Method and system for controlling liquid flow of eyewash equipment

Abstract

The invention provides an eyewash equipment liquid flow control method and system, and relates to the technical field of eyewash equipment liquid flow control. The method comprises the following steps: judging whether a liquid flow path at an outlet of a nozzle is blocked or not according to a fluid pressure signal; when the micro pump is judged to be blocked, controlling the micro pump to suspend or reduce the liquid flow, and recording the blocking duration; when it is judged that the liquid flow path is smooth, liquid conveying is recovered, and the duration time when the liquid flow path is blocked is accumulated; and after the preset total conveying time is over, extra time for supplementing conveying is calculated, and the micro pump is controlled to carry out extra liquid conveying according to the extra time. The method aims at overcoming the physical interruption of instant eye reflection of a user on the micro liquid flow and solving the problem that an existing open-loop control system cannot sense the interruption so that the dosage of the liquid medicine is inaccurate, and therefore it is ensured that the total amount of the liquid medicine finally acting on the eyeballs is accurately consistent with the preset treatment dosage.

Description

Technical Field

[0001] This invention relates to the field of liquid flow control technology for eyewash stations, and more specifically, to a method and system for controlling liquid flow in eyewash stations. Background Technology

[0002] Following ophthalmic surgery, such as cataract extraction or corneal transplantation, the patient's eye tissues are in a sensitive recovery period. During this time, regular and measured cleaning of the eye is necessary to remove surgical residue and secretions, and the application of medicated solutions with anti-inflammatory or healing-promoting properties. These medicated solutions are usually expensive, and the accuracy of dosage is strictly required. Overuse may cause fluctuations in intraocular pressure or drug side effects, while insufficient dosage will fail to achieve the desired therapeutic effect and may even delay the recovery process.

[0003] To address this, a microfluidic eyewash device has emerged in the prior art, designed to provide precise and gentle medication delivery to the eye after surgery. This eyewash device integrates a micropump and a microfluidic chip with a network of microchannels. When the device is activated, the micropump precisely pumps the medication from the reservoir into the microfluidic chip at a constant, preset, extremely low flow rate (e.g., 0.05 ml / s). After passing through the microchannel structure within the chip, the liquid is ejected from an array of nozzles at the front of the device in the form of multiple fine, stable jets, directly acting on the patient's ocular surface. The main purpose of this microfluidic design is to minimize physical impact on the sensitive postoperative eye, achieving an extremely gentle rinsing process, and theoretically enabling precise medication delivery.

[0004] However, in practical use, the accuracy of this microfluidic eyewash device faces an unavoidable challenge from a physiological phenomenon: the human blink reflex. Even with professional training, it is difficult for patients to completely suppress this natural protective reflex during the rinsing process, which can last from several seconds to tens of seconds, when the liquid approaches the eyeball. When a patient blinks, their upper and lower eyelids close rapidly.

[0005] Because the liquid column generated by a microfluidic system has extremely low kinetic energy, its shape and flow direction are highly susceptible to minute external disturbances. At the moment the eyelid closes, the moving eyelid directly contacts and physically intercepts the fine liquid column ejected from the nozzle towards the cornea. Some of the intercepted medicinal liquid adheres to the eyelid margin and eyelashes, while another portion may be carried away from the eyeball surface by the eyelid's movement and flow onto the skin around the eye, thus failing to effectively act on the target area (such as the cornea or conjunctival sac).

[0006] More seriously, the control system inside existing microfluidic eyewash devices is a typical open-loop system, its design logic entirely based on the calculation model of "preset flow rate × running time = total delivery volume". This means that the control system does not integrate any feedback mechanism regarding whether the external liquid delivery path is physically blocked. Therefore, even if the external micro-fluid flow is physically blocked by the eyelid, the internal micro-pump continues to work according to the preset program instructions, pumping out the same amount of liquid. This directly leads to a serious consequence: in a single flushing session, any medication pumped out by the device during the patient's blinking fails to actually act on the effective target area of ​​the eyeball and is wasted.

[0007] This waste of medication not only results in economic losses from expensive medications, but more importantly, it causes the actual effective dose delivered to the ocular surface to be lower than the preset therapeutic dose. For example, in a 10-second irrigation procedure planned to deliver 0.5 ml of medication, if the patient blinks three times during this period, with each blink and eyelid closure lasting 0.5 seconds, a total of 1.5 seconds of pumped-out fluid is wasted. This translates to a loss of nearly 15% of the medication dose, which is sufficient to seriously affect the clinical outcome of postoperative recovery. To compensate for the potential dose deficiency, users may try to extend the irrigation time, but this makes the actual dose per irrigation uncontrollable, completely deviating from the original intention of using the device for precise control. Therefore, existing microfluidic eyewash devices cannot effectively solve the problems of medication waste and inaccurate dosage caused by the user's blink reflex in practical applications, which severely limits their clinical application value for precise drug delivery in postoperative eye care. Summary of the Invention

[0008] The purpose of this invention is to provide a liquid flow control method and system for an eyewash station, which aims to overcome the physical interruption of the micro-fluid flow caused by the user's blink reflex and solve the problem that existing open-loop control systems cannot detect such interruptions, resulting in inaccurate drug dosage, thereby ensuring that the total amount of drug finally acting on the eyeball is precisely consistent with the preset treatment dose.

[0009] In a first aspect, the present invention provides a method for controlling the liquid flow rate of an eyewash station, comprising the following steps: Acquire the fluid pressure signal at the nozzle outlet of the microfluidic eyewash station; Based on the fluid pressure signal, determine whether the liquid flow path at the nozzle outlet is blocked; When it is determined that the liquid flow path is blocked, the micro pump is controlled to pause or reduce the liquid flow rate, and the duration of the liquid flow path blockage is recorded. When it is determined that the liquid flow path has been restored, the micro pump is controlled to resume liquid delivery according to the original liquid flow rate, and the duration of the liquid flow path being blocked is accumulated; After the preset total delivery time ends, the additional delivery time required is calculated based on the preset total delivery time and the cumulative duration of liquid flow path blockage, and the micro pump is controlled to deliver additional liquid according to the additional time.

[0010] The present invention provides a liquid flow control method for eyewash stations, aiming to solve the problem of interrupted micro-fluidic liquid flow due to user blinking, which affects the accuracy of medication dosage when delivering medication to sensitive postoperative eyes using microfluidic eyewash stations. By integrating a miniature pressure sensor near the outlet of the microfluidic nozzle, the system can detect local pressure fluctuations caused by flow obstruction in real time. Once a pressure fluctuation is detected, the control unit immediately pauses or reduces the liquid delivery of the micro-pump and records the interruption duration. When the liquid flow is restored, the micro-pump resumes normal delivery. After the entire rinsing task is completed, the system calculates and supplements additional delivery time based on the accumulated liquid flow interruption duration, ensuring that the actual effective delivery volume of medication matches the preset dosage.

[0011] In a second aspect, the present invention provides a liquid flow control system for an eyewash station, comprising: The acquisition module is used to acquire the fluid pressure signal at the nozzle outlet of the microfluidic eyewash station; The judgment module is used to determine whether the liquid flow path at the nozzle outlet is blocked based on the fluid pressure signal; The first control module is used to control the micro pump to pause or reduce the liquid flow rate when it is determined that the liquid flow path is blocked, and to record the duration of the liquid flow path being blocked. The second control module is used to control the micro pump to resume liquid delivery according to the original liquid flow rate when it is determined that the liquid flow path has been restored to unobstructed, and to accumulate the duration of the liquid flow path being blocked. The third control module is used to calculate the additional time required for supplementary delivery based on the preset total delivery time and the cumulative duration of liquid flow path blockage after the preset total delivery time has ended, and to control the micro pump to deliver additional liquid according to the additional time.

