Dioptric dura-nucleus cataract dynamic intraocular pressure stable control ultrasonic emulsification system adaptive to dual-channel operation

Abstract

The invention discloses a dioptric scleroderma cataract dynamic intraocular pressure stable control ultrasonic emulsification system adaptive to a dual-channel operation, which comprises a host control unit, an ultrasonic emulsification handle, a perfusion and suction system, an intraocular pressure monitoring unit, a pressure balance module and a scleroderma fragmentation module, through cooperation of the intraocular pressure control module and the two-way operation type adaptive control module, a high-precision filling valve and a closed-loop suction pump are synchronously adjusted in real time according to anterior chamber built-in and external monitoring fusion data, and intraoperative intraocular pressure fluctuation is controlled within + / -2 mmHg; through pulse modulation and a self-adaptive negative pressure curve of the hardcore fragmentation enhancement module, the stability of the anterior chamber is ensured while the hardcore fragmentation efficiency is improved; fluid dynamics and energy parameters can be automatically optimized according to conventional incisions or micro incisions; according to the system, the anterior chamber stability problem in the high-difficulty cataract surgery is solved.

Description

Technical Field

[0001] This invention relates to the field of phacoemulsification technology, and more particularly to a dynamic intraocular pressure stabilization control phacoemulsification system for refractive hard cataracts adapted to dual-pathway procedures. Background Technology

[0002] Currently, in order to achieve less surgical trauma and faster postoperative recovery, cataract surgery has developed into two approaches: the conventional approach based on the limbal incision and the dual-pathway approach based on the clear cornea micro-incision. Compared with the former, the dual-pathway approach has a smaller incision and less interference with the corneal tissue structure. Existing phacoemulsification systems all provide energy release modes for different nuclear hardness and basic perfusion / aspiration (I / A) control functions. Some systems are also equipped with basic intraocular pressure monitoring devices to maintain anterior chamber intraocular pressure during surgery.

[0003] Existing systems are mostly set to static or semi-static modes. When switching between different surgical pathways, key parameters such as ultrasound energy release mode, perfusion flow rate, and aspiration negative pressure often require manual adjustment by the surgeon based on experience. They lack automatic adaptation functions for different incision hydrodynamic characteristics (such as changes in the outflow resistance of perfusion fluid under micro-incisions), which can easily lead to pressure fluctuations in the anterior chamber during surgery, thereby increasing the risk of corneal endothelial damage. At the same time, when dealing with hard nuclei, increasing ultrasound energy and negative pressure to ensure fragmentation efficiency often contradicts the requirement to maintain stable low pressure in the anterior chamber. Existing systems lack the ability to monitor and control intraocular pressure in real time, and sudden increases or decreases in intraocular pressure are difficult to avoid, which may lead to complications such as choroidal leakage or inadequate perfusion injury.

[0004] Therefore, in response to the problems mentioned above, this invention proposes a dynamic intraocular pressure stabilization control phacoemulsification system for refractive hard cataract surgery adapted to dual-pathway procedures. Summary of the Invention

[0005] To overcome the shortcomings of existing phacoemulsification systems in adapting to dual-pathway procedures and in achieving both high accuracy and stability of intraocular pressure control during hard cataract surgery, this invention proposes a dynamic intraocular pressure stabilization control phacoemulsification system for refractive hard cataract surgery adapted to dual-pathway procedures, which aims to achieve high safety and high precision throughout the entire refractive hard cataract surgery process.

[0006] The technical solution of this invention is: a dynamic intraocular pressure stabilization control phacoemulsification system for refractive hard-core cataract surgery adapted to dual-pathway procedures, comprising:

[0007] The main control unit integrates an intraocular pressure control module and a dual-pathway surgical adaptation control module.

[0008] The phacoemulsification handpiece has a switchable dual-channel interface at its front end, including a conventional phacoemulsification channel for limbal incisions and a micro-incision phacoemulsification channel for clear corneal incisions.

[0009] The infusion and aspiration system includes independently controlled infusion and aspiration lines. The infusion line is equipped with a flow regulating valve with a flow regulation resolution of 0.1 ml / min, and the aspiration line is equipped with a negative pressure sensor and a speed regulating pump with a speed control accuracy of ±1 RPM.

