A kind of vest type oxygen generator and oxygen generator control system

Abstract

The present application relates to medical devices and respiratory oxygen supply equipment technical field, disclose a kind of vest type oxygen generator and oxygen generator control system, including vest main body and sequentially fluid communication air inlet module, oxygen generation module, compressor module, oxygen storage bag and control module;Control module is communicated with oxygen mask and is built-in with pressurized impeller;System is configured with deformation sensor, pressure sensor and blood oxygen acquisition module;Main control unit obtains the deformation data on the surface of oxygen storage bag to close-loop regulation the gas production rate of compressor module;According to the airway pressure change data in mask, determine breathing phase, and output pulse airflow through feedforward control pressurized impeller in inspiration phase;Extract peripheral blood oxygen saturation, when break through the set threshold, dynamically calibrate the basic maintenance speed of compressor module.The present application overcomes the defects of pulse oxygen supply hysteresis and open-loop setting, realizes the dynamic self-adaptive matching of bottom oxygen generation equipment gas production end and user terminal physiological consumption end.

Description

Technical Field

[0001] This invention relates to the field of medical devices and respiratory oxygen supply equipment, specifically a vest-type oxygen concentrator and an oxygen concentrator control system. Background Technology

[0002] Portable oxygen concentrators typically employ a pulsed oxygen delivery mode, releasing oxygen transiently during the inhalation phase by detecting the user's breathing movements to improve oxygen utilization and extend the device's battery life. Traditional portable oxygen concentrators usually feature a highly centralized, integrated structure with relatively short and direct airflow output tubing. In contrast, vest-style oxygen concentrators have a significantly different physical architecture: to achieve ergonomic weight distribution and reduce unilateral fatigue, the oxygen generation module, power components, and oxygen storage unit often need to be distributed across multiple areas such as the user's waist, back, and chest. Wearable vest-style oxygen concentrators are limited by these factors in their design. The dispersed wearable layout and weight distribution mean that the oxygen generated by the bottom oxygen-generating unit usually needs to travel through a relatively tortuous and lengthy airway to be temporarily stored in a flexible oxygen storage bag before being delivered to the oxygen mask via external fluid tubing. Under this specific physical structure, when the sensor at the mask end detects an inhalation and triggers oxygen supply, the volume expansion property of the flexible oxygen storage bag itself absorbs some of the transient airflow energy at the beginning of the supply. Combined with the inherent fluid resistance of the long tubing transmission caused by the dispersed layout, this results in a significant physical lag in the output of the terminal pulse airflow, preventing oxygen from arriving on time during the early inhalation phase when the lung's gas exchange efficiency is highest, thus affecting the actual oxygen therapy effect.

[0003] Besides the physical lag at the fluid transport level, existing portable oxygen concentrators generally employ open-loop operating logic based on fixed speeds in their control systems. System operating parameters largely depend on initial settings manually configured by the user, with the device producing oxygen and outputting pulses at a fixed rate during operation. This static control mechanism cannot detect the actual remaining oxygen level inside the storage bag, nor does it provide monitoring and feedback on the body's actual oxygen deficiency. When the user's physical activity increases and respiratory rhythm changes, leading to a surge in physiological oxygen consumption, the original fixed oxygen production rate cannot be increased in time, resulting in insufficient gas supply from the lower gas source and failing to prevent a continuous drop in the user's peripheral blood oxygen levels. Conversely, when the user is in a low-oxygen-consumption state such as at rest, maintaining a fixed power output can lead to excessive oxygen production, causing gas pressure buildup and ineffective energy loss in the system. The current control architecture struggles to achieve dynamic adaptive matching between the hardware's oxygen production end and the physiological consumption end. Summary of the Invention

[0004] To address the shortcomings of existing technologies, this invention provides a vest-style oxygen concentrator and its control system, which solves the problems of physical lag in the pulse oxygen supply response of existing portable oxygen concentrators and the inability of fixed open-loop oxygen production settings to dynamically match the user's real-time physiological oxygen consumption needs.

[0005] To achieve the above objectives, the present invention provides the following technical solution: The first aspect of the present invention provides a vest-type oxygen concentrator, comprising: a vest body, an oxygen inhalation mask, a control module, an oxygen generation module, a weight-bearing waist belt, a compressor module, an oxygen storage bag, an oxygen outlet pipe, an air inlet module, and a nitrogen outlet. The oxygen generating module is located at the lower end of the vest body, and the load-bearing waist belt is located at the lower edge of the oxygen generating module; the air inlet module and the nitrogen outlet are respectively located on the surface of the oxygen generating module; the compressor module is located on the front side of the load-bearing waist belt; the oxygen storage bag and the control module are respectively located on both sides of the chest of the vest body; The output end of the air inlet module is connected to the raw gas input end of the oxygen generating module, and the nitrogen-enriched purge gas output end of the oxygen generating module is connected to the nitrogen outlet. The oxygen generating module is equipped with a membrane separation component, and the oxygen-enriched output end of the oxygen generating module is connected to the input end of the compressor module. The compressor module creates a negative pressure on the permeate side of the membrane separation component through suction. One end of the oxygen outlet pipe is connected to the compressor module, and the other end extends upward so that the compressor module, the oxygen storage bag, the control module, and the oxygen mask are in sequential fluid communication.

[0006] A second aspect of the present invention also provides an oxygen concentrator control system, applied to the vest-type oxygen concentrator described in the first aspect above, comprising a main control unit, and a deformation sensor, a pressure sensor, and a blood oxygen acquisition module all electrically connected to the main control unit; the control module has a built-in pressurizing impeller connected to the main control unit; the deformation sensor is disposed on the surface of the oxygen storage bag, and the pressure sensor is disposed inside the oxygen mask; the blood oxygen acquisition module is worn on the user's peripheral tissue surface; The main control unit is configured to: acquire the deformation data of the oxygen storage bag collected by the deformation sensor to adjust the gas production and delivery rate of the compressor module in a closed loop; determine the breathing phase based on the airway pressure change data acquired by the pressure sensor, and control the pressurizing impeller to output pulse airflow during the inhalation phase through feedforward control; extract the blood oxygen saturation characteristics acquired by the blood oxygen acquisition module, and dynamically calibrate the basic maintenance speed constant of the compressor module when the blood oxygen saturation drops below a set threshold, thereby realizing dynamic adaptive oxygen supply calibration from the physiological terminal to the physical gas source.

[0007] Furthermore, a straight-through inner gas guide tube is provided inside the oxygen storage bag along the main axis of airflow transmission, and an external elastic buffer chamber surrounds the outer perimeter of the straight-through inner gas guide tube; several fluid damping micropores are arrayed on the tube wall of the straight-through inner gas guide tube; the deformation sensor is attached to the maximum displacement area at the center of the external elastic buffer chamber, and the external elastic buffer chamber receives gas through the fluid damping micropores and converts the hydrostatic pressure into physical deformation parameters for the deformation sensor to read; this structure transmits airflow through the central straight-through channel, and the external buffer chamber converts the hydrostatic pressure into the deformation potential energy of the elastic film for gas buffering and storage.

