Temperature detection control and heating integrated photo-thermal hemostasis device based on Bragg grating fiber

Abstract

The invention provides a temperature detection control and heating integrated photo-thermal hemostasis device based on a Bragg grating optical fiber, and belongs to the technical field of medical instruments. The system comprises an excitation source module, a photo-thermal module, a temperature measurement module and a coupler, wherein the excitation source module is connected with the photo-thermal module, and the photo-thermal module is connected with the temperature measurement module through the coupler; the excitation source module comprises a laser; the photo-thermal module comprises an optical fiber, a photo-thermal material and a light blocking piece; the optical fiber is connected with the excitation source module; the photo-thermal material is coated on the surface of the optical fiber, and the light blocking piece is arranged at a port of the optical fiber; the temperature measuring module comprises a temperature measuring mechanism and a fiber bragg grating, the fiber bragg grating is etched in a fiber core of the optical fiber, and the temperature measuring mechanism is connected with the coupler; and the difference between the spectrum width entering the photo-thermal module and the reflection spectrum bandwidth of the fiber bragg grating is within a preset range. According to the invention, integration of heating and temperature measurement can be realized, and functions of initial light emitting power detection and temperature out-of-control prevention are realized.

Description

Technical Field

[0001] The present invention belongs to the technical field of medical devices, and in particular relates to a photothermal hemostasis device based on integrated temperature detection control and heating of Bragg grating optical fiber. Background Art

[0002] Traditional photothermal therapy equipment mainly relies on the absorption of laser by tissues to convert light energy into heat energy to heat and denature blood vessels at the wound surface to achieve the purpose of hemostasis. As Chinese patent application document CN115804642A discloses an implantable hemostatic device for puncture surgery, which achieves hemostasis at the puncture wound site through photothermal effect. When this implantable hemostatic device is used to stop bleeding at the puncture wound of a puncture biopsy, it is necessary to rely on the temperature data of the thermocouple sensor installed at the heating site to determine whether the device is working properly, and to remind the operator to stop heating when the tissue temperature exceeds the safe temperature of 90°C (363 Kelvin temperature).

[0003] In the conventional scheme, the photothermal material is coated on the inner wall of the heating shell, and the thermocouple is installed on the heating shell for temperature sensing. This scheme invisibly increases the design size of the hemostatic needle and has the risk of falling off, increasing the safety risk of clinical surgery.

[0004] Conventional temperature measurement schemes also include etching fiber Bragg gratings in optical fibers located at the heating target position to measure temperature. However, so far, only some papers have briefly discussed the combination of fiber Bragg grating temperature sensing and optical fiber for photothermal conversion, which has not been realized. On the one hand, there are few applications and developments for this type of device. The more important problem is that fiber Bragg grating sensors generally require the use of a tunable laser source in combination with a demodulator for temperature measurement, and a wavelength division multiplexer to multiplex the temperature measurement light and the heating light for photothermal conversion. The overall device will be more complicated and the industrialization cost will be higher. Since there are relatively few theoretical studies on this type of device, the quality of Bragg reflected light may be affected by multiple factors, and there is less industrial verification. Some people have tried to abandon the solution of using one optical fiber and use two optical fibers to achieve temperature sensing and photothermal conversion respectively, but this solution increases the design size, complicates the device, and may also destroy the uniformity of heating.

[0005] Moreover, as a clinical instrument, the device needs to put the safety of the patient first. First of all, it is necessary to detect whether the hemostatic device is working properly. If it does not work properly, it will be inserted into the human body but cannot stop bleeding, which will put the patient's life in danger. On the other hand, if the device is out of control and the tissue temperature rises above 100°C, the protein will vaporize, which may also cause serious harm to the patient. In actual clinical operations, for the safety of patients, it should be possible to detect whether the optical power at the photothermal material is normal when the device is started, and to avoid "insurance" technology that heats the tissue temperature above a safe temperature (such as 90°C).

[0006] In summary, there is currently a lack of a solution in clinical practice that can realize the integration of photothermal conversion and temperature measurement, which can not only detect whether the initial light output power is normal, but also prevent the temperature from continuing to rise when the device is out of control. Summary of the invention

[0007] The purpose of the present invention is to overcome the shortcomings of the prior art and to propose a photothermal hemostasis device based on Bragg grating optical fiber with integrated temperature detection control and heating, which can realize the integration of photothermal conversion and temperature measurement, detect whether the device is working normally, and prevent the temperature from continuing to rise when the device is out of control.

