Tissue constant-temperature coagulator and tissue constant-temperature coagulation device

Abstract

The utility model discloses a tissue constant-temperature coagulator and a tissue constant-temperature coagulation device, the tissue constant-temperature coagulator comprises: a housing in which a tissue coagulation assembly, a temperature sensing assembly and an impedance detection electrode are installed; the tissue solidification assembly is arranged at the front end of the shell and comprises a first end, a second end and a heating circuit, the first end is used as a tissue contact part, the second end is used as a temperature measuring part, and the heating circuit is arranged in the tissue solidification assembly and used for providing heat energy for the tissue contact part; the temperature sensing assembly is in close contact with the temperature measuring part and is used for measuring the real-time temperature of the tissue contact part in a working state in real time; the impedance detection electrode is arranged to be in contact with the detected tissue in a working state and is used for detecting the electrical impedance value of the detected tissue in real time. According to the utility model, under the condition of not depending on the operation experience of a doctor, the optimal temperature required by the coagulated tissue can be accurately output, and the optimal duration required by the coagulated tissue can be accurately controlled, so that the tissue to be coagulated can be effectively coagulated, and the over-damage or scabbing of the tissue caused by excessive heating can be avoided.

Description

Technical Field

[0001] The utility model belongs to the technical field of medical devices, and in particular relates to a tissue constant temperature coagulator with precise working temperature and accurate coagulation time, and a tissue constant temperature coagulation device comprising the tissue constant temperature coagulator. Background Art

[0002] Lung air leakage is a common and significant challenge in thoracic surgery. This occurs in two ways: First, during various lung surgeries, after a portion of lung tissue is removed, the remaining lung tissue wound, due to ruptured alveoli and lack of visceral pleural coverage, leaks air during breathing, making recovery difficult or even life-threatening. Second, in some cases of refractory pneumothorax caused by complex bullae, the lung tissue surface often contains multiple, diffuse, thin-walled, and easily ruptured bullae. Once ruptured, this can cause persistent, difficult-to-heal, or recurrent pneumothorax, seriously endangering the patient's health.

[0003] The commonly used methods for treating air leakage in lung wounds during lung surgery include suturing and adhesive spray covering. Suturing refers to suturing the leaking local lung tissue. Its disadvantages are that it affects lung expansion and there are problems with pinhole tears and recurrence of air leakage. Adhesive spray covering refers to spraying or applying commercial medical materials on the leaking lung wound. This method is often ineffective and has disadvantages such as high cost and large-area application that affects lung expansion. In general, the treatment methods for air leakage in lung wounds during lung surgery generally have the disadvantages of relying on the surgeon's personal experience, poor sealing of lung leakage, and affecting lung expansion.

[0004] For refractory spontaneous pneumothorax caused by complex bullae, the most commonly used treatment is thoracoscopic surgery, which involves bullae resection and pleurodesis. The former eliminates air leaks, while the latter allows the lung tissue to expand and adhere to the chest wall, preventing recurrence of pneumothorax. This approach is effective for single or clustered bullae. However, for diffuse, multiple bullae scattered across the lung surface, surgeons must resect larger bullae while preserving smaller ones to preserve necessary lung volume and function. Some pneumothorax patients also have widespread, microscopic bullae or subpleural air accumulation that is not visible to the naked eye and cannot be surgically removed. These microscopic bullae or air accumulations can further expand and rupture, causing postoperative air leaks or recurrence of pneumothorax. Pleurodesis involves sanding, peeling, or injecting chemical adhesives into the chest cavity, attempting to create adhesions between the visceral pleura on the lung surface and the parietal pleura on the chest wall, thereby eliminating the pleural cavity and preventing recurrence of pneumothorax. However, due to the irregularity of the pleural cavity, the ineffectiveness of adhesives, and the constant movement of the lungs during breathing, these attempts at adhesion are often ineffective.

[0005] For the two aforementioned lung leaks, another treatment option is low-power electrocoagulation. This involves utilizing the most commonly used electrosurgical platform, adjusting the output power to 10-15W, and using an electrocoagulation hook or spatula to cauterize and coagulate the localized lung tissue affected by the leak. This method is currently used for small, diffuse air leaks and scattered, multiple bullae. However, the operating current is significantly affected by variations in the contact surface and tissue resistance, making the duration, extent, range, and depth of electrocoagulation highly dependent on surgeon experience. Experienced surgeons can achieve excellent results, but inexperienced surgeons can easily produce carbonized scabs or inadequate coagulation, making effective results difficult to guarantee.

[0006] Therefore, there is an urgent need to invent a newer and better lung tissue wound treatment device to improve the current lung leakage coagulation method, so as to provide a more intelligent, precise, and quality-controlled lung leakage solution, which will greatly improve the level and effect of thoracic surgery and benefit tens of millions of patients. Utility Model Content

[0007] The present invention aims to solve at least one of the technical problems existing in the prior art. To this end, the present invention provides a tissue constant temperature coagulator for treating and preventing lung leakage caused by air leakage from lung surgical wounds or complex bullae, bile leakage from liver surgical wounds, lymph leakage from lymph node dissection wounds, and bleeding / exudate caused by other wounds. The device is designed to accurately output the optimal temperature required for tissue coagulation without relying on the surgeon's surgical experience, while precisely controlling the optimal coagulation time required, thereby ensuring that the tissue to be coagulated can be effectively coagulated without overheating, which may cause excessive tissue damage or scab formation.

