Argon-oxygen mixed plasma jet coagulation device

Abstract

The present application relates to the technical field of medical devices, and provides an argon-oxygen mixed plasma jet coagulation device, which comprises a jet reactor, a power module and a gas supply assembly, the jet reactor comprises a discharge electrode, a dielectric tube and an insulating shell, the discharge electrode and the dielectric tube are arranged inside the insulating shell, two ends of the discharge electrode form a connecting end and a jet end respectively, the jet end is arranged through the insulating shell and is suitable for forming a plasma jet beam; the inside of at least one of the discharge electrode and the dielectric tube is constructed as an airflow channel; the power module is connected with the connecting end; the gas supply assembly is connected with the airflow channel and is used for supplying a preset proportion of argon-oxygen mixed gas to the airflow channel. The present application not only can reduce tissue thermal injury to protect normal tissue around a wound surface, but also can increase the role of a biological effect in a coagulation process, accelerate blood coagulation and significantly improve coagulation efficiency.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of medical devices, in particular to an argon-oxygen mixed plasma jet coagulation device. BACKGROUND

[0002] In the traditional coagulation technology, the high-frequency electrotome is mainly used to stop bleeding. The high-frequency electrotome uses the heat generated by high-frequency current to destroy cells and blood vessels to make them coagulate. However, this method is difficult to control the generation and transmission of heat in the coagulation process, which is easy to cause the local temperature to be too high and cause thermal injury to the normal tissue around the wound surface. At the same time, the high-frequency electrotome will produce carbonization and eschar when it contacts with the tissue to coagulate, and the knife head will be adhered. When the knife head leaves the tissue, it will bleed again, and the coagulation needs to be repeated.

[0003] With the increasing demand for the refinement of medical technology, reducing the heat loss and thermal injury in the coagulation process has become a key requirement. Argon plasma coagulation (APC) is a new coagulation technology that uses an activated electrode to ionize argon gas to form argon plasma, which is transmitted to the target tissue to achieve non-contact coagulation, solving the problem of carbonization and adhesion of the knife head when the high-frequency electrotome contacts the tissue.

[0004] Although argon plasma coagulation can solve the problem of carbonization and adhesion of the knife head when the high-frequency electrotome contacts the tissue. However, argon plasma coagulation uses high-frequency energy (350 kHz) to ionize argon gas to transmit electric energy to produce a thermal effect for coagulation. The coagulation working temperature is high, and the high temperature will cause thermal injury to the normal tissue around the wound surface, causing complications such as tissue necrosis and inflammatory reaction, affecting the healing process of the wound. SUMMARY

[0005] The present application provides an argon-oxygen mixed plasma jet coagulation device to solve the above technical defects in the prior art. It not only reduces the thermal injury to the tissue to protect the normal tissue around the wound surface, but also increases the role of biological effects in the coagulation process, accelerates blood clotting, and significantly improves the coagulation efficiency.

[0006] The present application provides an argon-oxygen mixed plasma jet coagulation device, comprising:

[0007] A jet reactor, comprising a discharge electrode, a dielectric tube and an insulating shell, the discharge electrode and the dielectric tube are arranged inside the insulating shell, the two ends of the discharge electrode form a connection end and a jet end respectively, the jet end is arranged in the insulating shell and is suitable for forming a plasma jet beam; the inside of at least one of the discharge electrode and the dielectric tube is constructed into an airflow channel;

[0008] A power module connected to the connection end;

[0009] A gas supply component, connected to the gas flow channel, is used to supply a preset ratio of argon-oxygen mixed gas to the gas flow channel.

[0010] According to the argon-oxygen mixed plasma jet coagulation device provided by the present invention, the ratio of argon to oxygen is between 9999:1 and 99:1.

[0011] According to the argon-oxygen mixed plasma jet coagulation device provided by the present invention, the dielectric tube is sleeved on the outside of the discharge electrode, and the gas flow channel is formed between the dielectric tube and the discharge electrode;

[0012] The side wall of the insulating shell is provided with an air inlet channel, and the side wall of the medium tube is provided with a branch air channel. The branch air channel is connected to the airflow channel and extends to the position of the air inlet channel and is connected to the air inlet channel; the air inlet channel is connected to the air supply assembly.

[0013] According to the argon-oxygen mixed plasma jet coagulation device provided by the present invention, a hollow tube of a predetermined length is formed between the connecting end and the jet end of the discharge electrode, and the side wall of the hollow tube is provided with an opening, and the airflow channel communicates with the opening.

[0014] According to the argon-oxygen mixed plasma jet coagulation device provided by the present invention, the gas supply component includes a first gas supply pipe, a second gas supply pipe, and gas supply sources connected to the first gas supply pipe and the second gas supply pipe, wherein the first gas supply pipe is connected to the first gas flow channel, and the second gas supply pipe is connected to the second gas flow channel;

[0015] The gas supply assembly includes a first gas supply pipe, a second gas supply pipe, and gas sources connected to the first gas supply pipe and the second gas supply pipe. The first gas supply pipe is connected to the first airflow channel, and the second gas supply pipe is connected to the second airflow channel.

[0016] The argon-oxygen mixed plasma jet coagulation device provided by the present invention further includes an adjustment component;

[0017] The side wall of the insulating shell is provided with an adjustment groove, the adjustment component is disposed in the adjustment groove and connected to the discharge electrode, and the adjustment component is adapted to adjust the position of the discharge electrode to move closer to or further away from the target tissue.

[0018] According to the argon-oxygen mixed plasma jet coagulation device provided by the present invention, the insulating shell has a first end and a second end disposed opposite to each other;

[0019] The first end is provided with a lead wire channel, the second end is provided with a positioning hole, the connection end of the discharge electrode passes through the lead wire channel and is connected to the power module; the jet end of the discharge electrode passes through the positioning hole.

[0020] The argon-oxygen mixed plasma jet coagulation device provided by the present invention further includes a jet nozzle assembly, which is disposed at the second end of the insulating shell, and the airflow channel is connected to the jet nozzle assembly.

