Liquid plasma activating treatment device

Abstract

The utility model relates to a liquid plasma activating treatment device which mainly comprises a containing cavity and a plasma discharging structure, and the containing cavity is of a hollow cylindrical structure and is used for containing a liquid container; the plasma discharge structure is arranged on the inner wall of the accommodating cavity; the high-voltage line interface connects the plasma discharge structure and the high-voltage pulse power supply. The device adopts a non-contact activation design, takes the tube wall of a liquid container as a dielectric barrier layer, and generates plasma through dielectric barrier discharge, so that active components penetrate through the tube wall to act on internal liquid, and direct contact between an electrode and the liquid is avoided. A limiter is arranged at the bottom of the containing cavity and can adjust the position of the liquid container to control the liquid level. The device can further comprise a liquid level sensor, a temperature sensor, a temperature control component, a gas circulation path and a control system, and accurate control over the liquid level height, the treatment temperature and the gas environment is achieved. And by arranging a plurality of parallel containing cavities, the device can also realize high-throughput treatment.

Description

Technical Field

[0001] This application relates to the field of plasma processing technology, and in particular to a liquid plasma activation processing device. Background Technology

[0002] Plasma activation technology, as a non-thermodynamic equilibrium surface treatment method, utilizes high-energy active particles (such as electrons, ions, and free radicals) generated by gas ionization to physically etch, introduce chemical functional groups, and immobilize biomolecules on material surfaces, thereby enhancing biocompatibility, antibacterial properties, and tissue integration capabilities. Low-temperature plasma treatment can form hydrophilic hydroxyl (-OH) and amino (-NH2) groups on the surface of biomaterials, promoting cell adhesion and growth.

[0003] Traditional plasma applications primarily involve direct treatment of living organisms, which suffers from limitations such as small treatment area, shallow penetration depth, short effective time, and insufficient stability, thus restricting their applicability and effectiveness. To address this, researchers have developed plasma-activated medium technology. This technology uses plasma to activate media materials such as gases, liquids, or hydrogels, loading active particles into the medium material before application, thus shifting plasma biomedicine from direct to indirect treatment. The application scope of this technology has expanded from simple material surface modification to the field of liquid activation, generating plasma-activated liquids (PALs) rich in reactive oxygen species (ROS) through the interaction between plasma and liquid media. The core function of plasma-activated liquids stems from their high concentration of reactive oxygen species (H₂O₂, O₂). - (NO, ·OH, etc.) and reactive nitrogen (RNS) components (NO, ONOO) - These active ingredients endow plasma-activated liquids with new properties and applications, and since they have no significant toxicity to mammalian cells, they show great promise in the biomedical field.

[0004] Despite the potential of plasma-activated liquid technology, current technologies still face obstacles in medical and healthcare applications. The primary issue is that existing plasma activation devices activate liquids exposed to air through direct contact, lacking a sterile, non-contact environment. During activation, dust particles, microorganisms, and material debris inevitably fall into the liquid, causing contamination and making it difficult to guarantee the purity and sterility of the activated solution. This limits the clinical application of plasma activation technology.

[0005] Existing device designs typically lack integrated aseptic environment maintenance systems, such as high-efficiency particulate air (HEPA) filters or inert gas protection systems. This makes the activation process susceptible to environmental factors, leading to difficulties in ensuring the consistency and reliability of the final product. Secondary contamination during material transfer is another concern. Even with some environmental control during the plasma activation stage, current technologies lack end-to-end aseptic protection measures from activation solution collection and dispensing to storage. The activation solution may be contaminated during material transfer, affecting the sterility of the final product. Inaccurate temperature control is also a concern. While studies have proposed plasma atomization sterilization devices below 80°C suitable for processing heat-sensitive materials, more precise temperature control strategies are needed for heat-sensitive active ingredients in biomedical applications. These issues collectively limit the clinical application of plasma-activated liquid technology in the biomedical field, especially when used as medical preparations or devices, where strict requirements exist for product sterility, stability, and consistency. Therefore, to realize the clinical application of plasma-activated liquid formulation technology, there is an urgent need to develop a plasma activation device that ensures a sterile and contactless activation process. Utility Model Content

[0006] The purpose of this application is to achieve plasma activation outside the liquid container by integrating a plasma discharge structure into the cavity wall in a non-contact design, thereby avoiding direct contact and ensuring a sterile environment for the activation process. This device adapts to liquid containers of different sizes through a limiter structure and utilizes a gas circulation and temperature control system to achieve precise control of the activation environment, meeting the requirements for sterile activation of liquid preparations in the medical and health fields.

[0007] The purpose of this application is achieved through the following technical solution: the liquid plasma activation treatment device of this application includes a containment cavity, a plasma discharge structure, a high-voltage line interface, and a low-voltage grounding line interface;

[0008] The cavity is a hollow cylindrical structure used to hold liquid containers;

[0009] The plasma discharge structure is disposed on the inner wall of the receiving cavity, and the plasma discharge structure includes a capacitor electrode sheet or an inductor.

[0010] The power interface is connected to the plasma discharge structure and is used to electrically connect the plasma discharge structure to a high-voltage pulse power supply.

[0011] The bottom of the receiving cavity is provided with a limiter, which moves within the receiving cavity to adjust the length of the liquid container within the receiving cavity.

[0012] In one embodiment, a plurality of the receiving cavities are included.

[0013] In one embodiment, the receiving cavity is arranged vertically.

[0014] In one embodiment, a liquid level sensor is also included, which detects the liquid level in the liquid container and is used to adjust the position of the limiter.

[0015] In one embodiment, the plasma discharge structure is embedded in the inner wall of the receiving cavity.

[0016] In one embodiment, the plasma discharge structure is detachably disposed on the inner wall of the receiving cavity.

[0017] In one embodiment, the plasma discharge structure is disposed on the outer wall of the liquid container.

[0018] In one embodiment, a temperature sensor and a temperature control component are also included, the temperature sensor being used to detect the temperature of the receiving cavity and the temperature control component being used to adjust the temperature of the receiving cavity.

[0019] In one embodiment, a gas circulation passage is further included, the gas outlet of which is at the bottom of the receiving cavity, and the gas inlet of which is at the opening of the receiving cavity.

