Low-pressure dual-parameter feedback adaptive air pressure breathing auxiliary system and control method

Abstract

This invention discloses a low-pressure dual-parameter feedback adaptive air-pressurization respiratory assist system and its control method, belonging to the technical field of special respiratory assist equipment. The system includes an air supply module, a parallel compliant energy storage branch array, a semi-open partitioned mouth and nose interface, an air supply microchannel, an exhaust gas stripping microchannel, a dual-parameter feedback detection module, a control module, and a passive failure safety bypass module. The control module dynamically calculates the comprehensive physical benefit value of each microchannel and reconstructs the conduction weight and release sequence online based on dual-parameter feedback of local mouth and nose pressure and gas composition, as well as respiratory phase information. This invention overcomes the limitations of traditional closed-cavity pressure maintenance by using directional air supply through the mouth and nose main flow lines and preferential physical stripping of the high CO2 boundary layer during the exhalation phase. Under conditions such as dynamic mask leakage and extreme cold ice blockage, it significantly improves inspiratory synchronicity, exhaust gas removal rate, and system failure safety.

Description

Technical Field

[0001] This invention relates to the field of special respiratory assistance equipment and individual life support technology in extreme environments. Specifically, it relates to a low-pressure dual-parameter feedback adaptive air pressurization respiratory assistance system for dynamic working conditions such as high altitude and low pressure, extreme cold and freezing, and high physical load, as well as a low-level linkage control method based on multi-dimensional physiological parameter benefit reconstruction and local exhaust gas physical stripping. Background Technology

[0002] In applications such as high-altitude mountaineering, plateau patrol, cold-region rescue, polar construction, and portable life support outside the hospital, users are often in environments with low air pressure, low temperature, and high physical exertion. In such environments, the volume fraction of oxygen in the air remains relatively stable, but due to the decrease in total ambient pressure, the partial pressure of oxygen in the air inhaled by the human body is significantly reduced, which can easily lead to difficulty breathing, rapid decline in physical strength, and in severe cases, can induce altitude sickness, hypoxia, disability, or even endanger life.

[0003] For a long time, respiratory support solutions for high-altitude environments have primarily relied on high-pressure oxygen cylinders, where oxygen stored at high pressure is depressurized and then delivered to a mask for inhalation. While this approach can alleviate hypoxia to some extent, it suffers from several significant drawbacks: First, the oxygen cylinders and depressurization components are quite heavy, making them unsuitable for prolonged carrying. Second, high-pressure containers pose significant safety risks under conditions such as collisions, drops, and alternating low temperatures. Third, gas cylinders are consumable resources, making resupply difficult and costly in remote areas. Fourth, the temperature drops after depressurization, resulting in poor inhalation comfort. Fifth, continuous flow or simple threshold control methods cannot adapt to the respiratory phase changes during high-intensity activities, easily leading to wasted gas or asynchrony between the user and the machine.

[0004] On the other hand, with the development of portable batteries, miniature compressors, and miniature sensors, mechanical pressurization using ambient air has become feasible in engineering. Existing technologies propose compressing ambient air and sending it into the mask, controlling the intake and exhaust valves based on the pressure and oxygen concentration signals inside the mask to achieve a cyclical breathing assistance system of inflation-maintenance-exhaust. This type of solution has advantages over the high-pressure oxygen cylinder route, such as lighter weight, convenient energy replenishment, and higher safety.

[0005] For example, one type of portable air-pressurized breathing aid typically includes a compressor, an air tank, a mask, a pressure sensor, an oxygen concentration sensor, an intake valve, and an exhaust valve. The controller controls the compressor and valves based on the internal pressure of the mask and the oxygen concentration threshold, maintaining a certain air pressure and oxygen concentration inside the mask within a preset range. This type of solution represents a relatively typical closed-cavity pressure maintenance + dual-parameter threshold control technology approach in this field.

[0006] However, the inventors have discovered that existing solutions of this type have at least the following limitations: Firstly, existing solutions mainly focus on controlling the average state of the internal cavity of the mask. By default, maintaining the cavity pressure and oxygen concentration is sufficient to achieve effective respiratory assistance. However, in actual use, what the human body is really concerned about is not the average state of the entire mask cavity, but whether the main flow areas of the mouth and nose can obtain enough flow and oxygen partial pressure of gas in time during inhalation. Once the local area of ​​the mouth and nose is not supplied with enough air, even if the average cavity pressure is up to standard, there will still be difficulty in inhaling, delayed air supply, and subjective suffocation.

[0007] Secondly, existing solutions generally employ sealed or semi-sealed mask structures to improve pressure stability within the cavity. However, in scenarios involving high altitude, low temperatures, prolonged wear, and motion disturbances, air leakage inevitably occurs at the mask edges. Simultaneously, mouth breathing, facial movements, posture changes, frost adhesion, and mask misalignment all alter the seal. Because current technologies rely on the sealing of a single cavity for system effectiveness, fluctuations in sealing conditions significantly reduce air supply efficiency.

[0008] Third, existing inflation-maintenance-exhaustion cycles are usually triggered based on pressure or oxygen concentration thresholds, which are essentially delayed feedback. When the human body experiences rapid, irregular, or rapidly changing respiratory rhythms during high-intensity activities, the system has difficulty sensing the inspiratory demand in advance. It often only responds passively after the cavity pressure drops or the oxygen concentration deteriorates, resulting in delayed inspiratory phase air supply and significant human-ventilator asynchrony.