[0008] Furthermore, the total flow cross-sectional area of ​​all the fluid damping micropores is set to 10% to 20% of the cross-sectional area of ​​the straight-through air guide inner tube; when the pressure impeller inside the control module accelerates during the intake phase, it forms an active suction negative pressure at its fluid input end, which pulls the oxygen-rich gas in the external elastic buffer chamber to penetrate the fluid damping micropores in the reverse direction, and superimposes with the oxygen flow pushed upward in the straight-through air guide inner tube to form the pulse airflow; this structure generates a fluid throttling effect in the radial direction of the air guide inner tube, and reasonably maintains the flow distribution between the main shaft airflow delivery and the lateral air volume accumulation.

[0009] Furthermore, when adjusting the gas production and delivery rate of the compressor module, the main control unit extracts the current deformation data and calculates the dimensionless filling parameter by combining it with the pre-calibrated deformation constant of the venting state and the deformation constant of the expansion upper limit state. The main control unit sums the preset static baseline maintenance speed constant with the proportional adjustment component of the filling deviation and the differential feedforward adjustment component of the instantaneous change rate of filling to obtain the target speed command and outputs it to the compressor module to directly change the negative pressure and transmembrane pressure difference on the permeate side of the membrane separation component. At the same time, the main control unit performs amplitude saturation limitation on the target speed command based on the rated maximum speed of the compressor module. The introduction of the differential term can reflect the gas consumption change trend in advance and compensate for the physical lag of long-distance fluid transmission.

[0010] Furthermore, after acquiring the raw pressure data collected by the pressure sensor, the main control unit performs a moving average calculation on the raw pressure data within a set long-period time window to extract the DC bias reference pressure component. The raw pressure data and the DC bias reference pressure component are then subtracted to obtain the instantaneous relative pressure value after eliminating baseline drift. The main control unit simultaneously calculates the time derivative of the instantaneous relative pressure value as a pressure change rate parameter. This step effectively eliminates baseline drift interference caused by mask displacement or natural fluctuations in external air pressure.

[0011] Furthermore, the main control unit determines the breathing phase based on the following logic: when the instantaneous relative pressure value falls below a preset inspiratory trigger negative pressure threshold and the pressure change rate parameter is negative, it determines that the breathing phase has begun; when the instantaneous relative pressure value exceeds a preset expiratory trigger positive pressure threshold and the pressure change rate parameter is positive, it determines that the breathing phase has begun; when the instantaneous relative pressure value is within the dead zone between the inspiratory trigger negative pressure threshold and the expiratory trigger positive pressure threshold, it determines that the breathing phase has begun; the dead zone effectively prevents phase misjudgment caused by weak airflow disturbances.

[0012] Furthermore, the main control unit outputs discretized state function parameters to the control buffer based on the respiratory phase determination result. When the respiratory phase is determined, the state function parameter is assigned an integer value of 1, and the main control unit controls the pressurizing impeller to operate with the calibrated pulse peak value driving parameter. At the same time, the main control unit adds trapezoidal ramp limiting logic to the transition of the pulse width modulation signal output to the pressurizing impeller drive circuit to smoothly approximate the target parameter. When the respiratory phase or the resting phase is determined, the state function parameter is assigned a preset minimum normal quantity coefficient, and the pressurizing impeller runs at a reduced speed according to the coefficient and maintains a set basic micro-positive pressure state inside the terminal pipeline to prevent backflow of exhaled gas. The ramp limiting logic takes into account both the agility of motor start-up and the prevention of transient overcurrent protection shutdown.

[0013] Furthermore, when dynamically calibrating the base maintenance speed constant of the compressor module, the main control unit first performs multi-cycle time-weighted smoothing calculation on the feature sequence acquired by the blood oxygen acquisition module to extract the effective blood oxygen saturation parameter. When it is determined that the effective blood oxygen saturation parameter falls below the set physiological safety threshold, the main control unit calculates the difference between the physiological safety threshold and the effective blood oxygen saturation parameter, and combines it with the preset blood oxygen compensation gain coefficient and the initial base speed to dynamically reconstruct and calculate a new base maintenance speed variable. The base maintenance speed variable replaces the static base maintenance speed constant during the closed-loop operation of the system in real time. The smoothing calculation effectively filters out signal artifact interference caused by physical motion, realizing the dynamic self-calibration of the compressor's base speed.

[0014] Furthermore, the main control unit is configured with a one-way compensation cutoff judgment function. When the extracted effective blood oxygen saturation parameter is determined to be greater than or equal to the physiological safety threshold, the algebraic subtraction calculation result of the difference is forced to zero. This is to prevent the compressor module command speed after reconstruction from being lower than the basic operating limit of the gas path due to the negative deviation calculation when the effective blood oxygen saturation parameter recovers overshoot.

[0015] Furthermore, the air intake module blows ambient air into the material side of the membrane separation component inside the oxygen generation module, establishing a slight positive pressure on the material side to purge the nitrogen enriched on the membrane surface along a specific flow path to the nitrogen outlet for continuous discharge. The nitrogen outlet is equipped with a microporous sound-absorbing filter material; the microporous sound-absorbing filter material is used to attenuate the aerodynamic noise generated when the exhaust gas is discharged and to prevent external particulate matter from reversibly intruding into the air path component.

[0016] This invention provides a vest-type oxygen concentrator and an oxygen concentrator control system, which have the following beneficial effects: 1. This invention features a composite fluid structure consisting of a straight-through inner air-guiding pipe with fluid-damping micropores and an external elastic buffer chamber inside the oxygen storage bag. A pressure impeller at the air supply terminal provides feedforward control. When the pressure impeller accelerates according to the intake phase, the active suction negative pressure generated at its input end pulls the pre-accumulated oxygen-rich gas in the buffer chamber through the damping micropores in the opposite direction, directly superimposing with the upward-flowing oxygen gas from the bottom layer. This design reduces the absorption loss of transient airflow energy by the flexible airbag, overcomes the physical lag in long pipeline fluid transmission, and greatly improves the response speed and instantaneous air supply of the terminal pulse airflow.

[0017] 2. This invention employs a gas supply regulation mechanism that coordinates deformation state and airway pressure difference. The main control unit uses deformation sensor data to calculate the fullness parameter to adjust the gas production speed of the compressor module in a closed loop, thereby adjusting the transmembrane pressure difference to change the oxygen production rate. Combined with the true pressure difference obtained by the pressure sensor after eliminating baseline drift, the breathing phase is accurately determined. The gas supply regulation mechanism ensures that the system actively outputs oxygen supply flow during the inspiratory phase and maintains a slight positive pressure on the pipeline base according to the minimum normal volume coefficient during the expiratory or resting phase to prevent backflow of exhaled waste gas. This allows the oxygen production rate of the bottom gas source to dynamically follow the user's terminal oxygen consumption rhythm, avoiding equipment load redundancy or insufficient oxygen storage caused by fixed parameter open-loop operation.

