Portable tuberculosis drug aerosol inhalation device

Abstract

The invention belongs to the technical field of medical equipment, and particularly relates to a portable tuberculosis drug aerosol inhalation device. The device comprises a medicine storage chamber, an outflow channel and a controller, the top of the medicine storage chamber is provided with a medicine tank groove with a conical pricking pipe, and one-step medicine filling through placing and pressing can be achieved; the respiratory rhythm of a user is identified through lip contact and a respiratory airflow sensor, and the atomizer is synchronously controlled to start and stop; the system has the functions of liquid medicine identity recognition, heating temperature control and self-adaptive power adjustment based on liquid medicine storage, efficient, safe and comfortable tuberculosis medicine inhalation treatment is achieved, and the medication compliance and the treatment effect are remarkably improved.

Description

Technical Field

[0001] This invention belongs to the field of medical device technology, specifically relating to a portable tuberculosis drug nebulization inhalation device. Background Technology

[0002] Tuberculosis is a chronic infectious disease caused by Mycobacterium tuberculosis, with pulmonary tuberculosis being the most common. Drug therapy is the core of tuberculosis control. In addition to oral and injectable treatments, nebulized inhalation therapy can deliver drugs directly to the lesions in the lungs, increasing local drug concentration and reducing systemic side effects, and has become an important adjunctive treatment method.

[0003] However, currently common nebulizers in clinical practice have many shortcomings, affecting their widespread application and efficacy among patients. Firstly, traditional nebulizers are extremely cumbersome in terms of medication dispensing: patients need to open the bottle cap, carefully pour the medication into the reservoir, and precisely control the dosage. This process is difficult for patients with limited mobility, impaired vision, or tremors, easily leading to spills, inaccurate dosages, or even contamination, severely reducing medication adherence.

[0004] Secondly, the nebulization process of existing devices is not synchronized with the patient's spontaneous breathing rhythm. Most devices continuously nebulize after activation. When the patient exhales, their mouth inevitably leaves the device. If the device continues to nebulize the medication, some of the drug will be directly lost into the air, resulting in drug waste and environmental pollution, while also increasing the risk of cross-infection among family members. Furthermore, during the initial inhalation phase, due to the delayed nebulization activation, the patient cannot immediately inhale the effectively nebulized medication, leading to low drug delivery efficiency. This waste is particularly pronounced for expensive anti-tuberculosis drugs.

[0005] Furthermore, many tuberculosis drugs have high viscosity at room temperature, and the aerosol particles produced after nebulization are large and uneven in size, making it difficult to deposit in the small airways deep in the lungs. In addition, inhaling low-temperature nebulizers can irritate the respiratory tract, causing patients to cough and feel uncomfortable, further affecting the smooth progress of treatment.

[0006] Finally, existing devices generally lack intelligent drug management functions. They cannot automatically identify drug types and match optimal nebulization parameters, nor can they dynamically adjust the output power based on real-time changes in drug concentration and viscosity during treatment. This results in nebulization efficiency gradually decreasing as treatment progresses, and inconsistent dosages within a single treatment session.

[0007] Therefore, there is an urgent need in the field for a portable tuberculosis drug nebulization inhalation device that is easy to operate, can synchronize patient breathing, intelligently control nebulization parameters, and ensure consistent drug administration throughout the entire course of treatment. Summary of the Invention

[0008] The purpose of this invention is to provide a portable tuberculosis drug nebulization inhalation device that solves the problems of cumbersome operation, drug waste, and low drug delivery efficiency in existing technologies by inserting and pressing the device in one step, nebulizing the drug while breathing, and intelligent temperature control and power adjustment, thereby improving patient medication compliance and treatment efficacy.

[0009] A portable tuberculosis drug nebulizer includes a drug storage chamber, an outflow channel, and a controller. The drug storage chamber contains tuberculosis medication. The inlet of the outflow channel is connected to the drug storage chamber, and an atomizer is installed between the drug storage chamber and the outflow channel to atomize the flowing medication. The outlet of the outflow channel has a mouthpiece contact sensor unit, with a mouthpiece fitted on the outside. The controller is electrically connected to the atomizer to control its start / stop and power. The top of the drug storage chamber has a medicine container slot, which is designed to hold a bottle-shaped medicine container. A conical tube is installed at the bottom of the medicine container slot. When the bottle-shaped medicine container is inserted into the medicine container slot and pressed downwards, its flexible opening is punctured by the conical tube, connecting the inside of the medicine container to the drug storage chamber, allowing the medication to flow into the storage chamber under gravity. This device simplifies the traditional complex steps of "opening the cap, pouring, and metering" into a simple one-step action of "inserting and pressing." Users simply place the bottle-shaped medicine container into the medicine container slot and press down; the system automatically breaks the bottle and dispenses the medication, significantly reducing the operational barrier. This design is particularly suitable for patients with limited mobility, poor eyesight, or those self-administering medication in non-clinical environments (such as at home), improving medication adherence. Traditional pouring methods expose the medication to air, increasing the risk of contamination. In this design, after the conical tube punctures the bottle opening, the medication flows directly into the storage chamber within a closed system by gravity, minimizing contact between the medication and air. This is crucial for tuberculosis medications, as many of these drugs are inherently toxic or require sterility. The closed-loop delivery system protects the user from inhaling contaminated medication and also ensures the stability of the medication itself.

[0010] A portable tuberculosis drug nebulizer inhalation device includes a controller mounted on the top surface of the outflow channel. An airflow sensor is located on the side of the controller. When the user's lips contact the outlet end of the outflow channel, the airflow sensor's detection port faces the user's nostrils to detect the user's respiratory airflow. The device features a highly sensitive airflow sensor at the corresponding position in the user's nostrils, enabling direct and accurate detection of changes in respiratory airflow and reducing the probability of false alarms. The controller's built-in algorithm predicts the start of the inspiratory phase based on the end-of-expiration characteristic point, thereby improving timing control accuracy and achieving efficient synchronization between the nebulization process and the user's respiratory cycle. This design reduces reliance on independent respiratory sensors, contributing to a more compact and portable device suitable for home or mobile healthcare scenarios.