[0020] In one embodiment, the system further includes a control system, an interactive interface, and a processing unit.

[0021] Compared with the prior art, this application has the following beneficial effects:

[0022] By integrating the plasma discharge structure into the inner wall of the containment cavity, a non-contact activation method is formed, avoiding direct contact between the electrodes and the liquid. This allows for direct use of the liquid container without the need for liquid transfer, providing a sterile activation environment that meets medical and hygiene requirements for liquid formulations. The movable limiter structure at the bottom of the containment cavity allows a single device to be adapted to and securely fixed to liquid containers of various heights and sizes, improving the device's versatility.

[0023] The integrated temperature sensor and temperature control components of the device can detect and adjust the temperature inside the containment chamber in real time, preventing excessively high or low temperatures from affecting plasma activation efficiency and the stability of active components in the liquid, thus improving the consistency and reproducibility of the processing. Furthermore, the synergistic effect of the liquid level sensor and limiter allows for automatic adjustment of the limiter position based on the liquid level detection, ensuring that liquid containers of different sizes are within the optimal plasma action range, guaranteeing uniform activation. In addition, the design of the plasma discharge structure being detachably mounted on the inner wall of the containment chamber facilitates subsequent cleaning, maintenance, or component replacement, contributing to the long-term maintenance of the device's performance.

[0024] By introducing a control system, interactive interface, and processing unit, multiple parameters (such as temperature and liquid level) in the plasma activation process can be centrally monitored and automatically controlled, reducing human error, improving production efficiency and batch consistency, and providing a foundation for large-scale production of medical preparations. Attached Figure Description

[0025] Figure 1 This is a cross-sectional structural schematic diagram of a liquid plasma activation treatment apparatus according to an embodiment of this application;

[0026] Figure 2 This is a top view of a liquid plasma activation treatment apparatus according to an embodiment of this application;

[0027] Figure 3 This is a schematic cross-sectional view of the liquid plasma activation treatment apparatus according to an embodiment of this application after placing the liquid container.

[0028] Explanation of reference numerals in the attached drawings: 101, main structure; 102, receiving cavity; 103, high-voltage line interface; 104, low-voltage grounding line interface; 105, high-voltage electrode plate; 106, low-voltage electrode ring; 107, electrical limit switch component; 108, temperature sensor; 109, liquid crystal display screen; 110, limit switch; 201, blood collection tube; 203, blood collection tube wall; 212, liquid preparation; HV is high-voltage line; LV is low-voltage grounding line. Detailed Implementation

[0029] To make the above-mentioned objectives, features, and advantages of this application more apparent and understandable, the specific embodiments of this application will be described in detail below with reference to the accompanying drawings. It should be understood that the specific embodiments described herein are for illustrative purposes only and are not intended to limit the scope of this application. Furthermore, it should be noted that, for ease of description, only the parts relevant to this application are shown in the accompanying drawings, not the entire structure. Based on the embodiments in this application, all other embodiments obtained by those skilled in the art without inventive effort are within the scope of protection of this application.

[0030] The terms “comprising” and “having”, and any variations thereof, used in this application are intended to cover non-exclusive inclusion. For example, a process, method, system, product, or apparatus that includes a series of steps or units is not limited to the steps or units listed, but may optionally include steps or units not listed, or may optionally include other steps or units inherent to such process, method, product, or apparatus.

[0031] In this document, the term "embodiment" means that a particular feature, structure, or characteristic described in connection with an embodiment may be included in at least one embodiment of this application. The appearance of this phrase in various places throughout the specification does not necessarily refer to the same embodiment, nor is it a separate or alternative embodiment mutually exclusive with other embodiments. It will be explicitly and implicitly understood by those skilled in the art that the embodiments described herein can be combined with other embodiments.

[0032] The core of this application lies in providing a liquid plasma activation treatment device that meets the sterility requirements of the medical and health fields. By constructing a closed or controlled plasma activation environment and employing a non-contact activation method, it effectively avoids the contamination problems that may be introduced by traditional direct contact processing, thereby ensuring the purity and sterility of the final plasma-activated liquid. The structure of the plasma activation treatment device will be described in detail below, along with various specific implementation methods and optional configurations of each component. Please refer to [link / reference]. Figures 1 to 3 The liquid plasma activation treatment device includes a receiving cavity 102, a plasma discharge structure, a high-voltage line interface 103, and a low-voltage grounding line interface 104. The receiving cavity 102 is a hollow cylindrical structure used to contain a liquid container. The plasma discharge structure is disposed on the inner wall of the receiving cavity 102 and includes a capacitor electrode plate or an inductor. The high-voltage line interface 103 is connected to the plasma discharge structure for electrically connecting the plasma discharge structure to a high-voltage pulse power supply. A limiter 110 is provided at the bottom of the receiving cavity 102. The limiter 110 moves within the receiving cavity 102 to adjust the length of the liquid container within the receiving cavity 102.

[0033] The receiving cavity 102 forms a hollow cylindrical receiving cavity 102, with an inner diameter of approximately 17 mm and a depth of approximately 10 cm. This size is designed to accommodate a standard medical blood collection tube 201, which serves as a liquid container. The plasma discharge structure is integrated into the inner wall of the receiving cavity 102 in a non-contact manner. Specifically, a high-voltage electrode plate is embedded in a groove on the inner wall approximately 1 cm deep from the opening, with a width of approximately 1 cm. This discharge structure can be specifically implemented as two arc-shaped metal electrode plates. The high-voltage electrode plate 105 has an arc consistent with the inner wall of the receiving cavity 102 to form a uniform electric field distribution. A ring-shaped low-voltage electrode ring 106 is embedded in a groove approximately 3 cm high from the bottom of the receiving cavity 102, with an inner diameter consistent with the inner wall of the receiving cavity 102. One high-voltage electrode 105 is fixedly installed, while the high-voltage electrode 105 near the temperature sensor 108 can move within a certain range through an electrical limit switch 107 on its back. This allows for fine-tuning to accommodate the slight differences in the diameter of the blood collection tubes 201, ensuring an appropriate distance between the electrode and the tube wall. The core of the design of embedding the discharge structure within the cavity wall is to achieve non-contact activation, so that the plasma discharge occurs inside the blood collection tube 201 and above the liquid preparation 212. The active components in the plasma directly act on the liquid preparation 212 inside the blood collection tube 201, thereby avoiding direct contact between the electrode and the liquid and fundamentally preventing contamination introduced by the electrode material.