[0018] 3. This invention introduces a dynamic calibration mechanism for oxygen supply benchmark based on blood oxygen saturation characteristics. When the effective blood oxygen saturation obtained by the blood oxygen acquisition module falls below the physiological safety threshold, the main control unit directly reconstructs the basic maintenance speed constant of the underlying compressor module by calculating the deviation. The dynamic calibration mechanism for oxygen supply benchmark makes up for the lack of perception of the body's true hypoxia state by purely physical pneumatic parameter feedback. It directly and adaptively raises the basic gas production baseline of the gas source based on the user's physiological metabolic deficit. Combined with a one-way compensation cutoff judgment function to prevent command abnormalities caused by overshoot, it fully ensures the safety and reliability of clinical oxygen supply for users under different activity states. Attached Figure Description

[0019] Figure 1 This is a perspective view of the present invention; Figure 2 This is a schematic diagram of the control method for the vest-type oxygen concentrator of the present invention; Figure 3 This is a schematic diagram of the air intake and oxygen generation separation gas path topology of the present invention; Figure 4 This is a schematic diagram of the bottom pressurization and fluid delivery air passage structure of the present invention; Figure 5 This is a timing diagram of the gas generation closed-loop control logic based on deformation state according to the present invention; Figure 6 This is a schematic diagram of the airway micropressure sensing and respiratory rhythm extraction algorithm of the present invention; Figure 7 This is a schematic diagram of the pulse direct oxygen supply control principle based on respiratory feedforward of the present invention; Figure 8 This is a schematic diagram illustrating the dynamic calibration principle of the gas production benchmark based on blood oxygen feedback in this invention. Figure 9 This is a schematic diagram of dynamic tracking of blood oxygen saturation during exercise testing according to the present invention; Figure 10 This is a schematic diagram of the multi-level sensor coupling and cooperative control waveform of the present invention; Figure 11 This is a schematic diagram of the instantaneous relative gauge pressure fluctuation in the terminal respiratory airway of the present invention; Figure 12 This is a schematic diagram of the pressure impeller feedforward pulse drive command of the present invention.

[0020] The components include: 1. Vest body; 2. Oxygen mask; 3. Control module; 4. Oxygen generation module; 5. Weight-bearing waist belt; 6. Compressor module; 7. Oxygen storage bag; 8. Oxygen outlet pipe; 9. Air inlet module; and 10. Nitrogen outlet. Detailed Implementation

[0021] The technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0022] See attached document Figure 1 , Figure 1 This is a schematic diagram of the overall structure of a vest-type oxygen concentrator according to an embodiment of the present invention. The present invention provides a vest-type oxygen concentrator, including: a vest body 1, an oxygen mask 2, a control module 3, an oxygen generation module 4, a weight-bearing waist belt 5, a compressor module 6, an oxygen storage bag 7, an oxygen outlet pipe 8, an air inlet module 9, and a nitrogen outlet 10.

[0023] The oxygen generating module 4 is located at the lower end of the vest body 1, and the load-bearing waist belt 5 is located at the lower edge of the oxygen generating module 4; the air inlet module 9 and the nitrogen outlet 10 are respectively located on the surface of the oxygen generating module 4; the compressor module 6 is located on the front side of the load-bearing waist belt 5; the oxygen storage bag 7 and the control module 3 are respectively located on the front chest sides of the vest body 1.

[0024] The output end of the air inlet module 9 is connected to the raw material gas input end of the oxygen generating module 4. The nitrogen-enriched purge gas output end of the oxygen generating module 4 is connected to the nitrogen outlet 10. The oxygen-enriched output end of the oxygen generating module 4 is connected to the input end of the compressor module 6. The compressor module 6 forms a negative pressure on the permeation side through suction. One end of the oxygen outlet pipe 8 is connected to the compressor module 6, and the other end extends upward so that the compressor module 6, the oxygen storage bag 7, the control module 3 and the oxygen mask 2 are fluidly connected in sequence.

[0025] The present invention also provides an oxygen concentrator control system, applied to the above-mentioned vest-type oxygen concentrator, which includes a main control unit, and a deformation sensor, a pressure sensor and a blood oxygen acquisition module, all electrically connected to the main control unit; the control module 3 has a built-in pressurizing impeller connected to the main control unit; the deformation sensor is disposed on the surface of the oxygen storage bag 7; the pressure sensor is disposed inside the oxygen inhalation mask 2; and the blood oxygen acquisition module is worn on the surface of the user's peripheral tissues.

[0026] The deformation sensor, pressure sensor, and blood oxygen acquisition module transmit the collected physiological and physical signals to the signal input terminal of the main control unit, respectively. The signal output terminal of the main control unit is electrically connected to the control terminal of the air intake module 9, the compressor module 6, and the pressurizing impeller, respectively, thereby regulating the gas production and delivery rate and controlling the feedforward pulse oxygen supply in a closed loop during operation.

[0027] See attached document Figure 2 , Figure 2 This is a flowchart of a vest-type oxygen concentrator control method according to an embodiment of the present invention. The present invention provides a vest-type oxygen concentrator control method, comprising the following steps: The main control unit controls the operation of the air intake module 9. Air enters the oxygen generation module 4 through the air intake module 9 for gas separation. The nitrogen formed by separation is discharged from the equipment through the nitrogen outlet 10, and the oxygen formed by separation enters the compressor module 6. The main control unit sends control commands to the compressor module 6. After being pressurized by the compressor module 6, the oxygen is transported upward through the oxygen outlet pipe 8 and directly enters the oxygen storage bag 7 for storage. The deformation sensor collects the deformation electrical signal of the oxygen storage bag 7 in real time and transmits it to the main control unit. The main control unit calculates the filling parameter of the oxygen storage bag 7 based on the deformation electrical signal, and outputs a speed adjustment command to the compressor module 6 according to the filling parameter to adjust the oxygen production rate. The pressure sensor collects airway pressure data in real time and transmits it to the main control unit, which then determines the breathing phase based on the airway pressure data. When the inhalation phase is determined, the main control unit outputs an acceleration command to the pressurizing impeller, which draws in and pressurizes the oxygen in the oxygen storage bag 7 and outputs a pulsed airflow to the oxygen mask 2; when the exhalation or resting phase is determined, the main control unit outputs a deceleration command to the pressurizing impeller, which maintains the base speed to maintain a slightly positive pressure state in the flow path. The blood oxygen acquisition module acquires the user's blood oxygen characteristic data in real time and transmits it to the main control unit. When the main control unit determines that the extracted effective blood oxygen saturation parameter falls below the physiological safety threshold, the main control unit dynamically reconstructs the basic maintenance speed constant of the underlying compressor module 6 in combination with the blood oxygen deviation, so as to realize dynamic adaptive oxygen supply calibration from the physiological terminal to the physical gas source.

[0028] The following will provide a detailed explanation of each step in the above workflow and its specific control logic. (Refer to the appendix.) Figure 3 , Figure 3 This is a topology diagram of the air intake and oxygen generation separation gas path according to an embodiment of the present invention. The specific control process of air intake and gas separation during the equipment startup phase includes multiple steps. In this embodiment, the main control unit generates a startup control signal and sends it to the air intake module 9 via the internal control bus. The air intake module 9 is equipped with a motor drive circuit and two sets of parallel-connected micro DC fans. The motor drive circuit integrates a current sampling resistor and a matching signal conditioning feedback link in series. The motor drive circuit receives the startup control signal and converts it into a drive current input to the micro DC fan. As a preferred method, the startup control signal adopts a pulse width modulation signal. The motor drive circuit adjusts the output equivalent drive voltage according to the duty cycle parameter of the pulse width modulation signal to achieve precise intervention of the speed of the micro DC fan. At the same time, the main control unit collects the working current data flowing through the micro DC fan in real time through the above-mentioned signal conditioning feedback link. The micro DC fan operates under the action of the drive current and generates a fluid negative pressure environment at the air intake end of the air intake module 9. Under the action of negative pressure, the outside air is drawn into the equipment through the grille outside the air intake module 9 to form a raw material airflow.

