A laser ablation device

Abstract

The present application discloses a laser ablation device, which includes a first optical fiber and crystalline silicon. One end of the first optical fiber is docked to the output end of a laser light source, and the other end is docked to the crystalline silicon to form an ablation probe. When the ablation probe enters the lesion area, the crystalline silicon can convert the light transmitted by the second end of the first optical fiber into heat energy. Since the crystalline silicon has penetrated into the lesion area, the converted heat energy can be conducted to the lesion tissue. The ablation probe can withstand high temperatures, with a maximum temperature reaching over one thousand degrees Celsius, and can accumulate relatively high heat to raise the temperature of the lesion tissue and perform laser ablation on the lesion tissue. The temperature of the crystalline silicon is directly conducted to the lesion tissue in the way that the crystalline silicon contacts the lesion tissue, and the lesion ablation efficiency and the lesion ablation effect are not affected by light scattering. The heat can be quickly transferred to the deep lesion tissue to achieve ablation. It can not only achieve the expected ablation target for the lesion tissue, but also greatly reduce the risk of damage to healthy tissues.

Description

Technical Field

[0001] This application relates to the technical field of medical devices, and particularly to a laser ablation device. Background Art

[0002] Laser ablation is a technique for ablating tumors using lasers. The basic principle of laser ablation is to absorb the laser and convert it into heat energy, causing the tumor temperature to rise and form irreversible damage. Currently, in laser ablation, an optical fiber is generally inserted into the tumor, and the light is directly irradiated into the tumor through the optical fiber. After the tumor absorbs the light energy, it gradually heats up until it solidifies, vaporizes, or carbonizes, achieving the purpose of eliminating the tumor. However, this will cause the surface of the charred tumor tissue to become rough, increasing light scattering. The increase in light scattering further reduces the power of the subsequent light absorbed by the tumor, affecting the tumor ablation efficiency, and the operation time has to be extended. Even in some possible cases, due to the too high power of the scattered light, the power of the light actually absorbed by the tumor is so low that the temperature of the remaining tumor tissue cannot be raised to the degree that can achieve ablation. It can be seen that in the above implementation method, due to the too strong light scattering, not only the ablation efficiency of the tumor is affected, but also the ablation effect of the tumor is not very ideal.

[0003] Moreover, because the tumor tissue absorbs light slowly and the temperature rises slowly, resulting in slow local heat accumulation. If the local heat accumulation is not rapid enough, the temperature for apoptosis or necrosis of cells (usually 50 - 60 degrees Celsius) cannot be reached quickly, which will cause the temperature of the surrounding tissue to also rise. This means that this will cause the heat to gradually transfer to healthy tissues, causing unnecessary damage. In addition, due to the too small penetration of the laser into the tumor, the above laser ablation solution is only applicable to ablating superficial tumor tissues and is difficult to apply to ablating deep tumor tissues. Summary of the Invention

[0004] Based on the above problems, this application provides a laser ablation device, aiming to improve the laser ablation efficiency and laser ablation effect on lesion tissues, avoid ablation affecting healthy tissues, and broaden the applicable range of the laser ablation device, so as to achieve the purpose of being applicable to both superficial and deep tumor tissues.

[0005] The embodiments of this application disclose the following technical solutions:

[0006] This application provides a laser ablation device, which includes: a first optical fiber and crystalline silicon; wherein, the first end of the first optical fiber is used to dock with the output end of a laser light source, and the second end of the first optical fiber is used to dock with the crystalline silicon to form an ablation probe.

[0007] When the ablation probe enters the lesion area, the crystalline silicon is used to convert the light transmitted by the second end of the first optical fiber into heat energy and conduct the heat energy to the lesion tissue to perform laser ablation on the lesion tissue.

[0008] In a possible implementation manner of the present application, the laser ablation device further includes: a switch control element and an N×1 optical switch, where N is an integer greater than 1. The optical switch includes N first ends and one second end. Among them, the N first ends are respectively used to dock with the output ends of N different types of laser light sources, and the second end of the optical switch is used to dock with the first end of the first optical fiber;

[0009] The switch control element is used to control an optical path to be formed between the second end of the optical switch and one of the first ends of the optical switch.

[0010] In a possible implementation manner of the present application, the optical switch is of a 2×1 structure, and the two first ends of the optical switch are respectively docked with the output ends of a continuous laser and a pulsed laser through two second optical fibers;

[0011] The switch control element is used to control an optical path to be established between the second end of the optical switch and one of the first ends of the optical switch according to the size of the remaining ablation area of the lesion tissue and / or the distance between the remaining ablation area and adjacent healthy tissue.