[0034] The preferred discharge mode of this device is dielectric barrier discharge. In this configuration, the barrier medium is the wall of the blood collection tube 201 inserted into the receiving cavity 102. It is worth noting that conventional medical blood collection tubes 201 are made of insulating glass or polymer materials, which naturally act as the insulating dielectric layer in dielectric barrier discharge. When a high-frequency electric field is applied to the electrodes, the gas inside the blood collection tube 201 (usually air; for blood collection tubes 201 under negative pressure, the residual air layer of 0.5-0.8 atm above the liquid surface can serve as the ionization medium) is broken down to generate plasma. Utilizing the physical properties of existing medical containers, no additional barrier medium component is needed, simplifying the device structure. The discharge structure is not limited to dielectric barrier discharge; for example, replacing the metal electrode plates embedded in the inner wall with a metal coil surrounding or embedded in the outer wall of the receiving cavity 102 can transform the discharge mode into inductively coupled discharge. This mode may be suitable for scenarios with higher requirements for activation intensity and processing speed.

[0035] At the bottom of the receiving cavity 102, a piston limiter 110 is provided, which can be implemented as an arc-shaped rubber piston and extends to the outside of the receiving cavity 102 via a connecting handle. By pushing and pulling this handle, the height of the blood collection tube 201 inserted into the receiving cavity 102 can be precisely adjusted, so that the liquid level of the liquid preparation 212 to be activated in the blood collection tube 201 can be positioned slightly below the lower edge of the discharge structure. This ensures that the plasma activation area covers the main liquid part and may also facilitate the stable ionization of the gas medium above the liquid surface. To further improve the accuracy of control, a Hall sensor is integrated at the end of the long handle of the piston limiter 110. This sensor, in conjunction with a displacement-voltage conversion circuit, can convert the displacement of the piston (i.e., the blood collection tube 201) (directly related to the liquid level height) into a digital signal and display it, thereby realizing digital monitoring and feedback of the liquid level height and providing technical support for the controllability and reproducibility of the process.

[0036] The high-voltage line interface 103 and the low-voltage grounding line interface 104 are disposed on the outer wall of the insulating body, and are electrically connected internally to the plasma discharge structure (whether electrode sheet or coil) to introduce external high-voltage pulse power to the discharge structure. The entire device, through a combination of the above-mentioned technical features, particularly the non-contact discharge design, precise dimensional adaptation for specific medical containers, adjustable limiting mechanism, and liquid level monitoring, works together to meet the requirements for sterile activation of liquid preparation 212 in the medical and health field.

[0037] The interfaces are located on the outer wall of the insulating reactor, specifically implemented as three independent physical interfaces: two high-voltage line interfaces 103 connected to the two high-voltage electrode plates 105 respectively, and a low-voltage grounding line interface 104 connected to the annular low-voltage electrode ring 106. This design, which separates the high-voltage and low-voltage circuits at the physical interface, is a common electrical safety isolation measure in plasma equipment. Its function is to clearly define the high-voltage path and the grounding path, avoid the risk of short circuits due to wiring errors, and facilitate the operation of specific circuits during maintenance and debugging. The high-voltage interface and the low-voltage interface are functionally defined as being used to connect the high-voltage line and the low-voltage grounding line of the high-voltage pulse power supply output, respectively. In addition, some power supplies adopt a composite pulse control method. Through a clearly defined universal interface, users can flexibly select different models of plasma power supplies according to specific activation process requirements (e.g., the high electric field strength required for the generation of high-concentration active species, or the pulse frequency and waveform required for a specific discharge mode), thereby improving the configuration flexibility and scalability of the entire system, and also facilitating the integration of this activation treatment device as a standard module into more complex systems.

[0038] See Figures 1 to 3 The specific assembly is as follows:

[0039] The main structure 101 is a cylindrical shell made of polytetrafluoroethylene (PTFE) insulating material, approximately 12cm high and 35mm in outer diameter. The receiving cavity 102 is a hollow cylindrical cavity (inner diameter Φ17±0.1mm, depth 10cm) located inside the main body, used to accommodate the blood collection tube 201. The limiter 110 is an arc-shaped rubber piston head (diameter Φ17mm) placed at the bottom of the reaction chamber; a long handle (5cm in length) is connected to the bottom of the piston, extending through a sealing hole at the bottom of the reaction chamber to the outside of the vessel; a Hall sensor is integrated at the end of the long handle, and the piston displacement is displayed in real time on an LCD screen via a displacement-voltage conversion circuit. The plasma discharge structure includes two arc-shaped 316L stainless steel sheets (10mm wide) 105, each covered with a 3μm Al2O3 ceramic coating, embedded in a groove 1cm deep in the inner wall of the reaction chamber from the vessel opening; a 316L stainless steel ring 106 (approximately 5mm wide) also covered with a 3μm Al2O3 ceramic coating; and an electrical limit switch 107, a short, rubber-insulated handle (1.5cm long) connected to the back of the low-voltage electrode, passing through a small hole in the vessel wall to allow manual fine-tuning of the electrode position (diameteral range ±4mm). An integrated miniature temperature sensor 108, a PT100 type sensor, is embedded in the inner wall of the reaction chamber 1cm below the discharge structure. The high-voltage line interface 103 and the low-voltage grounding line interface 104 are magnetic waterproof connectors with embedded opto-isolation modules, directly connected to the high-voltage electrode sheet 105 and the low-voltage electrode ring 106. The LCD screen 109 is a 1.28-inch segment display (driven by Synaptics S1D15G10). It receives displacement signals and temperature data from the Hall sensor via the SPI bus and displays the liquid level (accuracy ±0.1mm), temperature (±0.5℃), and timing parameters in real time.

