An implantable hemostatic device for puncture surgery

Abstract

The embodiment of the present application discloses a kind of implantable hemostatic device for puncture operation, the device includes: laser, for output laser;Optical fiber, length is greater than the length of puncture needle sheath and diameter is less than the diameter of the puncture needle sheath, for transmitting the laser;Hemostatic component is arranged at the end of the optical fiber, including heat-conducting shell and the light-heat structure arranged in the heat-conducting shell, the cross-sectional diameter of the heat-conducting shell is less than the cross-sectional diameter of the puncture needle sheath, the heat-conducting shell is opened with the opening for receiving the laser, the laser is used to irradiate light-heat structure, the light-heat structure converts the light energy of laser into heat energy, and the temperature of the heat-conducting shell is increased to the set temperature range that can carry out tissue hemostasis.The problem that the hemostatic method used by existing hemostatic instrument exists health hidden danger is solved.

Description

Technical Field

[0001] The present invention relates to the field of medical devices, and more particularly to an implantable hemostatic device for puncture surgery. Background Technology

[0002] Intraoperative and postoperative bleeding is unavoidable in biopsy procedures, and there are certain risks of complications and death. Currently, hemostatic instruments used in biopsy procedures include high-frequency electrosurgical units, PK knives, radiofrequency ablation, microwave ablation, and cryotherapy. High-frequency electrosurgical units release high-frequency, high-power sine waves from their two tips, generating a thermal effect on the electrocoagulated human tissue, coagulating proteins to achieve hemostasis. Due to its significant thermal effect, it is mostly used for the removal of lesions and is not suitable for hemostasis in narrow puncture tracts. PK knives have a smaller thermal effect, with an effective temperature of 40–70°C and a thermal damage range not exceeding 4 mm. They can close blood vessels smaller than 7 mm, but they produce toxic fumes and are large in size and diameter, making them unsuitable for deep hemostasis in narrow pathways after fine needle punctures. Radiofrequency ablation uses electromagnetic waves within a specific range to cause plasma oscillation in tumor cells. The continuous collision of ions generates heat, but it is greatly affected by the medium and blood perfusion rate, resulting in a smaller ablation area and the same risk of needle tract bleeding. Furthermore, radiofrequency ablation needles are difficult to match with biopsy needle sheaths, making them unsuitable for hemostasis in internal puncture tracts. Microwave ablation needles, guided by CT or ultrasound, are inserted into the central region of the lesion. Microwaves are released at the tip, causing surrounding molecules to rotate at high speed and generate frictional heat. The ablation range is typically a 360° ellipsoid centered on the central needle shaft. This allows for simultaneous tumor ablation and wound hemostasis. However, due to the lack of guidance and real-time temperature monitoring devices, the ablation range is difficult to control precisely, and there is a risk of needle tract bleeding after needle withdrawal. Furthermore, it is relatively expensive and not suitable for in vivo hemostasis. Cryotherapy, such as argon-helium cryosurgery, only provides temporary hemostasis and cannot suppress postoperative bleeding.

[0003] In summary, due to the deep depth of puncture procedures (such as lung puncture) and the small puncture wound, there is a lack of precise, efficient, and non-invasive puncture hemostasis methods and instruments among the commonly used hemostasis techniques. Summary of the Invention

[0004] This invention provides an implantable hemostatic device for puncture surgery, which solves the health risks associated with existing hemostatic methods.

[0005] In a first aspect, embodiments of the present invention provide an implantable hemostatic device for puncture surgery, comprising:

[0006] A laser, used to output laser light;

[0007] An optical fiber, longer than the length of the puncture needle sheath and smaller in diameter than the diameter of the puncture needle sheath, is used to transmit the laser.

[0008] A hemostatic assembly, disposed at the end of the optical fiber, includes a heat-conducting housing and a photothermal structure disposed inside the heat-conducting housing. The cross-sectional diameter of the heat-conducting housing is smaller than the cross-sectional diameter of the puncture needle sheath. The heat-conducting housing has an opening for receiving the laser. The laser is configured to be transmitted to the heat-conducting structure. The photothermal structure converts the light energy of the laser into heat energy. The heat energy raises the temperature of the heat-conducting housing to a set temperature range suitable for tissue hemostasis.