[0021] According to the argon-oxygen mixed plasma jet coagulation apparatus provided by the present invention, the jet nozzle assembly includes:

[0022] The nozzle component is connected to the second end of the insulating housing;

[0023] A flow guide cylinder is rotatably disposed inside the nozzle component. The flow guide cylinder has a through hole inside, through which the jet end of the discharge electrode passes. A flow guide groove is provided on the outer circumferential surface of the flow guide cylinder. The flow guide groove is spirally arranged along the axial direction of the flow guide cylinder and is connected to the airflow channel.

[0024] According to the argon-oxygen mixed plasma jet coagulation device provided by the present invention, the power supply module includes a power supply body and a self-calibrating impedance matching system. The self-calibrating impedance matching system is electrically connected to the power supply body and is used to adjust the power of the power supply body according to the impedance between the argon-oxygen mixed gas and the coagulation load.

[0025] The argon-oxygen mixed plasma jet coagulation device provided by this invention uses low-power energy output from a power module to provide stable electrical energy for the entire device. The output energy is regulated to adapt to different coagulation requirements. Simultaneously, the gas supply component is connected to the airflow channel, suitable for supplying a preset proportion of argon-oxygen mixed gas to the airflow channel. This configuration not only reduces heat loss to protect normal tissue around the wound but also increases the role of biological effects in the coagulation process, accelerating blood coagulation, promoting wound healing, and significantly improving coagulation efficiency and shortening coagulation time. Attached Figure Description

[0026] To more clearly illustrate the technical solutions in this invention or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are some embodiments of this invention. For those skilled in the art, other drawings can be obtained from these drawings without creative effort.

[0027] Figure 1 This is a schematic diagram of the argon-oxygen mixed plasma jet coagulation device provided in Embodiment 1 of the present invention.

[0028] Figure 2 This is a schematic diagram of the argon-oxygen mixed plasma jet coagulation device provided in Embodiment 2 of the present invention.

[0029] Figure 3 yes Figure 2 The diagram shows an exploded view of the jet nozzle assembly in the argon-oxygen mixed plasma jet coagulation device.

[0030] Figure 4 This is a schematic diagram of the argon-oxygen mixed plasma jet coagulation device provided in Embodiment 3 of the present invention.

[0031] Figure 5 yes Figure 4 The diagram shows an exploded view of the argon-oxygen mixed plasma jet coagulation device.

[0032] Figure 6 yes Figure 4 The isometric sectional view of the argon-oxygen mixed plasma jet coagulation device shown.

[0033] Figure 7 This is a schematic diagram of the argon-oxygen mixed plasma jet coagulation device provided in an embodiment of the present invention.

[0034] Figure 8 This is an equivalent circuit diagram of the argon-oxygen mixed plasma jet coagulation device provided in the embodiments of the present invention.

[0035] Figure 9(a) shows the relative intensity of the active particles as measured by a spectrometer in an argon plasma condensation apparatus.

[0036] Figure 9(b) shows the relative intensity of the active particles as determined by the spectrometer of the argon-oxygen mixed plasma jet coagulation device.

[0037] Figure 10(a) is a comparison of the coagulation rates of different devices during partial liver resection in pigs.

[0038] Figure 10(b) is a temperature comparison diagram of different devices during partial liver resection in pigs.

[0039] Figure 11 This is a comparative diagram illustrating the processing procedures of different devices during partial liver resection in pigs. (Figure labels:)

[0040] 10. Jet reactor; 11. Discharge electrode; 111. Connecting end; 112. Jet end; 12. Medium pipe; 121. Branch gas channel; 13. Insulating shell; 131. Inlet channel; 132. Positioning hole; 133. Lead wire channel; 134. Adjustment groove; 141. First gas flow channel; 142. Second gas flow channel;

[0041] 20. Power supply module;

[0042] 30. Gas supply assembly; 31. First gas supply pipe; 32. Second gas supply pipe;

[0043] 40. Adjustment components;

[0044] 50. Jet nozzle assembly; 51. Nozzle component; 52. Drainage cylinder; 521. Drainage groove. Detailed Implementation

[0045] To make the objectives, technical solutions, and advantages of this invention clearer, the technical solutions of this invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some, not all, of the embodiments of this invention. All other embodiments obtained by those skilled in the art based on the embodiments of this invention without creative effort are within the scope of protection of this invention.

[0046] In the description of the embodiments of this application, it should be noted that, unless otherwise explicitly specified and limited, the terms "connected" and "linked" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium. Those skilled in the art can understand the specific meaning of the above terms in the embodiments of this application based on the specific circumstances.

[0047] In the embodiments of this application, unless otherwise expressly specified and limited, "above" or "below" the second feature can mean that the first feature is in direct contact with the second feature, or that the first feature is in indirect contact with the second feature through an intermediate medium. Furthermore, "above," "on top of," and "over" the second feature can mean that the first feature is directly above or diagonally above the second feature, or simply that the first feature is at a higher horizontal level than the second feature. "Below," "below," and "under" the second feature can mean that the first feature is directly below or diagonally below the second feature, or simply that the first feature is at a lower horizontal level than the second feature.

[0048] In the description of this specification, the references to terms such as "one embodiment," "some embodiments," "example," "specific example," or "some examples," etc., refer to specific features, structures, materials, or characteristics described in connection with that embodiment or example, which are included in at least one embodiment or example of the embodiments of this application. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples. Moreover, without contradiction, those skilled in the art can combine and integrate the different embodiments or examples described in this specification, as well as the features of different embodiments or examples.

[0049] This invention provides an argon-oxygen mixed plasma jet coagulation device, including a jet reactor 10, a power module 20, and a gas supply assembly 30.