[0040] In a specific embodiment, multiple receiving cavities 102 can be further provided, specifically 5-10 receiving cavities 102 integrated in parallel. Each receiving cavity 102 can independently accommodate a standard medical blood collection tube 201, forming an independent plasma activation station. The parallel configuration of multiple receiving cavities 102 achieves parallel processing, enabling the activation of multiple samples to be completed simultaneously in a single operation. In clinical or laboratory scenarios, when a large number of samples need to be processed, compared to sequential processing at a single station, this design can significantly increase the sample processing capacity per unit time, meeting the needs of batch preparation.

[0041] Each receiving cavity 102 is equipped with a dielectric barrier discharge assembly, specifically comprising two semi-annular high-voltage electrode plates 105 embedded in the inner wall of the receiving cavity 102 and a corresponding annular low-voltage electrode ring 106 located below. When the vacuum blood collection tube 201 is inserted into the receiving cavity 102, the two semi-annular electrodes are respectively in close contact with the outer walls of the two sides of the blood collection tube 201, with the insulating tube wall of the blood collection tube 201 itself serving as a dielectric barrier layer. Under the excitation of the high-voltage pulse power supply, the electric field between the electrodes ionizes the gas (such as air) remaining above the liquid surface in the blood collection tube 201, which is in a negative pressure (0.5-0.8 atm) state, generating plasma. This avoids direct contact between the electrodes and the liquid to be activated, prevents contamination of the activation liquid due to electrode material detachment or reaction, ensures the aseptic safety of the activation process, and utilizes the inherent structure of the blood collection tube 201 as the discharge medium, eliminating the need for additional barrier media inside the device. A limiter is provided at the bottom of the receiving cavity 102. The main function of this structure is to adjust the height of the inserted vacuum blood collection tube 201 and maintain a constant relative position between its tube wall and the semi-annular electrode. A stable relative position is a prerequisite for ensuring uniform electric field distribution and uniform plasma discharge. At the same time, through precise mechanical design or a limiter mechanism linked to a liquid level sensor, the liquid level of the liquid preparation in the blood collection tube 201 can be precisely controlled to ensure that it reaches the optimal discharge range. The control of the container position and liquid level, combined with the temperature control module that may be integrated into the device (e.g., monitoring and adjusting the reaction environment temperature through temperature sensor 108 and temperature control components), works together to improve the controllability of the activation process and batch-to-batch consistency. In addition, multiple parallel receiving cavities 102 are usually centrally managed and coordinated by a unified control module. For example, by integrating a control system, interactive interface, and processing unit, the activation parameters (such as time and power) of each receiving cavity 102 can be set and monitored, further enhancing the convenience of operation and the level of automation of the process.

[0042] By employing multiple parallel receiving cavities 102, a non-contact discharge assembly using the blood collection tube wall 203 as a dielectric barrier layer, and a precision mechanical and control system to ensure process stability, a high-throughput, sterile, and highly controllable plasma activation solution for liquid preparations 212 such as platelet-rich plasma is constructed. This effectively addresses the problems of low throughput, high contamination risk, and complex operation in existing technologies.

[0043] Building upon the basic architecture of the liquid plasma activation processing device, this application further integrates a dedicated power management module with multiple parallel plasma reaction chambers. The device further integrates a power supply module, a boost module, a filter module, a rectifier isolation module, a voltage regulator module, and a high-frequency inverter module, collectively forming a dedicated and stable plasma excitation power supply system. This power supply system provides the necessary electrical energy for the subsequent multiple plasma reaction chambers. The high-throughput activation receiving chamber 102 has 5-10 chambers integrated in parallel, each chamber 102 precisely fitted with a standard medical vacuum blood collection tube 201, forming an independent activation station. The combination of the multi-chamber parallel design and the centralized power supply mode directly achieves parallel processing and efficient use of system resources. This allows the device to simultaneously and independently activate multiple samples, improving the processing capacity per unit time compared to sequential processing at a single station, making it suitable for clinical batch preparation scenarios. Meanwhile, the modular power supply design facilitates unified and precise control of output parameters (such as power and frequency), providing consistent energy input conditions for all parallel stations and helping to ensure the consistency of activation effects among different samples within a batch.

[0044] Each receiving cavity 102 contains a plasma discharge structure, specifically including a semi-annular high-voltage electrode 105 embedded in the inner wall of the receiving cavity 102 and a corresponding semi-annular high-voltage electrode 105 with a limiting buckle, as well as an annular low-voltage electrode ring 106 located below. Its core feature is that when the vacuum blood collection tube 201 is inserted into the receiving cavity 102, the two semi-annular electrodes are respectively in close contact with the outer walls of the two sides of the blood collection tube 201, with the insulating tube wall of the blood collection tube 201 itself (usually glass or polymer material) serving as a dielectric barrier layer. At this time, the residual air layer above the liquid surface in the blood collection tube 201, under negative pressure (0.5-0.8 atm), becomes the ionized medium. Under the excitation of the high-voltage pulse power supply, the high-frequency electric field between the electrodes penetrates the tube wall, causing the gas medium to ionize and generate plasma. The primary technical effect of this non-contact design is to completely avoid direct contact between the electrodes and the liquid to be activated, thereby fundamentally preventing contamination of the liquid preparation due to electrode material detachment or reaction, and ensuring the aseptic safety of the activation process.

[0045] To ensure the stability and reproducibility of the aforementioned non-contact discharge process, an elastic rubber ring is provided at the bottom of the receiving cavity 102. This structure provides a moderate clamping force after the vacuum blood collection tube 201 is inserted. Its main function is to fix the blood collection tube 201 and dampen external vibrations, while maintaining a constant and tight fit between its tube wall and the semi-annular electrode. A stable relative position is an important physical prerequisite for ensuring uniform electric field distribution and uniform plasma discharge. The high-voltage electrode plate 105 with a limit snap further assists in maintaining this positional stability. In addition, through precise mechanical design or a limiting mechanism linked to the liquid level sensor, the liquid level of the liquid preparation in the blood collection tube 201 can be precisely controlled to ensure that it is in the optimal plasma interaction area. The coordinated control of the container position and liquid level, combined with the temperature control module that may be integrated into the device (e.g., monitoring and adjusting the reaction environment temperature through the temperature sensor 108 and temperature control components), works together to improve the controllability of each station in the high-throughput activation process and the consistency of sample processing results between batches.

