Precision delivery device for delivery of drug aerosols

Abstract

The utility model provides a precise delivery device for delivering drug aerosol. Wherein the precise delivery device for delivering a drug aerosol comprises: a housing sized and shaped to be graspable in a hand of a user; the medicine bomb assembly can atomize a set dose of medicine into aerosol, and an aerosol channel used for conveying the aerosol is formed in the medicine bomb assembly; a flow generator for generating a positive pressure gas flow that delivers the aerosol to the respiratory tract; the control unit is used for receiving an operation instruction and driving the medicine bomb assembly to output aerosol of medicine and the flow generator to generate positive pressure airflow; wherein the cartridge assembly, the flow generator and the control unit are all received in the shell. The utility model has the beneficial effects of small and exquisite structure, easiness in carrying, convenience in use and capability of accurately dosing.

Description

Technical Field

[0001] This invention relates to the field of atomized drug delivery technology, and in particular to a precision delivery device for delivering drug aerosols. Background Technology

[0002] Nasal / oral inhalation is a very special route of administration that can be used to prevent and treat diseases of the central nervous system, respiratory system and other aspects. (1) Studies have confirmed that there is a direct anatomical channel between brain tissue and nasal cavity. Nasal administration bypasses the blood-brain barrier and delivers drugs directly to the brain non-invasively. That is, drugs can reach the central nervous system through the olfactory epithelium or respiratory epithelium of the nasal mucosa, quickly enter the brain tissue and act on the relevant receptors to produce therapeutic effects. The nasobrain connection can also activate peripheral nasal chemoreceptor neurons to trigger and regulate the olfactory-amygdala neural circuit without the need for the drug to directly bind to the neuronal receptors in the central nervous system of the brain, thereby limiting the transport of molecules into the blood circulation system and minimizing the potential systemic exposure of drugs. Regardless of the mechanism, its characteristics are that it avoids the blood-brain barrier, alveolar blood-gas barrier, liver first-pass effect and gastrointestinal metabolism. Therefore, the required dose is the lowest (10-6-10-12g), the onset of action is the fastest (a few seconds), the systemic toxicity is the least, and the compliance is the best. (2) Studies have confirmed that pulmonary absorption is also a good route of administration. The characteristics of lung-targeted drugs are: large absorption surface area, rich capillary network, and thin alveolar air-blood barrier, which can avoid gastrointestinal metabolism and liver first-pass effect; the required dose is lower than that of oral and injection administration, the onset of action is faster, the side effects are fewer, and the compliance is better. (3) Studies have confirmed that other drugs that do not belong to the central nervous system or respiratory system can also achieve better prevention and treatment effects through nasal / oral nebulization inhalation. For example, peptide diabetes drugs that require frequent injection, osteoporosis drugs, hormone drugs, and other oral and injection drugs that require rapid onset of action can be improved into inhaled dosage forms to meet the needs of users, which is of great practical significance.

[0003] Nebulized inhalation formulations refer to preparations in which drugs are delivered through a special device and inhaled through the deep respiratory tract, cavities, mucous membranes, etc., to exert local or systemic therapeutic effects, thereby achieving the purpose of painless, rapid and effective treatment.

[0004] Respiratory inhalation formulations can be further categorized into liquid nebulized inhalers, metered-dose inhalers (TMDs), dry powder inhalers, and soft inhalers. Liquid nebulized inhalers, as a specific dosage form for respiratory drug delivery, are typically aqueous solutions. A specific device converts the nebulized drug into an aerosol for the user to inhale. The inhaled dose is deposited at a certain rate and with appropriate particle size at different lesion sites in the respiratory tract. Aerosol particle size, as a major factor influencing the deposition site of respiratory drug delivery, has been extensively studied. Another factor is the user's inspiratory force and breathing habits. The same nebulizer and device can result in different inhaled doses and drug deposition sites for different users, thus producing different therapeutic effects. Aerosols, dry powder inhalers, and soft inhalers suffer from inaccuracies in nebulized dose, inhaled dose, and deposition site.

[0005] Existing nebulized inhalation therapy devices typically include a nebulizer, a drug storage device, and a nebulizer output tube. Some even require an oxygen storage device. These devices are complex and bulky, expensive, inconvenient to use and maintain, and generally only suitable for use in hospitals or other fixed locations. They are not easy to transport and carry, and cannot achieve precise nebulization, precise drug inhalation, or precise deposition. Utility Model Content

[0006] To overcome the shortcomings of the prior art, this utility model provides a precision delivery device for delivering drug aerosols, which has the advantages of being compact, easy to carry, convenient to use, and capable of precise drug delivery.

[0007] To achieve the above objectives, the technical solution adopted by this utility model is as follows:

[0008] A precision delivery device for delivering drug aerosols includes: a housing whose size and shape are configured to be held in the user's hand;

[0009] A drug delivery assembly capable of atomizing a predetermined dose of drug into an aerosol, the drug delivery assembly having an aerosol channel for delivering the aerosol;

[0010] A flow generator for generating a positive pressure airflow to deliver the aerosol to the respiratory tract; and

[0011] The control unit drives the drug delivery assembly to output drug aerosol according to the user's operation instructions, and drives the flow generator to generate a set amount of positive pressure airflow.

[0012] The propellant assembly, flow generator, and control unit are all housed within the casing. The above technical solution can be further improved through the following measures.

[0013] In a preferred embodiment, the propellant assembly includes:

[0014] The cartridge case, which internally defines the propellant storage compartment; and

[0015] A nebulizer is positioned within the cartridge case to atomize the drug.