[0010] The intraocular pressure monitoring unit includes an anterior chamber pressure sensor and an intraocular pressure monitor, and the data from both are fed back to the main control unit in real time.

[0011] The pressure balancing module includes a multi-stage buffer gas-liquid exchange chamber located between the infusion bottle and the anterior chamber, and a servo controller that adjusts the infusion fluid flow rate in real time based on changes in anterior chamber pressure. The servo controller is preferably a logic controller based on a field-programmable gate array (FPGA) to achieve ultra-high response PID control.

[0012] The hard core fragmentation module is integrated into the ultrasonic emulsification handpiece. It includes a pulse-modulated ultrasonic energy output circuit that adjusts in real time according to the core hardness and a negative pressure rise curve that is automatically matched according to the core hardness gradation. The pulse-modulated ultrasonic energy output circuit can generate variable waveforms (such as square wave and sine wave modulation), and its peak power is adjustable from 0 to 120% to match different needs from soft core to extremely hard core.

[0013] The intraocular pressure control module adjusts the perfusion flow rate and aspiration negative pressure in real time according to the trend of anterior chamber pressure changes, so that the intraocular pressure fluctuation range is controlled within ±2mmHg; the dual-pathway surgical adaptation control module adjusts the ultrasound energy release mode, perfusion flow limit and negative pressure ramp-up rate according to the selected path.

[0014] Preferably, the anterior chamber pressure sensor in the intraocular pressure monitoring unit is integrated into the emulsification handle or independent infusion cannula, with a sampling frequency of not less than 200Hz and a measurement accuracy of 0.5mmHg. The pressure sensor is preferably a MEMS piezoresistive sensor with a sensor head diameter of not more than 1.2m.

[0015] Preferably, the multi-stage buffer gas-liquid exchange chamber in the pressure balance module includes at least two elastic buffer membrane chambers connected in series, with the chambers connected by flow-limiting holes, and the volume of each buffer membrane chamber can be adjusted within the range of 5-15 ml.

[0016] It is worth noting that the elastic buffer membrane is made of a superelastic nickel-titanium alloy, and its deformation is linearly related to the pressure, which can effectively absorb instantaneous pressure fluctuations caused by suction pulses or operator operations.

[0017] Preferably, the servo controller adopts a fuzzy PID control algorithm, whose input variables include the instantaneous value of the anterior chamber pressure, the rate of change of pressure, and the acceleration of pressure change, and whose output variables are the opening degree of the flow regulating valve of the infusion line and the speed of the speed regulating pump of the suction line.

[0018] It is worth noting that the fuzzy PID algorithm includes a fuzzy rule library optimized for the dynamic characteristics of the anterior chamber, such as "if the pressure is negative and the rate of change is positive, then the pump speed is increased significantly and the valve is fine-tuned".

[0019] Preferably, the pulse-modulated ultrasonic energy output circuit of the hard core fragmentation module includes an adjustable frequency pulse generator, whose pulse frequency can be adjusted in the range of 30-80Hz according to the nuclear hardness grade, and the pulse duty cycle is positively correlated with the nuclear hardness.

[0020] It is worth noting that the system's built-in nucleus hardness grading (LOCS III grading) and pulse parameters are mapped as follows: for Class II-III nuclei, the pulse frequency is set to 40-50Hz and the duty cycle to 30-40%; for Class IV and above hard nuclei, the pulse frequency can be increased to 60-80Hz and the duty cycle to 50-70%, thereby achieving more efficient fragmentation and reducing thermal damage to tissues caused by continuous energy release through high frequency.

[0021] Preferably, the negative pressure rise curve includes three rising stages: the first stage is a linear and slow rise, the second stage is an exponentially accelerated rise, and the third stage is a plateau maintenance stage adjusted according to the stability of the anterior chamber.

[0022] It is worth noting that the specific parameters are as follows: The slope (negative pressure rise rate) of the first stage is set to a low value (e.g., 10 mmHg / s) and lasts for about 0.5 seconds to ensure that the nucleus is stably adsorbed. The time constant of the second stage is set according to the estimated size of the nucleus so that the negative pressure can quickly reach 80-90% of the preset target value. The third stage enters dynamic maintenance. If the anterior chamber pressure is stable, the negative pressure slowly reaches the 100% target value. If the anterior chamber pressure fluctuates more, the rise of negative pressure is paused or even slightly decreased.