[0008] In order to achieve the above purpose, the present invention adopts the following technical solutions:

[0009] In a first aspect, the present invention provides a tissue constant temperature coagulation device, comprising:

[0010] a housing in which a tissue coagulation component, a temperature sensing component, and an impedance detection electrode are installed;

[0011] The tissue coagulation assembly is disposed at the front end of the housing and includes a first end, a second end, and a heating circuit. The first end is configured to be shaped to contact the tissue to be coagulated and serves as a tissue contact portion. The second end is configured to be shaped to be in close contact with the temperature sensing assembly and serves as a temperature measuring portion. The heating circuit is disposed inside the tissue coagulation assembly and is used to provide heat energy to the tissue contact portion.

[0012] The temperature sensing component is arranged to be in close contact with the temperature measuring portion of the tissue coagulation component, and is used to measure the real-time temperature of the tissue contact portion in a working state in real time;

[0013] The impedance detection electrode is configured to contact the tissue to be coagulated in a working state, and is used for detecting the electrical impedance value of the tissue to be coagulated in real time.

[0014] Preferably, the surface of the tissue contact portion that contacts the tissue to be coagulated is constructed as a working surface, the working surface is a flat surface, and the cross-section of the working surface is any one shape selected from the group consisting of prism, triangle, square, rectangle, and circle.

[0015] Preferably, a negative pressure suction component is further provided in the tissue coagulation component, and the negative pressure suction component includes at least one suction pipe and at least one suction through-hole, wherein the suction through-hole is provided in the tissue contact portion, one section of the suction pipe is connected to the suction through-hole, and the other end can be externally connected to a negative pressure suction device for sucking and discharging the exudate and / or mist generated by the tissue to be coagulated during the coagulation process.

[0016] Preferably, the tissue contact portion is made of an insulating heating sheet, preferably a ceramic heating sheet.

[0017] Preferably, the impedance detection electrode includes an excitation electrode and a measurement electrode, and the excitation electrode and the measurement electrode are arranged on the surface of the tissue contact portion that contacts the tissue to be coagulated and are separated by a preset distance.

[0018] Preferably, the space enclosed by the second end of the tissue coagulation component, the temperature sensing component and the inner wall of the shell is filled with a heat insulation layer.

[0019] Preferably, a switch is provided on the housing for opening and closing the heating circuit of the tissue coagulation component.

[0020] In a second aspect, the present invention provides a tissue constant temperature coagulation device, comprising an industrial computer, a power supply device, and the tissue constant temperature coagulator described in the first aspect of the present invention, wherein the power supply device is used to supply power to the tissue constant temperature coagulator and the industrial computer, and the industrial computer includes a temperature control module and a bioimpedance meter; wherein the temperature control module is electrically connected to the temperature sensing component and the heating circuit respectively, and the temperature control module includes a micro PID controller and a solid-state relay, the micro PID controller receives the real-time measured temperature transmitted by the temperature sensing component, compares the real-time measured temperature with the preset temperature to calculate the temperature deviation, and generates a first control signal according to the temperature deviation, and then outputs the first control signal to the solid-state relay, the solid-state relay receives the first control signal and opens and closes and adjusts the power of the heating circuit, thereby maintaining the temperature of the tissue coagulation part at the preset temperature; the bioimpedance meter is electrically connected to the impedance detection electrode, and is used to calculate and output the real-time tissue electrical impedance value of the tissue to be coagulated.

[0021] Preferably, a cooling component is further included, which is arranged in the shell and contacts the second end of the tissue coagulation component. The cooling component is electrically connected to the micro PID controller, and is used to quickly reduce the real-time temperature of the tissue coagulation component to a preset temperature or normal temperature.

[0022] Preferably, the industrial computer further comprises an impedance warning module, which comprises a microcontroller and an alarm, wherein the microcontroller is configured to receive a real-time tissue electrical impedance value output from the bioimpedance meter, and compare the real-time tissue electrical impedance value with a preset electrical impedance value; when the real-time tissue electrical impedance value reaches the preset impedance value, the microcontroller sends a second control signal to the alarm, and the alarm sends an alarm signal when receiving the second control signal.

[0023] The utility model has the following advantages due to the adoption of the above technical solution:

[0024] 1. Improve electrocoagulation to thermal coagulation

[0025] Current electrocoagulation utilizes the heat energy generated locally by an electric current passing through the body to coagulate tissue. This method controls output power but not local temperature, making it prone to overheating and scabbing. In fact, for wound tissue, especially wounds with air leaks, effective coagulation depends on precise coagulation temperature. The present invention improves electrocoagulation to thermal coagulation, effectively and precisely controlling the coagulation temperature.