[0009] Furthermore, the heat-conducting shell is a cylindrical shell with one end open, and the closed end of the cylindrical shell is a spherical surface or a plane.

[0010] Furthermore, it also includes:

[0011] A sensor device, disposed on a heat-conducting housing, is used to acquire a set of set parameters of the environment in which the heat-conducting housing is located. The sensor device includes a temperature sensor and at least one of a position sensor, a blood flow sensor, and a blood pressure sensor.

[0012] A display device is used to display the data of each set parameter in the set parameter set;

[0013] The processor is used to control the display device to graphically display the data of each setting parameter in the set of setting parameters.

[0014] Furthermore, the processor is also configured to control the display device to output a prompt message and turn off the laser when any set parameter data in the set of set parameters exceeds the corresponding parameter threshold.

[0015] Furthermore, the laser can output laser with adjustable laser parameters;

[0016] The processor is also configured to output a control signal for adjusting the laser parameters based on the tissue temperature and the pre-stored correspondence between tissue temperature and laser parameters, so that after the laser with adjusted laser parameters acts on the photothermal structure, the heat energy output by the photothermal structure keeps the temperature of the heat-conducting shell within the set temperature range.

[0017] Furthermore, it also includes:

[0018] Input device for receiving laser parameters input by the operator;

[0019] The processor is also used to determine the laser parameters of the output laser based on the received laser parameters.

[0020] Furthermore, the photothermal structure is a coating disposed on the inner wall of the heat-conducting housing, the coating material including photothermal materials, and the propagation direction of the laser is parallel to the cross-section of the heat-conducting housing; or

[0021] The photothermal structure is a photothermal material filled inside the heat-conducting shell, and the propagation direction of the laser is perpendicular to the cross-section of the heat-conducting shell.

[0022] Furthermore, it also includes:

[0023] When the photothermal structure is a photothermal material filled inside the heat-conducting shell, it also includes a partition layer. The partition layer is disposed at the light-transmitting end of the heat-conducting shell and includes a non-light-transmitting sheet and a light-transmitting area disposed at the center of the non-light-transmitting sheet. The light-transmitting area is coaxially disposed with the laser.

[0024] Furthermore, when the photothermal structure is a coating disposed on the inner wall of the heat-conducting housing, the optical fiber is a columnar optical fiber.

[0025] Furthermore, the optical fiber is provided with a depth marking structure, which is used to indicate the depth at which the heat-conducting housing enters the body.

[0026] The technical solution of the hemostasis device provided in this invention uses a laser to output laser light, which is guided into the photothermal structure inside the hemostasis shell through an optical fiber with a length greater than the length of the puncture needle sheath and a diameter smaller than the diameter of the puncture needle sheath. This allows the heat-conducting shell to smoothly reach the puncture target point from inside the puncture needle sheath. The photothermal structure safely converts the light energy of the laser into heat energy to raise the temperature of the heat-conducting shell. By raising the temperature of the heat-conducting shell to a set temperature range, the heat-conducting shell heats and stops the bleeding of the tissue at the puncture target point. Furthermore, during the process of the puncture needle sheath pulling the heat-conducting shell out of the human body, the heat-conducting shell heats and stops the bleeding of the tissue in the puncture tract. This effectively avoids bleeding and related sequelae caused by bleeding in the puncture tract, and also reduces the risk of disease cell spread or even metastasis caused by the withdrawal of the puncture needle sheath. Attached Figure Description

[0027] To more clearly illustrate the technical solutions in the embodiments of the present invention, the accompanying drawings used in the description of the embodiments will be briefly introduced below. Obviously, the accompanying drawings described below are some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0028] Figure 1 This is a schematic diagram of the hemostatic device provided in an embodiment of the present invention;

[0029] Figure 2 This is a schematic diagram of the structure of another hemostatic device provided in an embodiment of the present invention;

[0030] Figure 3 This is a schematic diagram of another hemostatic device provided in an embodiment of the present invention. Detailed Implementation

[0031] To make the objectives, technical solutions, and advantages of this invention clearer, the technical solutions of this invention will be clearly and completely described below with reference to the accompanying drawings in the embodiments of this invention. Obviously, the described embodiments are only some embodiments of this invention, not all embodiments. Based on the embodiments of this invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this invention.