[0011] A portable tuberculosis drug nebulization inhalation device, wherein the controller is configured to: identify the user's expiratory phase based on the contact signal from the mouthpiece contact sensing unit and the respiratory airflow signal from the airflow sensor, and predict the start of the inspiratory phase based on the end of the expiratory phase; Specifically, the controller activates the nebulizer when the airflow sensor detects an end-of-exhalation signal, so that the nebulizer is in working condition before the user begins active inhalation; and keeps the nebulizer on until the airflow sensor detects an airflow signal that matches the exhalation characteristics, at which point the nebulizer is turned off.

[0012] This device predicts the start of the user's inspiratory phase and triggers the nebulizer in advance, allowing the user to inhale the nebulized medication at the beginning of inhalation, effectively eliminating the medication delay period at the start of inspiration. By recognizing the user's respiratory rhythm in real time, it dynamically adjusts the nebulization and delivery rate of the medication, avoiding both coughing caused by excessively fast delivery and reduced drug delivery efficiency caused by excessively slow delivery. Furthermore, traditional nebulizers continuously nebulize after activation, and patients habitually remove their mouths from the device during exhalation, resulting in many nebulized droplets escaping into the air, potentially causing cross-infection and medication waste. This device stops nebulizer operation based on the expiratory phase, further improving drug utilization and avoiding waste, especially suitable for expensive tuberculosis medications, offering significant economic benefits.

[0013] A portable tuberculosis drug nebulizer inhalation device has a drug storage chamber with a sandwich structure and its inner wall made of a heat-conducting material. Several thin-film heating pads are installed inside the sandwich and are attached to the outer side of the inner wall to heat the drug solution in the drug storage chamber through the heat-conducting inner wall. The controller is electrically connected to the thin-film heating element and configured to regulate and control its heating temperature. Many tuberculosis medications typically have high viscosity at room temperature. Heating significantly reduces this viscosity, increasing their fluidity. This makes the medication easier to atomize using a nebulizer, resulting in finer, more uniform drug aerosol particles. Finer particles can reach deeper into lung lesions, improving drug deposition and bioavailability. Simultaneously, increased nebulization efficiency means more effective medication can be delivered in the same amount of time, shortening the time required for a single inhalation therapy session. The controller precisely regulates and controls the heating temperature, maintaining a constant optimal nebulization temperature throughout the treatment. This avoids fluctuations in particle size and output rate due to changes in medication temperature with environmental or usage time variations, ensuring consistent dosage and particle distribution for each inhalation, and improving treatment reliability and repeatability. Inhaling room-temperature or cool nebulizer vapor may irritate the respiratory tract, causing coughing or discomfort, especially for patients with sensitive respiratory systems. Heating the medication to near body temperature before nebulization significantly reduces cold stimulation to the respiratory tract, making the inhalation process more comfortable and helping users better cooperate in completing the treatment.

[0014] A portable tuberculosis drug nebulizer inhalation device is disclosed. The outer wall of the bottle-shaped container is equipped with a barcode storing electronic information about the drug solution inside. A controller with a built-in code reader identifies the barcode. Pressure and temperature sensors are located at the bottom of the storage chamber to detect the volume and temperature of the drug solution. The controller's code reader, in conjunction with the barcode or similar code on the drug container, automatically and accurately identifies the identity information of the loaded drug solution, including drug type, concentration, and batch number. This identification mechanism effectively avoids potential errors introduced by manual settings, ensuring the accuracy of treatment information from the outset. The identified drug solution identity information serves as the basis for the controller to automatically set recommended heating temperature and nebulization power. This allows the device to adaptively match optimal nebulization parameters based on the physical properties (such as viscosity and surface tension) and chemical stability of different types of tuberculosis drugs, thereby improving drug nebulization efficiency and lung deposition rate while achieving personalized drug delivery and enhanced efficacy. The integrated pressure sensor monitors the medication volume in real time. When the medication is depleted, the controller promptly shuts off the nebulizer and heater, preventing damage from no-load operation and eliminating harmful substances generated by overheating. Furthermore, the sensor estimates the remaining medication and proactively alerts the user when the dosage is insufficient, ensuring complete administration during each treatment. A temperature sensor accurately detects the real-time temperature of the medication, forming the core of the closed-loop temperature control system together with the thin-film heater. The controller dynamically adjusts the heating power based on temperature feedback, keeping the medication temperature consistently within the optimal treatment range and preventing adverse effects on efficacy and user comfort caused by excessively high or low temperatures.

[0015] A portable tuberculosis drug nebulization inhalation device, wherein the controller has a pre-stored data table containing various drug identification information, and the identification information is associated with at least the recommended heating temperature and the recommended nebulization power; The controller is configured to query a data table based on received coded information and set the target temperature of the thin-film heating element and the target operating power of the nebulizer accordingly. Different tuberculosis drugs have different physicochemical properties (such as viscosity, surface tension, and thermal stability). These properties directly determine their optimal nebulization temperature and required energy. The controller can identify specific drug solutions and automatically call upon their unique "recommended heating temperature" and "recommended nebulization power." At the optimal temperature, the drug viscosity decreases, making it easier to disperse by a nebulizer of a specific power, producing smaller and more uniform aerosol particles. This ensures that the drug can be efficiently deposited into deep lung lesions, directly improving bioavailability and therapeutic efficacy. For temperature-sensitive drugs, the system automatically sets a safe and effective heating temperature to avoid drug decomposition or inactivation due to overheating, thus ensuring efficacy.