[0009] Fourth, existing solutions mostly use the overall replacement method to reduce the concentration of exhaust gas in the mask cavity. However, the area where the risk of re-inhalation first forms after exhalation is often not the entire mask cavity, but a local high CO2 boundary layer in front of the mouth and nose. If this local area cannot be cleared first, even if the average oxygen concentration in the cavity is still within an acceptable range, the next inhalation may still result in the inhalation of more exhaled exhaust gas, affecting comfort and safety.

[0010] Fifth, the exhaled air inside the mask has high humidity and temperature, which can easily cause condensation, frost, or ice formation at the exhaust points, sensor surfaces, and local flow channels in extremely cold environments. Valves, fine channels, and sensing components in existing solutions can easily become sources of failure, leading to poor exhaust, measurement distortion, or abnormal system response.

[0011] Therefore, how to provide a low-pressure dual-parameter feedback adaptive air pressurization breathing assist system and control method that no longer relies excessively on the overall sealing of the mask, can organize air supply around the true breathing phase and the mainstream airflow of the mouth and nose, can directionally remove exhaled waste air from the mouth and nose, and can still work effectively under conditions of low temperature, air leakage, posture changes and local blockage has become a technical problem that urgently needs to be solved in this field. Summary of the Invention

[0012] In view of the above-mentioned defects and technical bottlenecks of the prior art, the purpose of this invention is to provide a low-pressure dual-parameter feedback adaptive air pressurization breathing assistance system and control method.

[0013] This invention departs from the traditional paradigm of maintaining the average pressure of the entire sealed cavity of the mask as the sole control objective. Instead, it focuses on the instantaneous physical needs of the user's mouth and nose, the dynamic changes in the breathing phase, the need for targeted removal of local exhaust gas boundary layers, and the safety margin for system failure under extreme conditions. It constructs a low-pressure, semi-open, reconfigurable flow channel, and physically degradeable air-pressurized breathing aid underlying architecture. Through this architecture, this invention primarily aims to solve problems such as system performance degradation caused by mask leakage, human-machine interaction caused by control lag, and CO2 re-inhalation under high-altitude, extreme low-temperature, and high-intensity dynamic disturbance conditions, thereby significantly improving air supply effectiveness, physiological comfort, life safety, and system robustness.

[0014] To achieve the above objectives, the present invention adopts the technical solution as described in claims 1-10: A low-pressure dual-parameter feedback adaptive air-pressurization breathing assist system includes: The air supply module is used to draw in ambient air and output a reference pressurized airflow; A parallel compliant energy storage branch array is fluidly connected to the gas supply module and is used to perform time-sharing energy storage and pulsed release of the reference pressurized airflow. A semi-open partitioned mouth and nose interface is connected to the parallel compliant energy storage branch array to form a partially sealed local flow guiding space around the user's mouth and nose. Multiple air supply microchannels and exhaust gas stripping microchannels are set in the semi-open partitioned mouth and nose interface to organize air supply and exhaust in different areas; The dual-parameter feedback detection module is used to detect local pressure parameters and local gas composition parameters in the mouth and nose. The control module is electrically connected to the air supply module, the parallel compliant energy storage branch array, the air supply microchannel, the waste gas stripping microchannel, and the dual-parameter feedback detection module. The control module does not use the overall average pressure of the mask as the sole control basis. Instead, it dynamically adjusts the conduction weight, equivalent flow resistance, or opening / closing sequence of the air supply microchannel and the waste gas stripping microchannel based on respiratory phase locking, respiratory effort estimation, and comprehensive pathway benefit assessment. This aims to enhance the main air supply to the mouth and nose and prioritize the removal of localized waste gas. The passive failover safety bypass module is used to maintain low-resistance natural breathing when the active control fails.

[0015] As a further technical solution of the present invention, the semi-open partitioned oronasal interface includes a flexible flow guide skirt close to the mouth and nose and a low-resistance air guide mask located on its outer side. Controlled leakage is allowed between the flexible flow guide skirt and the user's face. Multiple partitioned microchannel areas are formed between the low-resistance air guide mask and the flexible flow guide skirt, rather than a single physically sealed cavity. The multiple air supply microchannels and exhaust gas stripping microchannels are respectively arranged in at least two regions of the nasal bridge area, nasal ala area, preoral area and buccal area, so as to form directional air supply towards the main flow line of the mouth and nose during the inspiratory phase and to form selective stripping flow against the high CO2 boundary layer in front of the mouth and nose during the expiratory phase.

[0016] As a further preferred technical solution of the present invention, the parallel compliant energy storage branch array includes at least two micro energy storage units with different flow resistance and physical compliance, each micro energy storage unit having a different inflation / deflation time constant, so that multiple micro energy storage units can release pulsating airflow in sequence during the same breathing cycle; the micro energy storage unit includes an elastic bladder, a deformable membrane cavity or a compliant gas storage branch, and each micro energy storage unit is independently provided with at least one of a pre-stage flow limiting component, a post-stage flow limiting component, a unidirectional component or a variable impedance component.

[0017] As a further preferred technical solution of the present invention, the exhaust gas stripping microchannel constitutes a CO2 boundary layer directional stripping ring arranged around at least two regions in the subnasal, preoral, and bilateral cheek areas; the CO2 boundary layer directional stripping ring preferentially removes the high CO2 boundary layer in front of the mouth and nose through negative pressure jet, Venturi suction, or jet flow physical action during the exhalation phase; and performs closing, throttling, or reducing its conduction duty cycle during the inhalation phase.