[0050] The jet reactor 10 includes a discharge electrode 11, a dielectric tube 12, and an insulating shell 13. The discharge electrode 11 and the dielectric tube 12 are disposed inside the insulating shell 13. The two ends of the discharge electrode 11 form a connection end 111 and a jet end 112, respectively. The jet end 112 penetrates the insulating shell 13 and is suitable for forming a plasma jet beam. At least one of the discharge electrode 11 and the dielectric tube 12 has an internal gas flow channel 14. That is, the gas flow channel 14 can be formed in the discharge electrode 11, or in the dielectric tube 12, or simultaneously in both the discharge electrode 11 and the dielectric tube 12. The gas flow channel 14 provides a passage for the working gas.

[0051] The power module 20 serves as the core energy supply for the argon-oxygen mixed plasma jet coagulation device, and is connected to the connection terminal 111 of the discharge electrode 11. The power module 20 provides stable electrical energy to the entire argon-oxygen mixed plasma jet coagulation device, and its output energy (30kHz-50kHz) is regulated by a self-calibrating impedance matching system to adapt to different coagulation requirements.

[0052] The power supply module 20 operates at a voltage of 90V-110V and a pulse width of 7μs-10μs. The power supply module 20 includes a power supply unit and a self-calibrating impedance matching system. The self-calibrating impedance matching system is electrically connected to the power supply unit and is used to adjust the power of the power supply unit based on the impedance between the argon-oxygen mixture and the coagulation load.

[0053] A self-calibrating impedance matching system mainly consists of an impedance matching network (adjustable element) and a main control module (self-calibrating controller). The main control module is used for feedback and control. The input of the impedance matching network (adjustable element) is connected to the output of the power supply unit, and the output of the impedance matching network (adjustable element) is connected to the load. The main control module is electrically connected to the impedance matching network (adjustable element) and is used to measure the system's input and output power in real time, providing a reference for impedance matching. By monitoring power changes, the system can adjust the matching parameters in a timely manner to ensure that the system is always in optimal operating condition. In other words, the self-calibrating impedance matching system can assess the coagulation effect based on the load impedance and actively reduce the output power when coagulation is basically complete, thereby reducing the occurrence of thermal damage.

[0054] The main control module, as the core controller of the system, receives signals from the power monitoring circuit, processes and analyzes the data, calculates the parameters required to achieve optimal impedance matching, and sends these parameters to the system. Based on the power information provided by the power monitoring circuit, the main control module calculates and determines the required impedance matching parameters. In other words, the main control module processes the data collected by the power monitoring circuit in real time, calculates the load impedance magnitude, determines the degree of mismatch between the current load impedance and the target impedance, and then sends signals for adjustment.

[0055] The gas supply assembly 30 is connected to the airflow channel 14 and is used to supply the airflow channel 14 with a preset proportion of argon-oxygen mixed gas. The structure of the gas supply assembly 30 corresponds to the arrangement of the airflow channel 14. For example, when the airflow channel 14 is arranged as a single channel, the gas supply assembly is connected to the airflow channel 14 and is suitable for supplying the airflow channel 14 with a preset proportion of argon-oxygen mixed gas. When the airflow channel 14 is arranged as a dual channel, the gas supply assembly 30 includes different gas delivery pipes, each of which supplies gas to the connected airflow channel 14.

[0056] Figure 1 This is a schematic diagram of the argon-oxygen mixed plasma jet coagulation device provided in Embodiment 1 of the present invention.

[0057] See Figure 1 In an embodiment of the present invention, an argon-oxygen mixed plasma jet coagulation device is provided. The jet reactor 10 includes a discharge electrode 11, a dielectric tube 12 and an insulating shell 13. The dielectric tube 12 is sleeved on the outside of the discharge electrode 11, and an airflow channel 14 is formed between the dielectric tube 12 and the discharge electrode 11.

[0058] Essentially, the jet reactor 10 includes a discharge electrode 11, a dielectric tube 12, and an insulating outer shell 13 arranged sequentially from the inside out. Specifically, the discharge electrode 11 is embedded inside the dielectric tube 12, and the discharge electrode 11 and the dielectric tube 12 are coaxially arranged. The two ends of the discharge electrode 11 form a connection end 111 and a jet end 112, respectively, with the jet end 112 suitable for forming a plasma jet beam. An airflow channel 14 is formed between the dielectric tube 12 and the discharge electrode 11. The discharge electrode 11 can be tubular, needle-shaped, rod-shaped, or knife-shaped. Different shapes of discharge electrodes 11 have different discharge parameters and forms, and correspondingly different coagulation efficiencies.

[0059] The side wall of the insulating shell 13 is provided with an air inlet channel 131, and the side wall of the medium pipe 12 is provided with a branch air channel 121. The branch air channel 121 is connected to the airflow channel 14. The branch air channel 121 extends to the position of the air inlet channel 131 and is connected to the air inlet channel 131. The air inlet channel 131 is connected to the air supply assembly.

[0060] Essentially, the working gas supplied by the gas supply component is input from the air intake channel 131, and the working gas is transported along the airflow channel 14 to the jet end 112 of the discharge electrode 11. After ionization, a plasma jet beam is formed and delivered to the target tissue for rapid coagulation.

[0061] The gas supply component is connected to the airflow channel 14 and is adapted to supply the airflow channel 14 with a preset ratio of argon-oxygen mixed gas. The preset ratio of the argon-oxygen mixed gas is between 9999:1 and 99:1. That is, the oxygen content in the argon-oxygen mixed gas is between 0.01% and 1%. Preferably, the oxygen content in the argon-oxygen mixed gas is 0.05%.

[0062] The gas supply components include a gas source and corresponding gas pipelines. The gas source includes argon and oxygen sources, such as argon cylinders and oxygen cylinders, or a gas generation system consisting of an oxygen generator and an argon generator, to provide a stable supply of argon and oxygen.

[0063] The gas supply assembly may also include a gas mixing device, which uses a high-precision gas mixer to precisely control the flow rate and ratio of argon and oxygen, ensuring that the output argon-oxygen mixed gas ratio meets the preset requirements.

[0064] The gas supply assembly may also include a pressure regulating device equipped with a pressure sensor and a regulating valve, which automatically adjusts the gas supply pressure according to the pressure changes in the airflow channel 14 to ensure a stable gas supply.