[0012] In a possible implementation manner of the present application, if the distance between the remaining ablation area and adjacent healthy tissue is less than a preset distance, the switch control element is used to control the second end of the optical switch to be connected to the first end of the optical switch that docks with the continuous laser; if the distance between the remaining ablation area and adjacent healthy tissue is greater than or equal to the preset distance, the switch control element is specifically used to control an optical path to be established between the second end of the optical switch and one of the first ends of the optical switch according to the size of the remaining ablation area of the lesion tissue.

[0013] In a possible implementation manner of the present application, if the distance between the remaining ablation area and adjacent healthy tissue is greater than or equal to the preset distance, and the size of the remaining ablation area is greater than a preset size threshold, the switch control element is specifically used to control the second end of the optical switch to be connected to the first end of the optical switch that docks with the continuous laser; if the distance between the remaining ablation area and adjacent healthy tissue is greater than or equal to the preset distance, and the size of the remaining ablation area is less than or equal to the preset size threshold, the switch control element is used to control the second end of the optical switch to be connected to the first end of the optical switch that docks with the pulsed laser.

[0014] In a possible implementation manner of the present application, if the size of the remaining ablation region is greater than a preset size threshold, the switch control element is used to control the second end of the optical switch to be connected to the first end of the continuous laser in butt joint with the optical switch; if the size of the remaining ablation region is less than or equal to the preset size threshold, the switch control element is used to control the second end of the optical switch to be connected to the first end of the pulsed laser in butt joint with the optical switch.

[0015] In a possible implementation manner of the present application, the laser ablation device further includes: a first optical detector;

[0016] The first optical fiber includes a first optical fiber section for conduction and a first optical fiber section for detection; the first end of the first optical fiber section for conduction is used to be in butt joint with the output end of the laser light source, the second end of the first optical fiber section for conduction is used to be in butt joint with the first end of the first optical fiber section for detection, and the second end of the first optical fiber section for detection is used to be in butt joint with the crystalline silicon to form an ablation probe with temperature detection ability;

[0017] The first optical fiber section for detection is connected to the first optical detector; the first optical fiber section for detection is used to receive the laser from the second end of the first optical fiber section for conduction, transmit it to the crystalline silicon, and reflect the laser matching the central wavelength of the first optical fiber section for detection to the first optical detector;

[0018] The first optical detector is used to detect the temperature of the ablation probe according to the change of the central wavelength of the laser reflected by the first optical fiber section for detection.

[0019] In a possible implementation manner of the present application, the laser ablation device further includes: a second optical detector, an optical coupler, and a third optical fiber; the optical coupler includes an input end, a first output end, and a second output end; the input end of the optical coupler is used to be in butt joint with the output end of the laser light source, and the first output end and the second output end are respectively used to be in butt joint with the first end of the first optical fiber section for conduction and the first end of the second optical fiber section for conduction in the third optical fiber;

[0020] The second end of the second optical fiber section for conduction is used to be in butt joint with the first end of the second optical fiber section for detection in the third optical fiber, and the second end of the second optical fiber section for detection is used to contact the lesion tissue to form a lesion temperature sensing probe;

[0021] The second optical fiber section for detection is connected to the second optical detector; the second optical fiber section for detection is used to receive the laser from the second end of the second optical fiber section for conduction, transmit it to the contacted lesion tissue, and reflect the laser matching the central wavelength of the second optical fiber section for detection to the second optical detector;

[0022] The second photodetector is configured to detect the temperature of the diseased tissue according to the change in the central wavelength of the laser reflected by the second detection fiber segment.

[0023] In a possible implementation manner of the present application, the laser ablation device further includes: a first circulator and a second circulator; the first circulator and the second circulator are each provided with a first port, a second port, and a third port;

[0024] The first port and the second port of the first circulator are disposed on the first conduction fiber segment, and the third port of the first circulator is connected to the input end of the first photodetector;

[0025] The first port and the second port of the second circulator are disposed on the second conduction fiber segment, and the third port of the second circulator is connected to the input end of the second photodetector.

[0026] In a possible implementation manner of the present application, the laser ablation device further includes: an optical switch with a 2×1 structure and a switch control element;

[0027] Two first ends of the optical switch are respectively docked with the output end of the continuous laser and the output end of the pulsed laser through two second optical fibers, and the second end of the optical switch is connected to the input end of the optical coupler;

[0028] The switch control element is configured to control the second end of the optical switch to establish an optical path with one of the first ends of the optical switch according to the size of the remaining ablation area of the diseased tissue and / or the distance between the remaining ablation area and the adjacent healthy tissue.

[0029] In a possible implementation manner of the present application, the laser ablation device further includes: a controller, the output end of the controller is connected to the control end of the pulsed laser, and the input end of the controller is connected to the output end of the first photodetector;

[0030] When the second end of the optical switch establishes an optical path with the first end of the pulsed laser docked by the optical switch, and the deviation between the temperature detected by the first photodetector and the target control temperature exceeds a preset deviation range, the controller is configured to adjust the current optical pulse parameters of the pulsed laser based on the correspondence between the optical pulse parameters and the heat to reduce the deviation.