[0018] As a further preferred technical solution of the present invention, the control module includes a respiratory phase locking layer, a respiratory effort estimation layer, and a pathway benefit reconstruction layer; the respiratory phase locking layer identifies the inspiratory initiation point, inspiratory acceleration, and expiratory end point through one or more of the following information: high-frequency micro-pressure waves, flow disturbances, chest wall motion signals, pre-larynx vibration signals, or changes in oral and nasal temperature and humidity; the respiratory effort estimation layer generates a respiratory effort index through one or more of the following: early inspiratory negative pressure slope, local flow resistance changes, chest belt effort index, or tidal volume estimation value; the pathway benefit reconstruction layer dynamically updates the conduction weight, equivalent flow resistance, or opening and closing sequence of each micropathway based on the comprehensive physical contribution of each micropathway in reducing respiratory work, improving effective inspiratory air supply, reducing CO2 reabsorption, reducing short-circuit losses, and improving local blockage tolerance within one or more recent respiratory cycles.

[0019] As a further preferred technical solution of the present invention, the passive failure safety bypass module includes a normally open low-resistance bypass channel, a mechanical expiratory one-way valve, and a power failure default safety position mechanism; the normally open low-resistance bypass channel plays a role in ensuring basic ventilation when the system is working normally, and instantly degenerates into a natural breathing pathway when the system loses power or the control fails; the power failure default safety position mechanism is used to automatically restore the electronically controlled valves of the air supply microchannel and the exhaust gas stripping microchannel to a low-resistance safety state when the control power is physically lost.

[0020] As a further preferred technical solution of the present invention, the gas supply module adopts one or more of a micro centrifugal fan, a diaphragm pump, or a micro compressor; the gas supply microchannel and the waste gas stripping microchannel are composed of one or more of a low-power microvalve, a flexible flap, a shape memory microbeam, an elastic channel, a flow limiting orifice, and a Venturi suction channel; the local gas component parameters of the mouth and nose collected by the dual-parameter feedback detection module include at least one of CO2 concentration and oxygen concentration.

[0021] The present invention also provides a low-pressure dual-parameter feedback adaptive air pressurization breathing assist control method based on the above system, comprising the following continuously flowing steps: Step S1: Control the air supply module to continuously draw in ambient air and provide a reference pressurized airflow to the parallel compliant energy storage branch array for time-sharing physical energy storage; Step S2: High-frequency real-time acquisition of local pressure parameters and local gas composition parameters of the mouth and nose through a dual-parameter feedback detection module; In step S3, the control module accurately identifies the breathing phase information based on the collected parameters and independently calculates the comprehensive benefit value of each air supply microchannel and exhaust gas stripping microchannel. Step S4: Based on the identified respiratory phase information and the comprehensive benefit value, dynamically adjust the conduction weight, equivalent flow resistance, or opening and closing sequence of the air supply microchannel and the waste gas stripping microchannel, so as to control the parallel compliant energy storage branch array to release pulsating airflow in sequence during the inspiratory phase to achieve directional air supply to the mouth and nose mainstream, and to control the waste gas stripping microchannel to achieve local waste gas preferential physical removal during the expiratory phase.

[0022] As a further preferred embodiment of this control method, the specific physical process of controlling the parallel compliant energy storage branch array to release pulsating airflow in sequence during the intake phase is as follows: at the moment of triggering at the intake leading edge, branches with low time constants are released first to pneumatically cover the intake initiation stage; branches with higher time constants are released later to pneumatically cover the intake acceleration stage and the subsequent plateau stage; the specific process of dynamically adjusting the conduction weights is as follows: the conduction priority of each path is updated online according to the comprehensive benefit value, strengthening physical paths with high benefits and suppressing physical paths with low benefits or high risks. Among them, pipeline blockage, frost, execution error, environmental noise interference and sensing uncertainty are introduced into the weight dynamic update process as algorithm penalty terms.

[0023] As a further preferred embodiment of this control method, the control method also includes blockage detection and physical degradation control logic: the control module compares the command opening degree and actual flow rate of each branch, the branch pressure decay slope and valve position response time in real time; when a suspected condensation blockage or frost branch is identified, the weight of the branch is actively reduced in subsequent cycles, and the gas supply and stripping tasks are seamlessly transferred to physically redundant branches or bypasses; the control module has preset multiple upper-level strategy modes, including high-altitude mode, motion mode, resting mode, nighttime conservative mode and industrial low-temperature mode. Different modes dynamically adjust the weight template of the benefit function so that the system prioritizes approaching different life support targets under different physical scenarios.

[0024] The beneficial effects and significant advancements of this invention are as follows: This invention introduces a semi-open partitioned mouth and nose interface and air supply microchannel, no longer relying on the pressure holding of a single sealed cavity for system efficiency. Through spatial geometric guidance and microchannel air supply, the limited pressurized airflow is directed to the main airflow line of the mouth and nose during the inhalation phase. Even if movement causes edge leakage, wear displacement, or mouth opening, the system can still maintain effective air supply to the main airflow line, effectively avoiding the defect of traditional masks that fail when leaking air.

[0025] This invention utilizes the timing release mechanism of the respiratory phase locking layer of the control module and the parallel compliant energy storage branch array to change the passive and lagging threshold compensation in traditional control to a feedforward active aerodynamic coverage. The relay release of low-time-constant and high-time-constant micro-energy storage units effectively fits the transient flow gap at the leading edge of human inspiration and the acceleration phase of inspiration, significantly reducing the feeling of difficulty in inspiration and improving human-machine interaction.