[0032] Example 1

[0033] Figure 1 This is a schematic diagram of an implantable hemostasis device for puncture surgery provided in Embodiment 1 of the present invention. The technical solution of this embodiment is applicable to puncture hemostasis. The hemostasis device includes a laser 11, an optical fiber 12, and a hemostasis component 13; the laser 11 is used to output laser light; the optical fiber 12 is longer than the length of the puncture needle sheath 2 and smaller in diameter than the diameter of the puncture needle sheath 2, and is used to transmit laser light; the hemostasis component 13 is disposed at the end of the optical fiber 12, including a heat-conducting shell 131 and a photothermal structure 132 disposed inside the heat-conducting shell 131. The cross-sectional diameter of the heat-conducting shell 131 is smaller than the cross-sectional diameter of the puncture needle sheath 2. The heat-conducting shell 131 has an opening for receiving laser light. The laser light is used to irradiate the photothermal structure, and the photothermal structure 132 converts the light energy of the laser light into heat energy. The heat energy raises the temperature of the heat-conducting shell 131 to a set temperature range suitable for tissue hemostasis.

[0034] Among them, the photothermal structure is a coating set on the inner wall of the heat-conducting shell, and the coating material includes photothermal materials. In this case, the propagation direction of the laser is parallel to the cross-section of the heat-conducting shell; or the photothermal structure is a photothermal material filled inside the heat-conducting shell, in which case the propagation direction of the laser is perpendicular to the cross-section of the heat-conducting shell.

[0035] Photothermal materials are materials that exhibit a strong photothermal effect on the laser emitted from the laser and are media that specifically absorb the laser wavelength. For example, for an 808nm laser, nano-gold, nano-platinum, black phosphorus, and carbon nanotubes (CNTs) can be selected as photothermal materials. The main mechanism of the photothermal effect lies in the fact that the photothermal conversion medium absorbs the laser energy during the exposure time and converts it into heat. This heat is transferred to the tissue in contact with it, causing tissue damage and achieving vascular coagulation. The principle of hemostasis based on the photothermal effect is as follows:

[0036] The expression for photothermal density Q is:

[0037] Q = μ a ET (1)

[0038] In the formula, E is the light intensity incident on the surface of the tissue, T is the exposure time, and μ aLet be the absorption coefficient of the tissue, and ET be the irradiation exposure. The resulting temperature rise ΔT0 on the tissue surface is:

[0039]

[0040] In the formula C p Let be the heat capacity, used to describe the tissue's ability to store heat energy; ρ be the density; and τ be the heat transfer efficiency from the photothermal conversion medium to the tissue. The temperature rise caused at a tissue depth z is:

[0041]

[0042] It is understandable that the range of hemostasis temperature under safe conditions, as well as the laser parameters required to maintain the hemostasis temperature within this range, can be derived based on formulas (1), (2), and (3). In practical applications, the laser parameters can be adjusted according to the correspondence between the hemostasis temperature and the laser parameters, as well as the hemostasis temperature of the tissue to be hemostatic.

[0043] To ensure the safety of hemostasis, this embodiment uses a heat-conducting shell to enclose the photothermal structure. The heat-conducting shell uses non-toxic materials with good thermal conductivity, including but not limited to metallic copper and quartz.