[0023] Preferably, the dual-pathway surgical adaptation control module reduces the upper limit of perfusion flow by 30-40% in the micro-incision emulsification path and adjusts the ultrasound energy release mode to a high-frequency low-amplitude pulse mode.

[0024] Preferably, the system also includes an anterior chamber stability early warning unit, which will activate the infusion compensation mechanism and issue an audio-visual alarm when it detects that the anterior chamber pressure changes by more than 80% of a preset threshold within 0.5 seconds.

[0025] It is worth noting that the preset threshold can be customized by the operator according to the patient's condition (the default value is 4 mmHg). The perfusion compensation mechanism refers to the instantaneous increase of the perfusion flow rate by a preset compensation amount (such as 50% of the base flow rate) while maintaining the current aspiration settings, for a short period of time (1-2 seconds), so as to quickly restore the anterior chamber volume. The audiovisual alarms include a red flashing light on the control panel and a specific prompt sound.

[0026] Preferably, the system also includes a control panel with tactile feedback, which can simulate the trend of anterior chamber pressure changes in real time and indicate the current intraocular pressure fluctuation status through vibration intensity.

[0027] The beneficial effects of this invention are:

[0028] 1. This invention achieves dynamic and stable control of anterior chamber pressure through the synergy of an intraocular pressure control module and a dual-pathway surgical adaptation control module. The system utilizes data fusion from anterior chamber micro-sensors and external monitoring instruments, and through synchronous adjustment of the flow valve and feedback pump by a servo controller, it can strictly control intraoperative intraocular pressure fluctuations within ±2 mmHg, thereby effectively avoiding complications such as choroidal leakage or corneal endothelial damage caused by sudden changes in intraocular pressure. At the same time, it automatically switches the preset fluid dynamics parameter package according to the selected surgical path (conventional incision or micro-incision), and intelligently adjusts the upper limit of perfusion flow and energy release mode. Thus, while ensuring absolute anterior chamber stability, it seamlessly adapts to the fluid dynamic differences caused by different incision sizes, thereby solving the anterior chamber stability problem caused by the reliance on manual experience and parameter adjustment lag during surgical procedure switching in traditional systems.

[0029] 2. The hard nucleus fragmentation module of this invention achieves synergy between hard nucleus processing efficiency and intraocular pressure stability through the combination of its adjustable frequency pulse generator and three-segment adaptive negative pressure rise curve. For different nucleus hardness grades, the system automatically matches high-frequency or low-frequency pulses with corresponding duty cycles. While achieving efficient fragmentation, it reduces the heat accumulation of tissue by continuous ultrasound through pulsed energy release. Furthermore, its negative pressure curve also has a plateau maintenance phase that dynamically adjusts according to anterior chamber stability, enabling real-time linkage between the high negative pressure adsorption of the hard nucleus and the pressure compensation of the perfusion system. Thus, even in the high negative pressure operation phase that pursues high fragmentation efficiency, the system can still maintain anterior chamber filling through rapid response. Attached Figure Description

[0030] Figure 1 The diagram shown is a schematic representation of the system framework of this invention.

[0031] Figure 2 The diagram shown is a schematic of the negative pressure rise curve of the present invention. Detailed Implementation

[0032] To make the objectives, technical solutions, and advantages of the embodiments of the present invention clearer, 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 some embodiments of the present invention, but 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.

[0033] Please see Figure 1 The present invention provides an embodiment:

[0034] The surgeon inputs or selects key parameters via the main control panel, such as the patient's nuclear hardness grade (e.g., using the LOCS III standard, divided into grades I to V), the proposed surgical approach (conventional limbal incision, typically 2.8-3.0 mm; or clear corneal micro-incision, typically 1.8-2.2 mm), and the target range for intraocular pressure control. The dual-pathway surgical adaptation control module is then activated, calling upon the built-in fluid dynamics model database based on the selected approach. This database stores a large number of parameter combinations based on computational fluid dynamics simulations and previous clinical trials. For example, for the micro-incision approach, the model predicts that its infusion fluid outflow resistance is about 35-50% higher than that of the conventional incision. Therefore, it automatically lowers the system's default infusion flow rate limit and slows down the rate of increase in suction negative pressure. At the same time, it presets the ultrasound energy release mode to a "high-frequency, low-amplitude" pulse mode to adapt to the smaller anterior chamber operating space and higher stability requirements.