[0012] As can be seen from the above, the eyewash liquid flow control method provided by this invention effectively solves the problems of liquid waste and dosage inaccuracy caused by blinking in the prior art by introducing pressure sensing and intelligent compensation mechanisms. Regardless of how the patient blinks, the system can dynamically adjust to ensure that the total amount of liquid ultimately acting on the eyeball always precisely matches the preset treatment dose, thereby ensuring the accuracy and effectiveness of postoperative eye care while avoiding the waste of expensive liquids. Specifically, the miniature pressure sensor integrated near the outlet of the microfluidic nozzle can directly and in real time sense the instantaneous increase in local fluid pressure at the nozzle outlet when the micro-flow is physically blocked by the eyelid. This pressure fluctuation is a direct physical manifestation of the obstruction of the micro-flow, avoiding the need for complex image recognition or external optical path detection of eyelid movement, and improving the directness and accuracy of interruption judgment. Once the control unit determines that the flow is interrupted based on the pressure signal, it immediately instructs the micro-pump to pause or reduce delivery, stopping the pumping of liquid to the blocked path. This effectively prevents the waste of liquid during blinking and solves the problem of expensive liquid loss. Furthermore, the system's internal timer precisely records the duration of each fluid flow interruption and accumulates this time after the rinsing task is completed. The actual effective delivery time is obtained by subtracting the accumulated interruption time from the total rinsing time. If this time is insufficient, the control unit instructs the micropump to deliver additional fluid for the corresponding duration, ensuring that the total amount of medication ultimately acting on the ocular surface is precisely consistent with the preset treatment dose, thus resolving the problem of inaccurate dosage affecting treatment efficacy. Simultaneously, the system responds to interruptions by pausing or reducing the flow rate, rather than overcoming obstacles by increasing jet pressure or changing the rinsing mode. This ensures that the gentle rinsing characteristics of the microfluidic eyewash device remain unaffected, preventing additional physical irritation to sensitive postoperative eyes and meeting the stringent gentleness requirements of this specific application scenario. Finally, the original open-loop control system was upgraded to a closed-loop control system with external environmental feedback, significantly improving the intelligence level and drug delivery reliability of the microfluidic eyewash device in complex physiological environments.

[0013] Other features and advantages of the invention will be set forth in the following description, and will be apparent in part from the description, or may be learned by practicing embodiments of the invention. The objects and other advantages of the invention may be realized and obtained by means of the structures particularly pointed out in the written description and the accompanying drawings. Attached Figure Description

[0014] Figure 1 This is a flowchart of a liquid flow control method for an eyewash station provided in an embodiment of the present invention.

[0015] Figure 2 This is a schematic diagram of a liquid flow control system for an eyewash station provided in an embodiment of the present invention.

[0016] Label Explanation: 100. Acquisition module; 200. Judgment module; 300. First control module; 400. Second control module; 500. Third control module. Detailed Implementation

[0017] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. The components of the embodiments of the present invention described and shown in the accompanying drawings can generally be arranged and designed in various different configurations. Therefore, the following detailed description of the embodiments of the present invention provided in the accompanying drawings is not intended to limit the scope of the claimed invention, but merely to illustrate selected embodiments of the invention. All other embodiments obtained by those skilled in the art based on the embodiments of the present invention without inventive effort are within the scope of protection of the present invention.

[0018] It should be noted that similar reference numerals and letters in the following figures indicate similar items; therefore, once an item is defined in one figure, it does not need to be further defined and explained in subsequent figures. Furthermore, in the description of this invention, terms such as "first," "second," etc., are used only to distinguish descriptions and should not be construed as indicating or implying relative importance.

[0019] Reference Appendix Figure 1 This invention provides a method for controlling the liquid flow rate of an eyewash station, comprising the following steps: Acquire the fluid pressure signal at the nozzle outlet of the microfluidic eyewash station; Based on the fluid pressure signal, determine whether the liquid flow path at the nozzle outlet is blocked; When it is determined that the liquid flow path is blocked, the micro pump is controlled to pause or reduce the liquid flow rate, and the duration of the liquid flow path blockage is recorded. When it is determined that the liquid flow path has been restored, the micro pump is controlled to resume liquid delivery according to the original liquid flow rate, and the duration of the liquid flow path being blocked is accumulated; After the preset total delivery time ends, the additional delivery time required is calculated based on the preset total delivery time and the cumulative duration of liquid flow path blockage, and the micro pump is controlled to deliver additional liquid according to the additional time.

[0020] Fluid pressure signal refers to the pressure information generated by the liquid medication during delivery at the nozzle outlet of a microfluidic eyewash station. It can be implemented using pressure sensors, piezoelectric sensors, or microelectromechanical systems (MEMS) pressure sensors, such as silicon-based pressure sensors or thin-film pressure sensors. These are primarily used to monitor the physical state of the liquid medication delivery path in real time, providing a basis for determining whether the flow is obstructed. Determining whether the flow path is blocked involves identifying whether the liquid medication is physically obstructed from the nozzle based on the change pattern or threshold of the fluid pressure signal. This can be achieved using methods such as pressure threshold comparison, pressure change rate analysis, or pressure signal pattern recognition. For example, comparing the real-time pressure with a preset normal range and analyzing the rising or falling trend of the pressure signal are mainly used to identify interruptions in liquid medication delivery caused by external interference. Controlling the micropump to pause or reduce the liquid flow rate refers to adjusting the operating state of the micropump to reduce or stop the output of the liquid medication when the flow path is blocked. This can be achieved by controlling the power supply of the micro-pump, adjusting the pump's drive frequency, or changing the pump's operating mode. For example, by cutting off the pump's power supply or reducing the pump's speed, it is mainly used to avoid wasting liquid during ineffective delivery. Recording the duration of each flow path blockage refers to measuring and storing the time from the occurrence of each flow path blockage event to the restoration of unobstructed flow. This can be achieved using a timer, timestamp recording, or interrupt counter. For example, using a system clock to record the start and end times of the blockage is mainly used to provide single-blockage data for subsequent calculations of compensation. Accumulating the duration of flow path blockage refers to summing the durations of multiple flow path blockages. This can be achieved using an accumulator, data storage, or software variables. For example, after each blockage ends, the duration is added to the total timer. This is mainly used to calculate the delivery time lost due to blockages during the entire delivery process. Calculating the additional delivery time required refers to determining the length of time required for additional liquid delivery based on the difference between the preset total delivery time and the actual delivery time. This can be achieved through time difference calculation, proportional calculation, or direct calculation based on cumulative blocking time. For example, subtracting the preset total delivery time from the cumulative blocking time is used to ensure that the final delivered total amount of medication reaches the preset dose. Controlling the micropump to deliver additional liquid according to the extra time refers to driving the micropump to continue delivering medication after the main delivery task is completed, based on the calculated extra time. This can be achieved through timer control, flow control, or pulse control. For example, setting an operating cycle equal to the extra time is used to compensate for insufficient medication delivery caused by blocking, ensuring consistency between the delivered amount and the preset amount.

[0021] The working principle of this invention is to use the local pressure change generated by the microfluidic nozzle when the liquid flow is obstructed as a feedback signal to achieve real-time, dynamic control and precise compensation of the micro-liquid flow delivery process.

[0022] When the microfluidic eyewash station is working normally, the micropump delivers the medication to the nozzle at a constant flow rate, and the medication is steadily sprayed out in the form of a fine liquid column. At this time, the local fluid pressure at the nozzle outlet is at a stable baseline state. Once the patient blinks, the eyelid closes and physically contacts the spraying fine liquid column. Due to the low kinetic energy characteristics of the liquid flow, its flow path is immediately blocked. At this moment, the medication at the nozzle outlet cannot be sprayed out smoothly, causing the local fluid pressure to rise rapidly in a short period of time, forming a detectable pressure fluctuation signal.