[0026] 2. The solidifier operating temperature is always at the precise set value

[0027] This is the first key innovation that distinguishes this utility model from traditional thermocoagulation. Upon turning on the switch, the temperature of the tissue-contacting surface of the tissue coagulation component instantly rises to the set temperature. Furthermore, throughout the entire operation, thanks to sensitive real-time temperature monitoring and precise power replenishment, the temperature of the tissue-contacting surface remains constant at the set value, ensuring both coagulation efficiency and quality.

[0028] 3. Improve the determination of coagulation time from relying on the operator's experience to relying on the precise monitoring of the equipment

[0029] Coagulation duration is another key factor in ensuring coagulation quality. The impedance detection electrode in this utility model accurately detects real-time changes in the voltage of the tissue being tested, calculating the impedance value to determine the degree of coagulation and its effectiveness. When optimal coagulation is achieved, an alarm in the tissue constant-temperature coagulation device sounds a warning, prompting the operator to cease operation, further ensuring coagulation quality. This is the second key innovation of this utility model over traditional thermal coagulation.

[0030] 4. Standardized quality control

[0031] The tissue constant temperature coagulator of the present invention can provide a standard temperature and a precise coagulation time, so that the outermost layer of tissue of the lung wound can be coagulated at the most ideal "temperature", forming a thin, tough, elastic, and well-quality controlled collagen coagulation layer, thereby completely solving the air leakage problem, improving the patient's cure rate, and alleviating the patient's pain.

[0032] 5. Reduce the difficulty of surgery

[0033] Since the tissue constant temperature coagulator provides standard coagulation temperature and coagulation time, the surgeon does not need to undergo repeated training and can use it directly. The operation is simple, which greatly reduces the difficulty of the operation.

[0034] 6. Improve surgical efficiency

[0035] Because the tissue constant temperature coagulation device can provide stable quality control in one pass, it avoids the time delays that surgeons previously had to repeat due to concerns about insufficient or excessive coagulation. This greatly reduces the surgeon's workload, shortens the operation time, and improves surgical efficiency.

[0036] 7. Reduce medical costs

[0037] This tissue thermostatic coagulator provides a novel surgical method for wound tissue treatment. Compared to traditional methods, particularly cutting and stapling excision and bioadhesive adhesion, it can effectively reduce the use of disposable consumables and lower medical costs. Furthermore, due to its stable treatment effect, it avoids the situation where poor treatment results, postoperative lung leakage, bile leakage, bleeding, or exudation, leading to prolonged postoperative hospital stays, repeated hospitalizations, and multiple surgeries, further reducing medical costs.

[0038] In summary, this utility model provides doctors with a new treatment method for wound tissue, improving the treatment of lung tissue wound air leakage, intractable pneumothorax, liver wound bile leakage, lymph node dissection wound exudate, and other wound exudate / bleeding, thereby alleviating patients' pain. Therefore, this utility model has broad market demand and good application prospects. BRIEF DESCRIPTION OF THE DRAWINGS

[0039] By reading the detailed description of the preferred embodiment below, various other advantages and benefits will become clear to those skilled in the art. The accompanying drawings are only used to illustrate the preferred embodiment and are not to be considered as limitations of the present invention. Throughout the accompanying drawings, the same reference numerals are used to represent the same components.

[0040] Figure 1 This is a structural diagram of a tissue constant temperature coagulator provided by a preferred embodiment of the present invention;

[0041] Figure 2 This is an end view of the tissue contact portion provided by a preferred embodiment of the present invention;

[0042] Figure 3 This is a working principle diagram of a four-electrode method for measuring electrical impedance provided by a preferred embodiment of the present invention;

[0043] Figure 4 This is a structural diagram of a tissue constant temperature coagulation device provided by a preferred embodiment of the present invention;

[0044] Figure 5 This is a working principle diagram of a tissue constant temperature coagulation device provided by a preferred embodiment of the present utility model.

[0045] The reference numerals in the figures are as follows:

[0046] 100. Tissue constant temperature coagulator; 1. Housing; 2. Tissue coagulation assembly; 3. Temperature sensing assembly; 4. Impedance detection electrode; 4-1. Excitation electrode; 4-2. Measuring electrode; 5. Negative pressure suction assembly; 5-1. Suction through-hole; 5-2. Suction pipe; 6. Thermal barrier; 7. Switch;

[0047] 200. Host; 8. Power supply equipment; 9. Temperature control module; 9-1. Micro PID controller; 9-2. Solid-state relay; 10. Bioimpedance meter; 11. Impedance warning module; 11-1. Microcontroller; 11-2. Alarm; 12. Wires. DETAILED DESCRIPTION

[0048] To further clarify the objectives, technical solutions, and advantages of the present invention, the following describes specific embodiments of the present invention in conjunction with the accompanying drawings. Although the accompanying drawings illustrate exemplary embodiments of the present invention, it should be understood that the present invention can be implemented in various forms and should not be limited by the embodiments described herein. Rather, these embodiments are provided to enable a more thorough understanding of the present invention and to fully convey the scope of the present invention to those skilled in the art.

[0049] In the description of the present invention, it should be understood that the terms "center", "longitudinal", "lateral", "length", "width", "thickness", "up", "down", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inside", "outside", "clockwise", "counterclockwise", "axial", "radial", "circumferential" and the like to indicate orientations or positional relationships based on the orientations or positional relationships shown in the accompanying drawings, and are only for the convenience of describing the present invention and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and therefore should not be understood as a limitation to the present invention.