[0016] Specifically, a base is attached to the bottom of the cartridge case, and the base and the cartridge case together define the cartridge compartment.

[0017] Specifically, the base is detachably attached to the cartridge case.

[0018] Specifically, the base is embedded with an electrode portion for transmitting electrical energy to the atomizer.

[0019] In a preferred embodiment, the top of the cartridge case has an upwardly extending mist nozzle, and there is at least one mist nozzle.

[0020] Specifically, the inner surface of the mist nozzle is configured in a cone shape to gather the aerosol.

[0021] Specifically, the nozzle and the atomizer are connected via a mist outlet pipe.

[0022] In one embodiment, the housing includes a cartridge sleeve for receiving the cartridge assembly, the cartridge assembly being detachably assembled in the cartridge sleeve.

[0023] Specifically, the bottom of the ammunition sleeve is provided with an upper air inlet, and the flow generator is connected to the upper air inlet.

[0024] Specifically, a converging shroud is provided between the flow generator and the projectile sleeve to gather and guide the airflow into the projectile assembly.

[0025] Specifically, the air-concentrating shroud has an air outlet pipe extending into the ammunition sleeve, and the air outlet pipe is connected to the upper air inlet of the ammunition assembly.

[0026] Specifically, the wind-gathering shroud has a conical inner cavity for concentrating airflow.

[0027] Preferably, the atomizer is a heating atomizing device or an ultrasonic atomizing device. The heating atomizer is a ceramic core heating atomizer or a cotton core heating atomizer, and the ultrasonic atomizer is a piezoelectric ceramic atomizer or a mesh screen vibration atomizer.

[0028] Preferably, the flow generator is a fan or an air pump.

[0029] Preferably, the control unit includes a circuit board vertically arranged in the gap between the propellant casing and the propellant assembly. The casing has an operating part, and the flow generator presses against the back of the circuit board to support the operating part. The propellant assembly is configured such that the aerosol output flow rate is 1.0–50 ml / s. The propellant assembly is configured such that the aerosol output duration is 0.2–5.0 s / cycle.

[0030] Preferably, an air inlet cavity is formed between the flow generator and the housing, and a battery is installed inside the air inlet cavity. The battery is placed horizontally inside the air inlet cavity.

[0031] By adopting the above technical solution, this utility model has the following beneficial effects:

[0032] This invention relates to a precise drug delivery device that actively delivers drug aerosols to the user's respiratory system, revolutionarily solving a long-standing problem with nebulized inhalation drug delivery: the inhaled drug dose and deposition location depend on the user's lung capacity, breathing force, inhalation technique, and aerosol particle size. Active nebulized delivery addresses the issue of some users, especially those with chronic lung disease, the elderly, and children, whose breathing force is weak and unable to generate sufficient inhalation power. It also solves the problem of self-administered medication for emergency situations such as type I allergic reactions that cause breathing difficulties. Furthermore, the delivery device is compact and can be held in the user's hand. Therefore, this aerosol delivery device is portable and easy to use. Through active nebulized delivery, this invention enables targeted drug deposition in part or all of the respiratory tract, significantly improving drug efficacy and reducing side effects such as liver damage.

[0033] This invention can also realize intelligent and personalized nebulized drug delivery. On-duty doctors or electronic doctors can formulate personalized drug delivery methods, i.e., electronic prescriptions, according to the user's individual situation. The electronic prescriptions are then transmitted to the precision delivery device and stored. The control unit executes the drug delivery program according to the electronic prescriptions, realizing personalized treatment for the user and significantly improving the best treatment effect for each user.

[0034] This invention enables precise delivery of a precise dose of medication to the user's treatment site, thereby achieving precision treatment, improving the therapeutic effect of the medication, and reducing its side effects. Attached Figure Description

[0035] To more clearly illustrate the technical solutions of the embodiments of this utility model, the accompanying drawings of the embodiments will be briefly introduced below. Obviously, the drawings described below only relate to some embodiments of this utility model, and are not intended to limit this utility model.

[0036] Figure 1 This is a schematic diagram of the closed-lid structure in Embodiment 1.

[0037] Figure 2 This is a schematic diagram of the open-lid state structure in Embodiment 1.

[0038] Figure 3 yes Figure 1 Exploded view.

[0039] Figure 4 This is a cross-sectional view of Embodiment 1.

[0040] Figure 5 This is an internal structural view of Embodiment 1.

[0041] Figure 6 This is a schematic diagram of the structure of the explosive assembly in Example 1.

[0042] Figure 7 yes Figure 6 A cross-sectional view.

[0043] Figure 8 yes Figure 6 Exploded view.

[0044] Figure 9 This is a distribution diagram of aerosol particles output by the propellant assembly.

[0045] Reference numerals: 1. Lid; 2. Shell; 2a. Left shell; 2b. Right shell; 2c. Air inlet; 3. Indicator light; 4. Button; 5. Medication cartridge assembly; 5a. Medication cartridge case; 5a1. Atomizer nozzle; 5b. Liquid holding part; 5c. Aerosol channel; 5d. Atomizer; 5e. Base; 6. Medication cartridge sleeve; 7. Condenser; 8. Flow generator; 9. Circuit board; 10. Battery. Detailed Implementation

[0046] To make the objectives, technical solutions, and advantages of the embodiments of this utility model clearer, the utility model will be further described in detail below with reference to the accompanying drawings. The components of the embodiments of this utility model described and shown in the accompanying drawings can be arranged and designed in various different configurations. All other embodiments obtained by those skilled in the art based on the embodiments of this utility model without inventive effort are within the scope of protection of this utility model.