[0031] In a possible implementation manner of the present application, both the first detection fiber segment and the second detection fiber segment are fiber gratings; the first photodetector and the second photodetector are any one of the following:

[0032] A fiber grating demodulator or a spectrometer.

[0033] In a possible implementation manner of the present application, the laser ablation device includes a plurality of spare crystalline silicons with different cross-sectional sizes; the crystalline silicon that docks with the second end of the first optical fiber to form an ablation probe is selected from the plurality of spare crystalline silicons based on the size of the remaining ablation area of the lesion tissue.

[0034] In a possible implementation manner of the present application, if the cross-sectional size of the selected crystalline silicon exceeds a first preset size, the first optical fiber is a plastic optical fiber.

[0035] In a possible implementation manner of the present application, the working wavelength band of the ablation probe is 980 nm or below 980 nm.

[0036] In a possible implementation manner of the present application, the crystalline silicon is columnar crystalline silicon, and the first end of the columnar crystalline silicon and the second end of the first optical fiber are fused together under the action of arc discharge heating of a fusion splicer to form the ablation probe.

[0037] Compared with the prior art, the present application has the following beneficial effects:

[0038] The laser ablation device proposed in the present application includes a first optical fiber and crystalline silicon. Among them, the first end of the first optical fiber is used to dock with the output end of a laser light source, and the second end is used to dock with the crystalline silicon to form an ablation probe. When the ablation probe enters the lesion area, since the crystalline silicon is connected to the second end of the first optical fiber, and the first end of the first optical fiber can transmit the light output by the laser light source to the second end of the first optical fiber, the crystalline silicon can accordingly convert the light transmitted by the second end of the first optical fiber into heat energy. That is, the conversion from light energy to heat energy is completed on the crystalline silicon. Then, since the crystalline silicon has penetrated into the lesion area, the converted heat energy can be conducted to the lesion tissue, thereby realizing laser ablation of the lesion tissue.

[0039] The ablation probe manufactured using the photothermal effect can convert the absorbed light energy into heat energy, and directly conduct the temperature of the crystalline silicon to the lesion tissue by contacting the crystalline silicon with the lesion tissue, without relying on the conversion of light energy by the lesion tissue itself. Therefore, the lesion ablation efficiency and the lesion ablation effect are not affected by light scattering. Since the melting point of crystalline silicon is 1400 degrees Celsius, the ablation probe can withstand high temperatures, and the maximum temperature can reach above one thousand degrees Celsius, and it can gather relatively high heat to raise the temperature of the lesion tissue. For example, by cooperating with a laser light source, it can achieve instantaneous evaporation of the moisture in the tumor tissue, causing the cell membrane of the tumor cells to rupture, thereby realizing the ablation of the tumor tissue, and further greatly shortening the operation time of the tumor ablation surgery. In addition, by virtue of the photothermal conversion effect of the crystalline silicon connected to the second end of the first optical fiber, the heat can be quickly transferred to the deep lesion tissue, and the penetration depth is greater than the penetration depth of the laser in human tissue. Therefore, this device can not only treat superficial lesion tissues, but also ablate deep lesion tissues. In addition, by cooperating with the laser light source, because the crystalline silicon can reach a transient high temperature in the ablation probe and the heating time is short (it can reach the nanosecond or picosecond level), this function of locally rapid temperature rise can immediately damage the lesion tissue, and the heat does not have enough time to spread from the tumor area to the surrounding healthy tissues. Therefore, it can not only achieve the expected ablation target for the lesion tissue, but also greatly reduce the risk of damage to the healthy tissues. Brief Description of the Drawings

[0040] In order to more clearly illustrate the technical solutions in the embodiments of the present application or the prior art, the following will briefly introduce the drawings required for use in the description of the embodiments or the prior art. Obviously, the drawings in the following description are only some embodiments of the present application. For those of ordinary skill in the art, without creative efforts, other drawings can also be obtained based on these drawings.