[0050] Furthermore, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of the technical features being referred to. Thus, a feature specified as "first" or "second" may explicitly or implicitly include one or more of such features. In the description of this utility model, "plurality" means more than two, unless otherwise specifically defined.

[0051] In this utility model, unless otherwise specified or limited, the terms "installed," "connected," "connect," "fixed," etc. should be understood in a broad sense. For example, they can refer to fixed connection, detachable connection, or integration; mechanical connection, electrical connection; direct connection, indirect connection through an intermediate medium, internal communication between two components, or interaction between two components. Those skilled in the art will understand the specific meanings of the above terms in this utility model based on specific circumstances.

[0052] In the present invention, unless otherwise expressly specified or limited, when a first feature is "above" or "below" a second feature, it may mean that the first and second features are in direct contact, or the first and second features are in indirect contact through an intermediary. Furthermore, when a first feature is "above," "above," or "above" a second feature, it may mean that the first feature is directly above or diagonally above the second feature, or simply means that the first feature is at a higher level than the second feature. When a first feature is "below," "below," or "below" a second feature, it may mean that the first feature is directly below or diagonally below the second feature, or simply means that the first feature is at a lower level than the second feature.

[0053] In the description of this specification, the reference terms "one embodiment", "some embodiments", "example", "specific example", or "some examples" mean that the specific features, structures, materials or characteristics described in conjunction with the embodiment or example are included in at least one embodiment or example of the present invention. In this specification, the schematic expressions of the above terms do not necessarily refer to the same embodiment or example. Moreover, the specific features, structures, materials or characteristics described can be combined in any one or more embodiments or examples in a suitable manner. In addition, those skilled in the art can combine and combine different embodiments or examples described in this specification and features of different embodiments or examples without contradiction.

[0054] The utility model can accurately output the optimal temperature required for coagulation of tissue without relying on the doctor's surgical experience, and accurately control the optimal time required for coagulation of tissue, thereby ensuring that the wound tissue can be effectively coagulated without overheating to cause excessive tissue damage or scabbing. It provides doctors with a new treatment method for treating wound tissue, which can improve the treatment effect of lung wound air leakage, refractory pneumothorax, liver wound bile leakage, lymph node clearance wound exudation and other wound exudation / exudation, alleviate patients' pain, and has broad market demand and good application prospects.

[0055] Hereinafter, the tissue constant temperature coagulation device and the tissue constant temperature coagulation apparatus provided by the embodiments of the present invention will be described in detail with reference to the accompanying drawings.

[0056] Example 1

[0057] See also Figure 1 The tissue constant temperature coagulator 100 provided in this embodiment includes a housing 1, a tissue coagulation assembly 2, a temperature sensing assembly 3, and an impedance detection electrode 4. The housing 1 is a hollow, handle-like structure, and the tissue coagulation assembly 2, the temperature sensing assembly 3, and the impedance detection electrode 4 are all mounted within the housing 1. The tissue coagulation assembly 2 is disposed at the front end of the housing 1 and includes a first end, a second end, and a heating circuit (not shown). The first end is configured to contact the tissue to be coagulated and serves as a tissue contact portion, while the second end is configured to closely contact the temperature sensing assembly 3 and serves as a temperature measurement portion. The heating circuit is disposed within the tissue coagulation assembly 2 to provide heat to the tissue contact portion. The temperature sensing assembly 3 is configured to closely contact the temperature measurement portion of the tissue coagulation assembly 2 and is used to measure the real-time temperature of the tissue contact portion in the operating state. The impedance detection electrode 4 is configured to contact the tissue to be coagulated in the operating state and is used to detect the electrical impedance value of the tissue to be coagulated in real time.

[0058] In the present invention, the heating circuit may include a heating element and a heating controller. In a specific embodiment, the heating element may be any one of a resistance wire, an electric furnace rod, a thermocouple, and the like. The heating controller is used to control the heating circuit and may be a temperature controller or a power controller. The temperature controller controls the operating state of the heating circuit by detecting the heat energy generated by the heating element according to a set temperature value, while the power controller controls the heating power of the heating element by adjusting the current or voltage.

[0059] In the present invention, the temperature sensing assembly 3 may include a temperature sensor. A temperature sensor is a sensor capable of sensing temperature changes and converting such changes into a usable output signal. In a specific embodiment, the temperature sensor may be a contact temperature sensor, such as a thermocouple, a thermistor, a resistance temperature detector, a semiconductor temperature sensor, or the like. In a preferred embodiment, the output signal of the temperature sensor may be a digital electrical signal or an analog electrical signal. When outputting an analog electrical signal, the temperature sensor may further include an analog-to-digital converter (ADC).