[0026] This invention incorporates a CO2 boundary layer directional stripping ring. During the expiratory phase, negative pressure or the Venturi effect is used to preferentially remove the high CO2 boundary layer concentrated directly in front of the mouth and nose. This localized physical boundary layer treatment method improves the quality of the inlet gas in the next respiratory cycle and enhances the efficiency of blood oxygen exchange.

[0027] The built-in pathway benefit reconstruction layer of this invention enables it to dynamically optimize and adaptively reconstruct. Based on the comprehensive benefits of each micropathway in reducing respiratory work and improving oxygen transport, the system dynamically migrates the dominant physical flow path online. This mechanism allows the system to better accommodate differences in facial features, spatial migration of leak locations, and various breathing postures among different users.

[0028] The multi-path gas supply and multi-path stripping physical topology of this invention has hardware redundancy characteristics. Combined with blockage detection and degradation control logic, when a local micro-path encounters condensation, frost or ice blockage in the early stage, the system can identify execution errors and apply algorithmic penalties, automatically and smoothly transferring the tasks of high-risk paths to redundant advantageous paths, thereby improving reliability in extremely cold industrial and rescue environments.

[0029] This invention integrates a normally open low-resistance bypass channel, a mechanical expiratory one-way valve, and a default safety position mechanism in the passive failure safety bypass module. In the event of serious failures such as battery depletion, valve core jamming, or motherboard crash, the system can degrade from an active pressurization device to a low-resistance open pipeline that allows users to freely inhale and exhale smoothly, significantly reducing the risk of single-point failure of the life support device.

[0030] This invention elevates the control target from the coarse average cavity pressure and average oxygen concentration to a comprehensive multi-dimensional index including effective mainstream gas supply during the inspiratory phase, additional respiratory work, local CO2 boundary layer stripping, and ineffective free breathing. This realizes the transformation of the respiratory control field from macroscopic physical quantity-based pressure to microscopic physiological-level gas exchange quality management.

[0031] By employing an architecture design that continuously charges the parallel compliant energy storage branch array with a steady-state air supply module, this invention avoids the practice of passively chasing the peak intake speed by simply relying on a high-power motor. This architecture reduces the motor's thermal load and transient high-current impact while controlling the peak air supply burst force and the average power consumption of the entire machine, thus extending the endurance of the soldier's carried equipment.

[0032] To further verify the aforementioned technological advancements with objective data, this application conducted comparative tests on the traditional servo feedback single-cavity system and the complete technical configuration of this invention under simulated altitude conditions of 6000 meters and -20°C. The test data are as follows: The aforementioned stringent physical test data show that, under boundary conditions where the leakage rate at the mask edge is even slightly higher than that of the traditional control group, the core life support indicators of the present invention, such as peak inspiratory flow rate satisfaction, increase in inspiratory nasal oxygen partial pressure, CO2 re-inhalation inhibition, reduction in additional respiratory work, and failure free breathing resistance, all exhibit significant advantages. This indicates that the performance improvement of the present invention does not rely on absolute high sealing, but rather stems from the system-level synergistic advantages stimulated by directional air supply through the main airflow path of the mouth and nose, preferential stripping of local boundary layer waste gas, and online dynamic reconstruction of multiple pathways. Attached Figure Description

[0033] Figure 1 This is a block diagram showing the overall physical architecture and system module connection relationship of the low-pressure dual-parameter feedback adaptive air-pressurization breathing assist system provided in this embodiment of the invention; Figure 2 This is a flowchart of the underlying logic flow and execution steps of the low-pressure dual-parameter feedback adaptive air pressurization breathing assistance control method provided in this embodiment of the invention; Figure 3 A schematic diagram of the spatial physical layout structure of the semi-open partitioned oronasal interface and the hybrid reconfigurable microfluidic network provided in an embodiment of the present invention. Figure 4 This is a schematic diagram of the underlying pneumatic path and electronic control connection between the pneumatic pulse generation mechanism and the core control module of the parallel compliant energy storage branch array provided in an embodiment of the present invention. Figure 5 A schematic diagram illustrating the data interaction and weight update relationship of an online reconfiguration controller based on a breathing benefit function under multidimensional physical parameters, provided in an embodiment of the present invention. Figure 6 This is a schematic diagram of the physical reconstruction of the regional gas supply channel and the triggering timing waveform of the multi-time constant pulsating branch in the intake phase of the system provided in the embodiment of the present invention; Figure 7 This is a schematic diagram of the working state of the CO2 boundary layer directional stripping ring and local exhaust gas physical outlet path of the system provided in the embodiment of the present invention during the exhalation phase.

[0034] In the diagram: 10 - Air supply module; 20 - Parallel compliant energy storage branch array; 21 - Micro energy storage unit; 30 - Semi-open partitioned nose and mouth interface; 31 - Flexible flow guide skirt; 32 - Low-resistance air guide hood; 33 - Partitioned microchannel area; 301 - Nasal bridge area; 302 - Nasal ala area; 303 - Preoral area; 304 - Buccal area; 40 - Air supply microchannel; 50 - Exhaust gas stripping microchannel; 51 - CO2 boundary layer directional stripping ring; 60 - Dual-parameter feedback detection module; 70 - Control module; 71 - Respiratory phase locking layer; 72 - Respiratory effort estimation layer; 73 - Pathway benefit reconstruction layer; 80 - Passive failure safety bypass module; 81 - Normally open low-resistance bypass channel; 82 - Mechanical expiratory one-way valve; 83 - Power failure default safety position mechanism. Detailed Implementation

[0035] To make the physical objectives, technical solutions, and beneficial effects of this invention clearer and more explicit, the technical solutions of this invention will be analyzed in detail below with reference to the accompanying drawings and specific engineering embodiments. The preferred embodiments described herein are for illustrative purposes only and are not intended to limit the invention. Any equivalent substitutions, improvements, or modifications made by those skilled in the art, based on their understanding of the essential spirit of this invention, fall within the protection scope of this invention.

