Portable high-frequency electrotome

Abstract

The embodiment of the invention provides a portable high-frequency electrotome. The portable high-frequency electrotome comprises a main machine, a battery base, bipolar electric tweezers and a battery bin, wherein the bipolar electric tweezers can be plugged and electrically connected relative to the main machine, and the battery bin can be plugged and electrically connected relative to the main machine; the host and the battery base are assembled in an L shape, the battery base and the host are matched to fix the battery bin, the host, the battery base and the battery bin are integrally in a cube shape after being assembled, a layered layout structure combining a double-layer circuit board and a heat dissipation assembly is adopted in the host, and the heat dissipation assembly comprises a fan and heat dissipation fins. The portable high-frequency electrotome provided by the scheme can work without relying on a mains supply, is compact in structure and can meet the use requirements of mobile medical scenes.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and more particularly to a portable high-frequency electrosurgical unit. Background Art

[0002] In medical surgery, high-frequency bipolar electrosurgical units are indispensable tools, primarily used for tissue hemostasis. Current high-frequency bipolar electrosurgical units are large, heavy, and dependent on mains power, resulting in a cumbersome design that hinders mobility. Due to their strong reliance on mains power, they cannot be used in scenarios where mains power is unavailable, such as emergency rescues, field surgeries, and community clinics. This limits their application scenarios, restricting their effectiveness to hospitals or locations with mains power. This limitation renders high-frequency bipolar electrosurgical units useless in situations without mains power.

[0003] Therefore, how to develop a portable high-frequency electrosurgical unit suitable for mobile medical scenarios and capable of on-site emergency treatment has become a technical problem that urgently needs to be solved in this field. Summary of the Invention

[0004] This invention provides a portable high-frequency electrosurgical unit that can be used without relying on mains power, thus meeting the needs of mobile medical scenarios.

[0005] In a first aspect, the portable high-frequency electrosurgical unit provided in this application includes: a main unit, a battery base, bipolar electric tweezers that are pluggable and electrically connected to the main unit, and a battery compartment that is pluggable and electrically connected to the main unit; the main unit and the battery base are assembled in an L-shape, and the battery base cooperates with the main unit to fix the battery compartment; the main unit, the battery base and the battery compartment are assembled into a cubic shape; the main unit adopts a layered layout structure combining a double-layer circuit board and a heat dissipation component, and the heat dissipation component includes: a fan and a heat sink.

[0006] This design enables a portable high-frequency electrosurgical unit to be assembled in an L-shape with the main unit and battery base. The main unit, bipolar electric forceps, and battery compartment are pluggable and electrically connected. The battery compartment is secured to the main unit. The assembled unit forms a cubic shape, and the internal structure of the main unit utilizes a layered layout combining a double-layer circuit board and a heat dissipation component. This solves the problems of large size, heavy weight, reliance on mains power, and inconvenience in portability associated with existing high-frequency bipolar electrosurgical units. This portable high-frequency electrosurgical unit does not rely on mains power, its pluggable design facilitates maintenance and replacement, and the L-shaped assembly and cubic structure achieve miniaturization and weight reduction. It meets the needs of mobile medical scenarios and is suitable for use in emergency rescue, field surgery, and other similar situations. Operators can easily carry it, and it can operate normally even in environments without a fixed power source, expanding the application scenarios of portable high-frequency electrosurgical units.

[0007] In conjunction with the first aspect, in a first possible implementation of the first aspect, the host internally adopts a layered layout structure combining a double-layer circuit board and a heat dissipation component, specifically including: the front panel of the host is provided with an air inlet, and the rear panel of the host is provided with an air outlet; the host housing is provided with a first circuit board fixed to the bottom surface and a second circuit board fixed to the top surface, the first circuit board and the second circuit board are parallel, and a heat sink with multiple branches of the fan is provided between the first circuit board and the second circuit board; the multiple branches of the heat sink are located around the fan, and at least a portion of the heat sink includes a double-layer structure; the branches of the heat sink cover the main heat-generating module of the portable high-frequency electrosurgical unit, which is mounted on the first circuit board and below the second circuit board using a surface mount process; the main control module is installed in the area below the second circuit board facing the fan; the fan is used so that, when the fan is running, the air inlet, the branches of the heat sink, the fan, and the air outlet constitute a heat dissipation airflow.

[0008] The above solution utilizes an air inlet on the front panel and an air outlet on the rear panel of the main unit. A fan and multi-branch heatsinks are positioned between the parallel first and second circuit boards, with the heatsinks featuring a double-layer structure that covers the main heat-generating modules. The main control module is positioned close to the fan, creating a highly efficient cooling airflow. With this solution, when the fan is running, airflow flows systematically through the air inlet, heatsink branches, fan, and air outlet. The fan-driven airflow quickly removes heat generated by the main heat-generating modules. The double-layer heatsink structure enhances the heat exchange area and efficiency, ensuring stable temperatures for the surface-mount heat-generating modules and the main control module during operation, preventing performance degradation or malfunctions due to overheating. Simultaneously, the rational layout of the circuit boards and heatsink components achieves efficient heat dissipation while fully utilizing the internal space of the main unit, accommodating the need for miniaturization, and improving the reliability of the portable high-frequency electrosurgical unit during continuous operation.

[0009] In conjunction with the first aspect, in a second possible implementation of the first aspect, the main heat-generating module includes: a high-frequency generator, a data monitoring module, and a power control module mounted on the first circuit board.