[0065] The gas supply assembly may also include a flow monitoring and control device, using equipment such as a mass flow controller to monitor and control the flow rates of argon and oxygen in real time, ensuring that the ratio and flow rate of the mixed gas are accurate and stable.

[0066] In this embodiment of the invention, the power module 20 uses RLC resonance to generate power. The output power is maximized when the circuit operates at the resonant frequency. The resonant frequency is determined by both the internal parameters of the power module and the load impedance parameters. By adjusting the internal parameters of the power module 20 to resonate with the equivalent impedance parameters of tissue in a non-clotting state, the power module can output maximum power to wounds in a non-clotting state. As the blood gradually coagulates, the equivalent circuit parameters of the tissue change, and the circuit operating point deviates from the resonant point. At this time, the output power decreases, reducing thermal damage to the tissue. The power module's power is adaptively adjusted based on the impedance changes in the power module-electrode-human biological tissue circuit.

[0067] It is understood that the argon-oxygen mixed plasma jet coagulation device provided in this embodiment of the invention uses low-power energy output from the power module 20 to provide stable electrical energy for the entire argon-oxygen mixed plasma jet coagulation device. The output energy (30kHz-50kHz) is regulated by a self-calibrating impedance matching system to adapt to different coagulation requirements. Simultaneously, the gas supply component is connected to the airflow channel 14, suitable for supplying a preset proportion of argon-oxygen mixed gas to the airflow channel 14. This configuration not only reduces heat loss to protect normal tissue around the wound but also increases the role of biological effects in the coagulation process, accelerating blood coagulation, promoting wound healing, and significantly improving coagulation efficiency and shortening coagulation time.

[0068] Compared to traditional argon plasma coagulation, which uses high-frequency energy (350 kHz) to ionize argon gas and transfer electrical energy to generate a thermal coagulation effect, the power module 20 of this invention uses lower output energy, reducing thermal damage to tissues and protecting surrounding healthy tissues. Simultaneously, it increases the amount of argon-oxygen mixed gas, which forms a plasma jet in the jet reactor 10. The presence of oxygen helps generate more reactive nitrogen oxides (RONS). These RONS have various biological effects, such as accelerating blood coagulation and promoting wound healing, significantly improving coagulation efficiency, shortening coagulation time, and reducing wound bleeding.

[0069] The power module 20 is connected to the discharge electrode 11 via a self-calibrating impedance matching system. This system adaptively adjusts its output power based on changes in the wound surface, such as impedance changes during blood clotting. As the blood gradually clots and the wound becomes solid or forms an eschar, impedance mismatch occurs, and the system reduces its output power. This adaptive power regulation mechanism avoids excessive energy input, thereby reducing thermal damage and protecting surrounding healthy tissue.

[0070] Meanwhile, the power module 20 provides a stable energy source for the device. Its fixed-frequency characteristic ensures a stable output frequency from the power module 20, contributing to the stable generation of the plasma jet. Compared to variable-frequency power supplies, fixed-frequency power supplies have a simpler circuit structure, higher reliability, and reduce the possibility of device failure due to power frequency fluctuations.

[0071] In some embodiments of the present invention, the branch air passage 121 is located near the connection end 111 of the medium pipe 12, and the position of the air inlet passage 131 corresponds to the position of the branch air passage 121.

[0072] In some embodiments of the present invention, a hollow tube of a predetermined length is formed between the connection end 111 of the discharge electrode 11 and the jet end 112, and the side wall of the hollow tube is provided with an opening, and the airflow channel 14 communicates with the opening.

[0073] In essence, the discharge electrode 11 provided in this embodiment of the invention is a hollow electrode with an opening on its side wall that communicates with the airflow channel 14. The working gas flows not only along the airflow channel 14 on the outside of the discharge electrode 11 but also along the hollow cavity of the discharge electrode 11 on the inside. By combining airflow on the inside and outside of the discharge electrode 11, the working gas's effective area is increased, while simultaneously increasing the concentration of active plasma substances per unit volume, thereby improving the coagulation rate.

[0074] The discharge electrode 11 can be a stainless steel hollow tube, and the side of the stainless steel hollow tube can be opened as a gas channel. The distance between the discharge electrode 11 and the opening of the dielectric tube 12 can be 13mm.

[0075] The dielectric tube 12 can be a glass tube, and the insulating shell 13 can be made of materials such as ABS (acrylonitrile-butadiene-styrene copolymer), PC (polycarbonate), and PP (polypropylene).

[0076] Continue reading Figure 1 In some embodiments of the present invention, the insulating shell 13 has a first end and a second end disposed opposite to each other; the first end is provided with a lead channel 133, the second end is provided with a positioning hole 132, the connection end 111 of the discharge electrode 11 passes through the lead channel 133 and is connected to the self-calibrating impedance matching system; at least one of the jet end 112 of the discharge electrode 11 and the dielectric tube 12 passes through the positioning hole 132.

[0077] In the argon-oxygen mixed plasma jet coagulation device, the arrangement of the insulating shell 13 and the discharge electrode 11 ensures precise control and safe operation of the plasma jet. The coagulation process can be precisely controlled by adjusting the position of the discharge electrode 11, reducing damage to surrounding tissues.

[0078] Continue reading Figure 1 In some embodiments of the present invention, the insulating shell 13 includes a first shell 135 and a second shell 136, which are detachably connected; a lead wire channel 133 is provided at the end of the first shell 135, and a positioning hole 132 is provided at the end of the second shell 136.

[0079] Figure 2 This is a schematic diagram of the argon-oxygen mixed plasma jet coagulation device provided in Embodiment 2 of the present invention. Figure 3 yes Figure 2 The diagram shows an exploded view of the jet nozzle assembly in the argon-oxygen mixed plasma jet coagulation device.

[0080] See Figure 2 and Figure 3In some embodiments of the present invention, the argon-oxygen mixed plasma jet coagulation device further includes a jet nozzle assembly 50, which is disposed at the second end of the insulating housing 13, and the airflow channel 14 is connected to the jet nozzle assembly 50 to disperse the plasma jet beam.