[0060] In the present invention, the tissue to be coagulated that the tissue coagulation component 2 contacts can be mammalian tissue, preferably lung wound tissue, liver wound tissue, lymph node dissection wound tissue, or other wound tissue. In a preferred embodiment, the lung wound tissue can be air-leaking lung wound tissue formed after bullae or rupture of bullae, or air-leaking lung wound tissue formed by lung surgery; the liver wound tissue can be bile-leaking liver wound tissue formed by liver surgery; the lymph node dissection wound tissue can be mediastinal wound tissue with suspected lymph leakage formed after lung cancer resection plus mediastinal lymph node dissection; and other wound tissues can be bleeding / exudate wound tissue formed by other surgeries.

[0061] In the present invention, mammals can be selected from bovines, equines, felines, canines, lagomorphs, porcines, camelids, rodents, and primates, including but not limited to cattle, horses, goats, sheep, cats, rabbits, pigs, camels, alpacas, rats, mice, guinea pigs, non-human primates (such as apes, monkeys, baboons, orangutans), and humans, preferably cattle, horses, dogs, goats, sheep, pigs, camels, rats, mice, monkeys, and humans. Preferably, the mammals are experimental animals, including but not limited to mice, rats, rabbits, guinea pigs, hamsters, monkeys, dogs, cats, pigs, sheep, horses, and the like.

[0062] In the present invention, the side of the tissue contact portion that contacts the tissue to be coagulated is constructed as a working surface, and the working surface is a flat surface. In a preferred embodiment, the cross-section of the working surface is any one of a prism, a triangle, a square, a rectangle, and a circle.

[0063] In this utility model, please refer to Figure 2 The impedance detection electrode 4 includes an excitation electrode 4-1 and a measuring electrode 4-2. The excitation electrode 4-1 and the measuring electrode 4-2 are arranged on the surface of the tissue contact portion that contacts the tissue to be coagulated and are separated by a preset distance. In a specific embodiment, a two-electrode method or a four-electrode method, also known as a 2-terminal or 4-terminal detection configuration, can be used for biological tissue impedance measurement. In the two-electrode method, one is the excitation electrode 4-1 for applying a small alternating current of a known frequency to the tissue to be coagulated, and the other is the measuring electrode 4-2 for detecting the voltage change after the current passes through the tissue to be coagulated. Please refer to Figure 3For the four-electrode method, two excitation electrodes 4-1 are used to apply a small alternating current of a known frequency to the tissue to be coagulated, and the other two measuring electrodes 4-2 are used to detect the voltage change after the current passes through the tissue to be coagulated. The electrical impedance is equal to the voltage between the two measuring electrodes 4-2 divided by the current between the two excitation electrodes 4-1, that is, Z=V / I, where Z is the electrical impedance, V is the voltage between the two measuring electrodes, and I is the current between the two excitation electrodes 4-1. The four-electrode method is preferably used to detect the electrical impedance of the tissue to be coagulated. Compared with the two-electrode method, the four-electrode method can reduce the impact of different contact between the electrodes and the tissue to be coagulated on measurement accuracy, thereby reducing measurement errors. In addition, the circuit structure of the four-electrode method is relatively simple and can accurately measure the modulus and phase angle of the bioelectrical impedance signal.

[0064] Furthermore, the specific placement of the impedance detection electrode 4 can be determined based on factors such as the shape of the wound surface, the nature and number of lesions (e.g., the size and number of lung leaks or bullae). Taking the two-electrode method as an example, in a preferred embodiment, the excitation electrode 4-1 and the measurement electrode 4-2 can be arranged on either side of the tissue contact portion along its major or minor axis. In another preferred embodiment, one electrode (either the excitation electrode 4-1 or the measurement electrode 4-2) is arranged at the center of the tissue contact portion, while the other electrode is arranged at the periphery of the tissue contact portion. The excitation electrode 4-1 and the measurement electrode 4-2 can be arranged on the surface of the tissue contact portion by inlaying or other means and are configured to contact the tissue to be coagulated in the operating state. The predetermined distance between the excitation electrode 4-1 and the measurement electrode 4-2 can be determined based on the size of the tissue to be coagulated and the associated surgical area. For example, for a lung wound, the predetermined distance can be at least 0.5 cm.

[0065] It will be understood by those skilled in the art that, in addition to the above-mentioned two-electrode method and four-electrode method, other methods may also be used to detect the coagulation effect of the tissue to be coagulated, such as the non-contact ultrasonic method. In this case, a piezoelectric ultrasonic probe may be integrated into the tissue constant temperature coagulator 100, and ultrasonic waves are continuously emitted to the tissue to be coagulated through the piezoelectric ultrasonic probe, and the changes in the reflectivity and absorptivity of the ultrasonic waves are monitored in real time, thereby accurately judging the coagulation effect of the tissue to be coagulated.

[0066] In this utility model, please refer to Figure 1 、 Figure 2A negative pressure suction assembly 5 is also provided within the tissue coagulation assembly 2. The negative pressure suction assembly 5 includes at least one suction through-hole 5-1 and at least one suction conduit 5-2. The suction through-hole 5-1 is provided in the tissue contact portion. One end of the suction conduit 5-2 is connected to the suction through-hole 5-1, and the other end can be connected to an external negative pressure suction device to promptly remove exudate and / or mist generated by the tissue to be coagulated during the coagulation process. In one embodiment, the suction through-hole 5-1 and the suction conduit 5-2 can be configured as a suction tube connected to an external negative pressure suction device, thereby allowing the negative pressure of the negative pressure suction device to remove exudate and / or mist generated by the tissue to be coagulated during the coagulation process.