[0041] Figure 1 An exemplary structural diagram of the laser ablation device provided by an embodiment of the present application;

[0042] Figure 2 A schematic diagram of the docking effect of the laser ablation device and a laser light source;

[0043] Figure 3 A simple effect diagram of the docking of the laser ablation device provided by an embodiment of the present application and multiple laser light sources;

[0044] Figure 4 A schematic diagram of establishing an optical path between the second end of the optical switch and one of the first ends of the optical switch;

[0045] Figure 5 A schematic diagram of establishing an optical path between the second end of the optical switch and the other first end of the optical switch;

[0046] Figure 6 Schematic structural diagram of an ablation probe for fiber optic connection provided by an embodiment of the present application;

[0047] Figure 7 Another exemplary structural diagram of a laser ablation device provided by an embodiment of the present application;

[0048] Figure 8 Yet another exemplary structural diagram of a laser ablation device provided by an embodiment of the present application;

[0049] Figure 9 Still another exemplary structural diagram of a laser ablation device provided by an embodiment of the present application. Detailed implementation manners

[0050] Currently, the method of directly inserting an optical fiber into a tumor to ablate the tumor can, although to some extent ablate the tumor tissue, but the effect is not ideal. This is because the light transmitted by the optical fiber is scattered more by the remaining tumor tissue with a rough surface after eliminating a part of the tumor tissue, resulting in the light transmitted by the optical fiber not being effectively concentrated on the remaining tumor tissue. It is difficult for the tumor tissue to quickly accumulate heat, and thus it is also difficult to quickly heat up to the temperature required to ablate the tumor tissue, and both the tumor ablation effect and efficiency are affected. In addition, the temperature of the tumor tissue rises slowly, but the surrounding healthy tissues are likely to be damaged unnecessarily due to the rising temperature. Moreover, the laser has low penetrability and poor ablation effect on deep tumor tissues.

[0051] After research, the inventor proposes a laser ablation device that can be used for laser ablation of lesion tissues in a medical scenario. In this device, crystalline silicon is connected to one end of an optical fiber to form an ablation probe. After the ablation probe contacts the lesion tissue, through the photothermal conversion function of the crystalline silicon, the heat of the crystalline silicon is directly conducted to the lesion tissue, regardless of the roughness of the surface of the lesion tissue. Thus, a rapid and efficient ablation effect on the lesion tissue can be achieved. This laser ablation device can be applied to superficial lesion tissues, and it can also ablate deep lesion tissues due to the penetrability of heat. Therefore, its applicability is wider. The rapid accumulation and transfer of heat by the crystalline silicon avoid the damage to healthy tissues caused by the long-term heating, and on the premise of realizing laser ablation of lesion tissues, it better protects the surrounding healthy tissues.

[0052] In order to enable those skilled in the art to better understand the solution of the present application, the technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present application. Obviously, the described embodiments are only a part of the embodiments of the present application, rather than all of the embodiments. Based on the embodiments in the present application, all other embodiments obtained by those of ordinary skill in the art without making creative efforts shall fall within the protection scope of the present application.

[0053] Example 1:

[0054] Figure 1 This is an exemplary structural diagram of the laser ablation device provided by the embodiments of the present application. As Figure 1 shown, the laser ablation device 10 includes a first optical fiber 11 and a crystalline silicon 12. Among them, the first end 11a of the first optical fiber 11 is used to dock with the output end of a laser light source, and the second end 11b of the first optical fiber 11 is used to dock with the crystalline silicon 12 to form an ablation probe. The ablation probe is as Figure 1 shown by the dotted line range in

[0055] In a medical scenario, when the laser ablation device 10 is in use, the ablation probe needs to be inserted into the lesion area. When the ablation probe enters the lesion area, the crystalline silicon 12 is used to convert the light transmitted by the second end 11b of the first optical fiber 11 into heat energy, and conduct the heat energy to the lesion tissue to perform laser ablation on the lesion tissue.

[0056] Specifically, the light energy converted by the crystalline silicon 12 comes from the laser light source docked with the first end 11a of the first optical fiber 11. To meet the ablation requirements for lesion tissue in a medical scenario, combined with the specific state of the lesion tissue or the specific treatment plan of medical workers, the first optical fiber of the laser ablation device can be docked with one type of laser light source or multiple different types of laser light sources. The effect of the laser ablation device docked with one laser light source can be referred to Figure 2 .

[0057] Figure 2 In

[0058] In a possible implementation manner of the embodiments of the present application, the laser light source 20 is a continuous laser. Thus, the laser light source 20 can continuously heat up the crystalline silicon 12 of the ablation probe of the laser ablation device 10 in the working mode of continuously emitting laser to achieve the purpose of ablating a large range (large size) of lesion tissue.

[0059] In another possible implementation manner of the embodiment of the present application, the laser light source 20 is a pulsed laser. Thus, the laser light source 20 can, in the pulsed mode, cause the temperature of the crystalline silicon 12 of the ablation probe of the laser ablation device 20 to rise extremely rapidly to achieve the purpose of ablating the diseased tissue. As the laser light source 20, the pulsed laser, due to its pulsed working mode, can generate high-power light energy in a short time, the continuous heating time can be very short, and it is easy to control. Coupled with the functions of the crystalline silicon 12 to withstand high temperatures and convert light into heat, it can precisely ablate small-scale (small-sized) diseased tissues, or specifically ablate the remaining small part of the diseased tissue. Specifically, the diseased tissue can be eliminated bit by bit, so as to achieve the purpose of precisely ablating the diseased tissue.