[0047] It should be noted that similar labels and letters in the following figures indicate similar items. Therefore, once an item is defined in one figure, it does not need to be further defined and explained in subsequent figures.

[0048] Unless otherwise defined, the technical or scientific terms used in this patent document shall have the ordinary meaning understood by one of ordinary skill in the art to which this utility model pertains. The terms "first," "second," and similar terms used in this utility model patent specification and claims do not indicate any order, quantity, or importance, but are merely used to distinguish different components. Similarly, the terms "a," "one," or "the," etc., do not indicate a quantity limitation, while "a," "a," etc., indicate the presence of at least one. The terms "comprising," "including," etc., mean that the elements or objects preceding "comprising" or "including" encompass the elements or objects listed following "comprising" or "including" and their equivalents, and do not exclude other elements or objects. The terms "center," "upper," "lower," "left," "right," "vertical," "horizontal," "inner," and "outer" are used only to indicate relative positional relationships. When the absolute position of the object being described changes, the relative positional relationship may also change accordingly. They are only used to facilitate the description of this utility model and to simplify the description, and are not intended to indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this utility model.

[0049] In the description of this utility model, it should be noted that, unless otherwise explicitly specified and limited, the terms "installation," "connection," and "joining" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; they can refer to a mechanical connection, an electrical connection, or a magnetic connection; they can refer to a direct connection or an indirect connection through an intermediate medium; and they can refer to the internal connection of two components. Those skilled in the art can understand the specific meaning of the above terms in this utility model based on the specific circumstances.

[0050] The following detailed description of some embodiments of the present invention is provided in conjunction with the accompanying drawings. Unless otherwise specified, the features in the following embodiments can be combined with each other.

[0051] Example 1:

[0052] Please see Figures 1-9This invention provides a precision delivery device for delivering drug aerosols, comprising a housing 2, a drug delivery assembly 5, a flow generator 8, and a control unit. The housing 2 is sized and shaped to fit comfortably in the user's hand. The drug delivery assembly 5 atomizes a predetermined dose of drug into an aerosol, and has an aerosol channel 5c for delivering the aerosol. The flow generator 8 generates a positive pressure airflow to deliver the aerosol to the respiratory tract, which includes the mouth, nose, trachea, and lungs, through which the aerosol enters the trachea and lungs. The flow rate and velocity of this positive pressure airflow can be set and adjusted to precisely deliver the drug to the user, achieving targeted drug delivery and significantly improving drug utilization and therapeutic efficacy. The control unit receives user commands and drives the drug delivery assembly 5 to output the drug aerosol, while simultaneously driving the flow generator 8 to generate a predetermined amount of positive pressure airflow to drive the aerosol into the respiratory system. The drug delivery assembly 5, the flow generator 8, and the control unit are all housed within the housing 2.

[0053] The aforementioned precision delivery device actively delivers drug aerosols to the user's respiratory system, revolutionarily solving a long-standing problem with nebulized inhalation drug delivery: the inhaled drug dose and deposition location depend on the user's lung capacity, breathing force, inhalation technique, and aerosol particle size. Active nebulized delivery addresses the issue for some users, especially those with chronic lung disease, the elderly, and children, whose breathing force is weak and unable to generate sufficient inhalation power. It also solves the problem of self-administering medication for emergency situations such as type I allergic reactions that cause breathing difficulties. Furthermore, the delivery device is compact and can be held in the user's hand. Therefore, this aerosol delivery device is portable, easy to use, and eliminates the need for hospitalization, saving medical resources and significantly improving user compliance. Through active precision nebulization and precise delivery, this invention achieves partial or complete targeted deposition of drugs in the respiratory tract, reducing damage to non-lesion sites.

[0054] like Figures 6-8 As shown, the drug delivery assembly 5 includes a drug cartridge case 5a and an atomizer 5d. The inside of the drug cartridge case 5a defines a drug storage chamber, and the atomizer 5d is positioned within the drug cartridge case 5a to atomize the drug. In this embodiment, the drug is loaded into the drug storage chamber in solid or liquid form. Specifically, the drug can be mixed with solid excipients to form a solid formulation (suitable only for heated atomization) or dissolved in a solvent to form an atomizable liquid, which is then filled into the drug storage chamber. Alternatively, a liquid retention part 5b can be installed inside the drug storage chamber, such as a cotton wick, porous ceramic, or an absorbent porous material. To prevent the liquid from becoming ineffective over time, the drug and the atomizing solvent can be packaged separately. When in use, the separating membrane is removed, and the drug is dissolved in the atomizing solvent, thereby extending the shelf life of the drug.

[0055] like Figure 7 As shown, to facilitate the addition of medication or the dissolution of drugs in a solution, a base 5e is attached to the bottom of the cartridge case 5a in this embodiment. The base 5e and the cartridge case 5a together define the drug storage compartment. Specifically, the base 5e is a rubber or silicone component. The base 5e is detachably attached to the cartridge case 5a and can be inserted into the opening at the bottom of the cartridge case 5a to seal the opening and prevent medication leakage. In another embodiment, the base 5e and the cartridge case 5a can be integrated, or welded or fixed together in a subsequent process. This structure has better sealing performance than a separate structure, but it does not allow users to replace the medication; it can only be discarded after use, resulting in relatively higher usage costs, but it does not cause cross-contamination.