[0067] The value of the negative pressure drainage component 5 is reflected in that, under normal circumstances, the lung tissue of the human or animal body is an air-containing honeycomb-like structure, but in lung surgery and pneumothorax surgery, due to the help of single-lung ventilation, the lung to be treated is in a collapsed state with no ventilation and little air. As the surface lung tissue is coagulated, some exudate may be produced on the lung wound surface. If it is not sucked away in the first time, the high temperature of the contact tissue contact part will coagulate the protein in the exudate to form protein clots, which will significantly reduce the coagulation quality and affect the accuracy of the electrical impedance value measurement of the coagulated tissue, resulting in an erroneous impedance alarm. In addition, the mist formed by local high-temperature vaporization will also affect the operator's observation and the respiratory health of the operator himself, so it is very necessary to suck it away in the first time.

[0068] In the present invention, the tissue contact portion is made of an insulating heating plate. In a preferred technical solution, the first end and the second end of the tissue coagulation component 2, that is, the tissue contact portion and the temperature measurement portion, have an integrated structure or a split structure connected in a detachable manner. In a specific embodiment, the first end and the second end of the tissue coagulation component 2 can both be insulating heating plates, or only the first end is an insulating heating plate, and the second end can be made of a thermally conductive material with good heat transfer performance. In the first case (that is, the first end and the second end are both insulating heating plates), the second end is an extension of the first end, and its shape can be set to match the shape of the temperature measurement component 3 or the temperature sensor in the temperature measurement component 3, so as to be suitable for the temperature measurement component 3 or the temperature sensor to sense temperature and temperature changes. The insulating heating plate can be selected from a silicone heating plate, a mica heating plate, a metal ceramic heater or a ceramic heating plate, preferably a ceramic heating plate. The thermal conductive material can be selected from metals (for example, copper, iron and aluminum), graphite materials, etc.

[0069] In this utility model, please refer to Figure 1The space enclosed by the second end of the tissue coagulation assembly 2, the temperature sensing assembly 3, and the inner wall of the housing 1 is filled with a thermal insulation layer 6. This thermal insulation layer 6 can be used to insulate, prevent secondary damage, and reduce heat loss. In a specific embodiment, the thermal insulation layer 6 can be made of a common thermal insulation material in the art, including but not limited to porous materials such as foam materials and fiber materials; and also includes aerogel, foamed polyurethane, expanded perlite, rock wool, glass wool, composite magnesium aluminum silicate insulation materials, aerogel felt, and the like.

[0070] In this utility model, please continue to refer to Figure 1 A switch 7 is also provided on the housing 1 for opening and closing the heating circuit of the tissue coagulation component 2 .

[0071] Example 2

[0072] Based on the tissue constant temperature coagulation device provided in the above embodiment 1, the present invention also provides a tissue constant temperature coagulation device. Figure 4 and Figure 5 The tissue constant temperature coagulation device includes an industrial computer, a power supply device 8 and the tissue constant temperature coagulator in Example 1. The power supply device 8 is used to supply power to the tissue constant temperature coagulator 100 and the industrial computer. The industrial computer includes a temperature control module 9 and a bioimpedance meter 10; wherein the temperature control module 9 is electrically connected to the temperature sensing component 3 and the heating circuit respectively, and the temperature control module 9 includes a micro PID controller 9-1 and a solid-state relay 9-2. The micro PID controller 9-1 receives the real-time measured temperature transmitted by the temperature sensing component 3, compares the real-time measured temperature with the preset temperature to calculate the temperature deviation, and generates a first control signal according to the temperature deviation, and then outputs the first control signal to the solid-state relay 9-2. The solid-state relay 9-2 receives the first control signal and adjusts the power of the heating circuit, so that the temperature of the tissue coagulation part is always accurately maintained at the preset temperature, thereby accurately outputting the optimal temperature required for coagulating the tissue; the bioimpedance meter 10 is electrically connected to the impedance detection electrode 4, and is used to calculate and output the real-time tissue electrical impedance value of the tissue to be coagulated.

[0073] In the present invention, the preset temperature of the tissue coagulation unit can be determined empirically or experimentally based on the tissue to be coagulated, in combination with factors such as the tissue source, anatomical site, and tissue type. In one specific embodiment, when the tissue to be coagulated is lung tissue, the preset temperature of the tissue coagulation unit is any temperature between 60°C and 140°C, for example, 60°C, 90°C, 100°C, 110°C, 120°C, 130°C, 140°C, etc.

[0074] In this utility model, please refer to Figure 1, further comprising a cooling assembly 12, which is disposed within the housing 1 and in contact with the second end of the tissue coagulation assembly 2. The cooling assembly 12 is electrically connected to the micro-PID controller 9-1. When the temperature sensing assembly 3 detects that the real-time temperature of the tissue coagulation assembly 2 exceeds a preset temperature, the micro-PID controller 9-1 activates the cooling assembly 12 to rapidly reduce the real-time temperature of the tissue coagulation assembly 2 to the preset temperature, thereby improving the temperature controllability of the tissue coagulation assembly 2. Simultaneously, the switch 7 can also turn the cooling assembly 12 on and off. When the coagulation operation is completed, pressing the switch 7 activates the cooling assembly 12, rapidly cooling the tissue coagulation assembly 2 to room temperature, thereby preventing accidental burns when removing the tissue constant-temperature coagulator 100.