[0023] The control unit inside the eyewash station continuously monitors the pressure signal from a miniature pressure sensor near the nozzle. When the detected increase in pressure or the duration of the increase reaches a preset threshold, the control unit immediately determines that the fluid flow path is blocked. At this point, to avoid wasting the medication, the control unit immediately sends a command to the miniature pump to stop the medication delivery or reduce the flow rate to an extremely low level. Simultaneously, the system's internal timer begins to precisely record the duration of this fluid flow interruption.

[0024] Once the patient blinks and the eyelids reopen, restoring unobstructed flow, the local pressure at the nozzle outlet quickly returns to a stable baseline. Upon sensing this return to normal pressure, the control unit immediately instructs the micro-pump to resume the preset normal flow rate and continue drug delivery. The timer stops recording the duration of this interruption and adds it to the total interruption duration.

[0025] After the entire rinsing process is completed, the control unit performs precise calculations based on the preset total rinsing time and the cumulative duration of fluid flow interruption. It calculates the actual effective delivery time of the medication via the micropump during the entire rinsing process. If this actual effective delivery time is less than the preset treatment duration (i.e., the time required to deliver the preset dose), the control unit instructs the micropump to deliver an additional duration of medication. For example, if the preset effective delivery time is 10 seconds, but due to a cumulative 1.5-second pause caused by blinking, the system will run the micropump for an additional 1.5 seconds after the original rinsing period to ensure that the total amount of medication delivered to the target area of ​​the eye is precisely consistent with the preset treatment dose, thereby guaranteeing the accuracy of drug administration and the therapeutic effect.

[0026] The core innovation of this application lies in the construction of a closed-loop feedback control mechanism by introducing real-time acquisition and analysis of fluid pressure signals at the nozzle outlet. This mechanism can dynamically determine whether the liquid flow path is blocked and adjust the liquid flow rate of the micro pump accordingly. At the same time, it compensates for insufficient delivery caused by blockage, thereby solving the problems of existing open-loop systems being unable to detect external blockages, resulting in liquid waste and inconsistent dosage. This achieves consistency between the liquid delivery volume and the preset volume.

[0027] Specifically, this method manages the liquid delivery process of the eyewash station by establishing a dynamic feedback control loop. First, the system continuously acquires the fluid pressure signal at the nozzle outlet of the microfluidic eyewash station, which serves as an input reflecting the liquid flow status. Based on the analysis of this fluid pressure signal, the system can determine whether the liquid flow path at the nozzle outlet is blocked. Once a blockage is detected, such as due to a user's blink or external contact, the system immediately instructs the micropump to pause or reduce the liquid delivery flow rate to avoid wasting liquid during ineffective delivery. Simultaneously, the system records the duration of the blockage. When the fluid pressure signal indicates that the liquid flow path is restored, the system controls the micropump to resume the original liquid flow rate and continues to accumulate all blocked durations. After the preset total delivery time ends, the system does not stop immediately but calculates the amount of additional delivery time required using the preset total delivery time and the accumulated blocked durations. Subsequently, the system will drive the micro-pump to replenish the medication during this extra time, thereby ensuring that the total amount of medication actually delivered to the target eye area during the entire eye washing process reaches the preset dose, making up for the loss of medication caused by the momentary interruption.

[0028] By employing the above-described solution, this application addresses the problems of medication waste and inconsistent dosage caused by obstructed fluid flow paths (e.g., user blinking reflex) in existing microfluidic eyewash devices during practical applications. This solution, through real-time monitoring and dynamic adjustment, avoids continuous pumping of medication during ineffective delivery periods, thereby reducing medication waste. Simultaneously, by recording the obstruction time and compensating for the obstruction, it ensures that the total amount of medication actually delivered to the target area reaches the preset dose, improving the accuracy of drug administration and the stability of therapeutic effects.

[0029] In some embodiments, the step of acquiring the fluid pressure signal at the nozzle outlet of the microfluidic eyewash station includes: Obtain the physical properties information of the currently delivered liquid medicine; the physical properties information includes temperature information and viscosity information; Based on physical property information, calibrate the detection benchmark for fluid pressure signals; Based on the testing criteria, the fluid pressure signal at the nozzle outlet of the microfluidic eyewash station was obtained.

[0030] Physical property information refers to data describing the inherent physical properties of the liquid medicine. This information can be obtained in real-time through sensors integrated into the eyewash station, such as temperature and viscosity sensors, or through user input or querying from a pre-set database. The detection benchmark refers to a reference standard or threshold used to determine whether the fluid pressure signal is within the normal range. This benchmark can be dynamically calculated or adjusted based on the physical property information of the liquid medicine using a pre-established physical model, empirical formula, or machine learning algorithm.

[0031] This solution addresses the impact of varying liquid properties on the accuracy of pressure signals by employing an adaptive pressure signal acquisition mechanism. Its working principle is as follows: First, the system acquires the physical properties of the currently delivered liquid, such as viscosity, density, or temperature. These physical properties influence the fluid dynamics of the liquid. Next, the system calibrates the detection benchmark for the fluid pressure signal based on the acquired physical properties of the liquid. This means that the system adjusts the pressure reference point or threshold used to determine the flow state according to the actual characteristics of the current liquid, rather than using fixed parameters. Finally, the system acquires the fluid pressure signal at the nozzle outlet of the microfluidic eyewash station based on this calibrated detection benchmark. In this way, the acquired pressure signal reflects the flow state of the liquid under specific physical properties, thereby ensuring the accuracy of subsequent flow state judgments and the robustness of the system. Even when different liquids are used or the properties of the liquid change, the flow state can still be sensed. Specifically, by acquiring the physical properties of the currently delivered liquid, particularly temperature and viscosity, this solution obtains key parameters affecting fluid pressure. Temperature and viscosity are important physical quantities that directly affect liquid flow resistance and the relationship between flow velocity and pressure. Acquiring this information provides the necessary data foundation for subsequent pressure signal calibration, ensuring a comprehensive understanding of the current state of the liquid. Secondly, based on this acquired physical property information, this solution can calibrate the detection benchmark for the fluid pressure signal. This means that the system no longer uses a fixed, preset pressure threshold to determine the flow state, but dynamically adjusts or determines a more realistic normal pressure range or benchmark point based on the current temperature and viscosity of the liquid. This dynamic calibration mechanism ensures that even if the physical properties of the liquid change, the system can accurately identify the pressure performance at the nozzle outlet under normal delivery conditions, thus providing an accurate reference for subsequent blocking judgments and avoiding misjudgments caused by changes in the liquid's own properties. Finally, based on the calibrated detection benchmark, the system acquires the fluid pressure signal at the nozzle outlet of the microfluidic eyewash station. The pressure signal acquired at this point, having already considered and compensated for the impact of changes in the liquid's own physical properties, can more realistically and accurately reflect the actual fluid state at the nozzle outlet. This makes the subsequent step of determining whether the fluid flow path is blocked based on the pressure signal more accurate and reliable, avoiding misjudgments caused by reference deviations, thus ensuring accurate delivery and effective utilization of the liquid and avoiding unnecessary waste. Through the above mechanism, this solution can adapt to the physical characteristics of different liquids when acquiring fluid pressure signals, ensuring that the acquired pressure signals can accurately reflect the fluid flow state. This provides an accurate and reliable data basis for subsequent determination of whether the fluid flow path at the nozzle outlet is blocked. When the fluid flow path is blocked, the system can accurately identify it based on the calibrated pressure signal and promptly control the micro-pump to pause or reduce the liquid flow rate, effectively avoiding liquid waste.When the fluid flow path is restored, the system can accurately determine and resume fluid delivery. Simultaneously, by accumulating the interruption time and performing additional delivery, the accuracy of the total medication delivery volume is ensured. This optimization of pressure signal acquisition allows the entire fluid flow control method to maintain its accuracy and robustness even when faced with varying medication characteristics, enhancing the clinical application value of eyewash stations for precise drug administration in postoperative eye care.