[0016] A portable tuberculosis drug nebulizer inhalation device, wherein the controller is further configured to execute a power control algorithm based on drug solution volume adaptation for dynamically adjusting the operating power of the nebulizer during a single treatment session, the algorithm comprising the following steps: S1: After the medicine tank is filled, the initial weight of the medicine liquid or the liquid level pressure value in the medicine storage chamber is obtained through the pressure sensor, and this is used as a reference. S2: During the user's inhalation phase, the atomizer is activated and operates at initial power; S3: Read the current value of the pressure sensor in real time and calculate the amount of medicine consumed or the current amount of medicine remaining; S4: Based on the amount of medicine consumed or the current amount of medicine remaining, query the pre-stored power adjustment mapping table and dynamically set the real-time operating power of the nebulizer; wherein, the power adjustment mapping table is configured to gradually increase the operating power of the nebulizer as the medicine is consumed, in order to compensate for the decrease in atomization efficiency caused by the concentration and increased viscosity of the medicine.

[0017] Most nebulized medications are not pure drugs, but rather solutions or suspensions formed by dissolving or suspending the active pharmaceutical ingredient (solute) in a solvent (usually water or ethanol). Nebulizers produce micron-sized aerosol droplets. The majority of the volume of these droplets is composed of solvent. Drug molecules or particles are "encased" within these solvent droplets and delivered. During nebulization, each generation of mist means an equal amount of solvent is preferentially carried away, while the drug solute remains mostly in the liquid remaining in the reservoir. Therefore, during nebulization, the drug concentration continuously increases, becoming increasingly viscous.

[0018] By directly linking nebulizer power to real-time monitored drug consumption, a precise, reliable, and low-cost reactive closed-loop control is achieved. This effectively combats the decline in nebulization efficiency caused by drug concentration during treatment, ensuring stable dosage and maximized efficacy throughout the entire treatment. The algorithm directly tracks "drug consumption," the root cause of decreased nebulization efficiency. Through a preset "power adjustment mapping table," the system can calculate the optimal compensation power in real time based on the precise remaining drug volume. This eliminates potential errors from prediction models based on fixed durations, ensuring perfect synchronization between the timing and intensity of power compensation and the actual physical state of the drug. This guarantees a highly stable output rate of the drug aerosol from the first inhalation to the last, thus ensuring uniform dosage. If treatment is interrupted and then resumed, time-based algorithms may experience compensation misalignment. However, this solution automatically adjusts the power based on the current actual remaining drug volume upon restarting, ensuring seamless compensation unaffected by the passage of time. The control baseline is an objective and direct pressure / weight signal, avoiding cumulative errors caused by clock drift or component aging, resulting in higher consistency and reliability of the device over long-term use. During operation, the algorithm naturally generates a data chain corresponding to the "drug concentration - power adjustment." This real-world data can be recorded and analyzed for continuous optimization of the "power adjustment mapping table" for different drugs. This gives the device the potential for continuous learning and evolution, enabling it to provide increasingly precise and personalized nebulization solutions for tuberculosis drugs with different characteristics.

[0019] Optionally, to improve drug utilization and avoid control conflicts, this invention links respiratory synchronization control with adaptive drug level control. Specifically, the controller is configured to dynamically adjust the maximum allowable nebulization duration (i.e., the "maximum inspiratory window") for each inspiratory phase based on the real-time monitored remaining drug level. When the remaining drug level is low or the drug viscosity is high, the adaptive power control algorithm increases the nebulizer power to maintain output. Simultaneously, the system extends the "maximum inspiratory window" duration accordingly, ensuring that the additional drug mist generated by this power increase can be fully inhaled by the user, thereby achieving consistent and efficient dosage throughout the entire treatment cycle.

[0020] A portable tuberculosis drug nebulizer inhalation device, The controller is also configured to execute a liquid temperature control algorithm for controlling the thin-film heating element, the algorithm including: Preheating stage: After the medicine container is detected to be filled and before the first use, the thin film heating element is controlled to heat the medicine liquid to the target temperature and maintain it; Maintenance phase: During nebulized inhalation, the temperature of the drug solution in the storage chamber is monitored in real time, and the on / off state of the thin-film heating element is controlled by pulse width modulation (PWM) to keep the drug solution temperature stable within ±1.5℃ of the target temperature.

[0021] Many tuberculosis drugs are proteins, peptides, or other temperature-sensitive biological agents. Excessive temperature or large temperature fluctuations can lead to drug inactivation, denaturation, or aggregation, thereby reducing efficacy and even causing adverse reactions. This algorithm rapidly raises the drug solution to a validated, safe target temperature (typically the temperature at which the drug is most stable) through "preheating" and then strictly controls it within a very narrow range of ±1.5°C throughout the entire use via a "maintenance phase." This provides a consistent, stable, and controllable physicochemical environment for the drug solution, maximizing the protection of its molecular structure and biological activity, and ensuring drug effectiveness from the first inhalation to the last. The viscosity and surface tension of the drug solution are highly sensitive to temperature. Even fluctuations of only a few degrees Celsius can alter the particle size distribution of the aerosol particles generated by the nebulizer. The precise temperature control (±1.5°C) during the "maintenance phase" means that the physical properties of the drug solution (viscosity, surface tension) remain constant throughout the nebulization process. This allows the nebulizer to operate under completely consistent conditions, outputting a highly stable drug aerosol and ensuring consistency in dosage and particle size with each inhalation, thus achieving precise and repeatable pulmonary drug delivery. Inhaling room temperature or excessively cold mist can irritate the respiratory tract, causing coughing or bronchospasm; while excessively high temperatures can cause a burning sensation in the mouth or respiratory tract. The "preheating phase" ensures that the user is exposed to a warm mist during the first inhalation, avoiding cold stimulation. The "maintenance phase" continuously provides this comfortable inhalation experience. The warm mist significantly improves the comfort of inhalation therapy, reducing patient resistance and coughing reactions, which is crucial for tuberculosis patients who require long-term treatment, indirectly improving medication adherence. Continuous, uncontrolled heating wastes energy and can put stress on the device's circuitry and battery life. A "pulse width modulation" control method is used, a highly efficient closed-loop control strategy. It precisely controls the average heating power by rapidly switching the heating element on and off, avoiding the large temperature fluctuations caused by traditional on-off control. This algorithm can achieve the highest precision temperature control with minimal energy consumption, which is of great value for extending battery life and improving energy efficiency in portable devices.