[0056] Since an atomizer 5d is installed inside the cartridge case 5a, an electrode portion for transmitting electrical energy to the atomizer 5d is embedded in the base 5e in order to supply electrical energy to the atomizer 5d. Specifically, there are two electrodes, which are metal parts or other conductive objects embedded in the base 5e.

[0057] like Figure 6-8As shown, the top of the drug cartridge 5a has an upwardly extending mist outlet 5a1, and there is at least one mist outlet 5a1. Specifically, in this embodiment, there are two mist outlets 5a1, one on each side, which are respectively matched with the nostrils. Therefore, the aerosol precision delivery device in this embodiment mainly delivers drugs through the nose, inducing the central nervous system through the nasal mucosa and olfactory bulb to treat diseases related to emotions and mental health. The delivery device of this utility model can actively deliver drugs according to the user's needs, solving the problem that some users have insufficient breathing strength and cannot actively inhale the appropriate dose of drugs and control the drug deposition site. The aerosol precision delivery device in this embodiment achieves precise and timely treatment or self-rescue for users through active targeted drug delivery (active drug delivery through the nasal cavity and respiratory tract). The awakening of anesthetized patients after surgery can usually only be achieved by injecting drugs; or when a type I allergic reaction occurs and causes breathing difficulties, the patient usually performs self-rescue by injecting backup drugs. The aerosol precision delivery device in this embodiment can completely replace injection drug delivery by actively delivering drugs through the nasal cavity and respiratory tract. The outlet diameter D of the mist outlet 5a1 is within the range of 1.0mm ≤ D ≤ 3.5mm. Within this diameter range, the mist outlet 5a1 achieves a balance between mist output and mist output speed, avoiding the problem of trapped air caused by an excessively small mist outlet 5a1, while a larger mist outlet 5a1 results in insufficient mist output force, failing to effectively deliver medication to the user. Simultaneously, the aforementioned diameter setting ensures a proper fit between the mist outlet 5a1 and the nasal cavity, improving user comfort. Specifically, the diameter D of the mist outlet 5a1 is 2.5mm, but can also be any value within the range of 1.0mm ≤ D ≤ 3.5mm. The inner surface of the mist outlet 5a1 is configured in a cone shape to gather the aerosol, facilitating a proper fit with the nostrils, preventing leakage, and improving the accuracy of aerosol delivery.

[0058] like Figure 6 and Figure 7 As shown, the atomizer 5d and the nozzle 5a1 are connected via an atomizing pipe. The function of the atomizing pipe is to guide the generated aerosol upwards to the nozzle 5a1 to prevent air entrapment. Specifically, a pipe can be connected to the atomizer 5d, through which the generated aerosol can flow into the nozzle 5a1. Specifically, the atomizing pipe is a metal tube extending from the top of the atomizer 5d to the bottom of the nozzle 5a1. In this invention, the aforementioned air entrapment refers to the situation where the outlet flow rate is less than the aerosol production flow rate, causing the aerosol to be unable to flow out effectively, seemingly trapped within the aerosol channel 5c, thus reducing delivery accuracy.

[0059] In this embodiment, the housing 2 includes a cartridge sleeve 6 for receiving the cartridge assembly 5. The cartridge assembly 5 is detachably assembled in the cartridge sleeve 6 to facilitate user replacement of the cartridge assembly 5. For users, the ability to easily replace the cartridge assembly 5 is essential, allowing them to use the same housing to replace cartridges of different medications for nebulized drug delivery, thus reducing usage costs.

[0060] It should be noted that the atomizer 5d in this utility model is a heating atomization device or an ultrasonic atomization device. For drugs with excellent thermal stability, the solid drug preparation or the liquid atomizing agent can be directly heated to evaporate and atomize it into an aerosol. Since some drugs are unstable at high temperatures and easily decompose and become ineffective, ultrasonic atomization devices are more advantageous than heating atomization devices for heat-labile drugs. Heating atomization devices are heating elements (solid atomizing agents), ceramic cores or cotton wicks for heating atomizers (liquid atomizing agents), and similar heating atomization methods are widely used in the electronic cigarette industry; ultrasonic atomization devices are piezoelectric ceramic atomizers or mesh atomizers. Ultrasonic atomization is also a conventional atomization method, widely used in the medical and beauty industries, and its specific structure will not be described in detail. Furthermore, the flow generator 8 in the application is a fan or an air pump. The fan is preferably a fan with adjustable airflow and speed, and the air pump can be a miniature air pump manufactured by Murata Manufacturing Co., Ltd. of Japan, whose flow rate can be adjusted by changing the current value. Specifically, in this embodiment, the flow generator 8 is a fan. It should be further explained that, in order to introduce the liquid medicine into the atomizer 5d for atomization, for heated atomizers 5d, a liquid guiding component is usually installed around the atomizer 5d to guide the liquid medicine to the periphery of the atomizer 5d. During heating, the liquid medicine in the liquid guiding component is directly atomized into an aerosol. The liquid guiding component is usually made of a porous, heat-resistant material, such as ceramics or cotton fibers.