[0032] This solution acquires the physical properties of the currently delivered liquid medicine, calibrates the detection benchmark for the fluid pressure signal based on this information, and then acquires the fluid pressure signal according to the calibrated benchmark, thus resolving the impact of different liquid medicine properties on the accuracy of the pressure signal. This ensures that the acquired fluid pressure signal accurately reflects the flow state of the liquid medicine under specific physical properties, thereby improving the accuracy and reliability of subsequent judgments on whether the liquid flow path is blocked. Even when different liquid medicines are used or the properties of the liquid medicine change, the system can accurately sense the liquid flow state, avoiding misjudgments caused by benchmark deviations and ensuring the precise delivery and effective utilization of the liquid medicine.

[0033] In some embodiments, the step of calibrating the detection reference of the fluid pressure signal based on physical characteristic information includes: Based on temperature and viscosity information, determine the reference pressure range of the drug solution under normal delivery conditions; The detection benchmark for fluid pressure signals is calibrated based on the reference pressure range.

[0034] Temperature information refers to parameters reflecting the current thermodynamic state of the liquid drug, which can be acquired using temperature sensors, such as thermistors or infrared thermometers. Viscosity information refers to parameters reflecting the magnitude of the flow resistance of the liquid drug, which can be acquired indirectly using a microrheometer or by measuring the pressure drop of the liquid drug in a specific flow channel. The reference pressure range refers to the expected range of fluctuations in the fluid pressure signal under normal delivery conditions. This range can be determined based on a pre-established empirical model of the relationship between the physical properties of the liquid drug and the pressure response, a lookup table method, or a real-time calibration algorithm. The calibration benchmark for the fluid pressure signal refers to dynamically adjusting the pressure threshold or reference point used to judge the flow state according to the determined reference pressure range. This can be achieved by adjusting the comparator threshold, updating the reference value in the software algorithm, or through a feedback control mechanism.

[0035] This solution addresses the impact of changes in drug liquid properties on the accuracy of pressure signal detection by introducing a drug liquid physical property sensing and adaptive benchmark calibration mechanism. Its working principle is as follows: First, before or during drug liquid delivery, the system acquires the temperature and viscosity information of the currently delivered drug liquid through built-in sensors or recognition modules. These are key parameters affecting the fluid dynamics of the drug liquid. Next, based on the acquired temperature and viscosity information, the system analyzes and determines the benchmark pressure range of the drug liquid under normal delivery conditions. This range reflects the normal flow pressure characteristics under specific drug liquid properties. Finally, the system calibrates the fluid pressure signal detection benchmark based on this determined benchmark pressure range. In this way, regardless of changes in the actual temperature or viscosity of the drug liquid, the system ensures that the acquired pressure signal reflects the true flow state of the drug liquid, thereby improving the accuracy of flow state judgment and the system's environmental adaptability, and avoiding misjudgments caused by changes in drug liquid properties. Building on this, this solution further refines the specific method of calibrating the fluid pressure signal detection benchmark by introducing the temperature and viscosity information of the drug liquid to determine a dynamic benchmark pressure range, making the entire flow state judgment process more accurate and adaptable.

[0036] Specifically, this scheme first clarifies the steps for calibrating the detection benchmark of the fluid pressure signal. The core improvement of this scheme lies in determining the benchmark pressure range of the drug solution under normal delivery conditions based on temperature and viscosity information. The temperature and viscosity of the drug solution are key physical characteristics affecting its flow resistance, velocity, and pressure in a microfluidic system. By combining these two factors to determine a benchmark pressure range, rather than a fixed benchmark point, it is possible to more comprehensively and accurately reflect the pressure fluctuations that may occur under normal delivery conditions. For example, even under normal delivery, the pressure generated by the drug solution may vary slightly at different temperatures or viscosities. A reasonable pressure range can accommodate these normal, non-blocking pressure changes, thus avoiding misinterpreting normal pressure fluctuations as flow path obstruction. Finally, based on the benchmark pressure range, the calibration of the fluid pressure signal detection benchmark involves comparing the actual detected fluid pressure signal with this normal pressure range determined by the current temperature and viscosity after determining the dynamic benchmark pressure range, thereby calibrating the detection benchmark. This means that only when the actual detected pressure signal deviates from this normal pressure range will it be considered abnormal and used to determine whether the flow path is obstructed. This calibration method, based on a dynamic reference pressure range, significantly improves the accuracy and robustness of fluid pressure signal detection, ensuring that the system can more reliably determine the unobstructedness of the fluid flow path under different physical properties of the liquid, thus providing a more accurate basis for subsequent flow control.

[0037] By determining the baseline pressure range of the medication solution under normal delivery conditions based on temperature and viscosity information, and calibrating the fluid pressure signal detection benchmark according to this baseline pressure range, this solution effectively addresses the impact of changes in the physical properties of the medication solution on the accuracy of fluid pressure signal detection. This allows the system to accurately acquire the fluid pressure signal at the nozzle outlet even when dealing with medication solutions from different batches, under different storage conditions, or at different ambient temperatures. This improves the accuracy of fluid flow state judgment and the system's environmental adaptability, avoids misjudgments caused by changes in medication properties, and ensures the reliability of precise drug delivery in postoperative eye care using the microfluidic eyewash device.

[0038] In some embodiments, the step of determining whether the fluid flow path at the nozzle outlet is blocked based on the fluid pressure signal includes: Continuously acquire fluid pressure signals and generate pressure signal sequences; By analyzing the pressure signal sequence, the duration, amplitude, and rate of pressure change of the pressure signal can be obtained. Based on the duration, pressure change amplitude, and pressure change rate, and in conjunction with preset physiological and non-physiological blocking characteristic parameters, it is determined whether the liquid flow path at the nozzle outlet is blocked.

[0039] Physiological blockage characteristic parameters refer to preset values ​​or ranges used to characterize the dynamic characteristics of pressure signals in fluid flow blockage events caused by physiological activities (such as blink reflexes). These parameters can be determined by experimental observation, data collection, and statistical analysis of a large number of physiological blockage events, combined with biomechanical modeling. Non-physiological blockage characteristic parameters refer to preset values ​​or ranges used to characterize the dynamic characteristics of pressure signals in fluid flow blockage events caused by equipment failure or external environmental factors (such as nozzle blockage or micropump malfunction). These parameters can be determined by simulating or actually testing the system response under different failure modes, and then analyzing and summarizing the acquired pressure data.

[0040] This application, in determining whether the fluid flow path at the nozzle outlet is blocked, no longer relies solely on instantaneous pressure values ​​or simple threshold judgments, but introduces in-depth analysis of the dynamic characteristics of the fluid pressure signal. Specifically, firstly, the system continuously acquires the fluid pressure signal at the nozzle outlet and organizes it into a pressure signal sequence. It is precisely this serialized data acquisition that allows the system to capture the complete dynamic process of pressure changes over time, laying the foundation for subsequent refined analysis and overcoming the limitation that a single instantaneous pressure value cannot fully reflect the dynamic characteristics of fluid flow obstruction. Based on this, the system performs in-depth analysis of the acquired pressure signal sequence, extracting three key dynamic features: the duration of pressure change, the amplitude of pressure change, and the rate of pressure change. The acquisition of these multi-dimensional features allows the system to more comprehensively characterize the pressure response patterns of different types of obstruction events. For example, obstruction caused by blink reflexes is usually characterized by a short duration, rapid pressure changes, and limited amplitude, while nozzle blockage may be characterized by a long duration, continuous pressure increases, or abnormal fluctuations. It is through these detailed feature extractions that the system can move beyond simple pressure threshold judgments and achieve a preliminary distinction between the nature of the obstruction. Furthermore, the system compares the extracted duration, pressure change amplitude, and pressure change rate with preset physiological and non-physiological blockage characteristic parameters. These preset parameters, determined based on extensive experimental data and accumulated experience, represent typical pressure characteristic patterns of transient physiological blockage and persistent non-physiological blockage, respectively. Through this intelligent comparison, the system can accurately identify the type of current fluid flow blockage, thus providing a precise basis for subsequent flow control. This refined judgment mechanism enables the system to distinguish between physiological and non-physiological blockages when the fluid flow path is determined to be blocked, and thus take more targeted response measures. For example, it may compensate for physiological blockages to ensure medication dosage, while triggering alarms or stopping operation for non-physiological blockages to avoid equipment damage, thereby significantly improving the intelligence level and reliability of the entire eyewash station fluid flow control method.