[0022] A portable tuberculosis drug nebulizer inhalation device features an openable cover on the outer wall of the drug reservoir. Tuberculosis treatment is a long process, and drug residues can adhere to the inner wall of the reservoir. If not thoroughly cleaned, these residues can breed bacteria and mold. The openable cover provides a direct and complete cleaning channel, allowing users to thoroughly rinse and disinfect the interior of the reservoir, fundamentally eliminating this safety hazard. Drug residues not only cause hygiene problems but can also crystallize or condense, potentially clogging the nebulizer or small outflow channels, leading to decreased nebulization efficiency, poor output, or even equipment malfunction. Regular and thorough cleaning keeps the reservoir and the entire flow path clean and unobstructed, ensuring the nebulizer always operates at its optimal state, producing aerosol particles of stable size, thus guaranteeing consistent and accurate dosage for each administration.

[0023] A portable tuberculosis drug nebulizer inhalation device, the nebulizer inhalation device also includes a handle with a non-slip texture on the surface.

[0024] The core advantage of this invention lies in its simplification of complex medication administration into a single action of inserting and pressing. It also achieves precise synchronization of nebulization and inhalation by intelligently sensing the user's breathing rhythm. Furthermore, it integrates intelligent algorithms for automatic identification, precise temperature control, and adaptive power enhancement as the medication is consumed. Ultimately, it comprehensively improves drug utilization, ensures consistent dosage, and protects drug activity, while providing patients with unprecedented convenience, safety, and comfort. It is particularly suitable for use in non-clinical environments such as homes. Attached Figure Description

[0025] To more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are merely exemplary, and those skilled in the art can derive other embodiments based on the provided drawings without creative effort.

[0026] Figure 1 This is a schematic diagram of the external structure of the overall device of the present invention; Figure 2 This is a top view of the overall device of the present invention; Figure 3 This is a schematic cross-sectional view of the internal structure of the overall device of the present invention; Figure 4 This is a schematic diagram of the bottled medicine container of the present invention; Figure 5 This is a flowchart of Embodiment 2 of the present invention; Figure 6 This is a flowchart of Embodiment 3 of the present invention.

[0027] Figure descriptions: 1-Medicine storage chamber, 2-Discharge channel, 3-Controller, 4-Medicine container trough, 5-Handle, 6-Lid, 11-Pressure sensor, 12-Temperature sensor, 21-Mouth contact sensing unit, 22-Mouthpiece, 31-Airflow sensor, 32-Nebulizer, 33-Thin film heating element, 41-Conical tube, 42-Bottle-shaped medicine container, 42a-Barcode. Detailed Implementation

[0028] The technical solutions of the embodiments of the present invention 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 the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0029] The concepts involved in this application will first be described with reference to the accompanying drawings. It should be noted that the following descriptions of various concepts are only for the purpose of making the content of this application easier to understand and do not constitute a limitation on the scope of protection of this application; furthermore, the embodiments and features in the embodiments of this application can be combined with each other unless otherwise specified. This application will now be described in detail with reference to the accompanying drawings and embodiments.

[0030] Example 1: This embodiment mainly describes in detail the specific implementation of the portable tuberculosis drug nebulizer, highlighting its convenient filling operation, user-friendly design for easy cleaning and maintenance, and its portable structure.

[0031] See attached document Figure 1 , Figure 2 , Figure 3 As shown, the portable tuberculosis drug nebulizer inhalation device of this embodiment mainly includes the following core components.

[0032] As the main structure of the device, the drug storage chamber 1 is used to hold the tuberculosis medication to be atomized. Its internal cavity is smoothed to reduce medication residue. The outflow channel 2 is connected to the upper part of the drug storage chamber 1 at its inlet end and has a mouthpiece 22 at its outlet end for the user to inhale by holding it in their mouth. An atomizer 32 is installed at the connection between the drug storage chamber 1 and the outflow channel 2 to convert the flowing medication into fine aerosol particles that can be inhaled. The medicine container 4 is constructed on top of the drug storage chamber 1, and its shape and size are precisely designed to accommodate a standard-sized bottle-shaped medicine container 42. A hollow conical piercing tube 41 is fixedly installed at the center of the bottom of the medicine container 4. The tip of the tube is sharp enough to pierce the flexible sealing film at the bottom of the bottle-shaped medicine container 42. The lid 6 is installed on the side of the outer wall of the drug storage chamber 1 by a hinge structure. The size of the lid 6 is large enough to allow the user's hand or cleaning tools to enter the inside of the drug storage chamber 1. The lid 6 has a sealing ring at its edge to ensure the airtightness of the medicine storage chamber 1 when closed. The lid 6 is also equipped with a snap-lock mechanism for reliable opening and closing. The handle 5 is integrally formed with or fixedly connected to the lower structure of the medicine storage chamber 1. The gripping area of ​​the handle 5 is textured with anti-slip patterns. These patterns can be regular ripples, dotted raised areas, or irregular frosted textures, and the material can be rubber with a high coefficient of friction or a soft plastic coating.

[0033] The overall workflow and operation method of the device are as follows: The user opens the protective cap (not shown) on top of the medicine container 4 and places a bottle-shaped medicine container 42 pre-filled with a measured amount of tuberculosis medication into the medicine container 4, with the bottle opening (flexible sealing film end) facing downwards. The user applies downward pressure to the handle 5. Because the handle 5 provides a stable grip and the anti-slip texture ensures that the user's hand will not slip during operation, the user can easily and stably complete the downward pressing action. During the pressing process, the flexible sealing film at the bottom of the bottle-shaped medicine container 42 is punctured by the conical tube 41 at the bottom of the medicine container 42, forming a channel for the medication to flow out. Under the influence of gravity, the medication inside the medicine container 42 flows completely into the storage chamber 1 below through the hollow tube of the conical tube 41. Thus, the traditional complex steps of "opening the cap, pouring, and measuring" for adding medication are simplified to a single action of "placing and pressing". After completing one inhalation treatment, the user can unfasten the buckle and open the cover 6. Opening the cover 6 provides the user with a direct and spacious passage, which can easily and thoroughly rinse and scrub the inner walls and corners of the drug storage chamber 1 as well as the outside of the cone tube 41 to ensure that there is no drug residue. After cleaning and drying, close the cover 6 and fasten the buckle to restore the drug storage chamber 1 to a sealed state, ready for the next use.