[0081] By dispersing the plasma jet beam and applying it more evenly to the wound, the coagulation efficiency of the wound can be improved; at the same time, the wound can be cooled by the wind speed, further reducing thermal damage.

[0082] Specifically, the jet nozzle assembly 50 includes a nozzle component 51 and a flow guide cylinder 52. The nozzle component 51 is connected to the second end of the insulating shell 13. The flow guide cylinder 52 is rotatably disposed inside the nozzle component 51. The flow guide cylinder 52 has a through hole inside, through which the jet end 112 of the discharge electrode 11 passes. The outer circumferential surface of the flow guide cylinder 52 is provided with a flow guide groove 521, which is spirally arranged along the axial direction of the flow guide cylinder 52 and is connected to the airflow channel 14.

[0083] The nozzle component 51 can be made of high-temperature and corrosion-resistant ceramic material, possessing good insulation properties and mechanical strength. The nozzle component 51 has an overall conical shape and can be securely connected to the second end of the insulating shell 13 via a threaded connection. The connection is sealed with sealant to prevent gas leakage. An annular groove is provided inside the nozzle component 51 for positioning and fixing the guide tube 52.

[0084] The nozzle component 51 can be a single integral structure or composed of multiple components. The main function of the nozzle component 51 is to connect the airflow channel 14 and the gas mixing chamber. The insulating shell 13 is a split design. During assembly, the nozzle component 51 can be fixed by clamping it between the insulating shells 13. Adhesive or other materials can also be used for fixation.

[0085] When the argon-oxygen mixture flows into the drainage groove 521 from the gas flow channel 14, the spiral gas flow surrounds the jet end 112 of the discharge electrode 11. When the jet end 112 of the discharge electrode 11 generates a plasma jet, the spiral gas flow constrains and guides the plasma jet, making the plasma jet more concentrated and stable; at the same time, the plasma jet beam disperses and acts more evenly on the wound surface, which can improve the coagulation efficiency of the wound surface.

[0086] Figure 4 This is a schematic diagram of the argon-oxygen mixed plasma jet coagulation device provided in Embodiment 3 of the present invention. Figure 5 yes Figure 4 The diagram shows an exploded view of the argon-oxygen mixed plasma jet coagulation device. Figure 6 yes Figure 4The isometric sectional view of the argon-oxygen mixed plasma jet coagulation device shown.

[0087] See Figures 4 to 6 In the argon-oxygen mixed plasma jet coagulation device provided in Embodiment 3 of the present invention, the jet reactor 10 includes a discharge electrode 11, a dielectric tube 12 and an insulating shell 13. The dielectric tube 12 and the discharge electrode 11 are arranged side by side inside the insulating shell 13. A first airflow channel 141 is formed inside the dielectric tube 12, and a second airflow channel 142 is formed inside the discharge electrode 11. A connection end 111 and a jet end 112 are formed at both ends of the discharge electrode 11, respectively. The jet end 112 is adapted to form a plasma jet beam.

[0088] The gas supply assembly 30 is connected to the first gas flow channel 141 and the second gas flow channel 142 respectively. One of the first gas flow channel 141 and the second gas flow channel 142 can deliver argon gas, and the other of the first gas flow channel 141 and the second gas flow channel 142 can deliver oxygen gas. That is, the first gas flow channel 141 and the second gas flow channel 142 can deliver different gases. Of course, the first gas flow channel 141 and the second gas flow channel 142 can also deliver the same gas.

[0089] When plasma jet coagulation requires utilizing the different properties of argon and oxygen, the first gas supply pipe 31 and the second gas supply pipe 32 supply different working gases. The first gas supply pipe 31 can supply argon, and the second gas supply pipe 32 can supply oxygen. For example, the first gas supply pipe 31 delivers 99.99% pure argon to the first gas flow channel 141 at a flow rate of 5 L / min through a gas supply source. The second gas supply pipe 32 delivers 99.5% pure oxygen to the second gas flow channel 142 at a flow rate of 3 L / min. The use of mixed gases, especially mixed oxygen, is mainly to achieve the generation of high concentrations of active oxygen particles at relatively low power, reducing thermal damage without compromising coagulation effectiveness.

[0090] In the generating chamber of the jet reactor 10, argon and oxygen flow in through their respective gas flow channels, and the two gases can be fully mixed and form an argon-oxygen mixed plasma jet under the action of a high-frequency electric field.

[0091] When it is necessary to increase the argon supply to enhance the plasma jet, both the first gas supply pipe 31 and the second gas supply pipe 32 supply argon. For example, the first gas supply pipe 31 supplies argon at a flow rate of 6 L / min, and the second gas supply pipe 32 simultaneously supplies argon at a flow rate of 4 L / min. In this way, more argon enters the generation chamber of the jet reactor 10, resulting in a higher energy density in the generated argon plasma jet, which may more rapidly denature and coagulate proteins in the blood during the coagulation process, while reducing thermal damage to surrounding tissues.

[0092] It should be noted that the gas supply assembly 30 may also include a pressure regulating device, which is equipped with a pressure sensor and a regulating valve to automatically adjust the gas supply pressure according to the pressure changes in the corresponding airflow channel, so as to ensure a stable gas supply.

[0093] The gas supply assembly 30 may also include a flow monitoring and control device, using equipment such as a mass flow controller to monitor and control the flow rates of argon and oxygen in real time, ensuring that the ratio and flow rate of the mixed gas are accurate and stable.

[0094] It is understood that the argon-oxygen mixed plasma jet coagulation device provided in this embodiment of the invention uses low-power energy output from the power module 20 to provide stable electrical energy for the entire argon-oxygen mixed plasma jet coagulation device. The output energy (30kHz-50kHz) is regulated by a self-calibrating impedance matching system to adapt to different coagulation requirements. Simultaneously, the gas supply component 30 is connected to the airflow channel 14, suitable for supplying a preset proportion of argon-oxygen mixed gas to the airflow channel 14. This configuration not only reduces heat loss to protect normal tissue around the wound but also increases the role of biological effects in the coagulation process, accelerating blood coagulation, promoting wound healing, and significantly improving coagulation efficiency and shortening coagulation time.