[0061] To enable the aerosol to be rapidly ejected from the nozzle 5a1, in this embodiment, the bottom of the cartridge case 6 is provided with an upper air inlet, which is connected to the fan outlet. The airflow generated by the fan enters the cartridge case assembly 5 through the upper air inlet. A converging shroud 7 is disposed between the flow generator 8 and the cartridge case 6 to gather and guide the airflow into the cartridge case assembly 5. The converging shroud 7 has an air outlet pipe extending into the cartridge case 6, which is connected to the upper air inlet of the cartridge case assembly 5. In another embodiment, to guide the airflow generated by the fan into the cartridge case assembly 5 more efficiently, the converging shroud 7 has a conical inner cavity for gathering the airflow. That is, the inner cavity of the converging shroud 7 is designed as a conical cavity, so that the airflow can be gathered and enter the cartridge case assembly 5 from the top of the conical inner cavity.

[0062] like Figure 3 and Figure 5As shown, the control unit includes a circuit board 9, on which an indicator light 3 and a button 4 are provided. To save space, the circuit board 9 is arranged vertically in the gap between the cartridge case 5a and the housing 2. This configuration can significantly reduce the size of the entire device, making the product easy to hold in the user's palm and convenient for user operation. The housing 2 is combined with an operating part for the user to press. The fan and the cartridge case 5a press against the back of the circuit board 9 to support the operating part, thereby reducing the installation difficulty and saving internal space. To prevent accidental activation and waste, such as when the user places the product in a pocket, handbag, or backpack, the items are squeezed together, which can easily cause accidental activation of the atomization and waste, and may also contaminate other items of the user, in this embodiment, the surface of the button 4 is flush with or slightly lower than the outer surface of the housing 2.

[0063] To further reduce the overall size of the product, the present invention places the battery 10 horizontally in the air inlet cavity. Specifically, an air inlet cavity is formed between the fan and the housing 2, and the battery 10 is installed in the air inlet cavity. To facilitate the installation of the internal structure, the housing 2 is divided into a left housing 2a and a right housing 2b, and the top of the housing 2 has an opening. The ammunition sleeve 6 is clamped between the left housing 2a and the right housing 2b, and the ammunition assembly 5 is slidably installed in the ammunition sleeve 6. Figure 5 The diagram shows the internal structure after removing the left shell 2a. The left shell 2a and right shell 2b can be fixed together using fasteners such as screws or clips. An air inlet 2c is provided on the right shell 2b. Additionally, a cover 1 is connected to the top of the shell 2, pivotally attached to it. Flipping the cover 1 allows for opening and closing, providing convenience and hygiene. (Refer to above) Figures 1-8 As shown, a precise drug delivery control method for aerosol delivery via positive pressure airflow is also provided, applicable to the aforementioned precise delivery device. The precise drug delivery control method includes:

[0064] The drug delivery assembly 5 is controlled to operate for a set time to generate drug aerosols; the fan is controlled to operate to generate a positive pressure airflow to expel the aerosols from the atomization chamber.

[0065] Preferably, the drug delivery assembly 5 can be controlled to operate for a set time to generate drug aerosols. Then, the fan is further controlled to generate positive pressure airflow to expel the aerosols from the nebulization chamber and into the respiratory tract. Specifically, in this embodiment, the set time is 2.5 seconds, but other time values ​​between 0.2 and 5 seconds, such as 1 second, 2 seconds, or 3.5 seconds, can also be used. Those skilled in the art can select an appropriate set time after thorough laboratory verification. The nebulizer 5d is a heated nebulizer 5d, meaning that aerosols are generated first, and then airflow is generated to expel the aerosols, thereby preventing the airflow from lowering the temperature of the nebulizer 5d and affecting the nebulization effect. In another embodiment, the drug delivery assembly 5 and the fan can also be controlled to operate simultaneously, meaning that airflow and aerosols are generated simultaneously. In this embodiment, to achieve precise drug delivery, the dosage of the aerosol can be controlled by the operating time and power of the nebulizer 5d, while the airflow and air speed can be controlled to precisely deliver the drug to the desired deposition site in the respiratory tract, achieving targeted drug delivery.

[0066] Furthermore, the precise drug delivery control method also includes: obtaining an electronic prescription set by a doctor based on user information, the electronic prescription including nebulization timing, frequency, interval, intensity, and dosage; and controlling the operation of the drug delivery assembly 5 and the flow generator 8 based on the electronic prescription. Specifically, the electronic prescription is formulated based on drug concentration, number of nebulizations, nebulization interval, nebulization duration, nebulization power, and individual user information, thereby enabling intelligent, precise, and personalized targeted drug delivery. The aforementioned user information may include the user's disease treatment history, drug allergy history, health status information, and genetic information. Precise drug delivery based on user information can better diagnose and treat symptoms, achieving optimal therapeutic effects.

[0067] The precision nebulization device involved in this invention delivers and nebulizes drugs in a manner equivalent to pulse theory in electromagnetism, and the terminology used in this invention is adopted here. Precision pulse nebulization drug delivery parameters include pulse length (pulse peak width), number of pulses (pulse frequency), interval (pulse period), amplitude (pulse peak height), and energy (pulse peak area), which are set as corresponding nebulization parameters in the precision drug delivery "electronic prescription": nebulization duration, drug delivery frequency, drug delivery interval, drug delivery intensity, and drug delivery dosage.

[0068] The pulse start time, pulse duration (width), pulse frequency (number of times), pulse interval (cycle), pulse amplitude (peak height), and pulse energy (peak area) can be synchronized with the user's inhalation start time, inhalation duration, number of inhalations, interval between inhalations, inhalation force, and inhaled dose. Alternatively, the time, duration, number of inhalations, interval, force, and dose of drug administration can be preset by manual buttons or programs to implement precise timed and quantitative drug administration.