[0060] In addition to Figure 2 the laser light source docking method shown, the present application can also achieve the configuration selection of various types of laser light sources through a switch control element. This will be described in conjunction with Embodiment 2 below.

[0061] Example 2:

[0062] In addition to the structural components introduced in Embodiment 1, the laser ablation device may further include: a switch control element and an N×1 optical switch. Wherein, N is an integer greater than 1, for example, N = 2 or N = 3, etc. The optical switch can be selected according to actual needs, and the value of N is not limited here. The N×1 optical switch includes N first ends and one second end, where the N first ends are respectively used to dock the output ends of N different types of laser light sources, and the second end of the optical switch is used to dock the first end of the first optical fiber. The switch control element is used to control a light path to be formed between the second end of the optical switch and one of the first ends of the optical switch. Correspondingly, when a light path is formed between the second end of the optical switch and a certain first end of the optical switch, a light path cannot be formed between the second end and the other first ends of the optical switch at the same time.

[0063] Next, in conjunction with Figures 3 to 5 , taking the optical switch as a 2×1 structure with two first ends and one second end as an example, this implementation manner will be introduced.

[0064] Figure 3 FIG. is a simple effect diagram of the laser ablation device provided in the embodiment of the present application docking with multiple laser light sources. Figure 3 Highlights the switch control element 13 and the 2×1 optical switch 14. The dotted connection line between the switch control element 13 and the optical switch 14 represents the control effect of the switch control element 13 on the optical switch 14.

[0065] In Figure 3In this case, the switch control element 13 and the optical switch 14 are separately shown. In other possible implementation manners, the switch control element 13 and the optical switch 14 can also be integrated into an integrated structure. The essence of the optical switch 14 is an optical path conversion device, and the optical switch 14 can be implemented by various technologies. For example, the optical switch 14 can be a mechanical optical switch, a thermo-optical switch, an acousto-optical switch, an electro-optical switch, a magneto-optical switch, a liquid crystal optical switch, a MEMS optical switch, etc. In the embodiments of the present application, a suitable type of optical switch can be selected according to specific usage requirements to perform optical path matching with the first optical fiber and the laser light source. Due to the diversity of the optional types of the optical switch 14, correspondingly, the switch control element 13 can also be diverse, and its control mechanism only needs to be matched with the optical switch. Therefore, the type and principle of the switch control element 13 are not limited herein.

[0066] Figure 3 In this case, two different types of laser light sources are shown, which are: a continuous laser 20a and a pulsed laser 20b. Figure 3 In this case, the laser travels from the left to the right and finally reaches the ablation probe at the rightmost end.

[0067] Figure 3 Three ports of the optical switch 14 are shown, which are two first ends 14a and 14b, and a second end 14c. Among them, the two first ends 14a and 14b can be understood as optical input ends, and one second end can be understood as an optical output end.

[0068] The two first ends 14a and 14b are respectively docked with the output end of the continuous laser 20a and the second end of the pulsed laser 20b through two second optical fibers 30a and 30b. As Figure 3 shown, one end of the second optical fiber 30a is connected to the output end of the continuous laser 20a, and the other end is connected to one first end 14a of the optical switch 14. One end of the second optical fiber 30b is connected to the output end of the pulsed laser 20b, and the other end is connected to the other first end 14b of the optical switch 14.

[0069] In practical applications, the switch control element 13 can control the second end 14c of the optical switch 14 to establish an optical path with the first end 14a of the optical switch 14, or control the second end 14c of the optical switch 14 to establish an optical path with the other first end 14b of the optical switch 14 according to the size of the remaining ablation area of the lesion tissue, and / or according to the distance between the remaining ablation area of the lesion tissue and the adjacent healthy tissue.

[0070] For example, if the size of the remaining ablation area of the lesion tissue is greater than a preset size threshold, the switch control element 13 is used to control the second end 14c of the optical switch 14 to be connected to the first end 14a of the optical switch 14 that is docked with the continuous laser 20a. Regarding the light energy flow direction in this implementation manner, reference can be made to Figure 4As shown by the arrow in the figure. If the size of the remaining ablation area of the lesion tissue is less than or equal to the preset size threshold, the switch control element 13 is used to control the second end 14c of the optical switch 14 to be connected to the first end 14b of the optical switch 14 docking the pulsed laser 20b. Regarding the light energy flow direction in this implementation method, reference can be made to Figure 5 As shown by the arrow in the figure.

[0071] In another example, according to the distance between the remaining ablation area of the lesion tissue and the adjacent healthy tissue and the size of the remaining ablation area of the lesion tissue, these two factors jointly determine the type of laser light source to be used. In this example, the distance between the remaining ablation area of the lesion tissue and the adjacent healthy tissue is a higher-priority consideration factor compared to the size of the remaining ablation area of the lesion tissue, so as to better protect the healthy tissue while achieving lesion ablation. The implementation of this example will be introduced below.