[0036] Example 1 This embodiment provides a low-pressure dual-parameter feedback adaptive air pressurization breathing assist system for high-altitude rescue, border patrol, and low-temperature industrial heavy-duty operations. The overall physical topology of the system is as follows: Figure 1 and Figure 4 As shown, its core hardware architecture is mainly composed of a gas supply module 10, a parallel compliant energy storage branch array 20, a semi-open partitioned mouth and nose interface 30, a control module 70, and a dual-parameter feedback detection module 60, all physically coupled together.

[0037] In the basic engineering configuration of this embodiment, the air supply module 20 uses a micro centrifugal fan with a high mean time between failures (MTBF) as the underlying fluid power source. Unlike the control logic in traditional respiratory assist devices that directly and passively chase the peak of human inhalation by drastically increasing the fan speed, the micro centrifugal fan in this embodiment is limited to not undertaking the task of supplying all instantaneous air for each inhalation. Instead, the control module 70 makes it operate continuously in a low-fluctuation steady-state condition, continuously injecting the reference pressurized airflow into the subsequent parallel compliant energy storage branch array 20.

[0038] The parallel compliant energy storage branch array 20 physically comprises multiple micro energy storage units 21 arranged in parallel. Each micro energy storage unit 21 is independently configured with a pneumatic compliant cavity with specific physical elasticity, a one-way component, a flow-limiting orifice, and an electrically controlled release valve. This creates different charging and discharging time constants at the fluid dynamics level. This physical architecture of steady-state charging and time-sharing release allows the main gas source to operate within a high aerodynamic efficiency range, while the transient high-flow release task during the peak intake period is undertaken by the parallel compliant energy storage branch array 20.

[0039] This embodiment changes the traditional form of a sealed face mask. The semi-open partitioned mouth and nose interface 30 adopts a double-layer asymmetrical interface structure: the inner side is a flexible airflow guide skirt 31 close to the mouth and nose, and the outer side is fitted with a low-resistance airflow shield 32. The flexible airflow guide skirt 31 is physically designed to allow controlled leakage between itself and the user's face, while the low-resistance airflow shield 32 and the flexible airflow guide skirt 31 are physically separated to form multiple independent partitioned microchannel areas 33, such as the nasal bridge area 301, nasal ala area 302, preoral area 303, and buccal area 304. This embodiment does not aim solely at forming a rigid, sealed cavity with strict pressure retention, but rather requires that within the time window triggered by the inspiratory phase, the pressurized airflow is guided along the main airflow path of the mouth and nose through the air supply microchannel 40 to achieve concentrated delivery.

[0040] In actual dynamic working conditions, when the user is in a relatively stable metabolic state, the dual-parameter feedback detection module 60 continuously collects physical parameters such as local micro-pressure fluctuations, regional flow velocity, temperature and humidity gradients, and ambient background pressure at a certain sampling rate. The respiratory phase locking layer 71 in the control module 70 predicts the user's true respiratory phase based on the characteristics of recent respiratory waveforms. Once the algorithm layer detects that the inspiratory front is about to arrive, the control module 70 immediately issues a feedforward command to trigger the first micro-energy storage unit 21 with a low time constant in advance, causing it to quickly release the airflow package and pneumatically cover the flow vacuum at the beginning of the inspiratory phase. Immediately afterwards, the second micro-energy storage unit 21 with a medium time constant is triggered to pneumatically cover the flow demand in the inspiratory acceleration phase. If the dual-parameter feedback detection module 60 detects that the local flow gap is widening, it calls the redundant backup branch for hydrodynamic compensation.

[0041] For example, in a typical application, the control module 70 determines, through sensor data fusion, that the current user exhibits a comprehensive state characterized by nasal inhalation dominance, excessive leakage in the nasal bridge region 301, and a slight tendency for mouth opening deformation in the preoral region 303. Based on this, the algorithm layer asymmetrically configures the regional air supply weights: reducing the air supply weight of the nasal bridge region 301, increasing the weight of the nasal alar region 302, maintaining a moderate weight in the preoral region 303, and reducing the weight of the buccal region 304. Under this configuration, the pulsating airflow released by the array will directionally penetrate into the core area of ​​the user's mouth and nose along the main flow lines of the nasal alar region 302 and the preoral region 303, thereby reducing the additional negative pressure work burden that the user must overcome when inhaling.

[0042] This embodiment demonstrates the air supply organization capability of the present invention: that is, without significantly increasing the overall battery power consumption and reducing dependence on airtightness, the hardware collaboration of the parallel compliant energy storage branch array 20 and the semi-open partitioned mouth and nose interface 30 achieves an improvement in the peak inhalation air supply hit rate; measured physical data show that, with the mask edge leakage rate at the same level as the traditional solution, the peak inhalation flow satisfaction and the improvement in local oxygen partial pressure in the mouth and nose of the corresponding architecture of this embodiment have significant advantages over the traditional static pressure-maintaining single-chamber solution, and the user's additional breathing work shows a significant decrease.

