the flow sensor 8, identify the inspiratory phase and expiratory phase in the breathing cycle, control the external compressed air source to start during the inspiratory phase to drive the nebulizer module 2 to work, and control the external compressed air source to pause or reduce power during the expiratory phase.

[0033] This invention also provides an intelligent intermittent nebulization drug delivery method based on the respiratory cycle. Utilizing the aforementioned nasopharyngeal airway device with nebulization drug delivery function, it achieves intermittent nebulization synchronized with respiration, administering the drug only during the patient's inhalation and stopping during exhalation, thereby significantly improving drug utilization. The method includes the following steps: S1 collects the patient's respiratory airflow flow signal in real time through the flow sensor 8.

[0034] S2, the flow sensor 8 transmits the flow signal to the controller 9, and the controller 9 identifies the inspiratory and expiratory phases in the respiratory cycle through a respiratory phase recognition algorithm. The respiratory phase recognition algorithm takes the airflow flow signal as input, and determines the start of the inspiratory phase when the airflow flow changes from negative to positive and continues to rise, and determines the start of the expiratory phase when the airflow flow changes from positive to negative.

[0035] S3, within a set delay time (50-200ms) after the start of the inhalation phase, the controller 9 sends a start command to the external compressed air source to drive the nebulization module 2 to work, and the drug aerosol enters the patient's airway with the inhaled airflow.

[0036] S4, within a set delay time (50-200ms) after the start of the expiratory phase, the controller 9 sends a pause or power reduction command to the external compressed air source to reduce or stop nebulization and avoid waste of medication during the expiratory phase.

[0037] To verify the technical effects of the present invention, the inventors conducted the following comparative experiments: Experiment 1: Comparison of drug delivery efficiency between this device and the external nebulizer solution Experimental conditions: The same model of simulated artificial airway (8 mm inner diameter, 15 cm length) was used to administer the drug via nebulization at the same dose (5 ml physiological saline + sodium fluorescein tracer). The drug was collected at the airway outlet (near the simulated glottis) and the proportion of drug reaching the target area and the deposition rate on the airway wall were measured.

[0038]

[0039] Conclusion: Because the atomization module 2 is located near the end of the ventilation tube 11, the aerosol formation location is close to the airway inlet. This device increases the proportion of drug reaching the target area by 71.7% compared to the traditional method, and reduces the tube wall deposition rate by 68.7%.

[0040] Experiment 2: Comparison of drug utilization rates between intelligent intermittent nebulization and continuous nebulization Experimental conditions: Using the same device as described in this application, drug administration was performed under conditions of controller 9 not being enabled (continuous nebulization mode) and controller 9 being enabled (intelligent intermittent nebulization mode), and drug utilization and waste rate were measured.

[0041]

[0042] Conclusion: The intelligent intermittent nebulization mode, through synchronized respiratory cycle control, improves drug utilization by 52.2% and reduces drug waste during the expiratory phase by 73.7% compared to the continuous mode.

[0043] The above description is merely a preferred embodiment of the present invention and is not intended to limit the present invention in any form or substance. It should be noted that those skilled in the art can make various improvements and additions without departing from the present invention, and these improvements and additions should also be considered within the scope of protection of the present invention. Any modifications, alterations, and equivalent changes made by those skilled in the art based on the above-disclosed technical content without departing from the spirit and scope of the present invention are equivalent embodiments of the present invention. Furthermore, any modifications, alterations, and evolutions made to the above embodiments based on the essential technology of the present invention still fall within the scope of the technical solution of the present invention.

Claims

1. A nasopharyngeal airway device with nebulized drug delivery function, characterized in that, The nasopharyngeal airway tube (1) has an airway body (11) and a connecting end tube (12) that are fitted together and sealed. An atomizing module (2) can also be detachably connected between the airway body (11) and the connecting end tube (12). The atomizing module (2) is used to introduce atomized drugs into the airway body.