[0010] The above solution clarifies that the main heat-generating modules include a high-frequency generator, a data monitoring module, and a power control module mounted on the first circuit board. Combined with the aforementioned heat dissipation structure, these heat-generating components are covered by multi-branch heat sinks, and the fan-driven airflow can directly and efficiently dissipate heat from these high-heat sources, avoiding the problem of uneven heat dissipation caused by dispersed layout. At the same time, concentrating these modules on the first circuit board not only facilitates compact assembly through surface mount technology, reducing internal space occupation and adapting to the miniaturization requirements of the equipment, but also shortens the signal transmission path between modules, reduces interference, ensures stable output of the high-frequency generator, accuracy of data monitoring, and precision of voltage control, thereby improving the operational reliability and efficiency of the equipment and ensuring the stable operation of key functions during surgery. In conjunction with the first aspect, in a third possible implementation of the first aspect, the battery base is equipped with a data detection transformer and an output transformer that are electrically connected to the first circuit board.

[0011] The above solution integrates the large data detection transformer and output transformer within the battery base and connects them electrically to the first circuit board. This design effectively utilizes the space of the battery base to accommodate large components, avoiding the transformers occupying the limited internal space of the host unit. This creates conditions for a compact layout of the double-layer circuit board and heat dissipation components within the host unit, contributing to the overall miniaturization of the device. At the same time, the direct electrical connection between the transformer and the first circuit board shortens the signal transmission path, reduces energy loss and interference, and ensures the stability of data detection and voltage output. While balancing device miniaturization, it also improves overall operating performance.

[0012] In conjunction with the first aspect, in a fourth possible implementation of the first aspect, the battery base is provided with a blind slot for assembling the battery compartment, and the host is equipped with a plug that is electrically connected to the battery compartment.

[0013] The above solution, by setting blind slots on the battery base for assembling the battery compartment, and configuring a plug for electrical connection between the main unit and the battery compartment, allows the battery compartment to be accurately positioned during installation via the blind slots, avoiding mis-insertion that could damage the interface. Simultaneously, the corresponding connection between the plug and the battery compartment ensures the stability of the electrical connection. This structural design not only provides a stable assembly base for the battery compartment using the blind slots, but also achieves reliable electrical transmission between the main unit and the battery compartment through the plug. While ensuring convenient battery compartment installation, it further optimizes the space utilization of the equipment. Combined with the design of the battery base accommodating the transformer, this contributes to the miniaturization of the equipment and prevents poor contact caused by vibration during use, improving the power supply reliability of the equipment in mobile scenarios.

[0014] In conjunction with the first aspect, in the fifth possible implementation of the first aspect, the battery compartment (103) is provided with a battery compartment switch, and by moving the battery compartment switch toward the battery base, it is locked into the corresponding slot provided on the battery base, so as to fasten the battery compartment to the battery base.

[0015] The aforementioned solution utilizes a switch on the battery compartment that can move towards the battery base, allowing it to snap into the base's slot for secure fastening. This structure not only simplifies operation and enables quick installation and locking of the battery compartment, but also ensures a stable connection between the battery compartment and the base through mechanical engagement, effectively preventing the risk of the battery compartment accidentally detaching during movement or vibration. Furthermore, this design, combined with the blind slot of the battery base and the plug of the main unit, forms a complete "positioning-connection-locking" assembly logic. This ensures convenient battery compartment installation and removal while further enhancing the reliability of the power supply system, meeting the stringent stability requirements of mobile medical scenarios, and providing structural support for rapid battery replacement.

[0016] In conjunction with the first aspect, in the sixth possible implementation of the first aspect, the portable high-frequency electrosurgical unit further includes: a mode monitoring module and an adaptive feedback module mounted on the first circuit board or the second circuit board; the mode monitoring module is used to monitor the current working mode corresponding to the operation of the mode switching button of the portable high-frequency electrosurgical unit, the current working mode including: manual mode or adaptive feedback mode; the adaptive feedback module is configured to: when the mode monitoring module detects that the current working mode is adaptive feedback mode, respond to the control command generated by the main control module based on the parameter value of the preset parameter obtained by the data monitoring module, control the intensity, duration or waveform parameters of the high-frequency current output by the high-frequency generator, the high-frequency current being conducted to the tissue to be coagulated through the bipolar electric tweezers, so that the output energy matches the coagulation requirements of the tissue.

[0017] The above solution incorporates a mode monitoring module and an adaptive feedback module on either the first or second circuit board. The mode monitoring module accurately identifies manual or adaptive feedback modes. In adaptive feedback mode, the adaptive feedback module flexibly adjusts the high-frequency current parameters output by the high-frequency generator based on control commands generated by the main control module using preset parameters, ensuring precise matching of output energy to the needs of the tissue to be coagulated. This design retains the manual mode to meet the needs of doctors' personalized operating habits while achieving intelligent adjustment of energy output through adaptive feedback mode. This avoids unstable coagulation effects caused by differences in doctor experience or operation by non-professionals, reduces the risk of tissue damage due to excessive coagulation or bleeding caused by insufficient coagulation, lowers the reliance on the operator's professional skills, and improves the safety and accuracy of operation, thus adapting to the needs of mobile medical scenarios.

[0018] In conjunction with the first aspect, in the seventh possible implementation of the first aspect, the preset parameters include: the impedance of the tissue to be coagulated.