[0095] Compared to traditional argon plasma coagulation, which uses high-frequency energy (350 kHz) to ionize argon gas and transfer electrical energy to generate a thermal coagulation effect, the power module 20 of this invention uses lower output energy, reducing thermal damage to tissues and protecting surrounding healthy tissues. Simultaneously, it increases the amount of argon-oxygen mixed gas, which forms a plasma jet in the jet reactor 10. The presence of oxygen helps generate more reactive nitrogen oxides (RONS). These RONS have various biological effects, such as accelerating blood coagulation and promoting wound healing, significantly improving coagulation efficiency, shortening coagulation time, and reducing wound bleeding.

[0096] The power module 20 is connected to the discharge electrode 11 after being adjusted by a self-calibrating impedance matching system. This system adaptively adjusts its output power based on changes in the wound surface (such as impedance changes during blood coagulation). As the blood gradually coagulates and the wound becomes solid or forms an eschar, impedance mismatch occurs, and the system reduces its output power. This adaptive power regulation mechanism avoids excessive energy input, thereby reducing thermal damage and protecting surrounding healthy tissue.

[0097] In some embodiments of the present invention, a hollow tube of a predetermined length is formed between the connection end 111 and the jet end 112 of the discharge electrode 11. This means that the discharge electrode 11 provided in the embodiments of the present invention is a hollow electrode.

[0098] The front end of the discharge electrode 11 can be solid and have a specific shape, such as needle-shaped or knife-shaped. The middle and rear ends of the discharge electrode 11 can be hollow stainless steel tubes, and the sides of the hollow stainless steel tubes can be opened as gas channels. The distance between the discharge electrode 11 and the opening of the dielectric tube 12 can be 13 mm.

[0099] The dielectric tube 12 can be a glass tube, and the insulating shell 13 can be made of materials such as ABS (acrylonitrile-butadiene-styrene copolymer), PC (polycarbonate), and PP (polypropylene).

[0100] Continue reading Figures 4 to 6 In some embodiments of the present invention, the gas supply assembly 30 includes a first gas supply pipe 31, a second gas supply pipe 32, and a gas supply source connected to the first gas supply pipe 31 and the second gas supply pipe 32. The first gas supply pipe 31 is connected to the first airflow channel 141, and the second gas supply pipe 32 is connected to the second airflow channel 142.

[0101] Essentially, the argon-oxygen mixed plasma jet coagulation device has dual gas inlet pipes, namely a first gas supply pipe 31 and a first gas flow channel 141 connected to the first gas supply pipe 31, and a second gas supply pipe 32 and a second gas flow channel 142 connected to the second gas supply pipe 32. The first gas supply pipe 31 and the second gas supply pipe 32 can be supplied with different working gases or the same working gas.

[0102] The gas supply assembly 30 is also equipped with a gas flow regulating valve and a pressure sensor. The gas flow regulating valve can control the gas flow rate entering the first gas supply pipe 31 and the second gas supply pipe 32. The pressure sensor is used to monitor the gas pressure in the first gas supply pipe 31 and the second gas supply pipe 32 in real time.

[0103] Continue reading Figures 4 to 6 In some embodiments of the present invention, the argon-oxygen mixed plasma jet coagulation device further includes an adjustment component 40; the side wall of the insulating shell 13 is provided with an adjustment groove 134, the adjustment component 40 is disposed in the adjustment groove 134 and connected to the discharge electrode 11, and the adjustment component 40 is adapted to adjust the position of the discharge electrode 11 to be closer to or further away from the target tissue.

[0104] During coagulation procedures, different tissue depths may require different positions for the discharge electrode 11. By adjusting the component 40, the discharge electrode 11 can be adjusted to a suitable position according to the tissue depth and coagulation requirements to ensure optimal coagulation results.

[0105] The adjusting component 40 can consist of a slider and a connecting rod. The slider is located on the outer wall of the insulating housing 13 for easy manual operation. One end of the connecting rod is connected to the slider, and the other end passes through the adjusting groove 134 and connects to the discharge electrode 11. By pushing the slider to slide within the adjusting groove 134, the position of the discharge electrode 11 can be adjusted.

[0106] Continue reading Figures 4 to 6 In some embodiments of the present invention, the insulating shell 13 has a first end and a second end disposed opposite to each other; the first end is provided with a lead channel 133, the second end is provided with a positioning hole 132, the connection end 111 of the discharge electrode 11 passes through the lead channel 133 and is connected to the self-calibrating impedance matching system; the jet end 112 of the discharge electrode 11 passes through the positioning hole 132.

[0107] The lead channel 133 is a circular hole, the diameter of which is designed according to the size of the connection end 111 of the discharge electrode 11. The inner wall of the channel is smooth to reduce wear on the discharge electrode 11. The positioning hole 132 can be circular or square, and its shape can also be formed in other ways. It is mainly determined according to the shape of the jet end 112 of the discharge electrode 11. Its size is slightly larger than the diameter of the jet end 112 of the discharge electrode 11 to facilitate the installation and positioning of the discharge electrode 11.

[0108] In the argon-oxygen mixed plasma jet coagulation device, the arrangement of the insulating shell 13 and the discharge electrode 11 ensures precise control and safe operation of the plasma jet. The coagulation process can be precisely controlled by adjusting the position of the discharge electrode 11, reducing damage to surrounding tissues.

[0109] Continue reading Figures 4 to 6 In some embodiments of the present invention, the argon-oxygen mixed plasma jet coagulation device further includes a jet nozzle assembly 50, which is disposed at the second end of the insulating housing 13, and the airflow channel 14 is connected to the jet nozzle assembly 50 to disperse the plasma jet beam.