[0075] In the present invention, the bioimpedance meter 10 can be a commercially available instrument capable of measuring the impedance of biological tissue, preferably a miniature bioelectrical impedance meter. Preferably, the bioimpedance meter 10 applies a low-frequency AC excitation signal to the excitation electrode 4-1 in the impedance detection electrode 4 to prevent polarization of the excitation electrode 4-1 and eliminate damage to human tissue.

[0076] In the present invention, the industrial computer also includes an impedance warning module 11, which includes a microcontroller 11-1 and an alarm 11-2, wherein the microcontroller 11-1 is configured to receive the real-time tissue electrical impedance value output from the bioimpedance meter 10, and compare the real-time tissue electrical impedance value with the preset electrical impedance value. When the real-time tissue electrical impedance value reaches the preset electrical impedance value, the microcontroller 11-1 sends a second control signal to the alarm 11-2. When the alarm 11-2 receives the second control signal, it sends an alarm signal to prompt the operator that coagulation is complete and the operation is ended, thereby accurately controlling the optimal time required for coagulation of the tissue.

[0077] In one embodiment, the alarm 11-2 may be a visual alarm, including but not limited to a device that alerts the user through a visual signal, such as a light bulb lighting device that alerts the user through a flashing light, or a display screen that displays an alarm message. In another embodiment, the alarm 11-2 may also be an auditory alarm, such as a buzzer or siren that alerts the user through sound. Accordingly, in some embodiments, the alarm signal may be a visual alarm signal or an auditory alarm signal.

[0078] In the present invention, the preset electrical impedance value can be determined through experience or experiments based on the tissue to be coagulated in combination with factors such as tissue source, anatomical site, and tissue type.

[0079] In a preferred embodiment, the tissue constant temperature coagulator 100 further includes a plurality of wires 13, one end of which is respectively connected to the heating circuit, temperature sensing component 3 and impedance detection electrode 4 of the tissue coagulation component 2, and the other end is respectively connected to the industrial computer and power supply equipment 8.

[0080] In a preferred embodiment, each module of the industrial computer can be connected to the corresponding components of the tissue constant temperature coagulation device by wired connection via a data transmission cable or by wireless communication.

[0081] In a preferred embodiment, the power supply device 8 may be connected to a built-in or external DC power supply, or an external AC power supply. When connected to an external AC power supply, it may include a voltage converter for converting AC power into DC power.

[0082] In a preferred embodiment, the tissue constant temperature coagulator 100 can be designed as a pre-sterilized disposable product with independent packaging, and the industrial computer and the power supply device 8 can be integrated into a host 200 .

[0083] Example 3

[0084] The following describes the specific operating steps of the tissue constant temperature coagulation device for treating lung tissue wounds provided by the present invention by taking an example of treating air leakage in lung tissue wounds during lung resection surgery:

[0085] Step 1: Tear open the packaging bag containing the pre-sterilized tissue constant temperature coagulator 100, put it on the operating table, and connect it to the host 200 through the wire 12.

[0086] Step 2: Apply a layer of anti-adhesion heat-conducting oil evenly on the patient's lung tissue wound, insert the head end of the tissue constant temperature coagulator 100 into the chest cavity through a thoracoscope or a thoracotomy incision, and apply the tissue contact part of the tissue coagulation component 2 to the leaking lung tissue wound. Press the switch 7 to start the heating circuit, and the working surface of the tissue contact part will quickly heat up to the preset temperature and stably maintain this preset temperature. At this time, the tissue constant temperature coagulator 100 can be slowly moved so that the working surface of the tissue contact part moves back and forth on the lung tissue wound that needs to be coagulated, so that the alveoli of the lung tissue wound will be quickly coagulated with a uniform and ideal "temperature", so that it will form a thin, tough and elastic coagulation layer, thereby achieving the purpose of treating lung wound leakage without affecting the expansion of the lung and the patient's lung function.

[0087] Step 3: At the same time, the impedance detection electrode 4 detects the electrical impedance value of the coagulated lung tissue in real time and sends it to the bioimpedance meter 10. The bioimpedance meter 10 calculates the real-time tissue electrical impedance value of the measured tissue based on the detected impedance value. When the alveoli in the lung tissue wound coagulate and the real-time tissue electrical impedance value increases significantly and reaches the preset electrical impedance value, the microcontroller 11-1 activates the alarm 11-2 and continuously emits a warning sound, prompting the operator that coagulation is complete and the operation can be ended.

[0088] Step 4: Turn off the switch 7, take out the tissue constant temperature coagulator 100, disconnect it from the host 200, and end the treatment.