[0029] The air inlet module 9 pumps the raw material airflow into the feed-side input end of the oxygen generation module 4. The oxygen generation module 4 contains a gas membrane separation component, which, as a preferred embodiment, adopts a hollow fiber membrane structure. The oxygen generation module 4 uses membrane separation technology, the principle of which is based on the different permeation rates of different gas molecules (such as oxygen and nitrogen) in the membrane material.

[0030] In this embodiment, the compressor module 6 operates, creating a negative pressure environment on the permeate side of the membrane separation assembly through its suction action. Simultaneously, the main control unit controls the air intake module 9 to blow ambient air into the feed side of the membrane separation assembly, establishing a slight positive pressure there. Driven by the transmembrane pressure difference formed by the negative pressure on the permeate side and the positive pressure on the feed side, various gas molecules in the air attempt to penetrate the membrane material. Since oxygen molecules are faster than nitrogen molecules and have a higher permeation rate, a large number of oxygen molecules preferentially penetrate the membrane material, gather on the permeate side to form an oxygen-rich flow, and are continuously extracted by the compressor module 6. Most of the nitrogen molecules with low permeation rates are trapped on the material side. The continuous flow of fresh air provided by the air inlet module 9 on the material side acts as a purging agent, carrying away the high concentration of nitrogen and other impurity gases enriched on the membrane surface along a specific flow path. Finally, they are continuously discharged to the outside of the equipment through the nitrogen outlet 10. To improve the acoustic comfort when wearing the actual equipment, the nitrogen outlet 10 is embedded with microporous sound-absorbing filter material, which is used to attenuate the aerodynamic noise generated when the exhaust gas is discharged and to block external particulate matter from reversibly intruding into the air path components.

[0031] The oxygen-enriched flow from the membrane separation component undergoes initial convergence and pressure stabilization in the gas collection chamber of the oxygen generation module 4. The output end of the gas collection chamber maintains fluid communication with the input end of the downstream compressor module 6. The low-pressure oxygen flow continues to enter the compressor module 6 under the negative pressure traction of the subsequent pipeline, thus completing the initial separation and gas volume storage of the bottom gas path. Throughout the separation cycle, the main control unit monitors the change in the operating current of the air intake module 9 to determine whether there is a mechanical stall phenomenon caused by foreign object inhalation. When the operating current is detected to exceed the preset safety range, the hardware power-off protection mechanism is triggered. In specific engineering implementations, the upper limit of this preset safety range is usually set based on the rated stall current value calibrated by the factory of the micro DC fan. For example, 80% to 90% of the rated stall current value is extracted as the power-off judgment benchmark, thereby avoiding the logic dead zone or false triggering of the protection algorithm in the critical state.

[0032] See attached document Figure 4 , Figure 4 This is a schematic diagram of the bottom pressurization and fluid transport gas path structure according to an embodiment of the present invention. After the device completes the initial gas separation, it needs to perform fluid pressurization and directional transport. After receiving the system start-up status signal, the main control unit outputs the initial drive waveform to the compressor module 6 through the internal pulse width modulation signal port. The compressor module 6 responds to the drive waveform and starts to operate to establish the initial positive pressure environment of the bottom gas path.

[0033] As a preferred approach, compressor module 6 uses a miniature oil-free diaphragm compression assembly. It first provides the core power for the membrane separation process through suction, and at the same time, it compresses the oxygen-enriched gas that permeates through the membrane separation assembly in a volumetric manner. This overcomes the hydrostatic pressure caused by the physical height difference between the waist and chest of the vest body 1 and the frictional resistance generated along the pipeline during fluid transmission. The compressed positive pressure oxygen enters the oxygen outlet pipe 8 under the pressure difference of the pipeline and flows upward.

[0034] The oxygen outlet tube 8 delivers airflow upwards and into the oxygen storage bag 7 located in front of the chest to establish a base pressure. Addressing the potential delay in terminal oxygen supply response caused by the absorption of transient airflow energy during the supply phase of conventional single-chamber elastic airbags, this embodiment employs a composite fluid structure with damping and diversion characteristics. A straight-through inner air guide tube runs through the bag along the main airflow axis. The fluid inlet of this inner air guide tube is sealed to the upper end of the oxygen outlet tube 8. Simultaneously, the outer periphery of this inner air guide tube is covered by an external elastic buffer chamber formed by welding a high-polymer medical elastic film. This composite nested structure gives the oxygen storage bag 7 both a central straight flow channel and a flexible outer energy storage capability. This central straight flow channel provides the necessary hardware architecture support for the lossless transfer of kinetic energy during the subsequent pressurization phase.

[0035] The oxygen flow inside the oxygen storage bag 7 undergoes dynamic and static pressure conversion and adaptive distribution based on the pipeline pressure distribution. Specifically, the inner wall of the aforementioned straight-through gas guide tube is arrayed with several fluid damping micropores according to fluid dynamics distribution rules. This maintains fluid communication between the core main channel of the straight-through gas guide tube and the sealed inner cavity of the external elastic buffer chamber. To ensure the effectiveness of the damping and diversion mechanism, the total flow cross-sectional area of ​​all fluid damping micropores is typically set between 10% and 20% of the cross-sectional area of ​​the straight-through gas guide tube to form a reasonable fluid throttling effect. When the gentle oxygen flow continuously pumped in by the compressor module 6 flows through the straight-through gas guide tube, since the distal pipeline has not yet formed an active negative pressure suction, The effect causes the static pressure of the fluid inside the pipe to gradually increase. Under the action of this static pressure, the oxygen flow overcomes the local aerodynamic resistance formed by the fluid damping micropores and seeps into the periphery, gradually filling the outer elastic buffer chamber. As the volume of gas inside continues to increase, the outer wall of the outer elastic buffer chamber undergoes physical stretching and expansion, converting the static fluid pressure into the elastic potential energy of the film to complete the buffering and energy storage of the oxygen at the bottom. For the power conversion principle of the eccentric wheel mechanism inside the compressor module 6 and the test specifications of the elastic modulus of the polymer film material, those skilled in the art can refer to the existing micro pneumatic component manual for conventional engineering configuration. Its mechanical transmission and basic mechanical mechanism are well known technologies in this field and will not be elaborated here.

[0036] See attached document Figure 5 , Figure 5This is a timing diagram of a gas production closed-loop control logic based on deformation state according to an embodiment of the present invention. During continuous operation, the equipment needs to dynamically adjust the gas production rate of the bottom gas path according to the oxygen storage state to maintain the gas supply and demand balance of the system. In this embodiment, the deformation sensor is attached to the maximum displacement area of ​​the center of the elastic buffer chamber outside the oxygen storage bag 7. The deformation sensor undergoes synchronous mechanical stretching and compression deformation along with the expansion and contraction of the buffer chamber. As a preferred embodiment, the deformation sensor is made of flexible piezoresistive thin film material, and its internal resistance value changes regularly with the increase of mechanical stretching. This resistance change is transmitted via a signal on the hardware board. The conditioning circuit converts the signal into a continuously changing analog voltage signal. The main control unit integrates an analog-to-digital converter to discretize and sample the analog voltage signal. To avoid interference from transient mechanical vibrations caused by the wearer's body movements, the main control unit uses a moving average filtering algorithm to smooth the sampling sequence before extracting the effective signal to obtain a stable deformable electrical signal. For the Wheatstone bridge architecture in the signal conditioning circuit and the code implementation of the conventional digital filtering program, those skilled in the art can refer to existing electronic circuit design manuals for configuration. The conventional electrical conversion and signal processing principles are well-known technologies in this field and will not be elaborated here.