[0019] The above scheme explicitly sets the preset parameter as the impedance of the tissue to be coagulated. This preset parameter directly reflects the electrical characteristics of the tissue and the output state of the device, making the control basis of the adaptive feedback module more targeted. Adjusting the high-frequency current parameter based on this core parameter can precisely optimize the coagulation effect and ensure that the coagulation effect is highly matched with the current tissue state. This scheme improves the accuracy of energy control and helps to reduce the risk of tissue damage while ensuring the surgical effect.

[0020] In conjunction with the first aspect, in the eighth possible implementation of the first aspect, the preset parameters include: the impedance of the tissue to be coagulated, and at least one of the following parameters: output voltage, ambient temperature, contact area between the bipolar electric forceps and the tissue, whether the bipolar electric forceps is in a raised state, and the duration of contact between the bipolar electric forceps and the tissue.

[0021] The above scheme presets parameters including the impedance of the tissue to be coagulated and at least one of the other listed parameters. The combined effect of multiple parameters can more comprehensively reflect the real-time coagulation scenario of the tissue to be coagulated. Through the synergy of multiple parameters, the output energy is optimized, further improving the coagulation effect and safety.

[0022] In conjunction with the first aspect, in the ninth possible implementation of the first aspect, the main unit, the battery base, and the outer shell of the battery compartment are made of nylon resin, and the first circuit board and the second circuit board are made of FR-4 material; the overall dimensions (width × height × length) of the main unit, the battery base, and the battery compartment after assembly are cubic in shape and do not exceed 43 mm × 60 mm × 108 mm, and the weight of the portable high-frequency electrosurgical unit does not exceed 400 grams.

[0023] In the aforementioned design, the main unit, battery base, and battery compartment shell are made of nylon resin, while the first and second circuit boards are made of FR-4 material. The overall dimensions of the assembled components do not exceed 43 mm × 60 mm × 108 mm, and the weight does not exceed 400 grams. Nylon resin is lightweight and possesses good corrosion resistance and mechanical strength, enabling it to adapt to complex environments. FR-4 material is heat-resistant and has good insulation properties, ensuring stable operation of the circuit boards. Simultaneously, the compact size and light weight make the device more portable and easier to operate, meeting the needs of mobile healthcare scenarios. While meeting the requirements of structural strength and functional stability, it achieves true miniaturization and lightweighting, providing operators with a more flexible and comfortable experience during operation. Attached Figure Description

[0024] In order to more clearly illustrate the specific embodiments of the present invention or the technical solutions in the prior art, the following briefly introduces the drawings required for use in the specific embodiments or the description of the prior art. Obviously, the drawings described below are some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative work.

[0025] Figure 1A This is a schematic diagram of the external structure of a portable high-frequency electrosurgical unit according to one embodiment of the present invention; Figure 1B yes Figure 1A Schematic diagrams of the external structure of the main unit and battery base from different perspectives; Figure 1C yes Figure 1A Schematic diagrams of the external structure from different perspectives in a part of the middle section; Figure 1D yes Figure 1A Schematic diagrams and perspective views of the structure from different perspectives in the middle section; Figure 1E yes Figure 1A A schematic diagram of the internal structure of the main unit and the battery base; Figure 1F This is a schematic diagram of the heat sink structure in one embodiment of the present invention; Figure 2A This is a schematic diagram of a structure including a heat sink, a fan, and a first circuit board in one embodiment of the present invention; Figure 2B This is a schematic diagram of the air duct inside the host unit in one embodiment of the present invention; Figure 2C This is a schematic diagram of a structure including a heat sink and a second circuit board in one embodiment of the present invention; Figure 3 This is a schematic diagram of the main circuit structure of a portable high-frequency electrosurgical unit provided in an embodiment of the present invention.

[0026] Explanation of reference numerals in the attached figures: 101. Main unit; 102. Battery base; 103. Battery compartment; 104. Connecting terminal; 105. Connecting cable; 106. Bipolar tweezers; 107. Display screen; 108. Output port; 109. Air inlet; 110. Air outlet; 111. Blind slot; 112. Card slot; 113. Battery compartment switch; 114. Plug; 115. Switch; 116. Button; 1031. Slot; 1032. Rib; 121. First circuit board; 122. Second circuit board; 123. Fan; 124. Heat sink; 125. Main control module; 1241. First branch of heat sink; 1242. Second branch of heat sink; 1243. Third branch of heat sink; 12421. First area of ​​the second branch of heat sink; 12422. Second area of ​​the second branch of heat sink; 131. Isolation circuit; 132. Energy storage inductor; 141. High frequency generator; 142. Power management module; 143. Data monitoring module; 144. Driver module; 145. Display control module; 146. Mode monitoring module; 147. Adaptive feedback module. Detailed Implementation

[0027] The terminology used in the following embodiments of this application is for the purpose of describing particular embodiments only and is not intended to be limiting of this application. As used in the specification and appended claims of this application, the singular expressions “a,” “an,” “the,” “the,” “the,” and “this” are intended to include the plural expressions as well, unless the context clearly indicates otherwise. It should also be understood that the term “and / or” as used in this application refers to any or all possible combinations including one or more of the listed items.

[0028] Hereinafter, the terms "first" and "second" are used for descriptive purposes only and should not be construed as implying or suggesting relative importance or implicitly indicating the number of indicated technical features. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature, and in the description of the embodiments of this application, unless otherwise stated, "multiple" means two or more.

[0029] In medical surgery, high-frequency bipolar electrosurgical units are essential surgical tools, primarily used for tissue hemostasis. Current high-frequency bipolar electrosurgical units rely on mains power, are bulky, inconvenient to carry, and have low operational flexibility. For example, common models are approximately 30cm × 40cm × 20cm in size and weigh over 10kg, requiring placement on a surgical trolley or fixed support, making them unsuitable for use in fixed environments with mains power, such as operating rooms.