[0034] This embodiment simplifies the medication administration process to a mere "insert and press," eliminating the need for complex operations or precise dosages. It is particularly suitable for patients with limited mobility, poor vision, or those self-administering medication in non-clinical environments (such as home), significantly improving patient adherence. After the conical tube punctures the bottle opening, the medication flows directly into the storage chamber within the closed system by gravity, minimizing contact between the medication and air and avoiding the risk of contamination—crucial for tuberculosis drugs that may possess some toxicity. The openable cap design makes daily cleaning and maintenance of the storage chamber extremely simple and thorough. This effectively prevents the growth of bacteria and mold from drug residues and avoids crystallization clogging the nebulizer or outflow channels, ensuring long-term stable operation of the device and accuracy of each dose. The non-slip handle design provides a stable point of force during medication administration, preventing slippage, and ensures a safe and comfortable grip during handheld inhalation and post-treatment cleaning, enhancing overall portability and ergonomics.

[0035] Example 2: This embodiment provides a portable tuberculosis drug nebulization inhalation device. Its core lies in achieving precise matching between the nebulization process and the user's breathing rhythm through high-precision sensors and intelligent control algorithms, and immediately taking safety measures when the user's stress response such as coughing is detected, thereby improving drug delivery efficiency and treatment safety.

[0036] See attached document Figure 1 , Figure 2 , Figure 3 As shown, the main body of the device is made of medical-grade ABS plastic. Its outer shell has an ergonomic handle 5 at the bottom, covered with soft rubber and textured with anti-slip features to ensure a secure grip. The drug storage chamber 1 has an inner wall made of thermally conductive aluminum alloy and an outer layer of heat-insulating plastic, forming a sandwich structure. Several thin-film heating elements 33 are tightly attached within this sandwich for indirect and uniform heating of the drug solution. The medicine container 4 is located at the top of the drug storage chamber 1 and is a vertical cylindrical cavity. A hollow conical tube 41 is fixed at the center of its bottom, with a sharp tip and an opening at the bottom connecting to the drug storage chamber 1. The bottle-shaped medicine container 42 is a disposable flexible plastic bottle, its opening sealed with an easily puncturable sealing film. A barcode 42a is affixed to the outer wall of the medicine container 42, recording information such as the type, concentration, batch number, and recommended treatment parameters of the drug solution. In use, the user inserts the medicine container 42 into the medicine container slot 4 and presses it down. The conical piercing tube 41 punctures the sealing membrane, and the medicine liquid automatically flows into the medicine storage chamber 1 under the action of gravity for later use. The bottom of the medicine storage chamber 1 is equipped with a pressure sensor 11 (used to determine the remaining amount of medicine liquid by liquid weight conversion) and a temperature sensor 12 (used to monitor the temperature of the medicine liquid in real time).

[0037] See attached document Figure 3As shown, the nebulizer 32 is located at the downstream outlet of the medication storage chamber 1. It employs piezoelectric ceramic mesh vibration technology to break the liquid medication into a fine mist with a particle size of 1-5 micrometers. The outflow channel 2 extends from the outlet of the nebulizer 32 to the top of the device, forming a tapering airflow pipe. A mouthpiece 22 is fitted onto its outlet end. This mouthpiece 22 is made of food-grade silicone, which is soft and conforms to the shape of the lips. A mouth contact sensing unit 21 is located around the outlet end of the outflow channel 2. When the user puts the mouthpiece 22 in their mouth, the mouth contact sensing unit 21 generates a sensing signal. In this example, it is a pressure sensor that can sensitively detect the contact between the user's lips and mouth.

[0038] The core of the controller 3 is a microcontroller unit (MCU) printed circuit board (PCB), which is encapsulated in a flat box and fixed to the top surface of the outflow channel 2, located above and behind the nozzle 22.

[0039] The airflow sensor 31 employs a thermal-film microelectromechanical system (MEMS) flow chip, with its sensing element located on the front side of the controller 3 housing. When the user's lips cover the mouthpiece 22, the detection port of the airflow sensor 31 is directly opposite and close to the user's nostrils, thus accurately detecting the speed and direction of airflow from the nostrils during breathing. An encoder is integrated on the PCB of the controller 3 for scanning and reading the barcode 42a on the bottle-shaped medicine container 42. The thin-film heating element 33, pressure sensor 11, temperature sensor 12, mouthpiece contact sensing unit 21, airflow sensor 31, encoder, and nebulizer 32 are all electrically connected to the controller 3.

[0040] See attached document Figure 5 As shown, controller 3 is configured to execute the following intelligent control algorithm: See attached document Figure 4 , 5 As shown, after the controller 3 reads the barcode 42a information through the encoder, it queries the internally stored data table to obtain the target heating temperature of the liquid medicine, for example, 37°C, and the target atomization power. The controller 3 then activates the thin-film heating element 33 to enter the preheating stage, heating the liquid medicine to the target temperature and maintaining it stably.