[0110] By dispersing the plasma jet beam and applying it more evenly to the wound, the coagulation efficiency of the wound can be improved; at the same time, the wound can be cooled by adjusting the wind speed, further reducing thermal damage.

[0111] Specifically, the jet nozzle assembly 50 includes a nozzle component 51 and a flow guide cylinder 52. The nozzle component 51 is connected to the second end of the insulating shell 13. The flow guide cylinder 52 is rotatably disposed inside the nozzle component 51. The flow guide cylinder 52 has a through hole inside, through which the jet end 112 of the discharge electrode 11 passes. The outer circumferential surface of the flow guide cylinder 52 is provided with a flow guide groove 521. The flow guide groove 521 is spirally arranged along the axial direction of the flow guide cylinder 52 and is connected to the airflow channel 14.

[0112] The nozzle component 51 can be made of a ceramic material that is resistant to high temperatures and corrosion, and has good insulation performance and mechanical strength. The overall shape of the nozzle component 51 is conical, and it can be firmly connected to the second end of the insulating housing 13 by means of threaded connection or other connection methods. A sealant is used at the connection to prevent gas leakage. An annular slot is provided inside the nozzle component 51, and the annular slot is used to position and fix the drainage cylinder 52.

[0113] The nozzle component 51 can be a single integral structure or composed of multiple components. The main function of the nozzle component 51 is to connect the air flow channel 14 and the gas mixing chamber. The insulating housing 13 is of a split design. During the assembly process, the nozzle component 51 can be clamped between the insulating housing 13 to achieve fixation, and at the same time, glue and the like can be used to assist in fixation.

[0114] When the argon-oxygen mixed gas flows from the air flow channel 14 into the drainage groove 521, the spiral air flow will surround the jet end 112 of the discharge electrode 11. When the jet end 112 of the discharge electrode 11 generates a plasma jet, the spiral air flow will have a constraining and guiding effect on the plasma jet, making the plasma jet more concentrated and stable; at the same time, the plasma jet beam spreads out and acts on the wound surface more evenly, which can improve the blood coagulation efficiency of the wound surface.

[0115] Figure 7 is a schematic diagram of the usage state of the argon-oxygen mixed plasma jet blood coagulation device provided by an embodiment of the present invention. Figure 8 is an equivalent circuit diagram of the argon-oxygen mixed plasma jet blood coagulation device provided by an embodiment of the present invention.

[0116] Refer to Figure 7 , the argon-oxygen mixed plasma jet blood coagulation device provided by an embodiment of the present invention has an adaptive blood coagulation function for the blood coagulation part, which is based on the impedance self-matching principle between the argon-oxygen mixed gas jet of the argon-oxygen mixed plasma jet blood coagulation device and the blood coagulation load.

[0117] Among them, the plasma generated by the argon-oxygen mixed gas jet contacts the blood coagulation site, and the blood at the blood coagulation site is quickly oxidized and coagulated to form a blood film substance with a slightly darker color, and the equivalent impedance parameter presented is Rh2. The equivalent impedance of the tissue at the non-blood coagulation site is Rh1, and there is Rh1 < Rh2. The equivalent current path is as Figure 8 shown. Even under the condition that the jet treatment position remains unchanged, due to the smaller impedance of Rh1, it will automatically share more of the current component of the Ar jet, thereby promoting the rapid blood coagulation and oxidation of the non-blood coagulation position to form a blood film, increasing the impedance value of Rh1 until the impedances of Rh1 and Rh2 are approximately equal, and completing the blood coagulation function of the entire blood coagulation site.

[0118] Continue to refer to Figure 7During plasma argon-oxygen jet treatment, the degree of coagulation changes with increasing treatment time. The difference in coagulation degree is directly reflected by the intensity of blood color, and this change can be represented by a difference in impedance (Rh1, Rh2). That is, as the treatment time increases, the darker the blood (higher coagulation degree), the greater the blood impedance. When the resistance of Rh2 increases (blood color), it causes an adaptive adjustment of the plasma current path, resulting in current shunting. This allows the plasma jet to automatically optimize energy distribution based on real-time impedance changes, thereby achieving continuous control of the coagulation process.

[0119] In this embodiment of the invention, the power module 20 uses RLC resonance to generate power. The output power is maximized when the circuit operates at the resonant frequency. The resonant frequency is determined by both the internal parameters of the power module and the load impedance parameters. By adjusting the internal parameters of the power module 20 to resonate with the equivalent impedance parameters of tissue in a non-clotting state, the power module 20 can output maximum power for wounds in a non-clotting state. As the blood gradually coagulates, the equivalent circuit parameters of the tissue change, and the circuit operating point deviates from the resonant point. At this time, the output power decreases, reducing thermal damage to the tissue. The power of the power module 20 is adaptively adjusted by the change in the impedance of the power supply-electrode-human biological tissue circuit.

[0120] Figure 9(a) shows the relative spectral intensity of active particles measured by a spectrometer in an argon plasma condensation apparatus. Figure 9(b) shows the relative spectral intensity of active particles measured by a spectrometer in an argon-oxygen mixed plasma jet coagulation apparatus.

[0121] In this embodiment of the invention, a partial liver resection model in pigs is used to simulate a clinical partial liver resection. Conventional argon plasma coagulation equipment and argon-oxygen mixed plasma jet device are used to treat the bleeding section of the liver.

[0122] During the experiment, the coagulation rate and the highest operating temperature were recorded.

[0123] Referring to Figures 9(a) and 9(b), the relative spectral intensities of the active particles were measured by a spectrometer. The results showed that the spectral emission intensities of the active nitrogen oxides (RONS) produced by the argon plasma condensation device, namely [OH(AX)], [O](777), etc., were lower than those of the RONS produced by the argon-oxygen mixed plasma jet device.

[0124] Figure 10(a) is a comparison of coagulation rates using different devices during partial hepatectomy in pigs. Figure 10(b) is a comparison of temperatures using different devices during partial hepatectomy in pigs.