[0030] In scenarios such as emergency rescue, field surgery, and community clinics, there are problems such as operators needing to carry equipment and move quickly, lack of mains power supply, and insufficient professional skills of operators. These issues make it impossible to use high-frequency bipolar electrosurgical units in scenarios where mains power cannot be connected, thus failing to meet the actual medical operation needs.

[0031] This invention provides a portable high-frequency electrosurgical unit and its usage method, which overcomes the shortcomings of existing technologies. The portable high-frequency electrosurgical unit and its usage method according to embodiments of this invention are described below with reference to the accompanying drawings.

[0032] In one embodiment, a portable high-frequency electrosurgical unit is shown below. Figures 1A to 1F ,as well as Figures 2A to 2C .like Figure 1A As shown, the portable high-frequency electrosurgical unit provided in this embodiment includes: a main unit 101, a battery base 102, bipolar electric tweezers 106 that are pluggable and electrically connected to the main unit 101, and a battery compartment 103 that is pluggable and electrically connected to the main unit 101; as Figure 1B As shown, the main unit 101 and the battery base 102 are assembled in an L-shape, as... Figure 1C As shown, the battery base 102 cooperates with the main unit 101 to fix the battery compartment 103. After assembly, the main unit 101, battery base 102, and battery compartment 103 form a cubic shape. The main unit 101 adopts a layered layout structure combining a double-layer circuit board and a heat dissipation component. Figure 2A As shown, the heat dissipation component includes: fan 123 and heat sink 124.

[0033] In some possible implementations, such as Figure 1A As shown, the bipolar electric tweezers 106 can be electrically connected to the output port 108 on the host 101 via the connecting wire 105 and the connecting terminal 104.

[0034] The portable high-frequency electrosurgical unit provided in this embodiment features an L-shaped assembly of the main unit and battery base, a pluggable and electrically connected main unit, bipolar electric forceps, and battery compartment, and a battery base that secures the battery compartment to the main unit. The assembled unit forms a cubic shape, and the main unit employs a layered layout structure combining a double-layer circuit board and a heat dissipation component. This solves the problems of large size, heavy weight, reliance on mains power, and inconvenience in portability associated with existing high-frequency bipolar electrosurgical units. This portable high-frequency electrosurgical unit does not rely on mains power, its pluggable design facilitates maintenance and replacement, and the L-shaped assembly and cubic structure achieve miniaturization and weight reduction, meeting the needs of mobile medical scenarios. It is suitable for use in emergency rescue, field surgery, and other similar situations. Operators can easily carry it, and it can operate normally even in environments without a fixed power source, expanding the application scenarios of high-frequency bipolar electrosurgical units.

[0035] In some possible implementations, such as Figure 1CAs shown, the battery base 102 is provided with a blind slot 111 for assembling the battery compartment 103, and the main unit 101 is provided with a plug 114 that is electrically connected to the battery compartment 103. Correspondingly, the battery compartment 103 is provided with a slot 1031 that is adapted to the plug 114, and a rib 1032 that corresponds to the blind slot 111.

[0036] This implementation method uses blind slots on the battery base to assemble the battery compartment, and the main unit is equipped with a plug that connects to the battery compartment. This allows the battery compartment to be accurately positioned during installation via the blind slots, preventing damage to the interface due to misinsertion. At the same time, the corresponding connection between the plug and the battery compartment ensures the stability of the electrical connection. This structural design not only provides a stable assembly base for the battery compartment using the blind slots, but also achieves reliable electrical transmission between the main unit and the battery compartment through the plug. While ensuring convenient installation of the battery compartment, it further optimizes the space utilization of the equipment. Combined with the design of the battery base to accommodate the transformer, it contributes to the miniaturization of the equipment and prevents poor contact caused by vibration during use, thereby improving the power supply reliability of the equipment in mobile scenarios.

[0037] See also some possible implementations. Figure 1C and Figure 1D The battery compartment 103 is provided with a battery compartment switch 113. By moving the battery compartment switch 113 toward the battery base 102, it is locked into the corresponding slot 112 on the battery base 102, so as to fasten the battery compartment 103 to the battery base 102.

[0038] See Figure 1B , Figure 1E and Figure 1F The main unit 101 employs a layered layout structure combining a double-layer circuit board and heat dissipation components. Specifically, the front panel of the main unit 101 has an air inlet 109, and the rear panel of the main unit 101 has an air outlet 110. It should be noted that the terms "front," "rear," "bottom," and "top" are relative to the usage state, for example... Figure 1AThe positions of the main unit 101, battery base 102, and battery compartment 103 are described. Inside the main unit 101 housing, there is a first circuit board 121 fixed to the bottom surface and a second circuit board 122 parallel to the first circuit board 121. A fan 123 and a heat sink 124 with multiple branches are disposed between the first circuit board 121 and the second circuit board 122. The multiple branches of the heat sink 124 are located around the fan 123, and at least a portion of the heat sink 124 includes a double-layer structure. The branches of the heat sink 124 cover the main heat-generating module of the portable high-frequency electrosurgical unit, which is mounted on the first circuit board 121 and below the second circuit board 122 using a surface mount technology. The main control module 125 is mounted on the area below the second circuit board 122 facing the fan 123. The heat-generating module includes a high-frequency generator, a data monitoring module, and a power control module mounted on the first circuit board. Figure 2B As shown, the fan 123 is used to form a heat dissipation air duct with the air inlet 109, the branches of the heat sink 124, the fan 123 and the air outlet 110 when the fan 123 is running.