[0041] When using this device, the user primarily inhales the atomized medication through the mouth and exhales through the nose for ventilation. When the user's lips contact the mouthpiece 22, the mouthpiece contacts the sensing unit 21, which sends a signal, activating the device. The airflow sensor 31 detects a continuous and stable outward airflow (from the user to the environment), indicating the user is in the exhalation phase. To prevent excessive accumulation of the medication mist in the outflow channel 2, which could form large droplets and cause coughing, and to conserve energy, the controller 3 shuts off the nebulizer 32 during this phase. The controller 3 analyzes the exhalation airflow in real time. When the exhalation airflow velocity drops below a low threshold (e.g., 0.3 L / min) and remains below this level for more than 200 ms, it determines that exhalation has ended and predicts that the user's mouth inhalation is about to begin. Because the inhalation phase occurs through the mouth, the airflow sensor 31 cannot directly detect a strong inhalation airflow, but the controller 3 predicts based on the respiratory rhythm that the user will begin active inhalation after exhalation.

[0042] During the inhalation phase, controller 3 executes an adaptive control algorithm: it starts atomizer 32 at the target operating power and monitors its load current in real time. If the current continuously deviates from the expected range due to changes in drug viscosity with temperature or consumption, controller 3 will fine-tune the operating power to bring the load current back to normal, thereby ensuring the stability of the atomized particle size.

[0043] Controller 3 analyzes nasal exhalation airflow in real time. When a significant decrease in nasal exhalation airflow rate is detected and it remains below a preset threshold (e.g., 0.5 L / min) for a very short time (e.g., 100-200 milliseconds), nasal exhalation is considered complete. Based on human respiratory rhythm, this strongly suggests that oral inhalation is about to begin or has already begun. Controller 3 immediately activates nebulizer 32. This allows the nebulizer to produce a stable mist of medication in the early or middle stages of the user's oral inhalation, ensuring that most of the medication is effectively inhaled.

[0044] After the nebulizer 32 is activated, the controller 3 immediately reads the current drug weight data W from the pressure sensor 11. c Based on a built-in calculation formula, the maximum allowable duration of the current inspiratory phase is dynamically determined. The mapping table or formula is configured such that the lower the current remaining drug volume, the longer T... max The longer the value, the better. This embodiment provides an optional formula: T max =T base +K1×(1-W c / W1); T base The base duration is K1, the extension coefficient is W1, and the initial weight of the medicine is W. c This represents the current weight of the liquid medicine. For example, assuming the device parameters are set to T... base =2s, K1=1.5, W 1=52.5g, so at the start of treatment, T max =2+0=2s, when the medicine is consumed to W c When T = 39.4g, max =2 + 1.5 × 0.25 = 2.375s, meaning that when approximately 25% of the medicine is consumed, the controller extends the inhalation window to 2.375s. Controller 3 will start a timer and, at the dynamically set T... max The signal from airflow sensor 31 is continuously monitored over a specified period. If during this T... max If an airflow signal matching the exhalation characteristics is detected again within a certain time, it is determined that the current inhalation has ended, and the nebulizer 32 is immediately turned off, and the system waits for the next breathing cycle.

[0045] At any stage of the nebulization process (whether at the end of expiration or during the inspiratory phase), controller 3 monitors in parallel for the presence of a stress airflow signal. This signal is characterized by a violent, pulsating airflow with a peak flow rate far exceeding that of normal expiration (e.g., >20 L / min) occurring within a very short time (<0.3 seconds). Once this signal is detected (indicating that the user may be coughing suddenly), controller 3 will immediately and unconditionally shut down nebulizer 32, interrupting the generation of the nebulizer mist. Simultaneously, controller 3 initiates a 4-second safety lockout. During this lockout, the system ignores any breathing signals, nebulizer 32 remains off, allowing the user to cough smoothly and resume steady breathing. After 4 seconds, the system automatically resets, awaiting the next normal respiratory cycle.

[0046] During a single treatment, the nebulizer automatically cycles until the preset treatment time is reached or the medication is depleted. Through this method of judgment based on specific airflow signal thresholds and timing logic, the device achieves high-precision, dynamic synchronization between the nebulization process and the user's spontaneous breathing rhythm, effectively improving drug utilization and treatment comfort.

[0047] Example 3: See attached document Figure 6 As shown, this embodiment details the specific implementation of the constructed portable tuberculosis drug nebulization inhalation device. This device, through the integration of sensing, identification, and intelligent control algorithms, achieves automatic identification of the drug solution, precise temperature control, and adaptive adjustment of nebulization power, thereby ensuring optimal nebulization performance and consistent drug delivery throughout the treatment process.

[0048] Reference Figure 3 and Figure 4 As shown, this device integrates the following key subsystems on the basic structure of Embodiment 1.

[0049] The drug storage chamber 1 has a sandwich structure, and its inner wall is made of a highly thermally conductive metal material (such as medical-grade stainless steel or aluminum alloy). Inside the sandwich of the drug storage chamber, several thin-film heating pads 33 are tightly attached and evenly distributed to ensure rapid and uniform heating of the drug solution.

[0050] Pressure sensor 11 is installed at the bottom of the medicine storage chamber 1 to monitor the weight or level pressure of the medicine liquid in the chamber in real time, thereby accurately calculating the initial medicine liquid volume and real-time consumption. Temperature sensor 12 is also installed at the bottom of the medicine storage chamber 1, with its probe in direct or indirect contact with the medicine liquid to accurately measure the real-time temperature of the medicine liquid.

[0051] The outer wall of the bottle-shaped medicine container 42 is printed with a barcode 42a, which encodes electronic information about the liquid medicine, including the type of medicine, concentration, batch number, and optimal nebulization parameters. The controller 3 of the device integrates an encoding reader (such as a miniature barcode scanning module) to automatically scan and read the information of barcode 42a when the medicine container is filled.

[0052] The controller 3 is electrically connected to the thin-film heating element 33, the nebulizer 32, the pressure sensor 11, the temperature sensor 12, and the code reader. Internally, it stores a data table containing identification information for various medications, which associates the identification information of each medication with its recommended heating temperature and recommended nebulization power.

[0053] This embodiment selects a rifampicin-isoniazid compound liposome suspension, which may be used in clinical trials, as an example drug solution. This type of drug solution has high viscosity and its stability is temperature-sensitive, making it very suitable for demonstrating the intelligent control advantages of this device.

[0054] Regarding drug liquid identification and parameter initialization.