[0044] Optionally, the heat-conducting housing 131 is a cylindrical housing with one open end. The open end of the cylindrical housing faces the optical fiber output end to guide the laser onto the photothermal material 132; the closed end of the cylindrical housing is a spherical surface or a plane; the cross-sectional diameter of the cylindrical housing is smaller than the cross-sectional diameter of the puncture needle sheath 2, thus, when combined with an optical fiber whose length is greater than that of the puncture needle sheath 2 and whose diameter is smaller than that of the puncture needle sheath 2, the cylindrical housing can reach the puncture target point from inside the puncture needle sheath; this cylindrical housing allows the operator to easily access the target point by withdrawing the puncture needle sheath 2 (see...). Figure 2 When the hemostatic assembly 13 is withdrawn, the heat-conducting housing 131 can fully interact with the surrounding tissue, thereby completing the hemostasis of the surrounding tissue.

[0045] In one embodiment, the device further includes a sensor device, a display device, and a processor disposed on the heat-conducting housing. The sensor device is used to acquire a set of set parameters of the environment in which the heat-conducting housing is located. The sensor device includes a temperature sensor and at least one of a position sensor, a blood flow sensor, and a blood pressure sensor. The display device is used to display the set parameter data in the set parameter set. The processor is used to control the display device to graphically display the set parameter data in the set parameter set. This embodiment acquires the corresponding set parameter data in real time by setting a sensor device on the heat-conducting housing, allowing the user to intuitively understand the working status of the heat-conducting housing in the human body through the set parameter data. For example, the position sensor determines the current hemostasis position of the device, the blood flow sensor and blood pressure sensor determine the hemostasis status, and the temperature sensor determines the current temperature of the heat-conducting housing.

[0046] like Figure 2 As shown, taking a sensor device including a temperature sensor as an example, the temperature sensor 14 is disposed on the heat-conducting housing 131 and is used to acquire the tissue temperature of the tissue in contact with the heat-conducting housing 131; the display device 15 is used to display the tissue temperature; the processor 16 is used to control the display device 15 to display the current tissue temperature, the set temperature range, and the current laser parameters. Optionally, in this embodiment, the temperature sensor 14 is disposed on the outer wall of the heat-conducting housing 131, including but not limited to various thermocouples; optionally, in this embodiment, the data line 141 used to feed back the tissue temperature is coupled in parallel with the optical fiber 12.

[0047] Understandably, the device can be configured to include a temperature sensor but not a display. The processor adjusts the laser parameters based on the tissue temperature fed back by the temperature sensor, but does not display the tissue temperature or the laser parameters.

[0048] In one embodiment, a temperature sensor 14 is disposed on the inner wall of the heat-conducting housing 131 to acquire the temperature of the heat-conducting housing 131. A processor 16 is used to determine the temperature of the tissue surrounding the heat-conducting housing based on the temperature of the heat-conducting housing 131.

[0049] In one embodiment, such as Figure 3As shown, taking a sensor device including a position sensor as an example, the position sensor 17 is disposed on the heat-conducting housing 131 and is used to collect the position data of the heat-conducting housing 131. The processor 16 is also used to acquire the position data of the heat-conducting housing 11 when the temperature of the tissue exceeds the set temperature range, and to turn off the laser 11 when the change in the position data of the heat-conducting housing 131 exceeds the set distance threshold, so that the laser stops outputting laser light, thereby stopping the photothermal structure 132 from converting light energy, that is, stopping the generation of heat energy to heat the heat-conducting housing 131, so as to reduce the temperature of the heat-conducting housing 131 and avoid burning the patient's skin due to the excessively high temperature of the heat-conducting housing when the hemostasis device is withdrawn by withdrawing the puncture needle sheath 2. Optionally, the set distance threshold in this embodiment can be set by the operator according to the length of the puncture needle sheath.

[0050] In one embodiment, when the heat-conducting housing 131 is equipped with a position sensor 17, the operator inputs a hemostasis start command when initiating hemostasis. Upon detecting this command, the processor 16 acquires the position data from the position sensor 17 in real time and outputs the corresponding position information to the display device 15. Optionally, the relative position of the heat-conducting housing 131 and the puncture needle sheath 2 is displayed graphically; specifically, the process of the heat-conducting housing reaching the puncture target point along the inside of the puncture needle sheath is graphically displayed. This embodiment allows the operator to intuitively observe the movement of the heat-conducting housing, facilitating real-time monitoring of the hemostasis process.