[0039] This implementation method utilizes an air inlet on the front panel and an air outlet on the rear panel of the main unit. A fan and multi-branch heatsinks are positioned between parallel first and second circuit boards, with the heatsinks featuring a double-layer structure that covers the main heat-generating modules. The main control module is positioned close to the fan, creating a highly efficient cooling airflow. With this design, when the fan is running, airflow flows systematically through the air inlet, heatsink branches, fan, and air outlet. The fan-driven airflow quickly removes heat generated by the main heat-generating modules. The double-layer heatsink structure enhances the heat exchange area and efficiency, ensuring stable temperatures for the surface-mount heat-generating modules and the main control module during operation, preventing performance degradation or malfunctions due to overheating. Furthermore, the rational layout of the circuit boards and heatsink components achieves efficient heat dissipation while fully utilizing the internal space of the main unit, accommodating the need for miniaturization, and improving the reliability of the portable high-frequency electrosurgical unit during continuous operation.

[0040] In some possible implementations, the battery base 102 is equipped with a data detection transformer and an output transformer that are electrically connected to the first circuit board 121.

[0041] This implementation method assembles the relatively large data detection transformer and output transformer inside the battery base and electrically connects them to the first circuit board. This design effectively utilizes the space of the battery base to accommodate large components, avoiding these transformers occupying the limited internal space of the host. This creates conditions for a compact layout of the double-layer circuit board and heat dissipation components inside the host, which helps to achieve the overall miniaturization of the device. At the same time, the direct electrical connection between the transformer and the first circuit board shortens the signal transmission path, reduces energy loss and interference, and ensures the stability of data detection and voltage output. While taking into account the miniaturization of the device, it also improves the overall operating performance.

[0042] In some possible implementations, such as Figure 3 As shown, the portable high-frequency electrosurgical unit also includes: a mode monitoring module 146 and an adaptive feedback module 147 mounted on the first circuit board 121 or the second circuit board 122; and a display control module 145 electrically connected to the display screen 107 and the main control module 125. The mode monitoring module 146 is used to monitor the current working mode corresponding to the operation of the mode switching button 116 of the portable high-frequency electrosurgical unit. The display control module 145, in response to the instructions of the main control module 125, can control the display screen 107 to display information such as the remaining battery power, the current working mode, or the power level (high or low). The current operating modes include: manual mode or adaptive feedback mode. The adaptive feedback module 147 is configured such that when the mode monitoring module 146 detects that the current operating mode is adaptive feedback mode, in response to the control command generated by the main control module 125 based on the parameter values ​​of preset parameters obtained by the data monitoring module 143, it controls the drive module 144 to drive the high-frequency generator 141 to output high-frequency current in terms of intensity, duration, or waveform parameters. The high-frequency current is conducted to the tissue to be coagulated through the bipolar electric tweezers 106, so that the output energy matches the coagulation requirements of the tissue. It should be noted that... Figure 3 The symbol represents the electrical connection relationship, which can be set on different circuit boards.

[0043] In some possible implementations, the outer shells of the main unit 101, battery base 102, and battery compartment 103 are made of nylon resin, while the first circuit board 121 and the second circuit board 122 are made of FR-4 material. The assembled main unit, battery base, and battery compartment form a cube with dimensions (width × height × length) no greater than 43 mm × 60 mm × 108 mm. The portable high-frequency electrosurgical unit weighs no more than 400 grams. The sample dimensions (width × height × length) generated according to this scheme can reach 43 mm × 60 mm × 107.5 mm. The dimensions are approximately one-tenth the volume of related products in the prior art, and the weight is approximately one-thirtieth the weight of related products in the prior art (approximately 12 kg).

[0044] Nylon resin is lightweight and possesses excellent corrosion resistance and mechanical strength, enabling it to adapt to complex environments. FR-4 material is heat-resistant and has good insulation properties, ensuring stable operation of the circuit board. Meanwhile, its compact size and light weight make the device more portable and easier to operate, meeting the needs of mobile healthcare scenarios. While meeting the requirements of structural strength and functional stability, it achieves true miniaturization and lightweighting, providing operators with a more flexible and comfortable experience during operation.

[0045] In some possible implementations, preset parameters include the impedance of the tissue to be coagulated. When the mode monitoring module detects that the current operating mode is adaptive feedback mode, in response to the control command generated by the main control module based on the parameter values ​​of the preset parameters obtained by the data monitoring module, it controls the intensity, duration, or waveform parameters of the high-frequency current output by the high-frequency generator. The high-frequency current is conducted to the tissue to be coagulated through bipolar electric forceps to match the output energy with the coagulation requirements of the tissue and avoid excessive damage. For example, in a practical scenario of coagulation operation using a portable high-frequency electrosurgical unit, this function can be implemented through the following process: When the doctor holds the tip of the bipolar electric forceps on the patient's bleeding tissue (such as liver tissue), the data monitoring module will detect the impedance value of the tissue in real time. If the detected impedance value is 500Ω, the main control module will generate a control command based on a preset impedance-energy matching algorithm. The command may require the high-frequency generator to output a high-frequency current with an intensity of 200mA, a duration of 0.5 seconds, and a sine wave waveform. After the high-frequency generator outputs current according to the command, the current is conducted to the held liver tissue through bipolar electric tweezers, enabling the tissue to coagulate under this energy. As the coagulation process proceeds, the tissue impedance gradually changes. When the data monitoring module detects that the impedance value has become 800Ω, the main control module will recalculate and generate new control commands, adjusting the intensity of the high-frequency current to 150mA, the duration to 0.8 seconds, and the waveform to a square wave, to adapt to the changes in tissue impedance during the coagulation process, ensuring that the output energy always matches the coagulation requirements of the tissue and preventing excessive tissue damage due to excessive energy.