[0072] If the distance between the remaining ablation area and the adjacent healthy tissue is less than the preset distance, the switch control element 13 is used to control the second end 14c of the optical switch 14 to be connected to the first end of the optical switch 14 docking the continuous laser 20a. That is, if the distance between the remaining ablation area and the adjacent healthy tissue is less than the preset distance, regardless of the size of the remaining ablation area of the lesion tissue, the optical switch 14 is controlled to use the continuous laser 20a as the laser light source providing light energy.

[0073] In this implementation scenario, by using the continuous laser 20a as the laser light source, the lesion tissue close to the healthy tissue is heated and ablated, avoiding the temperature of the healthy tissue being affected by the instantaneous high-temperature heating of the pulsed laser while inactivating the tumor. When the continuous laser 20a provides light energy, the ablation probe only needs to reach the lowest temperature for inactivating the lesion tissue, so as to ensure that the temperature of the ablation probe is not too high. As an example, the lowest temperature for inactivating the lesion tissue is 60°C. In some possible implementation methods, the temperature control can also be combined with the temperature sensitivity of the healthy tissue adjacent to the lesion tissue. For example, if the lesion tissue and the healthy tissue grow together, or the lesion tissue is close to an important organ or nerve, and the adjacent organ is the eyeball, the probe temperature is set not to exceed 60°C; if the temperature sensitivity of the healthy organ is relatively low, the probe temperature can be set not to exceed 65°C.

[0074] If the distance between the remaining ablation area and the adjacent healthy tissue is greater than or equal to a preset distance, the switch control element 13 is specifically configured to control the second end 14c of the optical switch 14 to establish an optical path with one of the first ends (14a or 14b) of the optical switch 14 according to the size of the remaining ablation area of the diseased tissue. That is, if the distance between the remaining ablation area and the adjacent healthy tissue is greater than or equal to the preset distance, the laser light source is selected specifically considering the size of the remaining ablation area of the diseased tissue, whether it is large or small.

[0075] Specifically, if the distance between the remaining ablation area and the adjacent healthy tissue is greater than or equal to the preset distance, and the size of the remaining ablation area is greater than the preset size threshold, the switch control element 13 is specifically configured to control the second end 14c of the optical switch 14 to be connected to the first end of the continuous laser 20a docked with the optical switch 13.

[0076] If the distance between the remaining ablation area and the adjacent healthy tissue is greater than or equal to the preset distance, and the size of the remaining ablation area is less than or equal to the preset size threshold, the switch control element 13 is configured to control the second end 14c of the optical switch 14 to be connected to the first end of the pulsed laser 20b docked with the optical switch 13.

[0077] In the above example, the preset distance is used as a reference to measure the relative distance between the ablation area of the diseased tissue and the adjacent healthy tissue. And laser light source selection schemes in the cases of relatively close distance and relatively far distance are given. In practical applications, the preset distance can be set in combination with various factors such as the growth mechanisms of the diseased tissue and the healthy tissue, the temperature sensitivity of the healthy tissue, and the attributes of the diseased tissue, or it can also be set as a default value. Here, the value of the preset distance is not limited.

[0078] In some of the above examples, it involves using a preset size threshold to distinguish the usage scenarios of two different types of laser light sources. For ease of understanding, taking the diseased tissue as a tumor tissue as an example, the usage scenarios of different types of laser light sources are described below.

[0079] (1) When real-time ablation of a relatively large tumor is to be performed, the ablation probe of the laser ablation device provided in the embodiment of the present application can be attached to or inserted into the tumor. By controlling the optical switch, the laser light source is switched to the continuous laser, so that the continuous light energy output by the continuous laser can be transmitted to the ablation probe, and the photothermal conversion is completed by the crystalline silicon of the ablation probe.

[0080] Under the action of continuous laser, the temperature of the ablation probe can reach an appropriate temperature (such as 60 degrees Celsius) and be maintained for a long time. At this time, the temperature that the ablation probe needs to maintain should not be too high, otherwise the ablation probe maintaining a high temperature for a long time will cause unnecessary heat conduction - heat is transferred from the tumor tissue to healthy organs and damages the healthy organs. Through limited heat conduction, the crystalline silicon transfers heat to the tumor tissue, raising the temperature of the tumor tissue and killing the tumor.

[0081] (2) When ablating a large-volume tumor, when most of the tumor tissue has been ablated and only a small part of the tumor remains to be ablated, since the remaining tumor tissue is small, using continuous laser to keep the ablation probe heating for a long time may cause heat to be transferred from the ablation probe to the tumor tissue first, and then to healthy organs, thus affecting the healthy organs. At this time, in the technical solution of the present application, the laser source can be switched to a pulsed laser by controlling the optical switch.