[0035] After the surgery begins, the intraocular pressure monitoring unit activates. The built-in miniature pressure sensor in the anterior chamber (integrated into the tip of the irrigation cannula) provides the most direct intracavitary pressure signal, with a sampling frequency of up to 200Hz, ensuring the capture of millisecond-level pressure fluctuations caused by aspiration pulses, nucleus movement, or surgeon manipulation. Simultaneously, the intraocular pressure monitor provides auxiliary monitoring data, primarily used to verify and calibrate long-term drift of the built-in sensor, and to provide backup data in special circumstances (such as temporary sensor failure). The data from both sources are then fused using a Kalman filter algorithm within the main unit. This algorithm can evaluate the noise level and reliability of the two signal sources in real time, dynamically adjust the weights, and output an optimally estimated anterior chamber pressure value with a comprehensive accuracy better than 0.5 mmHg and a data update latency of less than 20 milliseconds.

[0036] This optimal pressure estimate, along with its first derivative (rate of change) and second derivative (acceleration of change), is sent in real time to the intraocular pressure control module. This module is a fuzzy PID controller. Unlike traditional PID controllers, it incorporates a fuzzy rule base designed specifically for the physical characteristics of the human anterior chamber (viscoelasticity, finite volume, nonlinear response). For example, its rules include: "If the current pressure is below the target value and is rapidly decreasing (large negative rate of change), then significantly increase the perfusion flow rate and moderately decrease the suction pump speed." Based on these rules and a precise mathematical model, the controller calculates two independent but coordinated control commands.

[0037] One command is sent to the servo controller in the pressure balancing module, which drives the piezoelectric ceramic flow regulating valve to adjust the valve opening with micron-level precision, thereby controlling the instantaneous flow rate of the perfusion fluid. Simultaneously, another command is sent to the speed-regulating pump in the perfusion suction system to adjust its rotational speed, thereby controlling the level of suction negative pressure. In this step, these two adjustments are synchronized and linked. For example, if the system predicts that the operation of a high-negative-pressure adsorption nucleus may cause anterior chamber collapse, it will "pre-command" the perfusion valve to increase its opening in advance as feedforward compensation, rather than waiting for the pressure to drop before providing feedback relief.

[0038] The ultrasonic emulsification handpiece and its integrated hard nucleus fragmentation module are responsible for fragmenting and aspirating the lens nucleus. When the operator steps into the ultrasonic emulsification mode, the handpiece does not immediately operate at a fixed power. The hard nucleus fragmentation module first calls the corresponding pulse modulation parameters according to the preset nucleus hardness level. For a level IV hard nucleus, a powerful pulse mode with a frequency of 60Hz and a duty cycle of 60% may be activated. At the same time, the negative pressure rise curve is activated. When the needle contacts and attempts to aspirate the nucleus, the aspiration negative pressure does not rise linearly, but follows this three-segment adaptive curve. In the first stage (approximately 0-0.5 seconds), the negative pressure rises linearly at a low rate to 30% of the set value. This is to gently and stably grip the nucleus, preventing escape or anterior chamber turbulence due to excessive initial adhesion. Once stable adhesion is achieved, the system detects that the anterior chamber pressure remains stable and immediately enters the second stage. In this stage, the negative pressure rapidly climbs exponentially to 90% of the target value. Finally, in the third stage, the system fine-tunes based on real-time intraocular pressure feedback, ensuring the negative pressure smoothly reaches and maintains at 100% of the target value, or remains at a slightly lower value as needed for stability. Throughout the entire process, the intraocular pressure control module runs in the background, ensuring anterior chamber stability even during high-negative-pressure hard-core processing.