[0125] Referring to Figure 10(a), the average coagulation rate of the argon-oxygen mixed plasma jet device during partial liver resection in pigs was 0.078 s / cm. 2 The average coagulation rate of the argon plasma coagulation device is 0.096 s / cm. 2 .

[0126] Referring to Figure 10(b), during partial liver resection in pigs, the highest operating temperature of the argon-oxygen mixed plasma jet device during the coagulation process is 91.3℃; the highest operating temperature of the argon plasma coagulation device during the coagulation process is 117.3℃.

[0127] Figure 11 This is a schematic diagram comparing the processing procedures of different devices during partial liver resection in pigs.

[0128] See Figure 11 The degree of thermal damage was assessed by single-point treatment at a distance of 1 cm from the liver surface using an argon-oxygen mixed plasma jet device and an argon plasma condensation device for 5 s, 10 s, and 20 s, respectively, followed by hematoxylin-eosin staining.

[0129] The liver thermal injury area exhibits three distinct boundaries, forming a carbonization zone, a cavitation zone, and a sub-boiling zone. Compared to argon plasma condensation equipment, the argon-oxygen mixed plasma jet device exhibits a smaller total area of ​​liver thermal injury and a lower degree of thermal damage at the same treatment time.

[0130] Therefore, the argon-oxygen hybrid plasma jet coagulation device provided in this embodiment of the invention employs a fixed-frequency modulation power supply to reduce power consumption and utilizes a self-calibrating impedance matching system to adaptively adjust the output power according to changes in the coagulation wound surface, thereby reducing heat loss and protecting the surrounding normal tissue. Simultaneously, it utilizes the combined biochemical and thermal effects of the low-temperature plasma jet for coagulation. The addition of oxygen to the argon gas, after plasmaification, generates more active particles. These active particles activate platelets, accelerate coagulation, denature proteins, and accelerate fibrinogen aggregation, thus promoting coagulation. The coagulation effect generated through the biochemical mechanism reduces the heat required for some of the coagulation process. Experiments have shown that it can lower the operating temperature during coagulation, reduce the formation of carbonized eschar, and minimize the extent of thermal damage to surrounding normal tissue.

[0131] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, and not to limit them; although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features; and these modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of the present invention.

Claims

1. An argon-oxygen mixed plasma jet coagulation device, characterized in that, include: A jet reactor includes a discharge electrode, a dielectric tube, and an insulating shell. The discharge electrode and the dielectric tube are disposed inside the insulating shell. The two ends of the discharge electrode are respectively formed as a connection end and a jet end. The jet end passes through the insulating shell and is adapted to form a plasma jet beam. At least one of the discharge electrode and the dielectric tube has an internal airflow channel. A power module, connected to the connection terminal, outputs energy of 30kHz-50kHz. A gas supply component, connected to the gas flow channel, is used to supply the gas flow channel with a preset ratio of argon-oxygen mixed gas, wherein the ratio of argon to oxygen is between 9999:1 and 99:

1. The power module includes a power supply body and a self-calibrating impedance matching system. The self-calibrating impedance matching system is electrically connected to the power supply body and is used to adjust the power of the power supply body according to the impedance between the argon-oxygen mixed gas and the coagulation load. The self-calibrating impedance matching system is based on the RLC resonance principle. It achieves adaptive adjustment of output power by having the circuit operating point deviate from the resonance point as the impedance of the coagulation load changes.

2. The argon-oxygen mixed plasma jet coagulation device according to claim 1, characterized in that, The dielectric tube is sleeved on the outside of the discharge electrode, and the gas flow channel is formed between the dielectric tube and the discharge electrode; The side wall of the insulating shell is provided with an air inlet channel, and the side wall of the medium tube is provided with a branch air channel. The branch air channel is connected to the airflow channel and extends to the position of the air inlet channel and is connected to the air inlet channel; the air inlet channel is connected to the air supply assembly.

3. The argon-oxygen mixed plasma jet coagulation device according to claim 2, characterized in that, A hollow tube of a predetermined length is formed between the connection end and the jet end of the discharge electrode, and the side wall of the hollow tube is provided with an opening, and the airflow channel is connected to the opening.

4. The argon-oxygen mixed plasma jet coagulation device according to claim 1, characterized in that, The dielectric tube and the discharge electrode are arranged side by side inside the insulating shell. The interior of the dielectric tube forms a first airflow channel, and the interior of the discharge electrode forms a second airflow channel. The gas supply assembly includes a first gas supply pipe, a second gas supply pipe, and gas sources connected to the first gas supply pipe and the second gas supply pipe. The first gas supply pipe is connected to the first airflow channel, and the second gas supply pipe is connected to the second airflow channel.

5. The argon-oxygen mixed plasma jet coagulation device according to claim 4, characterized in that, It also includes adjustment components; The side wall of the insulating shell is provided with an adjustment groove, the adjustment component is disposed in the adjustment groove and connected to the discharge electrode, and the adjustment component is adapted to adjust the position of the discharge electrode to move closer to or further away from the target tissue.

6. The argon-oxygen mixed plasma jet coagulation device according to any one of claims 1 to 5, characterized in that, The insulating shell has a first end and a second end that are disposed opposite to each other; The first end is provided with a lead wire channel, the second end is provided with a positioning hole, the connection end of the discharge electrode passes through the lead wire channel and is connected to the power module; the jet end of the discharge electrode passes through the positioning hole.

7. The argon-oxygen mixed plasma jet coagulation device according to claim 6, characterized in that, It also includes a jet nozzle assembly, which is located at the second end of the insulating housing, and the airflow channel is connected to the jet nozzle assembly.

8. The argon-oxygen mixed plasma jet coagulation device according to claim 7, characterized in that, The jet nozzle assembly includes: The nozzle component is connected to the second end of the insulating housing; A flow guide cylinder is rotatably disposed inside the nozzle component. The flow guide cylinder has a through hole inside, through which the jet end of the discharge electrode passes. A flow guide groove is provided on the outer circumferential surface of the flow guide cylinder. The flow guide groove is spirally arranged along the axial direction of the flow guide cylinder and is connected to the airflow channel.

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