[0082] When the pulsed light is transmitted to the ablation probe, due to the very high peak power of the pulsed light, the ablation probe can reach a high temperature instantly (up to more than one thousand degrees Celsius), and the pulse width of the pulsed light is extremely small (as small as femtosecond level at least), so the probe can only maintain a high temperature for an extremely short time. When the light pulse ends, the ablation probe will no longer receive light energy and will no longer heat up and conduct heat to the contacted area.

[0083] Since the tumor tissue is heated by high temperature in an extremely short time, the water in the tumor tissue will evaporate rapidly, causing the cell membrane to rupture and tissue ablation. This extreme local temperature rise may immediately damage the tumor tissue. At the same time, since heat conduction is a relatively slow process, especially in biological tissues. Therefore, within this extremely short time when the pulsed light lasts, the heat does not have enough time to spread from the tumor area to the surrounding healthy tissues through the conduction mechanism, which will greatly reduce the risk of damage to healthy tissues during ablation.

[0084] (3) When treating small-volume tumors or very early tiny tumors, the ablation probe can be attached to or inserted into the tumor, and the light source can be adjusted to pulsed light. Relying on the pulsed light to enable the ablation probe to achieve instant heating in an ultra-short time, gradually inactivate small-volume tumors or very early tiny tumors (such as coagulation, vaporization or carbonization).

[0085] The above (1) corresponds to the case of using continuous light through the optical switch, see Figure 4 ; (2) and (3) correspond to the case of using pulsed light through the optical switch, see Figure 5 .

[0086] In order to better integrate the laser ablation device with the medical scenario and enable the laser ablation device to control the ablation process through sensitive perception, the present application also proposes to provide a photodetector in the laser ablation device and endow the ablation probe with temperature sensing capabilities. The following describes this implementation in conjunction with embodiments.

[0087] Example 3:

[0088] In the laser ablation device provided by the embodiment of the present application, in addition to including the first optical fiber and crystalline silicon mentioned in the above embodiments, it further includes a first photodetector. Moreover, the first optical fiber is divided into sections according to functions, and is specifically divided into an optical fiber section for conduction (referred to as the first conduction optical fiber section) and an optical fiber section for detection (referred to as the first detection optical fiber section). For ease of understanding, the following describes in conjunction with the accompanying drawings.

[0089] Figure 6 It is a schematic structural diagram of an ablation probe with optical fiber connection provided by the embodiment of the present application. As Figure 6 shown, the first optical fiber 11 includes a first conduction optical fiber section 111 and a first detection optical fiber section 112. Among them, the first end 111a of the first conduction optical fiber section 111 is used to dock with the output end of the laser light source. Therefore, it can also be regarded as the first end of the first optical fiber 11 in this embodiment. The second end 111b of the first conduction optical fiber section 111 is used to dock with the first end 112a of the first detection optical fiber section 112. The second end 112b of the first detection optical fiber section 112 is used to dock with the crystalline silicon 12 to form an ablation probe with temperature detection capabilities (as shown by the dotted line area in Figure 6 ). Therefore, the second end 112b of the first detection optical fiber section 112 can also be regarded as the second end of the first optical fiber 11 in this embodiment.

[0090] Although both the first detection optical fiber section 112 and the first conduction optical fiber section 111 belong to the basic form of optical fibers, there are subtle differences in their structures. The first conduction optical fiber section 111 has a conventional core and cladding structure. The first detection optical fiber section 112 can specifically be a fiber grating, which is a diffraction grating formed by axially periodic modulation of the refractive index of the core. The grating optical fiber has the advantages of small volume, small fusion loss, and full compatibility with optical fibers. Moreover, its resonant wavelength is relatively sensitive to temperature changes. Therefore, it can be used as a temperature sensor in the laser ablation device proposed by the technical solution of the present application.

[0091] In the laser ablation device provided by the embodiment of the present application, the fiber grating essentially forms a narrowband reflection filter or mirror in the core. When a beam of broadband light passes through the fiber grating, the wavelength that satisfies the Bragg condition of the fiber grating will be reflected, and the remaining wavelengths will continue to be transmitted through the fiber grating.

[0092] In the laser ablation device provided by the embodiment of the present application, the first detection optical fiber section 112 can be connected to a first photodetector (not shown Figure 6 in the figure). The first detection optical fiber section 112 is used to receive the laser from the second end 111b of the first conduction optical fiber section 111, transmit it to the crystalline silicon 12, and reflect the laser matching the central wavelength of the first detection optical fiber section 112 to the first photodetector. The first photodetector is used to detect the temperature of the ablation probe according to the change in the central wavelength of the laser reflected by the first detection optical fiber section 112. In a specific implementation, the first photodetector can be a fiber grating demodulator or a spectrometer.