[0046] In the overall architecture of the liquid plasma activation processing device, the receiving cavity 102 is arranged vertically. Specifically, the vertical arrangement of the receiving cavity 102 ensures that the medical blood collection tube 201 or similar liquid container adapted inside it is also in a vertical state, which helps maintain the stability of the interface between the liquid surface inside the container and the residual air layer above the liquid surface. During the plasma activation process, this residual air layer is the key ionization medium for generating plasma. A stable gas-liquid interface provides a reliable gas environment for dielectric barrier discharge, which helps maintain the stability of plasma generation and promotes a more consistent distribution of active particles towards the surface of the liquid container. From the perspective of equipment integration and high-throughput processing, the vertical arrangement of the receiving cavity 102 makes it easier to achieve a modular and compact arrangement. For example, in some embodiments, the device can have 5-10 high-throughput activation reaction chambers integrated in parallel, each reaction chamber being vertically arranged and adapted to a standard medical blood collection tube 201. This vertical parallel arrangement not only saves the planar space of the equipment, but also facilitates the construction of a unified plasma excitation source, gas passage, and control system, providing a structural basis for the batch and parallel processing of liquid preparations 212 in clinical or industrial scenarios. The vertical arrangement also demonstrates advantages in process control and aseptic assurance. The vertical orientation of the receiving cavity 102, combined with the limiter 110 (such as a movable rubber piston) at its bottom, facilitates precise adjustment of the depth of the liquid container within the cavity, thereby ensuring that the liquid surface to be activated is in the optimal plasma interaction zone. For example, by adjustment, the liquid surface can be precisely positioned near the lower edge of the discharge structure to optimize the activation effect.

[0047] In the overall architecture of the liquid plasma activation treatment device, a liquid level sensor can be further integrated. Real-time monitoring of the liquid level in the container provides a basis for adjusting the position of the limiter 110, thereby ensuring that the liquid surface to be activated is always within the effective working area of ​​the plasma discharge component. The primary purpose of introducing the liquid level sensor is to solve the problem of inconsistent liquid level caused by differences in liquid container specifications or loading volumes, which may affect the uniformity and reproducibility of the plasma activation effect. For example, in the quantitative liquid injection device of a plasma sterilizer, a liquid level sensor is used to achieve precise control and timely replenishment of the liquid quantity. In a specific embodiment of this application, the liquid level sensor is preferably a non-contact type or a sensing form without direct mechanical connection to the container. For example, a sensor based on capacitive sensing, optical reflection, or ultrasonic ranging principles can be used, and it can be placed on the side wall or top of the receiving cavity 102, facing the inside of the liquid container.

[0048] The liquid level sensor and the limiter 110 at the bottom of the receiving cavity 102 form a closed-loop control system. The liquid level height signal acquired in real time by the liquid level sensor is transmitted to the control system of the device (e.g., the control system, the interactive interface, and the processing unit). The processing unit compares the received liquid level signal with the preset optimal activation liquid level height range. If there is a deviation, it generates a control command to drive the actuator of the limiter 110 (e.g., the long handle of the piston limiter 110 can be precisely pushed and pulled by a stepper motor or a servo motor), thereby adjusting the longitudinal position of the liquid container in the receiving cavity 102. Furthermore, the end of the long handle of the piston limiter 110 can integrate a displacement detection element such as a Hall sensor. The mechanical displacement is converted into a digital signal that can be recognized by the processing unit through a displacement-voltage conversion circuit, realizing the digital mapping and feedback of the liquid level height and the position of the limiter 110. This ensures that even for containers with different initial liquid level heights, after automatic adjustment, the liquid level can be accurately guided to a predetermined spatial position slightly below the lower edge of the discharge component.

[0049] Stable control of the plasma interaction region is achieved through the synergistic action of the liquid level sensor and the adjustable limiter 110. Precisely maintaining the liquid level within a specific range below the discharge structure ensures sufficient and consistent interaction between active particles (such as reactive oxygen species (ROS) and reactive nitrogen species (RNS)) generated during plasma activation and the liquid surface. This is crucial for obtaining plasma-activated liquids with stable active component concentrations and reliable biomedical effects. Furthermore, this automatic adjustment mechanism reduces reliance on operator experience and simplifies the clamping process, especially in high-throughput embodiments (e.g., configurations with 5-10 parallel accommodating cavities 102), enabling rapid and accurate positioning of liquid containers at all stations.

[0050] In one embodiment, the plasma discharge structure is embedded in the inner wall of the receiving cavity 102. The plasma discharge structure, such as an electrode in the form of a capacitor electrode or an inductor, is configured to be embedded in the inner wall of the receiving cavity 102. Specifically, the structure can be embedded in a pre-machined groove in the inner wall of the receiving cavity 102. This embedded arrangement ensures that the discharge structure is flush with or slightly lower than the inner wall surface of the receiving cavity 102, thereby physically preventing the electrode structure from protruding from the cavity's internal space. When a liquid container (such as a medical blood collection tube 201) is inserted into the receiving cavity 102, a tight and uniform physical contact or micro-gap fit is formed between the outer wall of the container and the inner wall of the receiving cavity 102. This creates favorable physical conditions for achieving a uniform electric field distribution and stable plasma discharge. The embedded design physically isolates the discharge electrode from the liquid to be activated by the wall material of the receiving cavity 102 (typically an insulating material) and the wall of the liquid container itself (such as glass or a polymer material), achieving non-contact energy transfer.

[0051] In another embodiment, the plasma discharge structure is detachably mounted on the inner wall of the receiving cavity 102. This detachable mounting can be achieved through various mechanical connection mechanisms. For example, quick-release connectors or locking clips already used in plasma devices can be employed to achieve rapid locking and separation between the discharge structure and the cavity. Another feasible approach is to provide a combination of a guide plate and a limiting groove on the inner wall of the receiving cavity 102, allowing the discharge structure in the form of an electrode plate or coil to slide along a specific path into a predetermined position and be temporarily fixed. For discharge structures requiring electrical connection, plug-in electrical connectors can be used, for example, by providing plug holes with elastic clamps, allowing the plug plates on the discharge structure to be inserted and firmly pressed, thus establishing an electrical connection.