[0041] This application continuously acquires fluid pressure signals and generates pressure signal sequences. It then analyzes the duration, amplitude, and rate of pressure change, and combines these with preset physiological and non-physiological blocking characteristic parameters to accurately distinguish between transient physiological blockages and persistent non-physiological blockages in the fluid flow path at the nozzle outlet. This allows the system to take appropriate response measures for different types of blockages. For example, for transient physiological blockages, it avoids unnecessary flow interruptions or misjudgments, thereby reducing fluid waste and ensuring accurate fluid delivery. For persistent non-physiological blockages, it can promptly trigger alarms or stop operation, effectively preventing equipment damage or delays in troubleshooting. Therefore, this application significantly improves the intelligence and reliability of eyewash station fluid flow control, ensuring the accuracy and safety of fluid delivery.

[0042] In some embodiments, the step of determining whether the liquid flow path at the nozzle outlet is blocked, based on the duration, pressure change amplitude, and pressure change rate, and in conjunction with preset physiological and non-physiological blocking characteristic parameters, includes: Based on the physiological blockade characteristic parameters, the pressure characteristic pattern of physiological blockade is determined; Based on the non-physiological blockade characteristic parameters, the pressure characteristic pattern of non-physiological blockade is determined; The duration, magnitude, and rate of pressure change were compared with the pressure characteristic patterns of physiological blockade. When the comparison results match the pressure characteristic pattern of physiological blockage, it is determined that the liquid flow path at the nozzle outlet is physiologically blocked. When the comparison results do not match the pressure characteristic pattern of physiological blockade, the duration, pressure change amplitude, and pressure change rate are compared with the pressure characteristic pattern of non-physiological blockade. When the comparison results match the pressure characteristic pattern of non-physiological blockage, it is determined that the liquid flow path at the nozzle outlet is blocked by non-physiological blockage. If the comparison results do not match the pressure characteristic patterns of physiological blockage and non-physiological blockage, it is determined that the liquid flow path at the nozzle outlet is not blocked.

[0043] Physiological blockage characteristic parameters refer to the set of pressure signal characteristics used to describe fluid flow path blockage phenomena caused by human physiological activities (such as blinking and eye movement). These can be achieved by pre-collecting a large amount of pressure data during user blinking or eye movements, and then extracting and quantifying data sets such as pressure duration range, pressure change amplitude range, and pressure change rate range through statistical analysis and machine learning training. Non-physiological blockage characteristic parameters refer to the set of pressure signal characteristics used to describe fluid flow path blockage phenomena caused by non-human physiological activities (such as foreign object blockage, equipment failure, and nozzle blockage). These can be achieved by simulating or actually testing pressure data under different non-physiological blockage conditions, and then extracting and quantifying data sets such as pressure duration, pressure change amplitude, and pressure change rate through data analysis and threshold setting. The pressure characteristic pattern of physiological blockage refers to a typical pressure change curve or numerical range model that represents the physiological blockage phenomenon, established based on the physiological blockage characteristic parameters. This can be constructed using machine learning algorithms such as rule-based logical judgment models, decision tree models, or support vector machine models. The pressure characteristic pattern of non-physiological blockade refers to a typical pressure change curve or numerical range model that can represent the non-physiological blockade phenomenon, established based on the characteristic parameters of non-physiological blockade. It can be constructed using methods similar to those used in the construction of physiological blockade patterns, such as rule-based logical judgment, neural network models, or cluster analysis.

[0044] This application solves the technical problem of accurately distinguishing between physiological blockage, non-physiological blockage, and non-blockage after acquiring pressure signal characteristics by establishing a hierarchical, pattern-matching judgment logic, thus providing an accurate basis for subsequent flow control. Specifically, the scheme first determines the pressure characteristic pattern of physiological blockage based on preset physiological blockage characteristic parameters. This step is based on a deep understanding of pressure changes caused by specific physiological phenomena, constructing a standardized pressure pattern that provides a clear physiological blockage benchmark for subsequent real-time data comparison. Next, the pressure characteristic pattern of non-physiological blockage is determined based on preset non-physiological blockage characteristic parameters. This is similar to the determination of the physiological blockage pattern, but it targets pressure changes caused by non-physiological factors, thus constructing another standardized pressure pattern that provides a necessary reference for distinguishing different types of blockage. Subsequently, the system compares the real-time acquired duration, pressure change amplitude, and pressure change rate with the pressure characteristic pattern of physiological blockage. This comparison is the first step in the judgment process, aiming to prioritize the identification of common blockage situations caused by user physiological activities. By matching real-time data with preset physiological patterns, it is possible to quickly determine whether physiological blockage has occurred. When the comparison result matches the pressure characteristic pattern of physiological blockage, the system determines that the fluid flow path at the nozzle outlet is physiologically blocked. This explicit determination allows the system to take specific, humane measures for physiological blockages, such as considering user comfort during compensatory delivery. When the comparison result does not match the pressure characteristic pattern of physiological blockage, the system further compares the duration, pressure change amplitude, and pressure change rate with the pressure characteristic pattern of non-physiological blockage. This hierarchical judgment mechanism ensures that even if the current situation does not belong to physiological blockage, the system can continue to try to identify other potential blockage types, avoiding omissions in judgment. When the comparison result matches the pressure characteristic pattern of non-physiological blockage, the system determines that the fluid flow path at the nozzle outlet is non-physiologically blocked. This determination allows the system to take different, more urgent measures for non-physiological blockages, such as issuing an alarm or suspending delivery to protect equipment or users. Finally, when the comparison result does not match either the pressure characteristic pattern of physiological blockage or the pressure characteristic pattern of non-physiological blockage, the system determines that the fluid flow path at the nozzle outlet is not blocked. This final judgment ensures that a blockage determination is made only when a blockage characteristic matching a specific pattern is clearly identified, avoiding misjudgments. Through this hierarchical judgment logic, the solution of this application can accurately identify the nature of the blockage, thus providing an accurate basis for subsequent flow control. When the fluid flow path is determined to be physiologically blocked, the system can control the micro-pump to pause or reduce the fluid flow rate and record the duration of this blockage to reduce drug waste and provide data for subsequent compensation delivery.When the fluid flow path is determined to be non-physiologically blocked, the system can take more urgent measures, such as issuing an alarm or completely stopping delivery, to protect the user and the equipment. This refined identification of the blockage type enables the entire eyewash station's fluid flow control method to respond more intelligently and accurately to various situations in actual use, thereby ensuring the continuity and accuracy of fluid delivery and effectively solving the problems of fluid waste and inaccurate dosage caused by different types of blockages.