[0043] Example 2 Building upon the hardware foundation constructed in Embodiment 1, this embodiment further introduces an improved pathway benefit reconstruction layer 73 algorithm architecture and an expiratory phase CO2 boundary layer directional stripping ring 51, thereby constructing an enhanced respiratory assist system with cross-respiratory cycle adaptive capabilities. Details of its core physical flow path and algorithm interaction can be found in [link to documentation]. Figure 2 , Figure 5 , Figure 6 and Figure 7 .

[0044] In the physical topology of this embodiment, a ring-shaped or semi-ring-shaped CO2 boundary layer directional stripping ring 51 is embedded around the semi-open partitioned oronasal interface 30. This stripping ring 51 is spatially positioned close to the outer periphery of the preoral region 303 and the bilateral buccal regions 304, and connects upstream to an independent exhaust gas stripping microchannel 50. The exhaust gas stripping microchannel 50 can be physically connected to a Venturi ejector structure based on Bernoulli's principle, or it can be connected to a low-negative-pressure extraction branch driven by a micro-pump. This structure performs boundary layer gas extraction during the exhalation phase and shuts down or reduces weight during the inhalation phase. The significance of this mechanism is that the system prioritizes power resources to process the high CO2 dead space region directly in front of the mouth and nose, while avoiding the removal of fresh, pressurized gas that surges in along the main flow path during the inhalation phase.

[0045] The core algorithm of the pathway benefit reconstruction layer 73 is to change the long-term fixed supply and exhaust configuration of each microchannel region and instead give the system dynamic optimization capability. The algorithm layer updates the conduction weights of each supply microchannel 40 and exhaust gas stripping microchannel 50 online based on the actual performance of each microchannel in the recent several consecutive breathing cycles. The control module 70 rigorously calculates the marginal contribution of each independent physical pathway in the current time window to reducing additional breathing work, improving oxygen transport efficiency, improving CO2 stripping depth, and reducing short-circuit leakage loss, and incorporates physical factors such as pipeline condensation, frost adhesion, valve execution error, and sensor uncertainty as penalty terms into the benefit function calculation model. Subsequently, the pathway weights in the next time window are updated in a normalized manner, so that pathways with higher benefits and lower risks receive flow tilt, while pathways with poor benefits or low reliability are suppressed or shut down by the algorithm.

[0046] For example, in extreme inspection scenarios; when a user is performing heavy-load climbing above the snow line at -15℃, accompanied by rapid breathing and facial muscle deformation; at this time, the dual-parameter feedback detection module 60 collects the microscopic pressure drop in the preoral region 303 and the local CO2 concentration peaks, and the matrix operation of the pathway benefit reconstruction layer 73 determines that the current physical benefits of air supply and waste discharge in the preoral region 303 have significantly increased; in the next respiratory cycle, the control module 70 immediately sends a reconfiguration message to the underlying pneumatic actuator: During the inhalation phase, the duty cycle of the air supply microchannel 40 in the preoral region 303 is increased, so that the pulsating pressurized airflow hits the mainstream line of the oral cavity in a large-angle fan shape; when the respiratory phase locking layer 71 detects the moment the exhalation phase begins, the corresponding air supply microchannel 40 is cut off, and the exhaust gas stripping microchannel 50 of the preoral region 303 and the bilateral buccal regions 304 is opened, driving the CO2 boundary layer directional stripping ring 51 to perform strong negative pressure suction.

[0047] This online dynamic reconfiguration mechanism based on physical benefits enables the system to maintain superior gas exchange physical efficiency under complex boundary conditions such as differences in the user's facial geometry, spatial migration of the mask's physical leakage location, and frequent switching of breathing posture, thus improving the adaptability of traditional breathing equipment under dynamic operating conditions.

[0048] Example 3 Building upon the adaptive algorithm architecture constructed in Example 2, this example further addresses survival scenarios such as -20℃ extreme cold industrial operations and high-altitude extreme rescue without logistical support. It establishes a reliable failure safety defense line, condensation blockage protection mechanism, and mode degradation logic at both the mechanical and control layers. The system engineering layout and control flow are mainly described in [reference needed]. Figure 1 , Figure 4 and Figure 7 .

[0049] At the mechanical defense level, the passive failure safety bypass module 80 constitutes the lifeline of this system. This module physically integrates a normally open low-resistance bypass channel 81, a mechanical exhalation one-way valve 82, and a power failure default safety position mechanism 83. When the active pressurization system is operating normally, the normally open low-resistance bypass channel 81 only undertakes a small amount of auxiliary ventilation function. However, in the event of a serious failure such as a complete power failure of the active system, damage to the core control board, or severe damage to the pipeline, this channel instantly degenerates into a natural breathing physical pathway that allows external ambient air to enter. The mechanical exhalation one-way valve 82 is physically arranged on the outer wall directly below the preoral region 303. Its opening and closing are mechanically driven by unidirectional fluid dynamic pressure, ensuring that exhaled waste gas can be smoothly discharged to the external environment under extreme conditions, effectively preventing the physical backflow of high-concentration waste gas. The default safety position mechanism 83 preferably adopts a miniature solenoid valve structure with a built-in pre-tightening spring. When the power supply for maintaining the control logic is lost, the pre-tightening spring releases mechanical potential energy, driving the valve cores of all gas supply micro-passages 40 and exhaust gas stripping micro-passages 50 to mechanically reset to a low-resistance safety state with a larger flow area, thereby reducing the risk of single-point failure of life support equipment.