[0052] The most direct technical benefit of the detachable design is improved maintainability. When a discharge structure degrades in performance, becomes contaminated, or is damaged due to long-term use, operators can selectively disassemble it for cleaning, maintenance, or replacement without replacing the entire containment chamber 102 module or causing prolonged downtime. This is particularly true for the aforementioned high-throughput embodiments (e.g., configurations with 5-10 parallel containment chambers 102), enabling rapid recovery of individual faulty workstations and reducing overall equipment maintenance and time costs. Secondly, this design enhances the flexibility and adaptability of the device. Users can replace discharge structures with different electrode configurations (such as capacitive electrode sheets or inductive coils) or power characteristics according to different activation process requirements (e.g., for platelet-rich plasma and other different types of liquid formulations 212), achieving multi-purpose functionality and expanding the device's application range. Furthermore, the detachable structure facilitates upgrades and iterations of the discharge components.

[0053] Furthermore, the plasma discharge structure is disposed on the outer wall of the liquid container. The plasma discharge structure (e.g., a plasma discharge structure existing in the form of an electrode sheet or coil) is directly disposed on the outer surface of the liquid container (e.g., a medical blood collection tube 201). Specifically, this component can be fixed to a specific area of ​​the container's outer wall by means of deposition, printing, pasting, or mechanical snap-fitting. Upon energization, plasma is directly generated in the adjacent gas environment. The direct technical effect of this integrated design is that it minimizes the path of active particles (e.g., reactive oxygen species (ROS) and reactive nitrogen species (RNS)) from their generation location to the liquid surface within the container. This shortened path helps reduce recombination and energy loss of active particles during transport, potentially improving energy utilization efficiency and liquid activation efficiency. In a preferred embodiment, this plasma discharge structure disposed on the outer wall of the liquid container is configured to generate a dielectric barrier discharge (DBD). In this case, the insulating wall of the liquid container itself (e.g., the glass or specific polymer material typically used in medical blood collection tubes 201) acts as a dielectric barrier layer during the discharge process. When a high-frequency, high-voltage electric field is applied to the plasma discharge structure (as an electrode), the electric field penetrates the container wall, exciting the gas outside the structure (or within the tiny gap between the wall material and the electrode) to ionize. The container wall, acting as a barrier medium, effectively suppresses arc formation, ensuring the uniformity and stability of the discharge.

[0054] This embodiment, which places the plasma discharge structure on the outer wall of the liquid container, eliminates the need for a separate housing cavity 102 with built-in electrodes, thus reducing the overall size of the activation device and making it more compact. This is significant for developing portable devices or for use in space-constrained environments (such as certain clinical workbenches). Furthermore, in this configuration, if the liquid container is a disposable consumable (such as a specific size blood collection tube 201), the plasma discharge structure can also be designed as a matching disposable component. This may mitigate the risk of electrode cross-contamination during use and eliminate the need for cleaning and maintenance of reusable electrodes.

[0055] In the overall architecture of the liquid plasma activation treatment device, a temperature sensor 108 and temperature control components can be further integrated to form a closed-loop control system, ensuring that the treatment environment always meets the stringent temperature requirements of biological agents. The temperature sensor 108 is configured to detect the temperature of the containment cavity 102 in real time. In a specific embodiment, the sensor is preferably a miniaturized temperature sensing element, such as a K-type thermocouple sensor, whose temperature detection range (e.g., -40℃ to +300℃) completely covers the operating range of this device. The sensor is embedded in the inner wall of the containment cavity 102, approximately 1 cm below the plasma discharge structure. During plasma discharge, some electrical energy is converted into heat energy, which may cause the temperature of the discharge area and the adjacent container wall to rise. Placing the temperature sensor 108 close to the discharge area allows for more sensitive and rapid detection of local temperature rise changes directly caused by plasma discharge, providing timely and accurate feedback signals for subsequent temperature control.

[0056] The temperature control component dynamically adjusts the temperature of the receiving cavity 102 based on the signal fed back by the temperature sensor 108. Specific implementations may include an active cooling unit (such as a Peltier effect-based semiconductor cooler) or a controlled fluid circulation system (e.g., coolant channels around the cavity). The temperature control component is positioned below the high-throughput receiving cavity 102, facilitating uniform heat dissipation from bottom to top. A key technical feature is that the temperature control component is configured to maintain the temperature of the high-throughput receiving cavity 102 at no higher than 40°C during activation. This temperature threshold is primarily based on considerations of the heat sensitivity of bioactive components (such as growth factors and proteins in platelet-rich plasma). Excessively high temperatures may cause these bioactive components to denature and become inactive, thereby affecting the biomedical efficacy of the final activated liquid. Strictly controlling the temperature below 40°C provides a safe processing environment for heat-sensitive biological agents.

[0057] The temperature sensor 108 and the temperature control component form a closed-loop control circuit through the device's control system (e.g., the control system, interactive interface, and processing unit described above). The temperature data continuously collected by the temperature sensor 108 is transmitted to the processing unit, which compares it with a preset safe temperature threshold (e.g., 40°C). If the monitored temperature approaches or exceeds this threshold, the processing unit sends a command to the temperature control component to increase its cooling power, thereby stabilizing the system temperature within the set range. This real-time feedback and control mechanism effectively avoids thermal damage to the biological agent caused by temperature runaway. Furthermore, as described in some plasma devices, the integrated LCD display 109 can be used to visualize real-time temperature data and other key process parameters (e.g., activation time), which not only facilitates operator monitoring of the process status but also supports process reproducibility and data traceability.

[0058] By cooperating with the temperature sensor 108 and the temperature control component, and by setting a reasonable temperature control threshold, the liquid plasma activation treatment device of this application achieves precise monitoring and automatic adjustment of the activation process temperature. This technical feature effectively prevents the damage of heat-sensitive biological components to plasma heat generation. Combined with the overall sterile and non-contact design concept of the device, it jointly ensures the safety, efficacy, and batch-to-batch consistency of the finally obtained plasma-activated liquid formulation 212 in biomedical applications.