[0037] After acquiring a stable deformation electrical signal, the system enters the oxygen storage status assessment stage. The main control unit extracts the filtered deformation electrical signal and uses a linear normalized mathematical model to calculate the current fullness parameter of the oxygen storage bag 7. This fullness parameter is used to dimensionlessly characterize the current gas storage reserve status of the oxygen storage bag 7. The specific normalized mapping formula is expressed as follows: ; In the formula; For continuous operation, it is a time variable; The main control unit in time variable The dimensionless fullness parameter calculated at each time step; The effective deformable electrical signal extracted by the analog-to-digital converter at the current moment; The voltage constant recorded by the system when the oxygen storage bag reaches the preset safe expansion limit; The voltage constants recorded by the system when the gas inside the oxygen storage bag is emptied and deflated are the two calibration voltage constants mentioned above. The deformation voltage calibration is automatically performed by the system during the equipment's factory initialization self-test program and stored in the non-volatile memory of the main control unit to ensure the benchmark accuracy of the condition assessment model.

[0038] Based on the quantified fullness parameters, the system immediately initiates adaptive closed-loop regulation of the underlying gas production. The main control unit introduces a closed-loop control algorithm to calculate the output speed of compressor module 6, thereby dynamically compensating for the storage gap caused by terminal oxygen consumption. Due to the inherent physical delay in gas compression and long-distance pipeline transmission, relying solely on the current storage deviation often causes a lag in gas pressure transmission. Therefore, this closed-loop control algorithm integrates proportional and differential terms to balance the steady-state error correction and dynamic oxygen consumption trend response of the system. The specific formula for calculating the target speed of compressor module 6 is as follows: ; In the formula; For continuous operation, it is a time variable; For the system in time variable The speed command to be calculated and sent to the compressor module is calculated in real time. The baseline maintenance speed constant is set for when the system is in a state of supply and demand balance. This is the proportional gain coefficient; It is a dimensionless abundance parameter; The differential gain coefficient is used. It should be specifically noted that in the membrane separation technology of this embodiment, the command speed of the compressor module 6 is adjusted. Its physical essence is to directly change the negative pressure on the permeate side of the membrane separation module, thereby adjusting the transmembrane pressure difference of the entire module. Since the oxygen permeation flux is positively correlated with the transmembrane pressure difference, the main control unit can effectively and directly control the oxygen generation rate by adjusting the compressor speed; the derivative terms included in the formula... To characterize the instantaneous rate of change of the filling parameter, the system uses this derivative term to capture the user's oxygen consumption trend and applies feedforward control to pre-increase the oxygen production rate to counteract the physical hysteresis effect. For the determination of the values ​​of the proportional gain coefficient and the derivative gain coefficient, technicians can usually use the trial-and-error method based on engineering experience or the Ziegler-Nichols rule to tune the parameters, and both are taken as positive real numbers. In order to prevent the derivative term from generating command values ​​that exceed the physical limits of the compressor module 6 when the filling parameter undergoes high-frequency abrupt changes, the main control unit will perform amplitude saturation limitation on the calculated command speed based on the rated maximum speed of the compressor module 6 before outputting the drive waveform. The main control unit outputs the drive waveform with the corresponding duty cycle to the compressor module 6 based on the command speed after final amplitude limitation to complete the adaptive adjustment mechanism of the underlying gas production link.

[0039] See attached document Figure 6 , Figure 6This is a flowchart of an airway micro-pressure sensing and respiratory rhythm extraction algorithm according to an embodiment of the present invention. Before performing pulse oxygen supply, the device needs to obtain the real respiratory rhythm characteristics of the user terminal. In this embodiment, the pressure sensor is fixedly installed inside the oxygen mask 2 near the opening of the mouth and nose respiratory tract. The pressure sensor adopts a microelectromechanical system differential pressure sensing chip structure. One side of its pressure sensing end face is connected to the microenvironment inside the oxygen mask 2, and the other side is connected to the external atmospheric environment to obtain the real relative gauge pressure inside the airway relative to the external atmosphere. The pressure sensor continuously collects the physical quantity of airway pressure difference at a set sampling frequency and converts it into an analog electrical signal. The main control unit quantizes and reads the analog electrical signal through the built-in analog-to-digital conversion channel to construct a time-series pressure fluctuation curve.

[0040] Considering the displacement and natural fluctuations in atmospheric pressure during actual wear of the oxygen mask 2, the extracted time-series pressure fluctuation curve often exhibits baseline drift, leading to distortion of the reference for subsequent phase determination. To prevent baseline drift from interfering with the subsequent phase determination mechanism, the main control unit performs a dynamic baseline calibration procedure on the pressure time-series data before feature point extraction. Specifically, the calibration mechanism involves the main control unit performing a moving average calculation on the pressure sampling data within a set long-period time window to extract the current DC bias reference pressure component. In actual engineering configurations, this long-period time window is typically set to three to five typical respiratory cycles, approximately ten to fifteen seconds, to ensure that low-frequency non-respiratory fluctuations are filtered out while retaining an effective baseline. Subsequently, the system calculates the true instantaneous relative pressure value based on the deviation subtraction logic. The mathematical expression for this value conversion logic is: ; In the formula; For continuous operation, it is a time variable; The main control unit in time variable The instantaneous relative pressure value after eliminating baseline drift, calculated at each moment; This refers to the original table pressure data extracted from the analog-to-digital conversion channel at the current moment. The DC bias reference pressure component is extracted by the system through moving average calculation. For the hardware interface protocol of the microelectromechanical system sensor chip and the specific code implementation of the moving average algorithm, those skilled in the art can refer to existing electronic circuit design manuals for configuration. The conventional signal extraction and data cleaning principles are well-known technologies in this field and will not be elaborated here.

[0041] Based on the instantaneous relative pressure value after cleaning, the system executes phase feature recognition logic to accurately determine the current breathing state and perform discretization transformation. The main control unit synchronously calculates the time derivative of the instantaneous relative pressure value, i.e., the pressure change rate. When the instantaneous relative pressure value falls below the preset inspiratory trigger negative pressure threshold and the pressure change rate is in the negative range, the main control unit determines that the system enters the inspiratory phase and maintains this inspiratory phase determination state until the instantaneous relative pressure value rises back to the dead zone determination zone. Similarly, when the instantaneous relative pressure value rises above the preset expiratory trigger positive pressure threshold and the pressure change rate is in the positive range, the main control unit determines that the system enters the expiratory phase and maintains this expiratory phase determination state until the instantaneous relative pressure value falls back to the dead zone determination zone. To prevent frequent false triggers caused by weak airflow disturbances, the main control unit sets a dead zone determination zone between the inspiratory trigger negative pressure threshold and the expiratory trigger positive pressure threshold. The state is categorized as the resting phase by the system. As a preferred method, in the normal adult breathing mode, the above-mentioned inspiratory trigger negative pressure threshold is usually set between -1 and -3 cmH2O, and the above-mentioned expiratory trigger positive pressure threshold is usually set between 0.5 and 1 cmH2O. This parameter setting method can cover the breathing resistance characteristics of most people. The main control unit outputs the respiratory phase discretization state function to the control buffer for subsequent coordinated regulation based on the above logical judgment result. When it is determined to be the inspiratory phase, the respiratory phase discretization state function is assigned the integer value 1. When it is determined to be the expiratory phase or the resting phase, the respiratory phase discretization state function is assigned the preset minimum normal quantity coefficient. The value range of the minimum normal quantity coefficient is usually set to 0.1 to 0.2. It is mainly used to maintain the basic micro-positive pressure output command of the system during the expiratory phase and avoid the logical break of the speed command returning to zero in the subsequent control module.