[0008] The present invention provides a photothermal hemostasis device integrating temperature detection control and heating based on Bragg grating optical fiber, comprising an excitation source module, a photothermal module, a temperature measurement module and a coupler:

[0009] The excitation source module is connected to the photothermal module, and the photothermal module is connected to the temperature measurement module through the coupler;

[0010] The excitation source module includes a laser; the photothermal module includes an optical fiber, a photothermal material and a light blocking member; the optical fiber is connected to the excitation source module; the photothermal material is coated on the surface of the optical fiber, and the light blocking member is arranged at the port of the optical fiber;

[0011] The temperature measurement module comprises a temperature measurement mechanism and a Bragg fiber grating, the Bragg fiber grating is etched in the core of the optical fiber, and the temperature measurement mechanism is connected to the coupler;

[0012] The difference between the spectrum width entering the photothermal module and the reflection spectrum bandwidth of the fiber grating is within a preset range.

[0013] Preferably, the light blocking member is a coating.

[0014] Preferably, the light blocking member is a light blocking plate.

[0015] Preferably, the temperature measuring mechanism includes a power detector, which is connected to the coupler. The power detection is performed using the principle of Bragg fiber grating reflected light. The coupler (also called fiber beam splitter) is 1×2, and most of the reflected light enters the optical path of the power detector. The coupling ratio and splitting ratio can be set.

[0016] Preferably, the temperature measuring mechanism is a temperature sensitive material temperature measuring module, and the temperature sensitive material temperature measuring module is connected to the coupler.

[0017] Preferably, the laser emitted by the laser is in the near-infrared band.

[0018] Preferably, the photothermal material is at least one of nano-gold, nano-platinum, black phosphorus, and carbon nanotubes.

[0019] Preferably, when the difference between the laser spectrum of the laser and the reflection spectrum bandwidth of the fiber Bragg grating exceeds a preset range, a filter device is arranged between the laser and the photothermal module.

[0020] Preferably, the coating layer of the tail end of the optical fiber is stripped, and the photothermal material is coated on the bare fiber surface of the optical fiber.

[0021] Preferably, the photothermal material is doped in the coating layer, and the coating layer doped with the photothermal material is coated on the tail end of the optical fiber.

[0022] Preferably, the parameters of the fiber Bragg grating are adjusted so that when the temperature is a preset temperature, the reflection peak wavelength of the Bragg grating is exactly the peak wavelength of the incident laser, and the preset temperature is 100° C. lower than the protein vaporization temperature.

[0023] Preferably, the preset temperature is greater than or equal to 60°C and less than 100°C.

[0024] Preferably, the preset temperature is 90°C.

[0025] Preferably, when the photothermal hemostasis device is started, it is first determined whether the power value or spectrum of the reflected light detected by the temperature measuring mechanism is normal, so as to determine whether the optical path is unobstructed and whether the laser is working normally.

[0026] Preferably, when the photothermal hemostasis device is started, it is first determined whether the power of the reflected light detected by the temperature measuring mechanism changes slowly around a preset value, so as to determine whether the optical path is unobstructed and whether the laser is working normally.

[0027] Preferably, the preset threshold is set according to the proportion of the laser light that can be reached by the reflected light.

[0028] Compared with the prior art, the present invention has at least the following beneficial effects:

[0029] (1) The present invention is a photothermal hemostasis device that integrates temperature detection control and heating based on Bragg grating optical fiber. The part that enters the human tissue realizes an all-optical fiber structure. The functions of heating, temperature measurement, light detection, temperature control, etc. can be realized with only one optical fiber. It has a small size, a simple structure, a low cost, and a strong mass production capability.

[0030] (2) In the present invention, a Bragg fiber grating is provided, and the wavelength of the Bragg fiber grating is adjusted to the wavelength of the incident laser. When the tissue temperature rises to approximately 90°C, the optical power in the optical fiber decreases rapidly, so that the heating temperature cannot exceed 90°C, thereby achieving temperature control similar to a "fuse" and avoiding temperature runaway.

[0031] (3) When the present invention is started, it first detects whether the optical path is unobstructed and whether the laser is working normally, and can detect whether the device is working normally, so as to avoid the situation where the device cannot stop bleeding after being inserted into the human body due to abnormality, and the patient will not be in danger of life. BRIEF DESCRIPTION OF THE DRAWINGS

[0032] Figure 1 The schematic diagram of the structure of a photothermal hemostasis device integrating temperature detection control and heating based on Bragg grating optical fiber according to an embodiment of the present invention.