[0069] (a) The pulse cycle can be divided into long cycle and short cycle. For example, if the medication is taken 3 times a day on average, each medication needs to be delivered 5 times or inhaled 5 times (5 pulse doses), and each time takes 2.5 minutes. That is, the long cycle is about 24 / 3=8 hours, and the short cycle is about 2.5 / 5=0.5 minutes (i.e. 30s).

[0070] (b) Drug dosage includes: (1) the dose of each pulse nebulizer and the dose of the active drug contained therein (pulse dose); (2) the total dose of nebulizer and the total dose of active drug for each administration (cumulative total for multiple pulse administrations); (3) the total dose of nebulizer and the total dose of active drug for each day (cumulative total for multiple administrations per day).

[0071] (c) These parameters can be compiled by an intelligent "electronic doctor" based on drug concentration, number of nebulizations, nebulization duration, nebulization time, output power and user individuality into a "tailor-made" electronic prescription program for drug administration, which is then implanted into the user's nebulization device to determine the time point for each medication administration, the number of deliveries, the dose per pulse, the total number of pulses and the total dose per administration, and the total number of inhalations and the total dose per day;

[0072] (d) When users strictly follow the medication procedure set by the “electronic prescription”, the chip program records the medication and treatment effect in real time, and the data is immediately fed back to the “electronic doctor” and “electronic medical record” archives. The “electronic doctor” remotely monitors the user’s medication and treatment effect, and can modify the medication parameters and adjust the “electronic prescription” at any time. The nebulizer controls the medication according to the latest instructions. At the same time, the nebulizer or cloud establishes the user’s “electronic medical record” archive, receives and stores the user’s real-time medication, treatment effect and various adverse reactions, and feeds them back to the “electronic doctor” in a timely manner.

[0073] (e) Unlike fixed-specification (dosage) dosage forms such as tablets, capsules, patches and injections, intelligent nebulized drug delivery can theoretically adjust the nebulization nodes, nebulization duration, nebulization times, nebulization duration and nebulization dose at any time by modifying the program, dynamically changing the drug dosage "specification" and the number of times of administration, so that the dosage can be precisely and infinitely divided, always keeping the user's blood drug concentration in the best state, and achieving the best therapeutic effect.

[0074] (f) The intelligent “electronic doctor” can issue dynamic and personalized “electronic prescriptions” based on the user’s genetic information, race, gender, age, weight, height, medical history, and the latest collected test, examination and medication feedback data in the “electronic medical record” file. After receiving the new “electronic prescription”, the intelligent nebulizer strictly executes the program to administer the medication, realizing the data-driven medication goal of program control. At the same time, it continuously collects medication and efficacy data and feeds it back to the “electronic doctor” and continuously enriches the “electronic medical record” file data, forming a dynamic closed loop.

[0075] This invention successfully incorporates the pulse concept from electromagnetic theory, organically linking parameters such as pulse duration (peak width), frequency, interval (period), amplitude (peak height), and energy (peak area) with parameters such as nebulization duration, dosing frequency, dosing interval, dosing intensity, and dosage. This gives rise to the concept of an "electronic doctor," and further to the concepts of "electronic prescriptions" and "electronic medical records." Defining these basic parameters, coupled with the precise and infinitely divisible nature of the nebulized medication and the instantaneous variability of the liquid nebulizer's "specifications," lays a solid foundation for intelligent, precise, and personalized drug delivery.

[0076] Before the advent of truly intelligent "electronic doctors," intelligent nebulizers can utilize electronic monitoring systems to connect to the internet or other devices, reducing medication errors caused by equipment or operators through external or self-integration methods. External intelligent systems with integrated monitoring and feedback functions can record user medication information, enabling data sharing between doctors and patients, allowing doctors to adjust treatment plans promptly. In addition to reminder and recording functions, they can also upload information to a mobile phone via Bluetooth. The 5D intelligent nebulizer, with its own integrated features, employs adaptive nebulization delivery technology, analyzing the user's breathing patterns to determine the nebulization delivery time of the nebulized medication during inhalation.

[0077] Furthermore, to achieve precise drug delivery, the drug delivery assembly 5 of this invention is configured to controllably output atomized particles with a particle size range of 20nm to 20um. Aerosols of different particle sizes will deposit in corresponding respiratory tract sites to achieve partial or whole-respiratory tract targeted drug delivery. The respiratory tract is divided into upper and lower parts: the nose, pharynx, and larynx are collectively referred to as the upper respiratory tract. The trachea, bronchi, and lungs are collectively referred to as the lower respiratory tract, or tracheal tree. The applicant's research has shown that atomized particles of different sizes deposit in different locations within the respiratory tract. By controlling the particle size of the atomized particles, drug delivery can be targeted to different respiratory tract locations, thereby achieving precise drug delivery. For the heated cotton wick nebulizer 5d, the size of the atomized particles can be adjusted by controlling the viscosity of the atomizing agent, the power of the heating element, and the airflow. For ceramic core atomizers like the 5d, the size of the atomized particles can be adjusted by controlling the viscosity of the atomizing agent, the size of the porous ceramic pores, the power of the heating element, and the airflow speed. However, for ultrasonic atomizing plates, the particle size of the atomized particles must be controlled by using a mesh screen to control the aerosol particle size. Figure 9 This is a distribution map of aerosol particles output from the propellant assembly 5, measured using specialized instruments and equipment. For example... Figure 9As shown in the figure, the bar chart represents the probability of aerosols appearing in different particle size ranges, and the wavy line represents the percentage of aerosol quantity within that particle size range. The figure shows that the atomized particles produced by the nebulizer in this example have a particle size range of approximately 1–10 μm, with the aerosol quantity within this range approaching 100% and exhibiting a roughly normal distribution. Furthermore, the proportion of atomized particles in the 1–5 μm size range is approximately 60%, ensuring not only the stability of the particle size output but also enabling the atomized particles in this size range to deposit in the patient's lungs, thereby achieving precise drug delivery and improving the therapeutic effect. It should be noted that the aforementioned professional instruments and equipment can be the PSA series laser particle size analyzer manufactured by Anton Paar. This analyzer utilizes dynamic light scattering (DLS) technology for measurement. DLS is a physical technique used to characterize the particle and molecular size in suspensions or solutions.