[0039] Please see Figure 2For example, in the first stage (0-0.5 seconds), the curve rises slowly and linearly at a rate of about 10-20 mmHg / s. After reaching 10-15% of the preset total target negative pressure (e.g., 80 mmHg), it enters the second stage (0.5-1.5 seconds). At this time, the curve rises exponentially. When it reaches 80-90% of the preset total target negative pressure, it enters the third stage (after 1.5 seconds). At this time, the curve rises at a significantly slower rate and eventually becomes stable, as shown in the table below.

[0040] Curve phase Phase 1 Phase Two Phase Three Time range 0-0.5 0.5-1.5 1.5 - End negative pressure range 0 → 10-15% target value 10-15% → 80-90% target value 80-90% → 100% target value or dynamic adjustment Rising characteristics constant low slope Exponential acceleration Dynamically adjusted based on intraocular pressure feedback

[0041] The anterior chamber stability warning unit continuously monitors the trend of intraocular pressure changes. Once it detects that the pressure change exceeds 80% of the preset safety threshold in a very short time (such as 0.5 seconds), it will immediately activate a two-level response: the first-level response is to automatically execute a preset "pressure shock compensation" program to instantly increase the perfusion flow; the second-level response is to simultaneously issue visual (screen flashing), audible (specific tone), and tactile (control panel vibration) alarms to the surgeon.

[0042] This invention provides Embodiment 1:

[0043] This embodiment is used to verify whether the present invention, when adapted to both conventional and micro-incision approaches, has a higher ability to maintain intraocular pressure stability in the anterior chamber than the traditional static system.

[0044] This embodiment uses 60 isolated pig eye models, randomly divided into four groups of 15 eyes each. The results are validated through a four-group comparative experiment. Specifically:

[0045] Group 1 used the present invention and set it to "conventional incision mode" to perform phacoemulsification surgery with a 3.0mm limbal incision.

[0046] Group 2 used the present invention, set to "micro-incision mode", to perform phacoemulsification surgery through a 2.2mm clear corneal incision.

[0047] Group 3 used a traditional static system, where the surgeon manually set parameters (infusion bottle height, flow rate, negative pressure curve) based on experience and performed a 3.0mm incision.

[0048] Group 4 used a traditional static system, with the surgeon manually adjusting parameters (mainly reducing the height of the infusion bottle to accommodate the micro-incision) to perform a 2.2mm incision surgery.

[0049] All surgeries in this embodiment were performed by the same doctor, simulating the Level IV hard emulsification process. Pressure sensors were used to record the intraocular pressure in the anterior chamber throughout the entire surgical process. The analysis focused on the standard deviation of intraocular pressure (SD, reflecting the magnitude of fluctuation), the percentage of time the intraocular pressure exceeded the safe range (defined as the set value ± 4 mmHg), and the maximum fluctuation amplitude of intraocular pressure (peak value - trough value).

[0050] Group Group A Group B Group C Group D Mean intraocular pressure (mmHg) 25.1 24.8 24.9 23.5 Standard deviation of intraocular pressure (mmHg) 0.8 2.5 1.1 3.8 Time spent outside the safe range (%) 1.2% 18.7% 3.5% 35.4% Maximum fluctuation range (mmHg) 5.1 12.8 6.3 18.2

[0051] From the table above, we can see that:

[0052] (1) Regardless of whether it is a conventional incision or a micro-incision, the standard deviation of intraocular pressure, the time ratio of out-of-range and the maximum fluctuation amplitude of the present invention are significantly higher than those of the traditional static system. This indicates that the intraocular pressure control mechanism of the present invention can effectively suppress intraocular pressure disturbances caused by surgical operations.

[0053] (2) Although the stability indicators of the present invention under micro-incision (group B) are lower than those under conventional incision (group A), the difference is small and still remains at a high level. However, when the traditional system is switched to micro-incision (group D), the effect is severely reduced and the indicators drop significantly, indicating that it lacks effective adaptation ability. The effect of relying on the surgeon's experience to adjust is limited and may introduce new problems (such as low mean intraocular pressure).

[0054] (3) The present invention controls the time of intraocular pressure out-of-control (exceeding ±4 mmHg) to within 3.5%, which shows that the surgery is in a highly stable and safe environment for most of the time, thereby greatly reducing the risk of complications caused by sudden changes in intraocular pressure.