[0059] In a further embodiment, a gas circulation path is also included, with a gas outlet at the bottom of the receiving cavity 102 and a gas inlet at the opening of the receiving cavity 102. This top-to-bottom arrangement helps to create a directional, generally bottom-up airflow path inside the receiving cavity 102. Gas flowing from the bottom gas outlet (which may be an inert protective gas, such as nitrogen, argon, or a gas mixture containing specific active components, depending on process requirements) is forced upward and eventually drawn out from the top gas inlet, completing one cycle. Its core function is to maintain a sterile environment inside the receiving cavity 102 and prevent the intrusion of external contaminants. Before the liquid container is placed inside, the plasma discharge structure is activated to sterilize the receiving cavity 102 and the opening of the receiving cavity 102 using plasma.

[0060] Furthermore, the gas circulation path can operate independently or in conjunction with other components already described in the device. For example, a flow sensor and a proportional valve can be integrated into the path, and the control system can adjust them in tandem to precisely control the gas flow rate and volume according to different activation process stages or different liquid container specifications. Moreover, if the temperature control component cools the containment cavity 102, the circulating gas flowing over its surface may also help remove some heat, indirectly contributing to the system's thermal management.

[0061] The device described in this application may further include a control system, an interactive interface, and a processing unit. The control system can be built upon a mature industrial control architecture. Its core may include a programmable logic controller (PLC) or a more complex modular architecture, responsible for executing the core control logic of the device. For example, the PLC can be used to receive input signals from various sensors (such as liquid level sensors and temperature sensors 108) and control the actions of actuators (such as limit switches 110 driving motors, temperature control components, and plasma power supplies) according to a preset program. In scenarios requiring the processing of large amounts of data or complex algorithms, the system can also integrate an industrial personal computer (IPC) as a host computer to work collaboratively with the PLC, processing production process data, archiving important formula parameters, and building a monitoring interface. To further improve reliability, the hardware of the control system can adopt a dual-redundant cluster architecture, enabling the master and slave clusters to operate synchronously and switch in a timely manner according to their status, thereby improving the system's fault tolerance and continuous operation stability.

[0062] The interactive interface, serving as a bridge between the user and the device, is of paramount importance in its design. This interface is typically a graphical user interface (GUI), designed to centrally visualize and provide feedback on key real-time operating parameters of the device, such as the temperature of the containment chamber 102, plasma processing time, and liquid level. The interface also needs to provide parameter configuration functionality, allowing operators to set and adjust preset parameters of the control algorithm. To decouple the user interface from the control algorithm and improve the system's flexibility and maintainability, an extensible markup language can be used to define these preset parameter information.

[0063] The processing unit (which can be embedded in a PLC, IPC, or a dedicated processing module) is responsible for data processing and instruction generation. It processes real-time data collected by sensors, for example, by transmitting data between the interface components and the control algorithm components via a publish / subscribe communication mechanism. The processing unit achieves precise closed-loop control by running control algorithms (such as PID control algorithms). For example, based on the signal fed back by the temperature sensor 108, the processing unit can perform PID calculations and issue instructions to the temperature control component to maintain the temperature of the containment cavity 102 within a set safety threshold (e.g., not exceeding 40°C). Similarly, the processing unit can receive signals from the liquid level sensor, perform calculations, and drive the actuator of the limit switch 110 to automatically adjust the height of the liquid container. This closed-loop control mechanism is key to achieving precise process automation. Furthermore, the processing unit is also responsible for managing historical data, storing important process parameters and event logs in a database (such as MySQL) for subsequent querying, analysis, and process reproducibility.

[0064] Centralized monitoring and automated control reduce human error and improve batch consistency during batch processing. Secondly, real-time alarms and status monitoring promptly alert to equipment malfunctions or deviations in process parameters, enhancing the safety and reliability of equipment operation. Thirdly, formula parameter management and historical data recording functions facilitate rapid switching between different activation processes (such as for platelet-rich plasma and other types of liquid formulations 212) and provide data support for quality traceability in the production process. Finally, a user-friendly interface simplifies the operation process, reduces the need for professional experience among operators, and improves the equipment's ease of use.

[0065] In the overall architecture of the liquid plasma activation treatment device, an integrated control module, an optical emission spectrum monitoring module, and a human-machine interface module constitute the core closed-loop control system for achieving precise, automated, and sterile activation processes. The integrated power supply module, located inside the main frame, comprises a power supply, a boost module, a filter module, a rectifier isolation module, a voltage regulator module, and a high-frequency inverter module connected in sequence. This design constitutes a dedicated multi-stage power conversion and supply system. The control module is configured to be electrically connected to the integrated power supply module and the dielectric barrier discharge assembly, precisely controlling the output voltage of the boost module within the 1-10kV range and adjusting the output frequency of the high-frequency inverter module within the 10-100kHz range. This provides a stable and waveform-controllable high-frequency high-voltage excitation for the dielectric barrier discharge, a prerequisite for maintaining stable and uniform plasma. Furthermore, the control module monitors the current flowing through each discharge assembly in real time using current sensors and limits it within a safe range of 1-10mA. When the current at any station exceeds a preset threshold, the control module automatically cuts off the power supply to that station. This overcurrent protection mechanism effectively prevents current surges caused by abnormal discharges (such as localized arcing), thus avoiding potential damage to plasma discharge components or liquid preparations to be activated (such as platelet-rich plasma), and improving the safety and reliability of equipment operation. This type of control strategy, based on PLC (Programmable Logic Controller) and sensors to monitor and adjust plasma process parameters, has precedents in plasma equipment in the semiconductor field. For example, some devices use PLC controllers to adjust various reaction conditions in plasma reactors to achieve closed-loop control.

[0066] To achieve precise control of the activation process and correlate it with biological endpoints, this device connects an optical emission spectrometer to the control module. The spectrometer's probe is positioned at a dedicated observation window on the side wall of the containment cavity for non-invasive acquisition of the light signals emitted by the plasma. Its core working mechanism involves the optical probe monitoring the plasma's emission spectrum in real time through the observation window and transmitting this data to a spectrometer for conversion and analysis. Specifically applied to platelet-rich plasma activation scenarios, the system can be programmed to automatically terminate the activation process at a given station when the spectrometer detects that the characteristic emission line intensity of specific active species such as hydroxyl radicals (·OH) reaches a preset threshold. For example, the concentration of hydroxyl radicals can be determined by monitoring the spectral line intensity at a specific wavelength (e.g., around 309 nm). This endpoint determination method based on the intensity of optical signals from specific active components links the termination conditions of the activation process to the concentration of key active species that may cause biological effects, achieving a shift from simple "time control" to "precise control based on biological endpoints." This helps ensure consistency in activation effects between different batches of samples, avoiding under- or over-activation.