[0045] This application establishes a hierarchical, pattern-matching judgment logic to accurately identify the obstruction nature of the liquid flow path at the nozzle outlet. Specifically, by determining the corresponding pressure characteristic patterns based on physiological and non-physiological obstruction characteristic parameters, and performing hierarchical comparison of the real-time acquired pressure signal characteristics, the system can accurately distinguish whether the liquid flow path is physiologically obstructed, non-physiologically obstructed, or unobstructed. This precise classification judgment allows for more targeted subsequent flow control strategies. For example, for physiological obstruction, the flow rate can be paused or reduced and the duration recorded to reduce medication waste and provide a basis for subsequent compensation delivery, while also considering user experience; for non-physiological obstruction, a more urgent alarm can be triggered or delivery can be completely stopped to protect the equipment or the user. This effectively solves the problem in existing technologies where the lack of specific judgment logic prevents accurate identification of the obstruction nature, thereby improving the accuracy and reliability of eyewash station liquid flow control, avoiding ineffective delivery and waste of medication, and ensuring the accuracy of drug dosage.

[0046] In some embodiments, the step of calculating the additional delivery time required after the preset total delivery time has ended, based on the preset total delivery time and the cumulative duration of liquid flow path obstruction, and controlling the micropump to perform additional liquid delivery according to the additional time includes: Obtain the preset single-time compensation delivery duration threshold and compensation delivery mode parameters; Compare the additional time with a single compensated delivery duration threshold; When the extra time exceeds the threshold for single compensation transport duration, the number of compensation transports and the duration of each compensation transport period are determined based on the extra time and the threshold for single compensation transport duration, and a preset transport interval is set between each compensation transport period. When the extra time is no greater than the threshold for the duration of a single compensation delivery, the extra time is taken as a single compensation delivery period, the number of compensation deliveries is determined to be one, and the extra time is the duration of the compensation delivery period. Adjust the delivery flow rate or jet mode of the micro pump according to the compensation delivery mode parameters; Repeat steps A1-A3 until the compensation delivery count is complete: A1. Control the micro pump to deliver liquid according to the duration of the current compensation delivery period; A2. After the current compensation delivery period ends, determine whether there are still unfinished compensation delivery periods; A3. If there is still an incomplete compensation delivery period, control the micro pump to pause delivery until a delivery interval has passed, then take the next compensation delivery period as the current compensation delivery period and return to step A1.

[0047] The single-session compensation delivery duration threshold refers to the maximum time limit for a single continuous compensation delivery, which can be preset based on clinical recommendations, patient tolerance, or drug characteristics. Compensation delivery mode parameters refer to the configuration information used to guide the micropump in adjusting its operating state during compensation delivery. These can include preset flow rate levels, spray angles, liquid column dispersion, or droplet size distribution to adapt to the needs of different drugs or ocular conditions. Delivery intervals refer to the preset pause time between adjacent compensation delivery periods during segmented compensation delivery, providing patients with a brief rest or adaptation time and allowing the drug to initially spread in the eye. Adjusting the micropump's delivery flow rate or spray mode refers to changing the rate at which the micropump delivers the drug or the way it is sprayed. For example, the flow rate can be reduced to decrease impact, or the nozzle spray angle, liquid column dispersion, or droplet size distribution can be changed to optimize drug spread and absorption in the eye.

[0048] The eyewash station fluid flow control method of this application calculates the additional delivery time required after the preset total delivery time has ended, based on the preset total delivery time and the cumulative duration of fluid flow path obstruction. The method then controls a micro-pump to deliver additional fluid according to this additional time. Furthermore, to further optimize the compensation delivery process, improve patient comfort and compliance, and avoid secondary irritation to sensitive eyes, this method introduces an adaptive compensation delivery strategy.

[0049] Specifically, the system first acquires the preset single-cycle compensation delivery duration threshold and compensation delivery mode parameters. The single-cycle compensation delivery duration threshold is used to set the maximum duration of a single continuous delivery to avoid discomfort caused by prolonged continuous delivery. The compensation delivery mode parameters provide a basis for subsequent adjustments to the delivery flow rate or jetting mode of the micro-pump, thereby achieving gentle delivery.

[0050] The system then compares the calculated extra time with a single compensation delivery duration threshold. This comparison is crucial in determining the compensation delivery strategy. If the extra time exceeds the single compensation delivery duration threshold, it indicates that a large amount of medication needs to be compensated, and a single delivery may cause patient discomfort. In this case, the system intelligently determines the number of compensation deliveries and the duration of each compensation delivery period based on the extra time and the single compensation delivery duration threshold, and sets a preset delivery interval between each compensation delivery period. This segmented, intermittent delivery method effectively avoids prolonged exposure of the patient's eyes to the medication, providing the patient with short periods of rest and adaptation time, thereby improving comfort. Conversely, if the extra time is not greater than the single compensation delivery duration threshold, it indicates that a small amount of medication needs to be compensated, and the extra time can be directly used as a single compensation delivery period, determining the number of compensation deliveries as one, and the extra time as the duration of the compensation delivery period, simplifying the operation process.

[0051] Before each compensating delivery, the system dynamically adjusts the delivery flow rate or spray pattern of the micro-pump according to preset compensating delivery mode parameters. For example, a lower flow rate or a gentler spray method can be used to further reduce irritation to sensitive eyes and optimize the spread and absorption of the medication in the eye.

[0052] Finally, the system executes a series of steps in a loop until the required number of compensatory deliveries is completed. During each compensatory delivery period, the micropump delivers fluid according to the duration of the current period, ensuring precise, short-duration delivery of the medication. After the current compensatory delivery period ends, the system determines if there are any unfinished periods. If so, the micropump pauses delivery until a preset delivery interval has elapsed before using the next compensatory delivery period as the current one and continuing delivery. This cyclical and interval mechanism ensures that all calculated compensatory medication is delivered segmented, intermittently, and gently, thereby significantly improving patient comfort and compliance while ensuring accurate total medication compensation and avoiding excessive irritation to sensitive postoperative eyes.

[0053] This method, combined with a scheme that calculates the additional delivery time required after the preset total delivery time has ended, based on the preset total delivery time and the cumulative duration of fluid flow path obstruction, and controls a micro-pump to deliver additional fluid according to this additional time, forms a complete, closed-loop drug delivery control system. While the basic scheme accurately identifies fluid flow obstruction and calculates the required compensation amount, this method further optimizes the execution of compensation delivery. The basic scheme ensures the accuracy of the drug dosage, while this method, through refined segmentation, intermittent, and mode adjustments, addresses the patient discomfort and compliance issues that may arise from prolonged continuous compensation. The combination of these two approaches allows the eyewash station to not only accurately deliver the preset dose of medication but also fully consider the patient's physiological sensations and comfort throughout the entire delivery process, especially during the compensation delivery phase, thereby improving the overall treatment experience and clinical outcomes.

[0054] This method refines the originally simple additional fluid delivery into a segmented, adjustable compensation delivery mode by introducing a single compensation delivery duration threshold and compensation delivery mode parameters. This segmented delivery, especially when the additional delivery time is long, effectively solves the problems of eye discomfort, anxiety, and even re-triggering of the blink reflex that may occur with prolonged continuous delivery. By setting delivery intervals, it provides patients with short rest and adaptation time, thereby improving patient compliance. Simultaneously, adjusting the delivery flow rate or spray pattern according to the compensation delivery mode parameters makes the drug delivery more intelligent and personalized, better adapting to different drug properties and ocular physiological conditions, thereby optimizing the spread and absorption of the drug in the eye and improving the effective utilization rate and therapeutic effect. Compared to simple and crude additional delivery methods, this method improves both user experience and drug delivery effectiveness, reflecting a deep consideration of the complexity of real-world application scenarios and user needs.