[0033] Figure 2 This is a schematic diagram of an embodiment of the present invention for implementing a light detection function when the device is initially started. The direction of the arrow represents the direction of light energy transmission, and the thickness of the arrow reflects the magnitude of the light energy.

[0034] Figure 3 This is a schematic diagram of the light energy transmission path and function implementation when the tissue temperature is less than 90° C. in one embodiment of the present invention. The direction of the arrow represents the direction of light energy transmission, and the thickness of the arrow reflects the magnitude of the light energy.

[0035] Figure 4 This is a schematic diagram of the light energy transmission path and function implementation when the tissue temperature is 90° C. in one embodiment of the present invention. The direction of the arrow represents the direction of light energy transmission, and the thickness of the arrow reflects the magnitude of the light energy.

[0036] In the figure, 1-laser, 21-optical fiber, 22-photothermal material, 31-power detector, 32-Fiber Bragg grating, 4-coupler, 5-light blocking element. DETAILED DESCRIPTION

[0037] The technical solution of the present invention will be clearly and completely described below in conjunction with the embodiments. Obviously, the described embodiments are only part of the embodiments of the present invention, rather than all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative work are within the scope of protection of the present invention.

[0038] The present invention provides a photothermal hemostasis device integrating temperature detection control and heating based on Bragg grating optical fiber, comprising an excitation source module, a photothermal module, a temperature measurement module and a coupler 4:

[0039] The excitation source module is connected to the photothermal module, and the photothermal module is connected to the temperature measurement module through the coupler 4;

[0040] The excitation source module includes a laser 1; the photothermal module includes an optical fiber 21, a photothermal material 22 and a light blocking member; the optical fiber 21 is connected to the excitation source module; the photothermal material 22 is coated on the surface of the optical fiber 21, and the light blocking member 5 is arranged at the port of the optical fiber 21;

[0041] The temperature measurement module includes a temperature measurement mechanism and a Bragg fiber grating 32, the Bragg fiber grating 32 is etched in the core of the optical fiber 21, and the temperature measurement mechanism is connected to the coupler 4;

[0042] The difference between the spectrum width entering the photothermal module and the reflection spectrum bandwidth of the fiber grating is within a preset range, and the preset range makes the spectrum width of the photothermal module and the reflection spectrum bandwidth of the fiber grating as close as possible.

[0043] According to a specific embodiment of the present invention, the light blocking member 5 is a coating.

[0044] According to a specific embodiment of the present invention, the light blocking member 5 is a light blocking plate.

[0045] According to a specific embodiment of the present invention, the temperature measuring mechanism includes a power detector 31 , and the power detector 31 is connected to the coupler 4 .

[0046] According to a specific embodiment of the present invention, the temperature measuring mechanism is a temperature sensitive material temperature measuring module, and the temperature sensitive material temperature measuring module is connected to the coupler 4. The temperature sensitive material temperature measuring module is an optical fiber temperature measuring system including a sensor made of a material that is sensitive to temperature using a reflected wavelength. The sensitive judgment standard is: according to the temperature-reflectivity curve, the reflectivity is required to be maximum at a temperature close to the protein vaporization temperature, such as 90°C.

[0047] According to a specific embodiment of the present invention, the temperature measurement mechanism is a gallium arsenide temperature measurement module.

[0048] According to a specific embodiment of the present invention, the laser emitted by the laser 1 is in the near-infrared band, and the wavelength of the near-infrared band is 800-2500nm. The light material in this band absorbs relatively large amounts of light.

[0049] According to a specific embodiment of the present invention, the photothermal material 22 is at least one of nano-gold, nano-platinum, black phosphorus, and carbon nanotubes.

[0050] According to a specific embodiment of the present invention, when the difference between the laser spectrum of the laser 1 and the reflection spectrum bandwidth of the fiber Bragg grating exceeds a preset range, a filter device is arranged between the laser 1 and the photothermal module.

[0051] According to a specific embodiment of the present invention, the coating layer of the tail end of the optical fiber 21 is stripped, and the photothermal material 22 is coated on the bare fiber surface of the optical fiber 21 .

[0052] According to a specific embodiment of the present invention, the photothermal material 22 is doped in the coating layer, and the coating layer doped with the photothermal material 22 is coated on the tail end of the optical fiber 21 .