[0055] Example of a drug solution: Rifampin-Isoniazid compound liposome suspension.

[0056] Medicine container identification: The barcode 42a on the outer wall of the bottle-shaped medicine container 42 contains DRUG_CODE:RIF-INH-LIP-50ML. After the encoder of the controller 3 scans the barcode, it queries the internal pre-stored data table, automatically obtains and sets the following personalized parameters for this treatment, as shown in Table 1.

[0057] Table 1. Rifampin-Isoniazid Liposome Parameters

[0058] Baseline establishment: Pressure sensor 11 reads the initial drug liquid weight W1 in the storage chamber as 52.5g.

[0059] Control objective: To rapidly and stably heat the drug solution from room temperature (assuming 22.0°C) to 40.0°C and maintain it at that temperature.

[0060] The PID formula is output(t) n )=K p ×e(t n )+K i ∫e(t n )dt+K d de(t n ) / dt; Where the PID parameter K p =20.0% / ℃, K i =0.8% / (℃·s), K d =3.0% / (℃ / s), for the simplified setting in this example, K p The proportional gain reflects the impact of the current error on the control output; K i K represents the integral gain, reflecting the impact of the cumulative error over time on the control output. d The differential gain reflects the impact of error variation on the control output; e n Let be the error at the nth sampling time.

[0061] At the initial time t0, the temperature T(t0) = 22℃, and the error e(t0) = T t -T(t0)=40-22=18℃, integral term ∫e(t0)dt=0, differential term de(t0) / dt=0, PWM modulation output power output(t0)=20.0×18.0+0+0=360%. The maximum power is 100%, so the controller starts the thin film heating element 33 at 100% full power, and the temperature rises rapidly.

[0062] After a period of time t1, T(t1) = 39.5℃, the error e(t1) = 40.0 - 39.5 = 0.5℃, the cumulative integral term ∫e(t1)dt = 15.2, and the error change rate de(t1) / dt = (0.5 - 0.8) / 1 = -0.3℃ / s (assuming the error at the previous moment was 0.8℃). The output power of the PWM modulation output(t1) = 20.0 × 0.5 + 0.8 × 15.2 + 3.0 × (-0.3) = 10.0 + 12.16 - 0.9 = 21.26%. The controller reduces the heating power to a duty cycle of 21.26% for precise heat preservation, preventing temperature overshoot and perfectly stabilizing the temperature within the range of 40.0 ± 1.5℃.

[0063] Implementation of the adaptive power control algorithm.

[0064] During the nebulization process of rifampicin-isoniazid liposome suspension, water evaporation and increased liposome and drug concentrations lead to a significant increase in the viscosity of the drug solution. Without increasing energy, the atomized particles will coarsen, and the output rate will decrease. To counteract the nebulization efficiency degradation caused by drug concentration, controller 3 executes the following algorithm to dynamically adjust the power of nebulizer 32 during each inhalation phase, with the core formula as follows: K w =1.0+α(△W / W1); Where K w α is the power adjustment coefficient; α is the compensation intensity coefficient, a programmable personalized parameter that determines the device's "sensitivity" or "response intensity" to the consumption of the drug solution; △W is the weight of the drug solution that has been consumed (in grams); and W1 is the initial total weight of the drug solution.

[0065] Get K w Then calculate the real-time atomization power P c , P c =P i ×K w ; Among them, P i K is the initial atomization power. w This is the power adjustment coefficient.

[0066] Table 2 illustrates the power adjustment process based on this formula: Table 2. Power Adjustment Mapping Table for Rifampin-Isoniazid Liposome Suspension

[0067] When the pressure sensor detects the weight W of the medicine liquid in the storage chamber c When the amount of medicine consumed is 39.4g, the amount consumed is ΔW = 13.1g, and α is set to 0.5 here.

[0068] K w= 1.0+α(△W / W1)=1+0.5(13.1 / 52.5)=1.125; P c =10×1.125=11.25W.

[0069] The controller immediately increases the power of nebulizer 32 from 10.0W to 11.25W. This additional 1.25W of energy is specifically designed to overcome the increased viscosity due to drug concentration, ensuring that the aerosol particle size (MMAD) and output rate generated by nebulizer 32 remain consistent with those at the start of treatment.

[0070] This embodiment, through the aforementioned integrated system and intelligent algorithm, achieves dual protection of efficacy and comfort, consistent dosage throughout the treatment cycle, and complete personalization and automation. Precise temperature control (40.0±1.5℃) protects the activity of the liposomal drug while providing a warm inhalation sensation and reducing cold stimulation. The adaptive power algorithm, through dynamic compensation, effectively combats the decline in nebulization efficiency, ensuring uniform dosage from the start to the end of treatment, significantly improving drug utilization and therapeutic effect. The system automatically retrieves all key parameters through identity recognition; users only need to "insert, press, and inhale," greatly reducing the operational threshold and improving medication adherence.

[0071] This embodiment uses rifampin-isoniazid compound liposome suspension as an example to fully and clearly demonstrate how the present invention solves the core problem of high viscosity and temperature-sensitive tuberculosis drugs in nebulization therapy through specific formulas and algorithms, providing sufficient feasibility support for the scope of protection claimed by the patent.

[0072] The embodiments and / or implementation methods described above are merely preferred embodiments and / or implementation methods for implementing the technology of the present invention, and are not intended to limit the implementation methods of the technology of the present invention in any way. Any person skilled in the art may make some modifications to other equivalent embodiments without departing from the scope of the technical means disclosed in the content of the present invention, but these should still be regarded as the technology or embodiments that are substantially the same as the present invention. This document uses specific examples to illustrate the principles and implementation methods of this application. The descriptions of the above embodiments are only for the purpose of helping to understand the methods and core ideas of this application. The above descriptions are only preferred embodiments of this application. It should be noted that due to the limitations of written expression, while there are objectively infinite specific structures, those skilled in the art can make several improvements, modifications, or changes without departing from the principles of this application, and can also combine the above technical features in an appropriate manner. These improvements, modifications, changes, or combinations, or the direct application of the inventive concept and technical solution to other situations without modification, should all be considered within the scope of protection of this application.