[0051] The output end of laser 11 is connected to optical fiber 12, and the optical fiber is equipped with an optical fiber coupler. A tunable laser beam is transmitted through the optical fiber and the optical fiber coupler; specifically, the laser parameters are adjustable, including output power, duty cycle, and other parameters. In one embodiment, when the photothermal structure is a coating disposed on the inner wall of a heat-conducting housing, the optical fiber is a columnar optical fiber. The laser beam output is parallel to the cross-section of the heat-conducting housing, i.e., perpendicular to the coating. Its penetration depth is small, the irradiation area is large, and it can irradiate the entire inner wall of the heat-conducting housing relatively uniformly.

[0052] In one embodiment, the operator determines whether laser parameters need adjustment based on the tissue temperature output by the display device 15, and inputs the laser parameters via the input device when adjustment is required; the processor 16 adjusts the laser parameters based on these parameters. In this embodiment, the introduction of the temperature sensor 14 and the tunable laser allows the user to adjust the laser parameters according to actual needs during hemostasis, improving the flexibility of the hemostasis device.

[0053] In one embodiment, to improve the safety of operators manually adjusting laser parameters, when the processor 16 detects that the tissue temperature is higher than the set temperature range, it controls the display device 15 to output a prompt message to remind the operator that the current tissue temperature is higher than the set temperature range. This prompt message may be an audible prompt output through a speaker and / or an icon-based prompt output through the display device.

[0054] In one embodiment, when the processor 16 detects that the tissue temperature is higher than a set temperature range, it updates the laser parameters of the current laser based on the current tissue temperature and the pre-stored correspondence between tissue temperature and laser parameters. This ensures that after the laser with the updated parameters interacts with the photothermal structure 132, the heat generated by the photothermal structure is transferred through the heat-conducting housing 131 to adjust the temperature of the surrounding tissue to the set temperature range. Automatic adjustment of the laser parameters based on the tissue temperature feedback from the temperature sensor improves the accuracy of laser parameter adjustment and ensures that the temperature of the surrounding tissue is within the set temperature range, such as 70-90°C. During the slow withdrawal of the puncture needle sheath, the tissue around the puncture channel undergoes high-temperature denaturation, leading to vascular coagulation and achieving hemostasis. It is understood that the set temperature range is related to the hemostatic temperature range corresponding to the tissue; therefore, this hemostatic device should use the appropriate set temperature range when performing hemostasis on tissues at different locations.

[0055] In one embodiment, when the photothermal structure is a photothermal material filled inside a heat-conducting shell, the laser is controlled to output an 808nm laser. The 808nm laser is transmitted along an optical fiber to a partition layer, and then guided onto the photothermal structure through the light-transmitting area of ​​the partition layer. The photothermal structure generates heat under the irradiation of the 808nm laser, and conducts the heat to the surrounding tissue through the heat-conducting shell, causing the tissue around the heat-conducting shell to heat up to 70-90°C. A temperature sensor installed on the heat-conducting shell acquires the temperature of the surrounding tissue in real time and sends the tissue temperature to a processor. When the processor detects that the tissue temperature is about to reach the upper limit of the set temperature range, such as 85-90°C, it adjusts the laser parameters to reduce its power density so that the temperature does not exceed the set temperature range.

[0056] In one embodiment, when the photothermal structure is a photothermal material filled inside a heat-conducting housing, the device further includes a partition layer 133. This partition layer 133 is disposed at the light-transmitting end of the heat-conducting housing 131 and includes a non-transparent sheet and a light-transmitting region disposed at the center of the non-transparent sheet, with the light-transmitting region coaxially aligned with the laser. It is understood that the non-transparent sheet is made of a non-transparent material, and the laser can only pass through the light-transmitting region to reach the photothermal material inside the heat-conducting housing, but cannot pass through the non-transparent sheet. Therefore, the light-transmitting region has a laser shaping function. On the other hand, the partition layer can prevent harmful gases generated by the photothermal material from contaminating the fiber optic output end and from being released into the human body during hemostasis, thus helping to improve the service life of the fiber optic output end and the safety of puncture hemostasis. The light-transmitting region is made of a light-transmitting material, and solids cannot pass through this material, nor can liquids permeate it.