[0046] In some possible implementations, the preset parameters include: the impedance of the tissue to be coagulated, and at least one of the following parameters: output voltage, ambient temperature, contact area between the bipolar tweezers and the tissue, whether the bipolar tweezers are in a raised state, and the duration of contact between the bipolar tweezers and the tissue. When the mode monitoring module detects that the current working mode is adaptive feedback mode, in response to the control command generated by the main control module based on the parameter values ​​of the preset parameters obtained by the data monitoring module, the intensity, duration, or waveform parameters of the high-frequency current output by the high-frequency generator are controlled. The high-frequency current is conducted to the tissue to be coagulated through the bipolar tweezers to match the output energy with the coagulation requirements of the tissue and avoid excessive damage.

[0047] The impedance of tissue undergoing coagulation reflects the coagulation state. For example, the impedance of tissue undergoing normal coagulation is typically between 300-1000 Ω. When bleeding begins, the presence of blood increases the conductivity of the tissue, and the impedance may decrease to around 300 Ω. As the coagulation process progresses and the blood gradually solidifies, the tissue impedance gradually increases. When it reaches around 1000 Ω, it indicates that coagulation is essentially complete. For instance, when treating minor skin abrasions, the initial impedance may be 400 Ω. As the coagulation procedure continues, the impedance gradually rises, and when it reaches 900 Ω, it indicates that the bleeding has been effectively controlled.

[0048] When using portable high-frequency electrosurgical units to treat superficial bleeding, the output voltage typically corresponds to a threshold range, such as a1-a2. When the output voltage is below a1, it may not provide sufficient energy for effective clotting, leading to prolonged clotting time or incomplete clotting. Conversely, when the output voltage is above a2, it may cause excessive damage to surrounding normal tissue, increasing the risk of complications such as tissue necrosis. For example, when treating severe superficial lacerations and bleeding, the initial output voltage can be set to (a1+a2) / 2. If poor clotting is observed, the output voltage can be cautiously reduced by 5%, while monitoring impedance and ambient temperature, but close observation of tissue response is necessary to avoid excessive damage.

[0049] Ambient temperature refers to the ambient temperature surrounding the portable high-frequency electrosurgical unit during operation. Whether this temperature is within a suitable range affects the device's operating status and coagulation effect. In adaptive feedback mode, ambient temperature is one of the parameters monitored by the system. When the temperature exceeds the appropriate range, it may affect the stability of power output, requiring adjustments based on other parameters to ensure normal coagulation operation. For example, if the operating temperature range is between 5-30℃, an ambient temperature below 5℃ may affect the performance of equipment such as the high-frequency generator, leading to unstable output energy and consequently affecting the coagulation effect. Conversely, when the ambient temperature exceeds 30℃, device heat dissipation may be affected, potentially causing overheating or even malfunction during prolonged operation. Therefore, the adaptive feedback mode process may include: normal output within the preset temperature range, considering tissue impedance; and conditional output based on other parameters when outside the preset temperature range.

[0050] The contact area between bipolar electric forceps and tissue affects energy transfer efficiency. An excessively large contact area may lead to energy dispersion and poor coagulation, while an insufficiently large contact area may result in excessively high local energy, causing tissue damage. In adaptive feedback mode, this parameter is used to determine whether the output energy matches the tissue's needs. The system dynamically adjusts the high-frequency current parameter based on the contact area to ensure effective coagulation while avoiding excessive damage.

[0051] Whether the bipolar electric forceps is in an elevated state is used to determine whether the forceps are in effective contact with the tissue: if the electrodes are elevated, it indicates that the forceps have lost contact with the tissue, and the system stops power output; if the electrodes are not elevated and are in contact, other parameters are used to determine whether normal power output is being performed. This state is one of the important bases for controlling the start and stop of power output in adaptive feedback mode.

[0052] The duration of contact between bipolar electric forceps and tissue reflects the time progression of the coagulation procedure. Too short a duration may lead to incomplete coagulation, while too long a duration may cause excessive tissue damage due to energy accumulation. In adaptive feedback mode, this duration can be combined with other parameters (such as impedance, output voltage, etc.) to dynamically adjust parameters such as the duration of the high-frequency current, so that the output energy is precisely matched with the coagulation requirements.

[0053] In adaptive feedback mode, at least some of the parameters above can be used to design the adaptive feedback process.

[0054] For example, in one possible adaptive feedback mode, the system first detects whether the impedance of the tissue to be coagulated is within the working range. If the impedance meets the requirements and the output voltage is qualified, it is determined that the output range is met, and the high-frequency generator output power is controlled. If the impedance exceeds the preset range or the output voltage is unqualified, the power is not output until the impedance returns to the working range and the output voltage is qualified, then the power output is started. When the flag reaches the preset value, the power output stops and the flag is cleared to zero.