[0053] According to a specific embodiment of the present invention, the parameters of the fiber Bragg grating 32 are adjusted so that when the temperature is a preset temperature, the reflection peak wavelength of the Bragg grating is exactly the peak wavelength of the incident laser. The preset temperature is 100° C. lower than the protein vaporization temperature.

[0054] According to a specific embodiment of the present invention, the preset temperature is greater than or equal to 60°C and less than 100°C.

[0055] According to a specific embodiment of the present invention, the preset temperature is 90°C.

[0056] According to a specific embodiment of the present invention, when the photothermal hemostasis device is started, it is first determined whether the power value or spectrum of the reflected light detected by the temperature measuring mechanism is normal, so as to determine whether the optical path is unobstructed and whether the laser is working normally.

[0057] According to a specific embodiment of the present invention, when the photothermal hemostasis device is started, it is first determined whether the power of the reflected light detected by the temperature measuring mechanism changes slowly around a preset value, so as to determine whether the optical path is unobstructed and whether the laser is working normally.

[0058] According to a specific embodiment of the present invention, the preset threshold is set according to the proportion of the laser light that can be reached by the reflected light.

[0059] The principle of temperature measurement and temperature control of Fiber Bragg Grating is as follows:

[0060] When the wavelength of the incident light is equal to the Bragg wavelength λ b (T), that is:

[0061] λ b (T) = 2n eff (T)Λ(T) (1)

[0063] Among them, n eff is the effective refractive index of the fiber core, Λ is the spacing between the gratings etched in the fiber, called the grating period, and T is the ambient temperature in Kelvin.

[0064] At this time, the light reflected back from each grating will accumulate and finally form a reflection peak in the opposite direction.

[0065] According to formula (1), adjust the parameters of the fiber Bragg grating so that λ b The value of (363K) is exactly the wavelength of the incident laser. Therefore, when the temperature rises to 90°C (the Calvin temperature is expressed as 363K), since the wavelength of the incident light is equal to the Bragg wavelength, the reflection peak of the fiber grating highly coincides with the peak of the incident light, the light reflection becomes very strong, and only a very small part of the light is transmitted to the photothermal material, and the photothermal conversion almost stops, thereby blocking the rise in tissue temperature.

[0066] When the device is just started, the Bragg grating is at room temperature, reflecting a small amount of light proportionally, and the reflectivity changes very slowly at this temperature. When the laser power is constant, the power of the reflected light changes slowly around the preset constant value in a short period of time. By measuring the power value or spectrum of this part of the light, it is possible to determine whether the optical path is unobstructed and whether the laser is working properly, thereby inferring whether the power used for photothermal conversion is normal.

[0067] When the external ambient temperature changes, the Bragg wavelength shift △λ caused by the change of period and effective refractive index caused by the thermo-optical effect and thermal expansion effect B for:

[0068]

[0069] As the Bragg wavelength shifts relative to the wavelength of the incident laser, the reflectivity of the incident laser will change accordingly. From equation (2), we can see that when the material parameters are determined, △λ B It is only affected by △T, so the reflectivity of incident light is only related to △T. By measuring the temperature corresponding to a specific reflectivity in advance, a temperature-reflectivity relationship curve can be obtained.

[0070] The power of the reflected light is detected by the power detector 31. When the power of the laser is known, the reflectivity can be calculated by detecting the power of the reflected light, thereby obtaining the temperature of the tissue.

[0071] Although the measured temperature is inaccurate when the temperature is relatively low because the reflectivity change is not obvious, when the temperature approaches 90°C, the reflectivity rises rapidly because the Bragg wavelength is close to the central wavelength of the incident laser, so the measured temperature accuracy also increases. According to the needs of clinical temperature measurement, accurate temperature measurement is not required at the beginning of heating, and high temperature measurement accuracy is sufficient when the tissue temperature approaches 90°C. Therefore, there is no need to use a tunable laser source and a demodulator to obtain the temperature as in the conventional solution, thereby simplifying the device and reducing costs.