[0050] At the control defense level, this embodiment strengthens the blockage detection and automatic degradation control logic based on fluid dynamics. A key engineering challenge in extremely cold environments is that the warm, moist air exhaled by the human body easily undergoes a phase change within the microchannels, leading to condensation, frost, and ice blockage. To address this, the control module 70 is equipped with a real-time fluid dynamics comparison function, which continuously monitors the opening degree of the electronic control command for each physical branch, the actual fluid flow rate, the branch pressure attenuation slope, and the valve core mechanical response time. Once it detects that a certain exhaust gas stripping microchannel 50 exhibits a phenomenon where the valve has received an opening signal but the internal pressure has not significantly decreased over several consecutive breathing cycles, the control module 70 identifies it as a suspected condensation / frost branch.

[0051] After a branch is identified as high-risk, the system applies an algorithmic penalty weight to the branch in the path benefit reconstruction layer 73 and lowers its conduction priority in the subsequent calculation window. At the same time, the control module 70 automatically and smoothly migrates the exhaust gas extraction task of the area to the non-frosted redundant exhaust gas stripping microchannel 50 on the opposite side, thereby effectively avoiding complete blockage of the pipeline that could obstruct the user's breathing.

[0052] In addition, the control module 70 has multiple preset upper-level strategy modes, including high-altitude mode, sports mode, rest mode, nighttime conservative mode, and industrial low-temperature mode. The system can switch modes by receiving external commands through a human-machine interface or wireless radio frequency communication. The difference between the different modes is that the system will call different benefit function weight templates. For example, in industrial low-temperature mode, the algorithm will appropriately amplify the weight of the blockage penalty term and the exhaust gas stripping to prioritize ensuring the smooth flow of the exhaust pipeline. In nighttime conservative mode, the algorithm will reduce the amplitude of the pulse trigger and the fan speed to prioritize reducing acoustic noise and improving the user's sleep comfort.

[0053] Through the physical and logical construction of the above embodiments, the present invention optimizes the aerodynamic organization structure of fluid pressurization and local microchannels at the hardware level, and realizes adaptive reconstruction based on multidimensional physiological benefits at the underlying control algorithm, thereby improving the adaptability of traditional respiratory assist devices under complex working conditions.

[0054] Finally, it should be noted that the embodiments described in detail above are merely preferred engineering implementations of the present invention, and their purpose is to help those skilled in the art understand the core essence of the present invention; any equivalent substitutions, structural modifications or logical parameter adjustments made within the principles of the pneumatic organization architecture and adaptive reconfiguration algorithm of the present invention shall fall within the scope of protection claimed by the present invention.

Claims

1. A low-pressure dual-parameter feedback adaptive air pressurization breathing assist system, characterized in that, include: Air supply module (10) is used to draw in ambient air and output a reference pressurized airflow; A parallel compliant energy storage branch array (20) is fluidly connected to the gas supply module (20) and is used to perform time-sharing energy storage and pulsating release of the reference pressurized airflow; A semi-open partitioned mouth and nose interface (30) is connected to the parallel compliant energy storage branch array (20) to form a non-completely sealed local flow guiding space around the user's mouth and nose; Multiple air supply microchannels (40) and exhaust gas stripping microchannels (50) are set in the semi-open partitioned mouth and nose interface (30) for organizing air supply and exhaust in different areas; A dual-parameter feedback detection module (60) is used to detect local pressure parameters and local gas composition parameters of the mouth and nose. The control module (70) is electrically connected to the air supply module (10), the parallel compliant energy storage branch array (20), the air supply microchannel (40), the waste gas stripping microchannel (50), and the dual-parameter feedback detection module (60); wherein, the control module (70) does not use the overall average pressure of the mask as the sole control basis, but dynamically adjusts the conduction weight, equivalent flow resistance, or opening and closing sequence of the air supply microchannel (40) and the waste gas stripping microchannel (50) based on breathing phase locking, breathing effort estimation, and comprehensive benefit assessment of the pathway, so as to achieve enhanced air supply to the mouth and nose mainstream and preferential removal of local waste gas; A passive failover safety bypass module (80) is used to maintain low-resistance natural breathing in the event of an active control failure.

2. The low-pressure dual-parameter feedback adaptive air pressurization breathing assist system according to claim 1, characterized in that: The semi-open partitioned mouth and nose interface (30) includes a flexible flow guide skirt (31) close to the mouth and nose and a low-resistance air guide hood (32) located outside it. Controlled leakage is allowed between the flexible flow guide skirt (31) and the user's face. Multiple partitioned microchannel areas (33) are formed between the low-resistance air guide hood (32) and the flexible flow guide skirt (31). The multiple air supply microchannels (40) and exhaust gas stripping microchannels (50) are respectively arranged in at least two regions of the nasal bridge region (301), nasal ala region (302), preoral region (303) and buccal region (304) to form directional air supply toward the oral and nasal mainstream during the inspiratory phase and selective stripping flow against the high CO2 boundary layer in the oral and nasal region during the expiratory phase.

3. The low-pressure dual-parameter feedback adaptive air pressurization breathing assist system according to claim 1, characterized in that: The parallel compliant energy storage branch array (20) includes at least two micro energy storage units (21) with different flow resistance and compliance. Each micro energy storage unit (21) has a different inflation and deflation time constant so that multiple micro energy storage units (21) can release pulsating airflow in sequence during the same breathing cycle. The micro energy storage unit (21) includes an elastic bladder, a deformable membrane cavity or a compliant gas storage branch, and each micro energy storage unit (21) is provided with at least one of a pre-stage flow limiting component, a post-stage flow limiting component, a unidirectional component or a variable impedance component.