[0042] See attached document Figure 7 , Figure 7This is a schematic diagram of a pulse direct-flow oxygen supply control principle based on respiratory feedforward according to an embodiment of the present invention. After completing respiratory phase recognition, the device needs to adjust the terminal airflow power element in real time to achieve precise targeted delivery of airflow. In this embodiment, the main control unit reads the respiratory phase discretization state function calculated by the previous stage in real time. When it is determined that the respiratory phase discretization state function at the current moment is assigned an integer value of 1, the system confirms that it is in the inspiratory phase. The main control unit issues a full-speed pulse acceleration command to the pressurizing impeller set inside the control module 3. As a preferred method, the pressurizing impeller is constructed with a brushless DC micro turbine fan with low rotational inertia to ensure the dynamic response characteristics to electrical signals. The full-speed pulse acceleration command is a high-level pulse width modulation signal with a duty cycle between 80% and 100%. After receiving the signal, the pressurizing impeller rapidly climbs to the peak operating speed within a time window of 50 to 100 milliseconds. Under the action of this high speed, the pressurizing impeller accelerates to the peak operating speed. The impeller creates a negative pressure at its fluid input end, i.e., the outlet of the straight-through air guide tube of the oxygen storage bag 7. The oxygen-enriched gas accumulated in the elastic buffer chamber of the oxygen storage bag 7 in the early stage is drawn back through the fluid damping micro-holes under the pull of this negative pressure difference and flows into the core main channel of the straight-through air guide tube. It merges and superimposes with the oxygen pushed upward synchronously by the bottom compressor module 6 to form a pulse airflow with a large instantaneous flow rate. This pulse airflow is directly injected into the oxygen mask 2 through the terminal pipe connecting the fluid output end of the control module 3 and the oxygen mask 2 to fill the peak flow rate demand of the wearer at the beginning of inhalation. Considering that the sudden change of the pure square wave command will induce the transient overcurrent protection of the brushless drive circuit and cause the hardware to crash, in the actual engineering implementation, the main control unit will add a trapezoidal ramp limiting algorithm along the transition of the pulse width modulation signal to make the drive command smoothly approach the target duty cycle within a set number of milliseconds, thereby taking into account both the agility of motor start-up and the electrical safety of the hardware.

[0043] When the inhalation action ends and the exhalation or resting cycle begins, the system needs to synchronously change the fluid control strategy to avoid oxygen waste and airflow conflict. When the main control unit detects that the respiratory phase discretization state function drops from an integer to the preset minimum normal coefficient, it determines that the system is in the exhalation or resting phase. At this time, the main control unit outputs a deceleration command to the pressurizing impeller according to the minimum normal coefficient. The pressurizing impeller leaves the peak speed and maintains operation in a lower base speed range according to the coefficient. In actual system configuration, this base speed is usually set between 10% and 20% of the rated maximum speed of the pressurizing impeller. This non-complete shutdown deceleration control mechanism can continuously maintain a basic micro-positive pressure state of 0.5 to 1 cm water column inside the terminal pipeline. This micro-positive pressure barrier can not only prevent the warm and humid exhaust gas rich in carbon dioxide exhaled by the user from flowing back into the oxygen pipeline and causing condensation and moisture on the sensing element, but also maintain the low-speed rotation of the impeller to counteract the inherent mechanical static friction resistance when the rotor is stationary. This allows the system to store initial kinetic energy for the transient speed increase of the next inhalation trigger cycle and shorten the physical response time of the pulse airflow.

[0044] The aforementioned feedforward control process based on state functions achieves direct signal-to-power conversion through a linear drive mapping algorithm. The specific formula for calculating the duty cycle of the terminal drive waveform of the pressurized impeller by the main control unit is as follows: ; In the formula: For continuous operation, it is a time variable; The main control unit in time variable The instantaneous pulse width modulation duty cycle parameters are calculated and output to the pressurized impeller drive circuit at all times. The pulse peak value driving duty cycle constant is entered for system calibration; The current breathing phase discretization state function is input to the previous algorithm. The system uses this single-step mapping mechanism, which directly uses the discrete state as a proportional multiplier, to remove the computational delay introduced by the complex closed-loop algorithm in the transient response process. For the electronic speed control drive circuit topology of the brushless DC motor and the underlying register hardware configuration method for pulse width modulation signal generation, those skilled in the art can refer to the existing micro motor control system design specifications for conventional arrangement. Its basic electrical drive and logic generation mechanism are well-known technologies in this field and will not be elaborated here.

[0045] See attached document Figure 8 , Figure 8This is a schematic diagram of the dynamic calibration principle of gas production benchmark based on blood oxygen feedback according to an embodiment of the present invention. Manual intervention based on the underlying closed-loop gas production and terminal pulse oxygen supply often has a certain physiological lag, thus requiring the introduction of actual vital signs parameters for macroscopic supply and demand balance calibration. In this embodiment, the blood oxygen acquisition module is worn as a detachable communication accessory in areas rich in microvessels, such as the fingertips or earlobes of the user. The blood oxygen acquisition module integrates infrared and red dual-wavelength light-emitting diodes and a photodetector. It acquires the photoplethysmography (PPG) signal of peripheral tissue through photoelectric transmission or reflection. This signal is converted into a voltage characteristic sequence characterizing changes in blood absorbance after transimpedance amplification and bandpass filtering by the internal analog front-end circuit. The main control unit continuously reads this characteristic sequence through the peripheral communication bus and calculates the current instantaneous blood oxygen saturation value using Beer-Lambert's law. For the hardware optical path arrangement of the photoelectric blood oxygen sensor and the basic digital calculation program of the PPG, those skilled in the art can refer to the existing conventional medical monitoring equipment design specifications for configuration. The basic optical detection and physiological calculation mechanism are well-known technologies in the field and will not be elaborated here.

[0046] Considering that the mechanical displacement generated by the wearer during daily walking or limb flexion and extension activities can introduce motion artifacts into the photoelectric signal, causing abnormal jumps in instantaneous blood oxygen saturation data, in order to reduce the probability of high-frequency fluctuations in air volume control commands caused by such non-physiological signal artifacts, the main control unit performs a multi-cycle time-weighted smoothing algorithm on the original time sequence before formally connecting the physiological data to the core control loop. Within a set long-cycle time window, the main control unit performs cumulative summation and averaging calculations on the instantaneous blood oxygen saturation values ​​to extract a relatively stable effective blood oxygen saturation parameter. As a preferred method, the time span of the aforementioned long-cycle time window is usually set between ten and twenty seconds to fully filter out brief physical motion interference and retain the body's true gradual trend of blood oxygen change. Subsequently, the main control unit compares the effective blood oxygen saturation parameter with the system's preset physiological safety threshold in real time to determine whether it is necessary to trigger the macro-adjustment mechanism of the underlying air source.