[0055] This invention provides Embodiment 2:

[0056] This embodiment is used to verify whether the present invention can improve emulsification efficiency without sacrificing or even improving the safety of the operation (indicating anterior chamber stability and tissue thermal damage) when dealing with highly complex hard cores.

[0057] In this embodiment, 40 high-hardness simulated cores (polymer material, hardness equivalent to LOCS IV-V) were prepared and randomly implanted into 40 excised pig eyes, divided into two groups, specifically:

[0058] The experimental group used this invention, and the system ran according to preset hard core parameters.

[0059] The control group used a traditional static system, while the surgeon used what he considered to be the most effective high-power pulse + high negative pressure mode.

[0060] All surgeries in this embodiment were performed by the same physician. The effective ultrasound time (EPT, the total time from ultrasound initiation to complete removal of the nucleus), cumulative energy released (CDE, unit: %), the standard deviation of the mean intraocular pressure throughout the surgery, and the highest temperature at the corneal incision site monitored by an infrared thermal imager were recorded and compared.

[0061] index experimental group control group Effective ultrasound time (EPT, s) 45.2±5.1 58.7±8.3 Cumulative energy released (CDE, %) 18.5±2.3 25.8±4.1 Standard deviation of intraocular pressure (mmHg) 1.0±0.2 2.8±0.6 Maximum temperature at corneal incision site (°C) 31.5±0.8 36.2±1.5

[0062] From the table above, we can see that:

[0063] (1) The effective ultrasound time of the experimental group was shortened by about 23% compared with that of the control group, and the cumulative energy released (CDE) was reduced by about 28%. This indicates that the optimized high-frequency pulse modulation of the hard core fragmentation enhancement module of the present invention generates a more efficient impact, making the core more easily fragmented. At the same time, its three-segment adaptive negative pressure curve ensures that the core is firmly adsorbed and efficiently removed, reducing the ineffective ultrasound time caused by the escape or unstable adsorption of the core. The lower CDE directly means less energy enters the eye.

[0064] (2) While efficiency was greatly improved, the standard deviation of intraocular pressure in the experimental group was much lower than that in the control group, indicating that the intraocular pressure control module could still maintain the stability of the anterior chamber even when dealing with the high negative pressure scenario required by the hard core.

[0065] (3) The highest temperature of the corneal incision in the experimental group was controlled within the safe threshold of 32℃, which was significantly lower than the 36.2℃ of the control group. This is because the shorter EPT and lower CDE reduced the total heat generation. At the same time, when the invention is used in "micro-incision mode" or high energy, it will automatically adopt "high frequency and low amplitude" pulses. This mode generates less heat per unit time and has a longer heat dissipation interval, thereby effectively avoiding high temperature burns to the incision tissue and promoting the sealing and healing of the incision after surgery.

[0066] The above are merely preferred embodiments of the present invention and are not intended to limit the present invention in any other way. Any person skilled in the art may make changes or modifications to the above-disclosed technical content to create equivalent embodiments that can be applied to other fields. However, any simple modifications, equivalent changes, and modifications made to the above embodiments based on the technical essence of the present invention without departing from the scope of the present invention shall still fall within the protection scope of the present invention.

Claims

1. A dynamic intraocular pressure stabilization and phacoemulsification system for refractive hard-core cataract surgery adapted to dual-pathway procedures, characterized in that: Including: The main control unit integrates an intraocular pressure control module and a dual-pathway surgical adaptation control module. The phacoemulsification handpiece has a switchable dual-channel interface at its front end, including a conventional phacoemulsification channel for limbal incisions and a micro-incision phacoemulsification channel for clear corneal incisions. The infusion and suction system includes independently controlled infusion and suction lines, wherein the infusion line is equipped with a flow regulating valve and the suction line is equipped with a negative pressure sensor and a speed regulating pump. The intraocular pressure monitoring unit includes an anterior chamber pressure sensor and an intraocular pressure monitor, and the data from both are fed back to the main control unit in real time. The pressure balancing module includes a multi-stage buffer gas-liquid exchange chamber located between the infusion bottle and the anterior chamber, and a servo controller that adjusts the infusion fluid flow rate in real time based on changes in anterior chamber pressure. The hard core fragmentation module, integrated into the ultrasonic emulsification handpiece, includes a pulse-modulated ultrasonic energy output circuit that adjusts in real time according to the core hardness and a negative pressure rise curve that is automatically matched according to the core hardness grading.