[0078] Furthermore, the drug delivery assembly 5 is configured to controllably adjust the aerosol output volume. Specifically, the aerosol output volume can be adjusted by controlling the power of the nebulizer 5d, the nebulization time, and the fan airflow. The drug delivery assembly 5 is configured to have an aerosol output flow rate of 1.0–50 ml / s, preferably 8 ml / s. This output volume adjustment can be programmed based on the aforementioned electronic prescription or manually adjusted based on the user's actual medication requirements. An adjustment device, such as a knob or screen, can be provided on the product for the user to adjust the aerosol output volume. That is, the control unit includes a dosage adjustment unit for operatively adjusting the aerosol output volume.

[0079] Furthermore, for precise drug delivery, an identification device for marking drug delivery information can be installed on the drug delivery assembly 5, and the control unit can be configured to acquire the drug delivery information and set the mist output rate per second and mist output duration of the drug delivery assembly 5 based on the drug delivery information. For example, the identification device can be RFID, NFC, or a barcode, etc. The drug delivery information is written into the identification device, and the control unit has a corresponding reading device to read the drug delivery information, thereby controlling the mist output rate per second and mist output duration of the drug delivery assembly 5 according to the drug delivery information. The above control can also be combined with electronic prescriptions to achieve a more precise drug delivery method.

[0080] It should be added that after the controlled shutdown of the drug delivery assembly 5, the control unit controls the flow generator 8 to shut down after a delay according to the set drug delivery location, so as to generate an incremental airflow to deliver the aerosol to the drug delivery location in the respiratory tract. The delay time ranges from 0.1 to 5.0 seconds, specifically 0.2 seconds, 0.3 seconds, 0.5 seconds, etc., and can be set according to the target location of the drug delivery. Within a certain time range, a longer operating time of the flow generator 8 can deliver the aerosol to deeper parts of the respiratory tract.

[0081] The above-mentioned precise drug delivery method can also be implemented in the following ways.

[0082] (1) The atomizing device (ammunition assembly + flow generator + control unit) is set to generate 100 pulses per gram of atomizing liquid (100 pulses / gram of atomizing liquid);

[0083] (2) Set the atomization duration to 2.5 seconds (i.e., pulse width = 2.5 seconds);

[0084] (3) The fan blows air for 3.0 seconds (with a delay of 0.5 seconds), the air delivery rate is 8 ml / second, and the total volume delivered to the mouth / nose each time is (2.5 x 8) + (0.5 x 8) = 24 ml. The first 20 ml of air delivery and atomization occur simultaneously, and the last 4 ml of air delivery only delivers the aerosol remaining in the airway to the mouth / nose along with the airway;

[0085] (4) If the drug is administered through the nasal cavity, the 24ml aerosol delivered will just fill the entire nasal cavity (the average volume of the nasal cavity = 24ml). At this time, the two mist outlets are placed close to the two nostrils without gaps and the breathing is closed for 5 to 10 seconds. The aerosol will be deposited on the nasal mucosa, and there is no need to spray the drug into the left and right nostrils separately.

[0086] (5) If nebulization and air delivery are started simultaneously through oral inhalation (with a microphone or gas-sensitive switch installed), after the 24ml aerosol is delivered to the oral cavity, inhalation or air delivery can continue (i.e., inhalation / air delivery time ≥ 3.0 seconds), and then the breath is held for 5 to 10 seconds. The aerosol will be deposited in different lesion sites in the oral cavity, pharynx, upper respiratory tract and lower respiratory tract. The specific deposition site depends on the inhalation / air delivery time and the length of the air delivery delay.

[0087] (6) The nebulizer dose for each pulse is 10 mg (i.e., 100 pulses / gram of nebulizer);

[0088] (7) Each administration is administered with N pulses, with a pulse interval of 30 seconds (i.e., the pulse short cycle is set to 30 seconds, and N = 1 to 20).

[0089] (8) Administer the drug M times per day (i.e., set the pulse long cycle = 24 / M hours);

[0090] (9) The dose of nebulized solution per pulse = 10 mg / pulse, the total dose of nebulized solution for each administration - N x 10 mg, and the total dose of nebulized solution for daily administration = M x N x 10 mg;

[0091] (10) If the drug concentration of the nebulizer is X%, the active drug dose per pulse is 10mgxX%, the total active drug dose per administration is Nx10mgxX%, and the total active drug dose per day is MxNx10mgxX.