[0047] When the effective blood oxygen saturation parameter falls below the physiological safety threshold, the system determines that the current baseline oxygen supply line can no longer meet the wearer's actual metabolic needs and initiates a dynamic calibration procedure. The main control unit dynamically reconstructs the baseline maintenance speed constant of the underlying compressor module 6 based on the extracted blood oxygen deviation. The mathematical expression for this baseline dynamic reconstruction control logic is as follows: ; In the formula: For continuous operation, it is a time variable; The main control unit in time variable The new base sustaining speed variable is calculated by reconstructing the time step, and this parameter includes a time variable to clearly distinguish it from the static base sustaining speed constant that does not change with time under the aforementioned supply and demand equilibrium state. ; The initial base speed is either the system's factory calibration or recorded by the user in a resting state; Physiological safety thresholds set for the system; The effective blood oxygen saturation parameter extracted by the main control unit at the current moment. The gain coefficient for blood oxygen compensation is typically calibrated by technicians based on empirical matching between the average physiological metabolic time constant of human blood oxygen recovery and the exhaust pressure boost curve of the underlying gas source hardware to prevent closed-loop over-adjustment. It is important to note that conventional closed-loop feedback can produce a negative deviation when the effective blood oxygen saturation parameter recovers and exceeds the target threshold, leading to an abnormal drop in the calculated speed below the baseline maintenance limit. To avoid such algorithm dead zones that endanger the basic operating environment of the gas path, the main control unit is equipped with a unidirectional compensation cutoff judgment function, i.e., when… Greater than or equal to The algebraic subtraction deviation calculation term in the time formula is forced to zero to ensure that the bottom pipeline can smoothly return to the initial basic operating state. At the same time, to ensure the life of pneumatic components, the main control unit has a rigid amplitude limit upper limit, so that the reconstructed basic maintenance speed constant is rigidly constrained within the effective operating speed range of compressor module 6. The system uses the above-mentioned cross-level parametric coupling mechanism to convert the reconstructed new basic maintenance speed variable into a fixed value. Real-time replacement and overwriting of the static basis maintaining constant speed in the aforementioned gas supply and demand closed-loop control algorithm. This enables a dynamic adaptive closed-loop oxygen supply system from physiological terminals to physical gas sources.

[0048] Application Examples: See attached document Figure 9 -Appendix Figure 12 To aid in understanding the actual operating mechanism of the vest-type oxygen concentrator and its multi-level control system of this invention, an application example of daily rehabilitation activities for patients with chronic obstructive pulmonary disease is provided below, along with detailed experimental verification and effect comparison analysis.

[0049] Quiet standby phase (0-5 minutes): The patient wears the vest-style oxygen concentrator of this invention and sits in a chair to rest; at this time, the system determines that the patient is in a resting state; the bottom compressor module runs at the initial base speed to maintain basic oxygen production; the terminal pressure sensor detects the patient's steady, low-frequency breathing rhythm; when the patient inhales, the pressurized impeller outputs a regular pulse airflow; when exhaling, the impeller decelerates to maintain a slight positive pressure; at this time, the patient's blood oxygen saturation is stable at about 95%, and the oxygen storage bag is kept at a safe high level of fullness.

[0050] Exercise trigger phase (5-10 minutes): The patient gets up and begins stepping rehabilitation exercises or climbing stairs. Due to increased metabolic demand, the patient's respiratory rate increases significantly, and the inspiratory negative pressure deepens.

[0051] The pressure sensor immediately detects the high-frequency inhalation action, and the pressurizing impeller then outputs a high-flow-rate pulsed airflow at a high frequency to ensure that the patient receives sufficient oxygen with each inhalation.

[0052] Due to the high-frequency pulse suction, the oxygen inside the oxygen storage bag is rapidly consumed. The deformation sensor detects that the outer wall of the oxygen storage bag is shrunken and the filling parameter drops rapidly. The main control unit immediately outputs an acceleration command to the underlying compressor module based on the decreasing filling trend to increase the oxygen production rate in order to make up for the gas shortage in the oxygen storage bag.

[0053] Macroscopic blood oxygen calibration phase (10-15 minutes): As the exercise load continues, even if the respiratory pulse oxygen supply is kept up normally, the patient's own physiological and pathological limitations still result in insufficient oxygen intake into the blood. The blood oxygen acquisition module detects that the patient's effective blood oxygen saturation slowly drops below the set physiological safety threshold (e.g., set to 92%).

[0054] The main control unit determines that the conventional dynamic closed loop is insufficient and immediately triggers the macroscopic dynamic calibration procedure; based on the current blood oxygen drop deviation, the system significantly increases the base maintenance speed constant of the compressor module; this means that the underlying physical gas source is forcibly raised to a higher production capacity baseline.

[0055] With the support of a higher basic oxygen production capacity, the gas supply pressure and single pulse output volume in the oxygen storage bag are both macroscopically improved; around the 12th minute of exercise, the patient's blood oxygen saturation stops falling and gradually rises to a safe level of over 94%.

[0056] Recovery to a stable phase (after 15 minutes): The patient stopped exercising and sat down to rest; the respiratory rate slowed down and the blood oxygen saturation stabilized at 96%; the main control unit detected that the blood oxygen was far above the threshold, and then cut off the macro gain compensation, gradually reducing the compressor speed back to the initial base state, and the system returned to the energy-saving quiet standby mode.

[0057] Experimental verification and effect comparison To verify the technical effect of the present invention, a vest oxygen concentrator with conventional constant flow oxygen supply function was selected as the control group, and the system of the present invention with pulse oxygen supply + dynamic blood oxygen calibration dual closed loop was selected as the experimental group; a standard 6-minute walk test was conducted on 5 patients with mild to moderate hypoxia for comparison.

[0058] Comparison of blood oxygen saturation maintenance effects: Control group (constant flow oxygen supply): In the first 3 minutes of walking, the patient's blood oxygen level slowly decreased from 95%. Between the 4th and 6th minutes, due to the sharp increase in exercise oxygen consumption and the fixed oxygen supply, the blood oxygen saturation dropped sharply to about 88%, resulting in obvious exercise hypoxemia.

[0059] Experimental group (invention): After the patient started walking, as the system detected a decrease in oxygen saturation and a drop in blood oxygen below 92%, the system adaptively increased the gas output and pulse volume. During the entire 6-minute walking period, the lowest blood oxygen saturation of the patients in the experimental group was successfully maintained above 91.5%, and then quickly rose to 93%, preventing the risk of deep hypoxia.

[0060] Terminal airway comfort and backflow prevention comparison: Control group: When the patient exhales, the constant flow oxygen supply continues to spray, which increases the patient's expiratory resistance and causes a significant feeling of stuffiness and carbon dioxide retention inside the mask.

[0061] Experimental group (this invention): The pressure sensor accurately determines the exhalation phase, and the impeller is reduced to the base speed to maintain only a slight positive pressure; the patient reported that the exhalation was extremely smooth; at the same time, the slight positive pressure prevents the warm and humid waste gas exhaled by the patient from flowing back into the oxygen outlet tube. The equipment was disassembled and inspected and found that there was no condensation inside the oxygen outlet tube of the experimental group.

[0062] Comparison of oxygen utilization rate and system range: Control group: Ignoring the respiratory phase, continuous gas production and exhalation occurred, with approximately 60% of the oxygen being wasted into the atmosphere during the exhalation phase, resulting in a battery life of only 2.5 hours at full load.

[0063] Experimental group (this invention): Through precise targeted delivery of oxygen by inhalation and oxygen storage by exhalation, the oxygen utilization rate is increased to over 90%; the bottom compressor can dynamically go into hibernation or reduce speed according to the oxygen storage bag status, and the measured battery life is increased to 4.2 hours, greatly enhancing the practicality of portable wearables.