[0072] Example 1

[0073] The present invention provides a photothermal hemostasis device integrating temperature detection control and heating based on Bragg grating optical fiber, comprising an excitation source module, a photothermal module, a temperature measurement module and a coupler 4:

[0074] The excitation source module is connected to the photothermal module, and the photothermal module is connected to the temperature measurement module through the coupler 4;

[0075] The excitation source module includes a laser 1; the photothermal module includes an optical fiber 21, a photothermal material 22 and a light blocking member; the optical fiber 21 is connected to the excitation source module; the photothermal material 22 is coated on the surface of the optical fiber 21, and the light blocking member 5 is arranged at the port of the optical fiber 21;

[0076] The temperature measurement module includes a temperature measurement mechanism and a Bragg fiber grating 32, the Bragg fiber grating 32 is etched in the core of the optical fiber 21, and the temperature measurement mechanism is connected to the coupler 4;

[0077] The difference between the spectrum width entering the photothermal module and the reflection spectrum bandwidth of the fiber grating is within a preset range, and the preset range makes the spectrum width of the photothermal module and the reflection spectrum bandwidth of the fiber grating as close as possible.

[0078] Example 2

[0079] like Figure 1-4 As shown, the present invention provides a photothermal hemostasis device based on Bragg grating optical fiber with integrated temperature detection control and heating, including an excitation source module, a photothermal module, a temperature measurement module and a coupler 4:

[0080] The excitation source module is connected to the photothermal module, and the photothermal module is connected to the temperature measurement module through the coupler 4;

[0081] The excitation source module includes a laser 1. In this embodiment, the laser emitted by the laser 1 is in the near-infrared band; the photothermal module includes an optical fiber 21, a photothermal material 22 and a light shield; the optical fiber 21 is connected to the excitation source module; the photothermal material 22 is coated on the surface of the optical fiber 21, and the light shield 5 is arranged at the end of the optical fiber 21; the light shield 5 is a coating for absorbing laser light and preventing the laser light from entering the tissue; in other embodiments, the light shield 5 can be set as a light shield. The photothermal material 22 is at least one of nano-gold, nano-platinum, black phosphorus, and carbon nanotubes.

[0082] The temperature measurement module includes a temperature measurement mechanism and a Bragg fiber grating 32, wherein the Bragg fiber grating 32 is etched in the core of the optical fiber 21, and the temperature measurement mechanism is connected to the coupler 4; in this embodiment, the temperature measurement mechanism includes a power detector 31, and the power detector 31 is connected to the coupler 4. In other embodiments, the temperature measurement mechanism may be a temperature sensitive material temperature measurement module, wherein the temperature sensitive material temperature measurement module is connected to the coupler 4, and uses the reflected wavelength to measure the temperature sensitivity.

[0083] The difference between the spectrum width entering the photothermal module and the reflection spectrum bandwidth of the fiber grating is within a preset range, and the preset range makes the spectrum width of the photothermal module and the reflection spectrum bandwidth of the fiber grating as close as possible.

[0084] In this embodiment, the parameters of the fiber Bragg grating 32 are adjusted so that the wavelength of the Bragg grating is exactly the wavelength of the incident laser when the temperature is a preset temperature, which is 100° C. lower than the protein vaporization temperature, and the preset temperature is 363 Kelvin (90° C.).

[0085] In other embodiments, when the difference between the laser spectrum of the laser 1 and the reflection spectrum bandwidth of the fiber Bragg grating 32 exceeds a preset range, a filter device may be further provided between the laser 1 and the photothermal module, and the difference between the laser spectrum of the laser 1 and the reflection spectrum bandwidth of the fiber Bragg grating is controlled within a preset range through the filter device.

[0086] In this embodiment, the coating layer of the tail end of the optical fiber 21 is stripped, and the photothermal material 22 is coated on the bare fiber surface of the optical fiber 21 .

[0087] In other embodiments, the photothermal material 22 can also be doped into the coating layer, and the coating layer doped with the photothermal material 22 is coated on the tail end of the optical fiber 21. There is no need to peel off the coating layer and apply the photothermal material later, which can prevent the photothermal material from falling off.

[0088] The use process of the photothermal hemostasis device based on Bragg grating optical fiber temperature detection control and heating integration of the present invention is as follows:

[0089] When the photothermal hemostasis device is just started, first determine whether the power value or spectrum of the reflected light detected by the temperature measuring mechanism is normal, so as to determine whether the optical path is unobstructed and whether the laser is working normally. After confirming that the device is working normally, the photothermal hemostasis device is inserted from the puncture needle sheath into the human tissue to reach the target position for hemostasis. After the light energy is transmitted to the photothermal material 22, it is converted into light and heat, so that the surrounding tissue is quickly heated up to stop bleeding. The axially output light energy is scattered and diffused into the photothermal material 22 by the coating 5, preventing the laser from entering the tissue. Part of the light energy is reflected by the Bragg fiber grating 32 etched in the core and transmitted to the power detector 31 through the coupler 4.