[0089] The above examples illustrate the specific operating steps of the tissue constant temperature coagulation device provided by the present invention. Through this method, the surgeon can effectively treat lung wound leaks during lung resection surgery, while avoiding reliance on the surgeon's surgical experience, improving the stability of the treatment effect, and avoiding affecting lung tissue expansion, reducing the possibility of delayed postoperative air leakage, and alleviating the patient's pain. The above examples only illustrate the operating steps of the present invention for treating lung wound leaks during lung resection surgery. The present invention can also be used to treat partial leaks and diffuse bullae in refractory pneumothorax caused by complex bullae, bile leakage caused by liver surgery wounds, suspected lymph leakage caused by lymph node dissection wounds, and coagulation treatment of bleeding / exudate caused by other surgical wounds.

[0090] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present application, rather than to limit them. Although the present application has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the aforementioned embodiments, or make equivalent replacements for some or all of the technical features therein. These modifications or replacements do not deviate the essence of the corresponding technical solutions from the scope of the technical solutions of the embodiments of the present application, and they should all be included in the scope of the claims and specification of the present application. In particular, as long as there is no structural conflict, the various technical features mentioned in the various embodiments can be combined in any way. The present application is not limited to the specific embodiments disclosed herein, but includes all technical solutions that fall within the scope of the claims.

Claims

1. A tissue constant temperature coagulator, characterized in that: include: a housing in which a tissue coagulation component, a temperature sensing component, and an impedance detection electrode are installed; The tissue coagulation assembly is disposed at the front end of the housing and includes a first end, a second end, and a heating circuit. The first end is configured to be shaped to contact the tissue to be coagulated and serves as a tissue contact portion. The second end is configured to be shaped to be in close contact with the temperature sensing assembly and serves as a temperature measuring portion. The heating circuit is disposed inside the tissue coagulation assembly and is used to provide heat energy to the tissue contact portion. The temperature sensing component is arranged to be in close contact with the temperature measuring portion of the tissue coagulation component, and is used to measure the real-time temperature of the tissue contact portion in a working state in real time; The impedance detection electrode is configured to contact the tissue to be coagulated in a working state, and is used for detecting the electrical impedance value of the tissue to be coagulated in real time.

2. The tissue constant temperature coagulator according to claim 1, characterized in that: The surface of the tissue contact portion that contacts the tissue to be coagulated is constructed as a working surface. The working surface is a flat surface, and the cross-section of the working surface is any one shape selected from the group consisting of prism, triangle, square, rectangle, and circle.

3. The tissue constant temperature coagulator according to claim 1, characterized in that: A negative pressure suction component is also provided in the tissue coagulation component, and the negative pressure suction component includes a suction pipe and at least one suction through-hole, wherein the suction through-hole is provided in the tissue contact part, one end of the suction pipe is connected to the suction through-hole, and the other end can be externally connected to a negative pressure suction device for sucking and discharging the exudate and / or mist generated by the tissue to be coagulated during the coagulation process.

4. The tissue constant temperature coagulator according to any one of claims 1 to 3, characterized in that: The tissue contact portion is made of a ceramic heating sheet.

5. The tissue constant temperature coagulator according to claim 1, characterized in that: The impedance detection electrode includes an excitation electrode and a measurement electrode. The excitation electrode and the measurement electrode are arranged on a surface of the tissue contact portion that contacts the tissue to be coagulated and are separated by a preset distance.

6. The tissue constant temperature coagulator according to claim 1, characterized in that: The space enclosed by the second end of the tissue coagulation component, the temperature sensing component and the inner wall of the shell is filled with a heat insulation layer.

7. The tissue constant temperature coagulator according to any one of claims 1 to 3, characterized in that: A switch is also provided on the housing for opening and closing the heating circuit of the tissue coagulation component.

8. A tissue constant temperature coagulation device, characterized in that: It includes an industrial computer, a power supply device and the tissue constant temperature coagulator according to any one of claims 1 to 7, the power supply device is used to supply power to the tissue constant temperature coagulator and the industrial computer, and the industrial computer includes a temperature control module and a bioimpedance meter; wherein the temperature control module is electrically connected to the temperature sensing component and the heating circuit respectively, the temperature control module includes a micro PID controller and a solid-state relay, the input end of the micro PID controller is electrically connected to the temperature sensing component, the output end of the micro PID controller is electrically connected to the solid-state relay, and the solid-state relay is used to adjust the power of the heating circuit to accurately maintain the temperature of the tissue coagulation part at a preset temperature; the bioimpedance meter is electrically connected to the impedance detection electrode, and is used to calculate and output the real-time tissue electrical impedance value of the tissue to be coagulated.

9. The tissue constant temperature coagulation device according to claim 8, characterized in that: It also includes a cooling component, which is arranged in the shell and contacts the second end of the tissue coagulation component. The cooling component is electrically connected to the micro PID controller. The cooling component is used to quickly reduce the real-time temperature of the tissue coagulation component to a preset temperature or normal temperature.

10. The tissue constant temperature coagulation device according to claim 8, characterized in that: The industrial computer further includes an impedance warning module, which includes a microcontroller and an alarm. The input end of the microcontroller is electrically connected to the bioimpedance measuring instrument, and the output end of the microcontroller is electrically connected to the alarm.

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