2. The dynamic intraocular pressure stabilization control phacoemulsification system for refractive hard-core cataract surgery adapted to dual-pathway procedures as described in claim 1, characterized in that: The intraocular pressure control module adjusts the perfusion flow rate and aspiration negative pressure in real time according to the trend of anterior chamber pressure changes, so that the intraocular pressure fluctuation range is controlled within ±2mmHg; the dual-pathway surgical adaptation control module adjusts the ultrasound energy release mode, perfusion flow limit and negative pressure ramp-up rate according to the selected path.

3. The dynamic intraocular pressure stabilization control phacoemulsification system for refractive hard-core cataract surgery adapted to dual-pathway procedures as described in claim 1, characterized in that: The anterior chamber pressure sensor in the intraocular pressure monitoring unit is integrated into the emulsification handle or independent infusion cannula, with a sampling frequency of not less than 200Hz and a measurement accuracy of 0.5mmHg.

4. The dynamic intraocular pressure stabilization control phacoemulsification system for refractive hard-core cataract surgery adapted to dual-pathway procedures as described in claim 1, characterized in that: The multi-stage buffer gas-liquid exchange chamber in the pressure balance module includes at least two elastic buffer membrane chambers connected in series, with the chambers connected by flow-limiting holes. The volume of each buffer membrane chamber can be adjusted within the range of 5-15 ml.

5. The dynamic intraocular pressure stabilization control phacoemulsification system for refractive hard-core cataract surgery adapted to dual-pathway procedures as described in claim 1, characterized in that: The servo controller uses a fuzzy PID control algorithm. Its input variables include the instantaneous value of the anterior chamber pressure, the rate of change of pressure, and the acceleration of pressure change. The output variables are the opening degree of the flow regulating valve in the infusion line and the speed of the speed regulating pump in the suction line.

6. The dynamic intraocular pressure stabilization control phacoemulsification system for refractive hard-core cataract surgery adapted to dual-pathway procedures as described in claim 1, characterized in that: The pulse-modulated ultrasonic energy output circuit of the hard core fragmentation module includes an adjustable frequency pulse generator, whose pulse frequency can be adjusted in the range of 30-80Hz according to the nuclear hardness grade, and the pulse duty cycle is positively correlated with the nuclear hardness.

7. The dynamic intraocular pressure stabilization control phacoemulsification system for refractive hard-core cataract surgery adapted to dual-pathway procedures as described in claim 1, characterized in that: The negative pressure rise curve includes three stages: the first stage is a linear and slow rise, the second stage is an exponentially accelerated rise, and the third stage is a plateau maintenance stage adjusted according to the stability of the anterior chamber.

8. The dynamic intraocular pressure stabilization control phacoemulsification system for refractive hard-core cataract surgery adapted to dual-pathway procedures as described in claim 1, characterized in that: The dual-pathway surgical adaptation control module will reduce the upper limit of perfusion flow by 30-40% in the micro-incision emulsification path and adjust the ultrasound energy release mode to a high-frequency low-amplitude pulse mode.

9. The dynamic intraocular pressure stabilization control phacoemulsification system for refractive hard-core cataract surgery adapted to dual-pathway procedures as described in claim 1, characterized in that: The system also includes an anterior chamber stability early warning unit, which will activate the infusion compensation mechanism and issue an audio-visual alarm when it detects that the anterior chamber pressure changes by more than 80% of a preset threshold within 0.5 seconds.

10. The dynamic intraocular pressure stabilization control phacoemulsification system for refractive hard-core cataract surgery adapted to dual-pathway procedures as described in claim 1, characterized in that: The system also includes a control panel with haptic feedback, which can simulate the trend of anterior chamber pressure changes in real time and indicate the current intraocular pressure fluctuation status through vibration intensity.

Images