4. The low-pressure dual-parameter feedback adaptive air pressurization breathing assist system according to claim 1, characterized in that: The exhaust gas stripping microchannel (50) forms a CO2 boundary layer directional stripping ring (51) around at least two regions in the subnasal, preoral and bilateral cheek areas. The CO2 boundary layer directional stripping ring (51) preferentially removes the high CO2 boundary layer in front of the mouth and nose during the expiratory phase through negative pressure jet, Venturi suction or jet flow; during the inspiratory phase, it is closed, throttled or reduced in its conduction duty cycle.

5. The low-pressure dual-parameter feedback adaptive air pressurization breathing assist system according to claim 1, characterized in that: The control module (70) includes a respiratory phase locking layer (71), a respiratory effort estimation layer (72), and a pathway benefit reconstruction layer (73). The respiratory phase locking layer (71) identifies the inspiratory start point, inspiratory acceleration, and expiration end point through one or more of the following information: high-frequency micro-pressure waves, flow disturbances, chest movement signals, prelarynx vibration signals, or changes in oral and nasal temperature and humidity. The breathing effort estimation layer (72) generates a breathing effort index by one or more of the following: early inspiratory negative pressure slope, local flow resistance change, chest girdle effort index, or tidal volume estimate. The pathway benefit reconstruction layer (73) dynamically updates the conduction weight, equivalent flow resistance, or opening and closing sequence of each micropath based on the contribution of each micropath to reducing respiratory work, improving effective gas supply during inspiration, reducing CO2 backflow, reducing short-circuit loss, and improving local blockage tolerance in one or more recent respiratory cycles.

6. The low-pressure dual-parameter feedback adaptive air pressurization breathing assist system according to claim 1, characterized in that: The passive failover safety bypass module (80) includes a normally open low-resistance bypass channel (81), a mechanical exhalation one-way valve (8c2), and a power failure default safety position mechanism (83). The normally open low-resistance bypass channel (81) serves as a backup ventilation function when the system is working normally, and becomes a natural breathing pathway when the system loses power or the control fails. The power failure default safety position mechanism (83) is used to automatically return the valves of the gas supply microchannel (40) and the exhaust gas stripping microchannel (50) to a low resistance safety state when the control power is lost.

7. The low-pressure dual-parameter feedback adaptive air pressurization breathing assist system according to any one of claims 1-7, characterized in that: The gas supply module (10) adopts one or more of a micro centrifugal fan, diaphragm pump or micro compressor; The gas supply microchannel (40) and the waste gas stripping microchannel (50) are composed of one or more of the following: low power microvalve, flexible flap, shape memory microbeam, elastic channel, flow limiting orifice and Venturi suction channel; The parameters of local gas composition in the mouth and nose include at least one of CO2 concentration and oxygen concentration.

8. A low-pressure dual-parameter feedback adaptive air pressurization breathing assistance control method based on the system described in any one of claims 1-7, characterized in that, Includes the following steps: Step S1: Control the air supply module (10) to continuously draw in ambient air and provide a reference pressurized airflow to the parallel compliant energy storage branch array (20) for time-sharing energy storage; Step S2: Real-time acquisition of local pressure parameters and local gas composition parameters of the mouth and nose through the dual-parameter feedback detection module (60); Step S3, the control module (70) identifies the breathing phase information based on the collected parameters and calculates the comprehensive benefit value of each air supply microchannel (40) and exhaust gas stripping microchannel (50); Step S4: Based on the identified respiratory phase information and the comprehensive benefit value, dynamically adjust the conduction weight, equivalent flow resistance, or opening and closing sequence of the air supply microchannel (40) and the waste gas stripping microchannel (50) so as to control the release of pulsating airflow in the parallel compliant energy storage branch array (20) during the inspiratory phase to achieve directional air supply to the oral and nasal mainstream lines, and control the waste gas stripping microchannel (50) during the expiratory phase to achieve priority removal of local waste gas.

9. The low-pressure dual-parameter feedback adaptive air pressurization breathing assistance control method according to claim 8, characterized in that: The specific process of releasing the pulsating airflow in the parallel compliant energy storage branch array (20) under the control of the intake phase is as follows: when the intake front is triggered, the branch with a low time constant is released first to cover the intake start stage; the branch with a higher time constant is released later to cover the intake acceleration stage and the subsequent plateau stage. The specific process of dynamically adjusting the conduction weights of the gas supply microchannel (40) and the exhaust gas stripping microchannel (50) is as follows: the conduction priority of each channel is updated online according to the comprehensive benefit value, the channel with high benefit is strengthened, and the channel with low benefit or high risk is suppressed. Among them, blockage, frost, execution error, noise interference and sensing uncertainty are introduced as penalty items into the weight update process.

10. The low-pressure dual-parameter feedback adaptive air pressurization breathing assistance control method according to claim 8, characterized in that, The control method also includes congestion detection and degradation control logic: The control module (70) compares the command opening of each branch with the actual flow, the branch pressure decay slope and the valve position response time in real time; when a suspected condensation blockage or frosting branch is identified, the weight of the branch is reduced in subsequent cycles, and the gas supply and stripping tasks are transferred to redundant branches or bypasses. The control module (70) has multiple preset upper-level strategy modes, including high-altitude mode, sports mode, rest mode, nighttime conservative mode and industrial low-temperature mode. Different modes adjust the weight template of the benefit function so that the system prioritizes different targets in different scenarios.

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