[0092] The aforementioned 1.0g (100 pulses) of nebulized drug (10%) is loaded into the drug reservoir of the "heated nebulization (ceramic core)" or "ultrasonic nebulization (mesh vibration)" of this invention. The control unit program controls nasal / oral inhalation pulsed administration 3 times / day, 5 pulses each time, 2.5 seconds per nebulization, and nebulization once every 30 seconds (2 pulses / minute); the dose per inhalation is 10mg / pulse; the fan air delivery time is 3.0 seconds (delay 0.5 seconds), and the air delivery rate is 8ml / second.

[0093] Corresponding electronic prescription parameters: Number of pulses per day = 3 x 5, pulse width 2.5 seconds, short cycle = 30 seconds, long cycle 1 = 24 / 3 hours (not considering sleep interval); nebulizer dose per inhalation = 10 mg / pulse, total nebulizer dose per inhalation = 5 x 10 mg / inhalation, total nebulizer dose per day = 3 x 5 x 10 mg / day; active drug dose per inhalation = 10 mg x 10% / pulse, total active drug dose per inhalation = 5 x 10 mg x 10% / inhalation, total active drug dose per day = 3 x 5 x 10 mg x 10% / day.

[0094] By inputting or reading the nebulization electronic prescription parameters (drug delivery information) into the control unit, the nebulizer will strictly follow the set electronic prescription, promptly reminding the patient of the medication time, accurately providing the drug dosage for each pulse, the number of pulses per inhalation, and the number of inhalations per day, thus performing intelligent, precise, and personalized nebulization drug delivery.

[0095] The above description is merely a specific embodiment of this utility model, but the protection scope of this utility model is not limited thereto. Any variations or substitutions that can be easily conceived by those skilled in the art within the technical scope disclosed in this utility model should be included within the protection scope of this utility model. Therefore, the protection scope of this utility model should be determined by the scope of the claims.

Claims

1. A precision delivery device for delivering drug aerosols, characterized in that, It includes: The casing, its size and shape are configured to fit comfortably in the user's hand; A drug delivery assembly capable of atomizing a predetermined dose of drug into an aerosol, the drug delivery assembly having an aerosol channel for delivering the aerosol; A flow generator for generating a positive pressure airflow to deliver the aerosol to the respiratory tract; and The control unit drives the drug delivery assembly to output drug aerosol according to the operation command, and drives the flow generator to generate a set amount of positive pressure airflow; The propellant assembly, flow generator, and control unit are all housed within the housing.

2. The precision delivery device according to claim 1, characterized in that, The explosive assembly includes: The cartridge case, which internally defines the propellant storage compartment; and A nebulizer is positioned within the cartridge case to atomize the drug.

3. The precision delivery device according to claim 2, characterized in that, A base is attached to the bottom of the cartridge case, and the base and the cartridge case together define the cartridge compartment.

4. The precision delivery device according to claim 3, characterized in that, The base is detachably attached to the cartridge case.

5. The precision delivery device according to claim 3 or 4, characterized in that, The base is embedded with an electrode section for transmitting electrical energy to the atomizer.

6. The precision delivery device according to claim 2, characterized in that, The top of the cartridge case has an upwardly extending nozzle, and there is at least one nozzle.

7. The precision delivery device according to claim 6, characterized in that, The inner surface of the mist nozzle is configured in a cone shape to gather the aerosol.

8. The precision delivery device according to claim 6, characterized in that, The nozzle and the atomizer are connected via an aerosol channel.

9. The precision delivery device according to claim 1, characterized in that, The housing includes a cartridge sleeve for receiving the cartridge assembly, the cartridge assembly being detachably assembled in the cartridge sleeve.

10. The precision delivery device according to claim 9, characterized in that, The bottom of the ammunition sleeve is provided with an upper air inlet, and the flow generator is connected to the upper air inlet.

11. The precision delivery device according to claim 10, characterized in that, A concentrator is provided between the flow generator and the projectile sleeve to gather and guide the airflow into the projectile assembly.

12. The precision delivery device according to claim 11, characterized in that, The air-concentrating shroud has an air outlet pipe extending into the ammunition sleeve, which is connected to the upper air inlet of the ammunition assembly.

13. The precision delivery device according to claim 11 or 12, characterized in that, The wind-gathering shroud has a conical inner cavity for concentrating airflow.

14. The precision delivery device according to claim 2, characterized in that, The atomizer is a heated atomizer or an ultrasonic atomizer.

15. The precision delivery device according to claim 14, characterized in that, The heating atomizer is a ceramic core heating atomizer or a cotton core heating atomizer, and the ultrasonic atomizer is a piezoelectric ceramic atomizer or a mesh screen vibration atomizer.

16. The precision delivery device according to claim 1, characterized in that, The flow generator is a fan or an air pump.

17. The precision delivery device according to claim 1, characterized in that, The control unit includes a circuit board that is vertically arranged in the gap between the housing and the explosive assembly.

18. The precision delivery device according to claim 17, characterized in that, The housing has an operating section, and the flow generator presses against the back of the circuit board to support the operating section.

19. The precision delivery device according to claim 1, characterized in that, The propellant assembly is configured such that the aerosol output flow rate is 1.0–50 ml / s.

20. The precision delivery device according to claim 19, characterized in that, The explosive assembly is configured such that the aerosol output time is 0.2 to 5.0 seconds per cycle.

21. The precision delivery device according to claim 1, characterized in that, An air inlet cavity is formed between the flow generator and the housing, and a battery is installed inside the air inlet cavity.

22. The precision delivery device according to claim 21, characterized in that, The battery is placed horizontally inside the air intake cavity.

23. The precision delivery device according to claim 1, characterized in that, The set amount of the positive pressure airflow includes the flow rate and duration.

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