[0064] Although embodiments of the invention have been shown and described, it will be understood by those skilled in the art that various changes, modifications, substitutions and alterations can be made to these embodiments without departing from the principles and spirit of the invention, the scope of which is defined by the appended claims and their equivalents.

Claims

1. A vest-type oxygen concentrator, characterized in that, include: Vest body, oxygen mask, control module, oxygen generation module, load-bearing waist belt, compressor module, oxygen storage bag, oxygen outlet pipe, air inlet module and nitrogen outlet; The oxygen generating module is located at the lower end of the vest body, and the load-bearing waist belt is located at the lower edge of the oxygen generating module; the air inlet module and the nitrogen outlet are respectively located on the surface of the oxygen generating module; the compressor module is located on the front side of the load-bearing waist belt; the oxygen storage bag and the control module are respectively located on both sides of the chest of the vest body; The output end of the air inlet module is connected to the raw gas input end of the oxygen generating module, and the nitrogen-enriched purge gas output end of the oxygen generating module is connected to the nitrogen outlet. The oxygen generating module is equipped with a membrane separation component, and the oxygen-enriched output end of the oxygen generating module is connected to the input end of the compressor module. The compressor module creates a negative pressure on the permeate side of the membrane separation component through suction. One end of the oxygen outlet pipe is connected to the compressor module, and the other end extends upward so that the compressor module, the oxygen storage bag, the control module, and the oxygen mask are in sequential fluid communication.

2. An oxygen concentrator control system, applied to the vest-type oxygen concentrator as described in claim 1, characterized in that, It includes a main control unit, and a deformation sensor, a pressure sensor, and a blood oxygen acquisition module, all electrically connected to the main control unit; the control module has a built-in pressurizing impeller connected to the main control unit; the deformation sensor is disposed on the surface of the oxygen storage bag, and the pressure sensor is disposed inside the oxygen mask; the blood oxygen acquisition module is worn on the user's peripheral tissue surface; The main control unit is configured to: acquire the deformation data of the oxygen storage bag collected by the deformation sensor to adjust the gas production and delivery rate of the compressor module in a closed loop; determine the breathing phase based on the airway pressure change data acquired by the pressure sensor, and control the pressurizing impeller to output pulse airflow during the inhalation phase through feedforward control; The blood oxygen saturation characteristics obtained by the blood oxygen acquisition module are extracted, and the basic maintenance speed constant of the compressor module is dynamically calibrated when the blood oxygen saturation drops below a set threshold, thereby realizing dynamic adaptive oxygen supply calibration from the physiological terminal to the physical gas source.

3. The oxygen generator control system as described in claim 2, characterized in that, The oxygen storage bag has a straight-through gas guide tube running through it along the main airflow transmission axis. The outer periphery of the straight-through gas guide tube is covered by an external elastic buffer chamber. Several fluid damping micropores are arrayed on the tube wall of the straight-through gas guide tube. The deformation sensor is attached to the maximum displacement area at the center of the external elastic buffer chamber. The external elastic buffer chamber receives gas through the fluid damping micropores and converts the hydrostatic pressure of the fluid into physical deformation parameters for the deformation sensor to read.

4. The oxygen generator control system as described in claim 3, characterized in that, The total flow cross-sectional area of ​​all the fluid damping micropores is set to 10% to 20% of the cross-sectional area of ​​the straight-through air guide inner tube; when the pressure impeller inside the control module accelerates during the intake phase, it forms a fluid active suction negative pressure at its fluid input end, which pulls the oxygen-rich gas in the external elastic buffer chamber to penetrate the fluid damping micropores in the opposite direction, and superimposes with the oxygen flow pushed upward in the straight-through air guide inner tube to form the pulse airflow.

5. The oxygen generator control system as described in claim 2, characterized in that, When adjusting the gas delivery rate of the compressor module, the main control unit extracts the current deformation data and calculates the dimensionless filling parameter by combining it with the pre-calibrated deformation constant of the venting state and the deformation constant of the expansion upper limit state. The main control unit sums the preset static baseline maintenance speed constant with the proportional adjustment component of the filling deviation and the differential feedforward adjustment component of the instantaneous change rate of filling to obtain the target speed command and outputs it to the compressor module to directly change the negative pressure and transmembrane pressure difference on the permeate side of the membrane separation component. At the same time, the main control unit performs amplitude saturation limitation on the target speed command based on the rated maximum speed of the compressor module.

6. The oxygen generator control system as described in claim 2, characterized in that, After acquiring the raw pressure data collected by the pressure sensor, the main control unit performs a moving average calculation on the raw pressure data within a set long-period time window to extract the DC bias reference pressure component. The raw pressure data and the DC bias reference pressure component are then subtracted to obtain the instantaneous relative pressure value after eliminating baseline drift. The main control unit simultaneously calculates the time derivative of the instantaneous relative pressure value as the pressure change rate parameter.

7. The oxygen generator control system as described in claim 6, characterized in that, The main control unit determines the breathing phase based on the following logic: when the instantaneous relative pressure value falls below a preset inspiratory trigger negative pressure threshold and the pressure change rate parameter is negative, it determines that it enters the inspiratory phase; when the instantaneous relative pressure value exceeds a preset expiratory trigger positive pressure threshold and the pressure change rate parameter is positive, it determines that it enters the expiratory phase; when the instantaneous relative pressure value is within the dead zone between the inspiratory trigger negative pressure threshold and the expiratory trigger positive pressure threshold, it determines that it enters the resting phase.

8. The oxygen generator control system as described in claim 7, characterized in that, The main control unit outputs discretized state function parameters to the control buffer based on the respiratory phase determination result. When the respiratory phase is determined, the state function parameter is assigned an integer value of 1. The main control unit controls the pressurizing impeller to operate with the calibrated pulse peak value. At the same time, the main control unit adds trapezoidal ramp limiting logic to the transition of the pulse width modulation signal output to the pressurizing impeller drive circuit to smoothly approximate the target parameter. When the respiratory phase or the resting phase is determined, the state function parameter is assigned a preset minimum normal quantity coefficient. The pressurizing impeller runs at a reduced speed according to the coefficient and maintains a set basic micro-positive pressure state inside the terminal pipeline to prevent backflow of exhaled gas.

9. The oxygen generator control system as described in claim 2, characterized in that, When dynamically calibrating the base maintenance speed constant of the compressor module, the main control unit first performs multi-cycle time-weighted smoothing calculation on the feature sequence acquired by the blood oxygen acquisition module to extract the effective blood oxygen saturation parameter. When it is determined that the effective blood oxygen saturation parameter falls below the set physiological safety threshold, the main control unit calculates the difference between the physiological safety threshold and the effective blood oxygen saturation parameter, and combines it with the preset blood oxygen compensation gain coefficient and the initial base speed to dynamically reconstruct and calculate a new base maintenance speed variable. The base maintenance speed variable is then used to replace the static base maintenance speed constant during the closed-loop operation of the system in real time.

10. The oxygen generator control system as described in claim 9, characterized in that, The main control unit is equipped with a one-way compensation cutoff judgment function. When the extracted effective blood oxygen saturation parameter is determined to be greater than or equal to the physiological safety threshold, the algebraic subtraction calculation result of the difference is forced to zero. This is to prevent the compressor module command speed after reconstruction from being lower than the basic operating limit of the gas circuit due to the negative deviation calculation when the effective blood oxygen saturation parameter recovers overshoot.

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