[0055] In another possible adaptive feedback mode, the system first checks whether the impedance of the tissue to be coagulated is within the working range. If the impedance is within the normal range and the output voltage meets the preset output range, the power is output normally. If the impedance is abnormal, no output is output, and the system continuously monitors impedance changes. Output resumes when the impedance meets the requirements and the output voltage meets the output range. For example, in adaptive feedback mode, the system first checks whether the impedance of the tissue to be coagulated is within the working range and whether the output voltage is qualified. If the impedance is 600Ω (normal range) and the output voltage is 1.2*a1 (qualified), it is determined to meet the output range, and the high-frequency generator output power is controlled. During continuous monitoring, when the flag corresponding to the tissue coagulation state reaches a preset value (such as a signal indicating coagulation completion), the system immediately stops power output and clears the flag to zero, ending the current coagulation operation. Output duration timing can also be implemented. For example, with an initial value of 0, during continuous power output, the count value increments by 1 every 5 seconds. When a preset value, such as 6, is reached, the output stops.

[0056] For example, if the tissue impedance (e.g., 600Ω) is within the normal operating range, but the output voltage does not meet the qualified standard, the system determines that it does not meet the output range and the power is temporarily not output; after the output voltage recovers to the qualified level, combined with the state that the impedance is still within the working range, the main control module controls the power output, continuously monitoring both parameters during the process until the flag reaches the preset value, at which point the power output stops and the flag is cleared.

[0057] For example, in adaptive feedback mode, if the tissue impedance is initially within the working range (e.g., 700Ω), the system outputs power; then, if the impedance suddenly exceeds the range (e.g., 1100Ω), the system immediately determines that it does not meet the output range and suspends power output; when the impedance falls back to the working range (e.g., 650Ω), the power output is restarted; this process repeats until the impedance stabilizes within the working range and the flag bit meets the standard, and finally, the output stops and the flag bit is cleared.

[0058] For example, preset parameters include: ambient temperature, impedance of the tissue to be coagulated, whether the bipolar forceps are in the raised state, contact area between the bipolar forceps and the tissue, duration of contact between the bipolar forceps and the tissue, and adaptive feedback mode including three modes: mode 1, mode 2 and mode 3.

[0059] Specifically, (1) if the ambient temperature is within the preset range (e.g., 5-30 degrees), then it operates according to mode 1; mode 1 includes: detecting whether the impedance of the tissue to be coagulated is within the working range, if yes, then controlling the output power of the high frequency generator; if no, then controlling the high frequency generator not to output power.

[0060] (2) If the ambient temperature is not within the preset range (above 30 degrees Celsius, below 5 degrees Celsius) and the impedance of the tissue to be coagulated is within the preset range, then the second mode will be used. The second mode includes determining whether the bipolar tweezers are in the raised state. If not, no power will be output. If so, the impedance of the tissue to be coagulated will be further determined. If not, no power will be output. If so, power will be output, and the impedance of the tissue to be coagulated will be determined again. When the impedance of the tissue to be coagulated is determined to be outside the preset range, the power output will be stopped. It is understandable that after outputting power, the duration of contact between the bipolar tweezers and the tissue can be used to determine whether to stop outputting power. Alternatively, the impedance of the tissue to be coagulated can be determined by both the duration of contact between the bipolar tweezers and the tissue. It should be noted that in some possible implementations, whether the bipolar tweezers are in the raised state can be determined based on the contact area between the bipolar tweezers and the tissue. If the contact area is relatively large, it is considered that the tweezers are not raised. When there is no contact, the bipolar tweezers are considered to be in the raised state. Other methods can also be used for specific judgment.

[0061] (3) If the ambient temperature is not within the preset range (above 30 degrees, below 5 degrees) and the impedance of the tissue to be coagulated is not within the preset range, then operate according to mode 3. Determine whether the contact area between the bipolar tweezers and the tissue exceeds the threshold. If not, it may be that the operator accidentally touched the tissue with the bipolar tweezers. If so, further determine whether the impedance of the tissue to be coagulated is within the preset range. If not, do not output power. If so, output power and determine whether to stop output power in combination with the flag bit. The flag bit can be determined according to the impedance of the tissue to be coagulated. For example, if the impedance of the tissue to be coagulated exceeds the threshold corresponding to the impedance, it means that the coagulation operation is completed. At this time, update the flag bit to the completed operation indicator and trigger the stop output power.

[0062] It is understandable that the adaptive feedback mode is not limited to the examples mentioned above. Other process designs can be made as needed. As long as the output energy can match the coagulation requirements of the tissue to be coagulated and excessive damage is avoided, the relevant designs are feasible and are considered to be within the scope of protection of this invention. They will not be listed in detail here.

[0063] Understandably, larger components in portable high-frequency electrosurgical units, such as... Figure 2A The isolation circuit 131, energy storage inductor 132, and other circuits can be mounted on the first circuit board and located in the area between the heat sink branches.

[0064] When using the portable high-frequency electrosurgical unit provided in this embodiment of the invention, the battery compartment 103 can be plugged in and unplugged according to the remaining power. After the battery compartment 103 is inserted into the plug of the main unit 101 and fixed in the blind slot of the battery base, it can be turned on or off using the switch 115. By triggering the buttons 116 (including three buttons), the current working mode can be selected, and when the current working mode is manual operation, the manual mode can be activated. The power level can also be switched. When the current working mode is adaptive feedback mode, automatic response and coagulation operations can be performed according to the process described above.