Claims

1. A portable tuberculosis drug nebulization inhalation device, comprising a drug storage chamber (1) and an outflow channel (2), wherein the inlet end of the outflow channel (2) is connected to the drug storage chamber (1), and an atomizer (32) is provided between the drug storage chamber (1) and the outflow channel (2), the atomizer (32) being provided between the drug storage chamber (1) and the outflow channel (2) for atomizing the flowing drug liquid; the outlet end of the outflow channel (2) is provided with a mouthpiece contact sensing unit (21), and an external mouthpiece (22) is provided thereon, the mouthpiece contact sensing unit (21) being used to detect the contact state between the user's lips and the mouthpiece (22), characterized in that, It also includes a controller (3), which is electrically connected to the atomizer (32) and is used to control the start and stop and power of the atomizer (32); the top of the medicine storage chamber (1) is provided with a medicine tank (4), which is constructed to accommodate bottle-shaped medicine tanks (42); the bottom of the medicine tank (4) is provided with a conical piercing tube (41). When the bottle-shaped medicine tank (42) is put into the medicine tank (4) and is pressed downward, its flexible bottle mouth is pierced by the conical piercing tube (41), so that the inside of the medicine tank (42) is connected to the medicine storage chamber (1), and the medicine flows into the medicine storage chamber (1) under the action of gravity.

2. The portable tuberculosis drug nebulizer inhalation device according to claim 1, characterized in that, The controller (3) is located on the top surface of the outflow channel (2). An airflow sensor (31) is provided on the side of the controller (3). When the user's lips come into contact with the outlet end of the outflow channel (2), the airflow sensor (31) detects the user's nostrils and is used to detect the user's breathing airflow.

3. The portable tuberculosis drug nebulizer inhalation device according to claim 2, characterized in that, The controller (3) is configured to: identify the user's expiratory phase based on the contact signal of the mouthpiece contact sensing unit (21) and the respiratory airflow signal of the airflow sensor (31), and predict the start of the inspiratory phase based on the end of the expiratory phase; Specifically, when the airflow sensor (31) detects the end of exhalation signal, the controller (3) starts the nebulizer (32) so that the nebulizer enters the working state before the user starts to inhale actively; and keeps the nebulizer (32) open until the airflow sensor (31) detects an airflow signal that matches the exhalation characteristics, then closes the nebulizer (32).

4. The portable tuberculosis drug nebulizer inhalation device according to claim 1, characterized in that, The medicine storage chamber (1) is a sandwich structure, and its inner wall is made of heat-conducting material; a number of thin film heating pads (33) are provided in the sandwich, and the thin film heating pads (33) are attached to the outer side of the inner wall to heat the medicine liquid in the medicine storage chamber (1) through the heat-conducting inner wall; The controller (3) is electrically connected to the thin film heating element (33) and is configured to adjust and control the heating temperature of the thin film heating element (33).

5. The portable tuberculosis drug nebulizer inhalation device according to claim 4, characterized in that, The outer wall of the bottle-shaped medicine container (42) is provided with a barcode (42a), which stores the electronic information of the medicine liquid inside the medicine container (42); the controller (3) has a built-in code reader for recognizing the barcode (42a); the bottom of the medicine storage chamber (1) is provided with a pressure sensor (11) and a temperature sensor (12) for recognizing the amount and temperature of the medicine liquid in the medicine storage chamber (1).

6. The portable tuberculosis drug nebulizer inhalation device according to claim 5, characterized in that, The controller (3) has a data table containing various drug liquid identity information stored in it. The identity information is associated with at least the recommended heating temperature and the recommended atomization power. The controller (3) is configured to query the data table based on the received encoded information and set the target temperature of the thin film heating element (33) and the target operating power of the atomizer (32) accordingly.

7. The portable tuberculosis drug nebulizer inhalation device according to claim 5, characterized in that, The controller (3) is further configured to execute a power control algorithm based on drug level adaptation for dynamically adjusting the operating power of the nebulizer (32) during a single treatment session. The algorithm includes the following steps: S1: After the medicine container (42) is filled, the initial weight of the medicine liquid or the liquid level pressure value in the medicine storage chamber (1) is obtained through the pressure sensor (11), and this is used as a reference; S2: During the user's inhalation phase, the atomizer (32) is activated and operates at initial power; S3: Read the current value of the pressure sensor (11) in real time and calculate the amount of medicine consumed or the amount of medicine remaining. S4: Based on the amount of consumed liquid or the current remaining liquid, query the pre-stored power adjustment mapping table and dynamically set the real-time operating power of the atomizer (32); wherein, the power adjustment mapping table is configured to gradually increase the operating power of the atomizer (32) as the liquid is consumed, in order to compensate for the atomization efficiency reduction caused by the concentration and viscosity increase of the liquid.

8. The portable tuberculosis drug nebulizer inhalation device according to claim 6, characterized in that, The controller (3) is also configured to execute a liquid temperature control algorithm for controlling the thin-film heating element (33), the algorithm including: Preheating stage: After the bottle-shaped medicine container (42) is detected to be filled, the thin film heating element (33) is controlled to heat the medicine liquid to the target temperature and maintain it before the first use; Maintenance phase: During the nebulization inhalation process, the temperature of the drug solution in the drug storage chamber (1) is monitored in real time, and the on / off state of the thin film heating plate (33) is controlled by pulse width modulation to stabilize the drug solution temperature within the range of ±1.5℃ of the target temperature.

9. The portable tuberculosis drug nebulizer inhalation device according to claim 1, characterized in that, The outer wall of the medicine storage chamber (1) is provided with an openable cover (6).

10. The portable tuberculosis drug nebulizer inhalation device according to claim 1, characterized in that, The atomizing inhalation device also includes a handle (5) with anti-slip texture on the surface.

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