[0055] In some embodiments, the step of adjusting the injection mode of the micropump according to the compensation delivery mode parameters includes: Obtain the surface tension and spreading coefficient information of the currently delivered drug solution; Obtain physiological structural features of the target eye region; these features include eyeball curvature and tear film thickness. Based on the parameters of the compensation delivery mode, surface tension information, spreading coefficient information, eyeball curvature information, and tear film thickness information, the expected spreading path and coverage area of ​​the drug solution are determined by analyzing the hydrodynamic behavior of the drug solution in the target eye region. Based on the expected spreading path and coverage area, and in conjunction with the compensation delivery mode parameters, target parameters for the micropump are generated. These target parameters include injection angle parameters, liquid column dispersion parameters, and droplet size distribution parameters. The target parameters aim to ensure that the drug solution achieves spreading and coverage of the target ocular area while reducing irritation. Based on the target parameters, adjust the injection mode of the micro-pump injection mechanism to deliver the drug solution according to the expected spreading path and coverage area.

[0056] Physiological structural characteristics refer to parameters related to the physical morphology and structure of specific parts of an organism. These can be obtained by acquiring three-dimensional model data of the eye through optical imaging equipment, measuring the thickness of eye tissue through ultrasound, or analyzing the characteristics of eye tissue through bioelectrical impedance analysis. Fluid dynamics refers to the laws governing the flow, diffusion, and interaction of liquids under specific physical environments and boundary conditions. This can be achieved using computational fluid dynamics (CFD) simulation models, empirical models based on experimental data, or by analyzing and predicting historical data through machine learning algorithms. Target parameters are setpoints used to precisely control the output characteristics of the micropump injection mechanism. These can be generated using a pre-set lookup table, a real-time calculation model, or an adaptive optimization algorithm. The injection mechanism refers to the component in the micropump responsible for spraying the liquid drug in a specific form. This can be implemented using piezoelectric nozzles, micro-solenoid valve nozzles, or microfluidic chip-integrated nozzles.

[0057] This solution addresses the optimization of drug spread and coverage on the ocular surface by introducing a spray pattern adjustment mechanism that combines the rheological properties of the drug solution with the physiological structural characteristics of the eye. Its working principle is as follows: First, the system acquires the surface tension and spread coefficient information of the currently delivered drug solution. These physical properties directly affect the wetting and spreading ability of the drug solution on the ocular surface, providing fundamental data for subsequent spray pattern optimization. Simultaneously, the system acquires physiological structural characteristic information of the target ocular region, including ocular curvature and tear film thickness. These physiological characteristics determine the physical boundaries and media environment of the drug flow on the ocular surface, influencing drug spread and coverage.

[0058] Next, the system comprehensively analyzes the hydrodynamic behavior of the medication in the target ocular region based on the compensated delivery mode parameters, acquired information on the surface tension of the medication, spreading coefficient, ocular curvature, and tear film thickness. This analysis can predict the flow trend and distribution characteristics of the medication under specific ocular conditions, thereby determining the expected spreading path and coverage area. This predictive capability solves the problem that adjusting the spray pattern based solely on experience cannot ensure spreading.

[0059] Then, based on the determined expected spreading path and coverage area, and again incorporating the compensation delivery mode parameters, the system generates injection angle parameters, liquid column dispersion parameters, and droplet size distribution parameters for the micropump. These parameters are calculated to ensure that the drug solution can achieve spreading and coverage of the target eye area while reducing irritation to sensitive eyes, thereby improving the bioavailability of the drug solution.

[0060] Finally, the system adjusts the micropump's jet mechanism based on the generated jet angle parameters, liquid column dispersion parameters, and droplet size distribution parameters. This adjustment directly affects the physical form of the drug jet, ensuring that the drug is delivered according to the expected spreading path and coverage area. This guarantees the distribution and effect of the drug on the ocular surface, solving the problem of reduced therapeutic effect due to uneven drug spreading or insufficient coverage, and improving the accuracy of drug delivery and therapeutic efficacy.

[0061] The implementation of this solution not only compensates for drug loss caused by blocked flow paths during the additional fluid delivery phase, but also ensures that the drug acts on the target ocular region in an optimized manner. By acquiring information on the surface tension and spread coefficient of the drug, the system can understand the physical properties of the drug itself. This is crucial for understanding how the drug behaves on the ocular surface, providing key input for subsequent fluid dynamics analysis and ensuring that subsequent spray pattern adjustments can adapt to the characteristics of different drugs. Simultaneously, by acquiring physiological structural characteristics of the target ocular region, including ocular curvature and tear film thickness, this solution can fully consider individual differences and the physiological environment of the patient's eyes. Ocular curvature affects the flow path and distribution of the drug on the ocular surface, while tear film thickness affects the initial conditions of drug contact with the ocular surface and subsequent mixing and diffusion. These physiological parameters are crucial for ensuring that the drug effectively reaches and covers the target area, avoiding discomfort or ineffective coverage that may result from a "one-size-fits-all" spray pattern, thus achieving personalized and precise drug delivery.

[0062] By integrating the properties of the medication itself, the physiological structure of the eye, and the overall strategy of compensatory delivery, the system can predict the specific flow trajectory and final coverage area of ​​the medication on the ocular surface through a complex fluid dynamics model. This predictive capability allows the system to pre-plan the optimal medication delivery method, ensuring that the medication accurately reaches the area requiring treatment and forms a uniform and effective coverage, thereby maximizing the therapeutic effect of compensatory delivery and avoiding ineffective medication loss. After determining the ideal medication spread and coverage method, this scheme works backward to derive the specific spray parameters that the micropump needs to achieve. The spray angle parameter controls the initial direction of the medication, ensuring that it can be accurately projected onto the target area; the liquid column dispersion parameter controls the concentration or dispersion of the liquid flow, affecting the impact force and coverage area of ​​the medication; and the droplet size distribution parameter affects the permeability, evaporation rate, and irritation to the eye. The generation of these target parameters is based on a deep understanding of the fluid dynamics of the medication in the eye, aiming to achieve effective coverage while minimizing physical irritation to the sensitive eye and improving patient comfort.

[0063] By applying the calculated, refined target parameters to the micropump's injection mechanism, the system can dynamically adjust the injection behavior. This precise control ensures that the medication is delivered along a pre-planned, optimized path, ultimately achieving ideal spread and coverage in the target ocular region. This not only compensates for medication loss due to blinking, but more importantly, it provides compensatory delivery in a highly personalized and gentle manner, significantly improving the accuracy and effectiveness of treatment while ensuring a superior patient experience. Combined with the aforementioned compensatory delivery strategy, this approach allows for further optimization of the medication formulation for each delivery after determining the number of compensatory deliveries and the duration of each delivery period. This ensures medication dosage compensation while significantly improving the bioavailability of the medication in the eye and patient comfort, achieving a dual optimization of the quantity and quality of medication delivery.

[0064] This solution comprehensively understands the drug's properties and the ocular environment by acquiring information on the surface tension and spread coefficient of the drug solution, as well as the physiological structural characteristics of the target ocular region, including eyeball curvature and tear film thickness. Based on this, by analyzing the hydrodynamic behavior of the drug solution in the target ocular region, the expected spread path and coverage area can be precisely determined, thus avoiding problems of uneven spread or insufficient coverage. Based on these predictions and combined with compensation delivery mode parameters, the injection angle, liquid column dispersion, and droplet size distribution parameters of the micropump are generated and adjusted. This effectively reduces irritation to sensitive eyes during drug delivery while ensuring sufficient spread and coverage on the ocular surface, improving the bioavailability of the drug in the target area. This solves the problem of poor drug efficacy in traditional compensation delivery modes, achieving precise and effective drug delivery.