[0057] In one embodiment, the optical fiber is provided with a depth marking structure to indicate the depth to which the heat-conducting housing has entered the body. Exemplarily, this depth marking structure is a scale marking or a color marking. The depth marking structure in this embodiment allows operators to promptly understand the depth to which the heat-conducting housing has entered the body.

[0058] In one embodiment, the hemostatic device further includes a fixing structure, which is used to secure the optical fiber to the puncture needle sheath when the heat-conducting housing reaches a predetermined depth, thereby preventing undesirable movement of the heat-conducting housing due to optical fiber movement during hemostasis. The fixing structure improves the safety and flexibility of the hemostatic device operation, as well as the safety of hemostasis.

[0059] The method of using the hemostasis device is as follows: After completing the puncture operation, the operator withdraws the puncture needle from the puncture needle sheath 2, leaving the sheath in place. Simultaneously, the heat-conducting housing 131 is inserted into the puncture needle sheath 2 and further extends along the sheath to the puncture target point. Then, the laser 11 is activated, and the laser 11 outputs laser light through an optical fiber. After the laser light irradiates the photothermal structure 132 inside the heat-conducting housing 131, the photothermal structure 132 converts the light energy of the laser light into heat energy. This heat energy raises the temperature of the heat-conducting housing 131 to a set temperature range. The heat-conducting housing 131, at a temperature within the set temperature range, achieves hemostasis of the surrounding tissue by heating it. After achieving hemostasis of the surrounding tissue, the puncture needle sheath 2 is slowly withdrawn from the body. As the puncture needle sheath 2 is withdrawn, it drives the heat-conducting housing 131 to move, and during this movement, the heat-conducting housing 131 achieves hemostasis of the tissue along the puncture path. When the processor detects that the temperature of the heat-conducting housing 131 has risen to a set temperature range, and the change in its position data exceeds a set distance threshold, it shuts off the laser 11. This prevents the photothermal structure 132 from generating heat due to no longer receiving laser irradiation. Since the photothermal structure 132 does not generate heat, the temperature of the heat-conducting housing 131 drops rapidly, thus preventing burns to the skin when the heat-conducting housing 131 is removed from the human body. It is understood that because the hemostatic device is used in conjunction with the puncture needle sheath, it avoids secondary trauma. While effectively coagulating and stopping bleeding in the blood vessels of the puncture site and preventing the spread or even metastasis of diseased cells, it avoids bleeding caused by secondary punctures; this is highly practical in clinical practice.

[0060] The technical solution of the hemostasis device provided in this invention uses a laser to output laser light, which is guided into the photothermal structure inside the hemostasis shell through an optical fiber with a length greater than the length of the puncture needle sheath and a diameter smaller than the diameter of the puncture needle sheath. This allows the heat-conducting shell to smoothly reach the puncture target point from inside the puncture needle sheath. The photothermal structure safely converts the light energy of the laser into heat energy to raise the temperature of the heat-conducting shell. By raising the temperature of the heat-conducting shell to a set temperature range, the heat-conducting shell heats and stops the bleeding of the tissue at the puncture target point. Furthermore, during the process of the puncture needle sheath pulling the heat-conducting shell out of the human body, the heat-conducting shell heats and stops the bleeding of the tissue in the puncture tract. This effectively avoids bleeding and related sequelae caused by bleeding in the puncture tract, and also reduces the risk of disease cell spread or even metastasis caused by the withdrawal of the puncture needle sheath.