[0067] The control module, as the core of the system, is electrically connected to the integrated power module, the cavity monitoring module (such as an optical emission spectrometer), and the dielectric barrier discharge assembly, coordinating the entire activation process. Regarding human-machine interaction, a human-machine interface module (e.g., a touchscreen) located on the front of the main frame handles information display and parameter input. This module centrally displays real-time activation parameters for each sample, such as voltage, frequency, and status information (e.g., "complete / incomplete"). It also supports user input or selection of preset activation times and other process parameters, providing operators with a centralized and intuitive process monitoring and interaction method. Combined with the control module's independent monitoring and management of multiple parallel stations, it reduces human error and improves the standardization and convenience of batch processing. Furthermore, the integrated cooling module maintains the reaction temperature below 40°C. This temperature control setting is based on protecting the heat-sensitive bioactive components (such as growth factors and proteins) in platelet-rich plasma, preventing them from denaturing and becoming inactive due to overheating. The temperature sensor 108 works in conjunction with the cooling module and achieves closed-loop control through the control module, together providing a safe thermal environment for the activation process.

[0068] By integrating precise electrical parameter control of the power module, real-time chemical endpoint monitoring of optical emission spectra, and collaborative management between the control module and the human-machine interface, the liquid plasma activation treatment device of this application constructs a multi-parameter precise automated control and accurate endpoint determination system for platelet-rich plasma activation. This combination of technical features effectively supports the core requirements of the device in clinical applications for aseptic assurance, process controllability, accurate endpoints, and ease of operation, providing process assurance for obtaining high-quality, highly consistent activated liquid formulation 212.

[0069] As described above, this application provides a liquid plasma activation treatment device, the core of which lies in achieving aseptic treatment of biomedical liquid preparations through a non-contact plasma activation method. The device's main structure consists of a receiving cavity and a plasma discharge structure. The receiving cavity adopts a hollow cylindrical structure, precisely adapted to a standard medical blood collection tube. The plasma discharge structure preferably uses a dielectric barrier discharge method, employing the blood collection tube wall as a natural barrier medium. Plasma is generated within the blood collection tube and above the liquid preparation through an electrode structure embedded in the inner wall of the receiving cavity, allowing the active components to directly act on the internal liquid, thereby avoiding direct contact between the electrodes and the liquid and fundamentally preventing contamination.

[0070] The device further incorporates a limiting mechanism and a liquid level sensing system. Through the coordinated operation of the movable limiter and the liquid level sensor, the position of the liquid container is precisely adjusted to ensure the liquid level is within the optimal activation zone. In an extended embodiment, the device can be configured with multiple parallel cavities to form a high-throughput processing system. Each station is equipped with an independent dielectric barrier discharge assembly, and parallel processing and centralized management are achieved through a unified control module.

[0071] To ensure the stability of the processing, the device integrates temperature sensors and temperature control components to monitor and control the processing temperature in real time, ensuring it does not exceed 40°C and protecting the activity of heat-sensitive biological components. The gas circulation pathway, with its bottom-intake and top-return design, creates a directional airflow within the containment chamber, maintaining a sterile environment. The introduction of the control system, interactive interface, and processing unit enables multi-dimensional and precise control of activation parameters, including adjustment of power output characteristics (voltage 1-10kV, frequency 10-100kHz), overcurrent protection, and activation endpoint determination based on optical emission spectra, thereby ensuring the consistency and reproducibility of the processing results.

[0072] This device supports functional expansion through modular design. The plasma discharge structure can be configured in various ways, including embedded, detachable, or integrated with liquid containers, to meet the needs of different application scenarios. The overall technical solution effectively solves the problems of contamination risk, throughput limitations, and insufficient process control precision in existing technologies, providing a reliable solution for the aseptic activation of clinical liquid preparations.

[0073] The above is only one specific implementation of this application, and any other improvements made based on the concept of this application shall be considered within the scope of protection of this application.

Claims

1. A liquid plasma activation treatment apparatus, characterized by, This includes a containment cavity, a plasma discharge structure, a high-voltage line interface, and a low-voltage grounding line interface; The cavity is a hollow cylindrical structure used to hold liquid containers; The plasma discharge structure is disposed on the inner wall of the receiving cavity, and the plasma discharge structure includes a capacitor electrode sheet or an inductor. The high-voltage line interface is connected to the plasma discharge structure and is used to electrically connect the plasma discharge structure to a high-voltage pulse power supply. The bottom of the receiving cavity is provided with a limiter, which moves within the receiving cavity to adjust the length of the liquid container within the receiving cavity.

2. The liquid plasma activation treatment apparatus according to claim 1, characterized by It includes multiple of the aforementioned receiving cavities.

3. The liquid plasma activation treatment apparatus according to claim 2, wherein The receiving cavity is arranged in a vertical direction.

4. The liquid plasma activation treatment apparatus according to claim 3, wherein It also includes a liquid level sensor that detects the liquid level in the liquid container and is used to adjust the position of the limiter.

5. The liquid plasma activation treatment apparatus according to claim 4, wherein The plasma discharge structure is embedded in the inner wall of the receiving cavity.

6. The liquid plasma activation treatment apparatus according to claim 1, wherein The plasma discharge structure is detachably mounted on the inner wall of the receiving cavity.

7. The liquid plasma activation treatment apparatus according to claim 1, wherein The plasma discharge structure is disposed on the outer wall of the liquid container.

8. The liquid plasma activation treatment apparatus according to claim 1, wherein It also includes a temperature sensor and a temperature control component, wherein the temperature sensor is used to detect the temperature of the receiving cavity, and the temperature control component is used to adjust the temperature of the receiving cavity.

9. The liquid plasma activation treatment apparatus according to claim 1, wherein, It also includes a gas circulation passage, the gas outlet of which is at the bottom of the receiving cavity, and the gas inlet of which is at the opening of the receiving cavity.

10. The liquid plasma-activated treatment apparatus according to claim 1, wherein, It also includes a control system, an interactive interface, and a processing unit.

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