[0065] Reference Appendix Figure 2 The present invention provides a liquid flow control system for an eyewash station, comprising: The acquisition module 100 is used to acquire the fluid pressure signal at the nozzle outlet of the microfluidic eyewash station. The judgment module 200 is used to determine whether the liquid flow path at the nozzle outlet is blocked based on the fluid pressure signal. The first control module 300 is used to control the micro pump to pause or reduce the liquid flow rate when it is determined that the liquid flow path is blocked, and to record the duration of the liquid flow path being blocked. The second control module 400 is used to control the micro pump to resume liquid delivery according to the original liquid flow rate when it is determined that the liquid flow path has been restored to unobstructed, and to accumulate the duration of the liquid flow path being blocked. The third control module 500 is used to calculate the additional time required for supplementary delivery based on the preset total delivery time and the cumulative duration of liquid flow path blockage after the preset total delivery time has ended, and to control the micro pump to deliver additional liquid according to the additional time.

[0066] In this document, relational terms such as first and second are used only to distinguish one entity or operation from another entity or operation, without necessarily requiring or implying any such actual relationship or order between these entities or operations.

[0067] The above description is merely an embodiment of the present invention and is not intended to limit the scope of protection of the present invention. For those skilled in the art, the present invention can have various modifications and variations. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present invention should be included within the scope of protection of the present invention.

Claims

1. A method for controlling the liquid flow rate of an eyewash station, characterized in that, Includes the following steps: Acquire the fluid pressure signal at the nozzle outlet of the microfluidic eyewash station; Based on the fluid pressure signal, determine whether the liquid flow path at the nozzle outlet is blocked; When it is determined that the liquid flow path is blocked, the micro pump is controlled to pause or reduce the liquid flow rate, and the duration of the liquid flow path blockage is recorded. When it is determined that the liquid flow path has been restored, the micro pump is controlled to resume liquid delivery according to the original liquid flow rate, and the duration of the liquid flow path being blocked is accumulated; After the preset total delivery time ends, the additional delivery time required is calculated based on the preset total delivery time and the cumulative duration of liquid flow path blockage, and the micro pump is controlled to deliver additional liquid according to the additional time.

2. The method for controlling the liquid flow rate of an eyewash station according to claim 1, characterized in that, The steps for obtaining the fluid pressure signal at the nozzle outlet of the microfluidic eyewash station include: Obtain information on the physical properties of the currently delivered drug solution; Based on physical property information, calibrate the detection benchmark for fluid pressure signals; Based on the testing criteria, the fluid pressure signal at the nozzle outlet of the microfluidic eyewash station was obtained.

3. The method for controlling the liquid flow rate of an eyewash station according to claim 2, characterized in that, Physical property information includes temperature information and viscosity information.

4. The method for controlling the liquid flow rate of an eyewash station according to claim 3, characterized in that, The steps for calibrating the detection reference of fluid pressure signals based on physical property information include: Based on temperature and viscosity information, determine the reference pressure range of the drug solution under normal delivery conditions; The detection benchmark for fluid pressure signals is calibrated based on the reference pressure range.

5. The method for controlling the liquid flow rate of an eyewash station according to claim 1, characterized in that, The steps for determining whether the fluid flow path at the nozzle outlet is blocked based on the fluid pressure signal include: Continuously acquire fluid pressure signals and generate pressure signal sequences; By analyzing the pressure signal sequence, the duration, amplitude, and rate of pressure change of the pressure signal can be obtained. Based on the duration, pressure change amplitude, and pressure change rate, and in conjunction with preset physiological and non-physiological blocking characteristic parameters, it is determined whether the liquid flow path at the nozzle outlet is blocked.

6. The method for controlling the liquid flow rate of an eyewash station according to claim 5, characterized in that, The steps for determining whether the fluid flow path at the nozzle outlet is blocked, based on the duration, magnitude, and rate of pressure change, and in conjunction with preset physiological and non-physiological blocking characteristic parameters, include: Based on the physiological blockade characteristic parameters, the pressure characteristic pattern of physiological blockade is determined; Based on the non-physiological blockade characteristic parameters, the pressure characteristic pattern of non-physiological blockade is determined; The duration, magnitude, and rate of pressure change were compared with the pressure characteristic patterns of physiological blockade. When the comparison results match the pressure characteristic pattern of physiological blockage, it is determined that the liquid flow path at the nozzle outlet is physiologically blocked. When the comparison results do not match the pressure characteristic pattern of physiological blockade, the duration, pressure change amplitude, and pressure change rate are compared with the pressure characteristic pattern of non-physiological blockade. When the comparison results match the pressure characteristic pattern of non-physiological blockage, it is determined that the liquid flow path at the nozzle outlet is blocked by non-physiological blockage. If the comparison results do not match the pressure characteristic patterns of physiological blockage and non-physiological blockage, it is determined that the liquid flow path at the nozzle outlet is not blocked.

7. The method for controlling the liquid flow rate of an eyewash station according to claim 1, characterized in that, After the preset total delivery time has ended, the steps of calculating the additional delivery time required based on the preset total delivery time and the cumulative duration of liquid flow path obstruction, and controlling the micro pump to deliver additional liquid according to the additional time include: Obtain the preset single-time compensation delivery duration threshold and compensation delivery mode parameters; Compare the additional time with a single compensated delivery duration threshold; When the extra time exceeds the threshold for single compensation transport duration, the number of compensation transports and the duration of each compensation transport period are determined based on the extra time and the threshold for single compensation transport duration, and a preset transport interval is set between each compensation transport period. When the extra time is no greater than the threshold for the duration of a single compensation delivery, the extra time is taken as a single compensation delivery period, the number of compensation deliveries is determined to be one, and the extra time is the duration of the compensation delivery period. Adjust the delivery flow rate or jet mode of the micro pump according to the compensation delivery mode parameters; Repeat steps A1-A3 until the compensation delivery count is complete: A1. Control the micro pump to deliver liquid according to the duration of the current compensation delivery period; A2. After the current compensation delivery period ends, determine whether there are still unfinished compensation delivery periods; A3. If there is still an incomplete compensation delivery period, control the micro pump to pause delivery until a delivery interval has passed, then take the next compensation delivery period as the current compensation delivery period and return to step A1.

8. The method for controlling the liquid flow rate of an eyewash station according to claim 7, characterized in that, The steps for adjusting the injection mode of the micro pump based on the compensation delivery mode parameters include: Obtain the surface tension and spreading coefficient information of the currently delivered drug solution; Obtain physiological structural features of the target eye region; Based on the parameters of the compensation delivery mode, surface tension information, spreading coefficient information, eyeball curvature information, and tear film thickness information, the expected spreading path and coverage area of ​​the drug solution are determined by analyzing the hydrodynamic behavior of the drug solution in the target eye region. Based on the expected deployment path and coverage area, and combined with the compensation delivery mode parameters, target parameters for the micro pump are generated. Based on the target parameters, adjust the injection mode of the micro-pump injection mechanism to deliver the drug solution according to the expected spreading path and coverage area.

9. The method for controlling the liquid flow rate of an eyewash station according to claim 1, characterized in that, The target parameters include the injection angle parameter, the liquid column dispersion parameter, and the droplet size distribution parameter.

10. A liquid flow control system for an eyewash station, characterized in that, include: The acquisition module is used to acquire the fluid pressure signal at the nozzle outlet of the microfluidic eyewash station; The judgment module is used to determine whether the liquid flow path at the nozzle outlet is blocked based on the fluid pressure signal; The first control module is used to control the micro pump to pause or reduce the liquid flow rate when it is determined that the liquid flow path is blocked, and to record the duration of the liquid flow path being blocked. The second control module is used to control the micro pump to resume liquid delivery according to the original liquid flow rate when it is determined that the liquid flow path has been restored to unobstructed, and to accumulate the duration of the liquid flow path being blocked. The third control module is used to calculate the additional time required for supplementary delivery based on the preset total delivery time and the cumulative duration of liquid flow path blockage after the preset total delivery time has ended, and to control the micro pump to deliver additional liquid according to the additional time.

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