[0065] In this implementation, the adaptive feedback module, in adaptive feedback mode, can flexibly adjust the high-frequency current parameters output by the high-frequency generator according to the control commands generated by the main control module based on preset parameters, so that the output energy is precisely matched with the needs of the tissue to be coagulated. This design retains the need for manual mode to meet the personalized operating habits of doctors, while realizing intelligent adjustment of energy output through adaptive feedback mode. It avoids unstable coagulation effects caused by differences in doctor experience or operation by non-professionals, reduces the risk of tissue damage caused by excessive coagulation or bleeding caused by insufficient coagulation, reduces the dependence on the professional skills of the operator, improves the safety and accuracy of operation, and can adapt to the usage needs of mobile medical scenarios.

[0066] It should be noted that the division of modules in this embodiment is merely exemplary and not fixed. In actual implementation, one module can be designed to perform the same function through the cooperation of multiple modules, or multiple modules can be integrated into one module. For example, the adaptive feedback module can be integrated into the main control module; both are feasible. Therefore, Figure 3 The structural diagram of the portable high-frequency electrosurgical unit shown is merely an example and should not impose any limitations on the functionality and scope of use of the embodiments of the present invention.

[0067] While several embodiments of the present invention have been described above, these embodiments are merely illustrative and not intended to limit the scope of the invention. These novel embodiments can be implemented in various other forms, and various omissions, substitutions, modifications, and combinations can be made without departing from the spirit of the invention. These embodiments or variations thereof are included in the scope or spirit of the invention, and are encompassed within the scope of the claims and their equivalents.

Claims

1. A portable high-frequency electrosurgical unit, characterized in that, include: The device includes a main unit, a battery base, bipolar electric tweezers that are pluggable and electrically connected to the main unit, and a battery compartment that is pluggable and electrically connected to the main unit. The main unit and the battery base are assembled in an L-shape. The battery base and the main unit cooperate to fix the battery compartment. The main unit, the battery base and the battery compartment are assembled into a cube shape. The main unit adopts a layered layout structure that combines a double-layer circuit board and a heat dissipation component. The heat dissipation component includes a fan and a heat sink.

2. The portable high-frequency electrosurgical unit according to claim 1, characterized in that, The host computer employs a layered layout structure combining a double-layer circuit board and a heat dissipation component, specifically including: The front panel of the main unit is provided with an air inlet, and the rear panel of the main unit is provided with an air outlet. The main unit housing contains a first circuit board fixed to the bottom surface and a second circuit board parallel to the first circuit board. A fan and a heat sink with multiple branches are disposed between the first and second circuit boards. The multiple branches of the heat sink are located around the fan, and at least a portion of the heat sink includes a double-layer structure. The branches of the heat sink cover the main heat-generating modules of the portable high-frequency electrosurgical unit, which are mounted on the first circuit board and below the second circuit board using a surface mount technology. The main control module is installed below the second circuit board in the area facing the fan. The fan is used so that, when the fan is running, the air inlet, the branches of the heat sink, the fan, and the air outlet form a heat dissipation air duct.

3. The portable high-frequency electrosurgical unit according to claim 2, characterized in that, The main heating module includes: a high-frequency generator, a data monitoring module, and a power control module installed on the first circuit board.

4. The portable high-frequency electrosurgical unit according to claim 3, characterized in that, The battery base is equipped with a data detection transformer and an output transformer that are electrically connected to the first circuit board.

5. The portable high-frequency electrosurgical unit according to claim 2, characterized in that, The battery base is provided with a blind slot for assembling the battery compartment, and the main unit is equipped with a plug that is electrically connected to the battery compartment.

6. The portable high-frequency electrosurgical unit according to claim 2, characterized in that, The battery compartment is equipped with a battery compartment switch, which is used to move the battery compartment switch toward the battery base and lock it into the corresponding slot on the battery base, thereby securing the battery compartment to the battery base.

7. The portable high-frequency electrosurgical unit according to claim 3, characterized in that, The portable high-frequency electrosurgical unit further includes: a mode monitoring module and an adaptive feedback module mounted on the first circuit board or the second circuit board; The mode monitoring module is used to monitor the current working mode corresponding to the operation of the mode switching button of the portable high-frequency electrosurgical unit. The current working mode includes: manual mode or adaptive feedback mode. The adaptive feedback module is configured to: when the mode monitoring module detects that the current working mode is adaptive feedback mode, respond to the control command generated by the main control module based on the parameter values ​​of the preset parameters obtained by the data monitoring module, control the intensity, duration or waveform parameters of the high-frequency current output by the high-frequency generator, and conduct the high-frequency current to the tissue to be operated through the bipolar electric tweezers so that the output energy matches the coagulation requirements of the tissue.

8. The portable high-frequency electrosurgical unit according to claim 7, characterized in that, The preset parameters include the impedance of the tissue to be clotted.

9. The portable high-frequency electrosurgical unit according to claim 7, characterized in that, The preset parameters include: the impedance of the tissue to be coagulated, and at least one of the following parameters: output voltage, ambient temperature, contact area between the bipolar electric forceps and the tissue, whether the bipolar electric forceps is in a raised state, and the duration of contact between the bipolar electric forceps and the tissue.

10. The portable high-frequency electrosurgical unit according to any one of claims 2 to 9, characterized in that, The main unit, the battery base, and the battery compartment are made of nylon resin. The first circuit board and the second circuit board are made of FR-4 material. The main unit, the battery base, and the battery compartment, when assembled, form a cube with dimensions (width × height × length) not exceeding 43 mm × 60 mm × 108 mm. The portable high-frequency electrosurgical unit weighs not exceeding 400 grams.

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