[0061] Note that the above description is merely a preferred embodiment of the present invention and the technical principles employed. Those skilled in the art will understand that the present invention is not limited to the specific embodiments described herein, and various obvious changes, readjustments, and substitutions can be made without departing from the scope of protection of the present invention. Therefore, although the present invention has been described in detail through the above embodiments, the present invention is not limited to the above embodiments, and may include many other equivalent embodiments without departing from the concept of the present invention, the scope of which is determined by the scope of the appended claims.

Claims

1. An implantable hemostatic device for puncture surgery, characterized in that, include: A laser, used to output laser light; An optical fiber, longer than the length of the puncture needle sheath and smaller in diameter than the diameter of the puncture needle sheath, is used to transmit the laser. A hemostatic assembly, disposed at the end of the optical fiber, includes a heat-conducting shell and a photothermal structure disposed inside the heat-conducting shell. The cross-sectional diameter of the heat-conducting shell is smaller than the cross-sectional diameter of the puncture needle sheath. The heat-conducting shell has an opening for receiving the laser to guide the laser onto the photothermal material. The laser is used to irradiate the photothermal structure, which converts the laser's light energy into heat energy. The heat energy raises the temperature of the heat-conducting shell to a set temperature range suitable for tissue hemostasis. The heat-conducting shell can be transported along the puncture needle sheath to the target point, and its end extends out of the puncture needle sheath. A partition layer is provided at the light-transmitting end of the heat-conducting shell. The partition layer includes a non-transparent sheet and a light-transmitting area disposed at the center of the non-transparent sheet. The light-transmitting area is coaxially arranged with the laser. The heat-conducting shell is also used to complete hemostasis of the surrounding tissue when the hemostatic assembly is withdrawn by withdrawing the puncture needle sheath. A sensor device is disposed on the heat-conducting housing for acquiring a set of set parameters of the environment in which the heat-conducting housing is located. The set of set parameters includes the tissue temperature of the tissue in contact with the heat-conducting housing and the position data of the heat-conducting housing. The processor outputs a control signal to adjust the laser parameters based on the tissue temperature and the pre-stored correspondence between tissue temperature and laser parameters, so that after the laser with adjusted laser parameters acts on the photothermal structure, the heat energy output by the photothermal structure keeps the temperature of the heat-conducting shell within the set temperature range; when the change in the position data of the heat-conducting shell exceeds a set distance threshold, the laser is turned off.

2. The hemostatic device according to claim 1, characterized in that, The heat-conducting shell is a cylindrical shell with one open end, and the closed end of the cylindrical shell is a spherical surface or a plane.

3. The hemostatic device according to claim 1, characterized in that, Also includes: The sensor device includes a temperature sensor and some or all of a position sensor, a blood flow sensor, and a blood pressure sensor, and the portion or all of the sensor includes the temperature sensor and the position sensor. A display device is used to display the data of each set parameter in the set parameter set; The processor is used to control the display device to graphically display the data of each setting parameter in the set of setting parameters.

4. The hemostatic device according to claim 3, characterized in that, The processor is also configured to control the display device to output a prompt message and turn off the laser when any set parameter data in the set of set parameters exceeds the corresponding parameter threshold.

5. The hemostatic device according to claim 3, characterized in that, Also includes: Input device for receiving laser parameters input by the operator; The processor is also used to determine the laser parameters of the output laser based on the received laser parameters.

6. The hemostatic device according to claim 1, characterized in that, The photothermal structure is a coating disposed on the inner wall of the heat-conducting housing, the coating material including photothermal materials, and the propagation direction of the laser is parallel to the cross-section of the heat-conducting housing; or The photothermal structure is a photothermal material filled inside the heat-conducting shell, and the propagation direction of the laser is perpendicular to the cross-section of the heat-conducting shell.

7. The hemostatic device according to claim 1, characterized in that, When the photothermal structure is a coating disposed on the inner wall of the heat-conducting housing, the optical fiber is a columnar optical fiber.

8. The hemostatic device according to any one of claims 1-7, characterized in that, The optical fiber is equipped with a depth marking structure, which is used to indicate the depth to which the heat-conducting housing enters the body.

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