2. The nasopharyngeal airway device with nebulized drug delivery function as described in claim 1, characterized in that, The inner wall of the end of the connecting pipe (12) connected to the vent pipe (11) is coaxially provided with a plug groove (121). The vent pipe (11) has a connecting part (111) with an outer diameter that is the same as the inner diameter of the plug groove (121). The plug groove (121) and the connecting part (111) are plugged in and sealed together. A magnetic body (3) is embedded in the bottom wall of the plug groove (121). A magnetic body (4) that is magnetically attracted to the magnetic body (3) is embedded in the end of the connecting part (111).

3. The nasopharyngeal airway device with nebulized drug delivery function as described in claim 2, characterized in that, The atomizing module (2) includes an atomizer tube (21) and an atomizing core (22). The atomizer tube (21) has a compressed air connection port (211), an installation port (212), and an atomization outlet (213). The atomizing core (22) is detachably connected to the atomizer tube (21) through the installation port (212). The atomizer tube (21) is connected to an external compressed air source through the compressed air connection port (211). The atomization outlet (213) is a T-shaped three-way connector, one of which is connected to the inner cavity of the atomizer tube (21), and the other two are connected to the ventilation tube (11) and the connecting end tube (12), respectively.

4. The nasopharyngeal airway device with nebulized drug delivery function as described in claim 3, characterized in that, The aerosol outlet (213) has a second connection part (2131) that is plugged into and sealed with the insertion groove (121), and the end of the second connection part (2131) is fitted with a third magnetic body (5) that is magnetically attracted to the first magnetic body (3).

5. The nasopharyngeal airway device with nebulized drug delivery function as described in claim 4, characterized in that, The aerosol outlet (213) also has an interface pipe section (2132) that is plugged into and sealed with the connecting part (111). The interface pipe section (2132) has a connecting groove (213A) with an inner diameter that matches the outer diameter of the connecting part (111). A magnetic body four (6) that is magnetically attracted to the magnetic body two (4) is embedded in the bottom wall of the connecting groove (213A).

6. The nasopharyngeal airway device with nebulized drug delivery function as described in claim 5, characterized in that, A one-way valve (7) is provided in one end of the aerosol outlet (213) connected to the connecting end pipe (12), and the flow direction of the one-way valve (7) is towards the vent pipe body (11).

7. The nasopharyngeal airway device with nebulized drug delivery function as described in claim 6, characterized in that, A flow sensor (8) can also be detachably connected to one end of the aerosol outlet (213) and the ventilation pipe (11). The flow sensor (8) is a flow sensor with bidirectional flow measurement capability, which distinguishes the airflow direction by the positive and negative directions of the output signal.

8. The nasopharyngeal airway device with nebulized drug delivery function as described in claim 7, characterized in that, It also includes a controller (9), the signal output terminal of the flow sensor (8) is electrically connected to the signal input terminal of the controller (9), and the control output terminal of the controller (9) is electrically connected to the control terminal of the external compressed air source; the controller is preset with a breathing phase recognition algorithm and configured to receive the breathing airflow signal collected by the flow sensor (8), identify the inspiratory phase and expiratory phase in the breathing cycle, control the external compressed air source to start in the inspiratory phase to drive the nebulization module (2) to work, and control the external compressed air source to pause or reduce power in the expiratory phase.

9. A smart intermittent nebulized drug delivery method based on respiratory cycles, applied to the nasopharyngeal airway device with nebulized drug delivery function as described in claim 8, characterized in that, Includes the following steps: S1, the patient's respiratory airflow flow signal is collected in real time through the flow sensor (8); S2, the flow signal is transmitted to the controller, and the controller (9) identifies the inspiratory phase and expiratory phase in the respiratory cycle through a respiratory phase recognition algorithm; S3, within a set delay time after the start of the inhalation phase, the controller (9) sends a start command to the external compressed air source to drive the atomizing module (2) to work and generate drug aerosol; S4, within a set delay time after the start of the exhalation phase, the controller (9) sends a pause or power reduction command to the external compressed air source to reduce or stop nebulization.

10. The intelligent intermittent nebulization drug delivery method based on respiratory cycle as described in claim 9, characterized in that, The respiratory phase recognition algorithm described in step S2 includes taking the airflow rate signal as input, determining the start of the inspiratory phase when the airflow rate changes from negative to positive and continues to rise, and determining the start of the expiratory phase when the airflow rate changes from positive to negative.

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