[0090] Changes in temperature lead to changes in power. When the laser power is known, the temperature is calculated by the detected power, so that real-time temperature data of heating can be obtained. As the temperature rises to close to 90°C (363K), the Bragg wavelength is close to the laser wavelength, resulting in a rapid increase in light reflectivity and a rapid decrease in the light power transmitted to the photothermal material 22, making it difficult for photothermal conversion to continue, and the heating temperature is limited to below 90°C. Moreover, since the power of the power detector 31 rises rapidly at this time, the temperature data is easier to measure and the measurement accuracy is improved, so that the device issues an alarm to remind the operator to reduce the input light power in time. When hemostasis is completed, the optical fiber 21 and the photothermal material 22, Bragg fiber grating 32, and coating 5 set behind are removed.

[0091] The above is only a preferred embodiment of the present invention. It should be understood that the present invention is not limited to the form disclosed herein, and should not be regarded as excluding other embodiments, but can be used in various other combinations, modifications and environments, and can be modified within the scope of the concept described herein through the above description or the technology or knowledge of the relevant field. The changes and modifications made by those skilled in the art shall not deviate from the spirit and scope of the present invention, and shall be within the scope of protection of the claims attached to the present invention.

Claims

1. A photothermal hemostasis device based on Bragg grating optical fiber with integrated temperature detection control and heating, characterized in that: Including excitation source module, photothermal module, temperature measurement module and coupler: The excitation source module is connected to the photothermal module, and the photothermal module is connected to the temperature measurement module through the coupler; The excitation source module includes a laser; the photothermal module includes an optical fiber, a photothermal material and a light blocking member; the optical fiber is connected to the excitation source module; the photothermal material is coated on the surface of the optical fiber, and the light blocking member is arranged at the port of the optical fiber; The temperature measurement module comprises a temperature measurement mechanism and a Bragg fiber grating, the Bragg fiber grating is etched in the core of the optical fiber, and the temperature measurement mechanism is connected to the coupler; The difference between the spectrum width entering the photothermal module and the reflection spectrum bandwidth of the fiber grating is within a preset range.

2. The photothermal hemostasis device integrating temperature detection, control and heating based on Bragg grating optical fiber according to claim 1 is characterized in that: The light blocking member is a coating or a light blocking plate.

3. The photothermal hemostasis device integrating temperature detection, control and heating based on Bragg grating optical fiber according to claim 1 is characterized in that: The temperature measuring mechanism comprises a power detector, and the power detector is connected to the optical fiber coupler.

4. The photothermal hemostasis device integrating temperature detection, control and heating based on Bragg grating optical fiber according to claim 1 is characterized in that: The temperature measuring mechanism is a temperature sensitive material temperature measuring module, and the temperature sensitive material temperature measuring module is connected to the coupler.

5. The photothermal hemostasis device integrating temperature detection, control and heating based on Bragg grating optical fiber according to claim 1 is characterized in that: The laser emitted by the laser device is in the near-infrared band.

6. The photothermal hemostasis device integrating temperature detection, control and heating based on Bragg grating optical fiber according to claim 1, characterized in that: When the difference between the laser spectrum of the laser and the reflection spectrum bandwidth of the fiber Bragg grating exceeds a preset range, a filter device is arranged between the laser and the photothermal module.

7. The photothermal hemostasis device integrating temperature detection, control and heating based on Bragg grating optical fiber according to claim 1, characterized in that: The photothermal material is doped in the coating layer, and the coating layer doped with the photothermal material is coated on the tail end of the optical fiber.

8. The photothermal hemostasis device integrating temperature detection, control and heating based on Bragg grating optical fiber according to claim 1, characterized in that: By adjusting the parameters of the fiber Bragg grating, when the temperature is a preset temperature, the reflection peak wavelength of the Bragg grating is exactly the peak wavelength of the incident laser, and the preset temperature is 100° C. lower than the protein vaporization temperature.

9. The photothermal hemostasis device integrating temperature detection, control and heating based on Bragg grating optical fiber according to claim 8, characterized in that: The preset temperature is greater than or equal to 60° C. and less than 100° C.

10. The photothermal hemostasis device integrating temperature detection, control and heating based on Bragg grating optical fiber according to claim 1, characterized in that: When the photothermal hemostasis device is started, it is first determined whether the power value or spectrum of the reflected light detected by the temperature measuring mechanism is normal, so as to determine whether the optical path is unobstructed and whether the laser is working normally.

Images