[0093] In practical applications, through the mutual cooperation of the crystalline silicon, the first detection grating section, and the first photodetector, the laser ablation device has the ability to sense the temperature and temperature change of the ablation probe. When ablating the lesion tissue, through the ability of the laser ablation device to sense the temperature of the ablation probe, it can assist in precisely controlling the temperature of the ablation probe. This can avoid situations where the temperature of the ablation probe is too low or too high, resulting in an unsatisfactory ablation effect on the lesion tissue or further damage to healthy tissues.

[0094] Example 4:

[0095] In the laser ablation device provided by the embodiment of the present application, in addition to including the components mentioned in the above-mentioned Embodiment 3, it further includes: a second photodetector, an optical coupler, and a third optical fiber.

[0096] Figure 7 This is another example structural diagram of the laser ablation device provided by the embodiment of the present application. In Figure 7 the shown laser ablation device, it includes an optical coupler 40, a first optical fiber (including a first conduction optical fiber section 111 and a first detection optical fiber section 112), a third optical fiber (including a second conduction optical fiber section 111' and a second detection optical fiber section 112'), and crystalline silicon 12.

[0097] As Figure 7 shown, the optical coupler 40 includes an input end 40a, a first output end 40b, and a second output end 40c. The input end 40a of the optical coupler 40 is used to dock with the output end of the laser light source 20, and the first output end 40b and the second output end 40c are respectively used to dock with the first end of the first conduction optical fiber section 111 (which can be understood as Figure 7 the left end of the first conduction optical fiber section 111 in the figure) and the first end of the second conduction optical fiber section 111' in the third optical fiber (which can be understood as Figure 7 the left end of the second conduction optical fiber section 111' in the figure). The second end of the second conduction optical fiber section 111' (which can be understood as Figure 7The right end of the second optical fiber section 111' for conduction (in the middle) is used to dock with the first end of the second detection optical fiber section 112' in the third optical fiber (which can be understood as Figure 7 the left end of the second detection optical fiber section 112' in the middle), and the second end of the second detection optical fiber section (which can be understood as Figure 7 the right end of the second detection optical fiber section 112' in the middle) is used to contact the lesion tissue to form a lesion temperature sensing probe.

[0098] After the laser is emitted by the laser light source 20, it is conducted through the optical fiber to the optical coupler 40, and is emitted from the first output end 40b and the second output end 40c of the optical coupler 40 respectively, and is conducted to the ablation probe and the lesion temperature sensing probe through the first optical fiber and the third optical fiber respectively. In Figure 7 the structure shown, the first optical fiber and the crystalline silicon present a series structure. The formed ablation probe and the lesion temperature sensing probe present a parallel structure. After the light is transmitted to the optical coupler 40, a part of it is transmitted to the branch where the ablation probe is located, and the other part is transmitted to the branch where the lesion temperature sensing probe is located. The splitting ratio of the two branches depends on the selection of the optical coupler 40. For example, if the optical coupler is a 1:1 splitter, it means that 50% of the laser received by the optical coupler 40 is output from the first output end 40b, and the other 50% is output from the second output end 40c.

[0099] Combined with the above introduction of the embodiments of the present application, in the embodiments of the present application, the temperature sensing ability of the laser ablation device is not only reflected in the ablation probe, but also reflected in the lesion temperature sensing probe realized based on the second detection optical fiber section 112'. When the laser ablation device is working, the lesion temperature sensing probe also needs to be inserted into the lesion tissue.

[0100] The second detection optical fiber section 112' is connected to a second photodetector ( Figure 7 not shown in the middle). The second detection optical fiber section 112' is used to receive the laser from the second end of the second conduction optical fiber section 111', transmit it to the contacted lesion tissue, and reflect the laser matching the central wavelength of the second detection optical fiber section 112' to the second photodetector. The second photodetector is used to detect the temperature of the lesion tissue according to the change of the central wavelength of the laser reflected by the second detection optical fiber section 112'.

[0101] In the laser ablation device, the second detection optical fiber section 112' is in direct contact with the tumor tissue and its temperature is detected. By observing the change of the central wavelength of the reflected light detected by the second photodetector, the temperature change of the detected tumor tissue can be measured. This temperature change can guide the temperature control of the ablation probe or the selection and switching of the laser light source. And by detecting the temperature of the lesion tissue, it can also be known whether the temperature rise of the lesion tissue meets the expectation and whether the purpose of ablating the lesion tissue can be achieved.

[0102] In practical applications, the second fiber optic section 112' for detection can also use fiber Bragg gratings. The working principle of fiber Bragg gratings has been specifically introduced in Embodiment 3 above and will not be elaborated here. The second optical detector can be a fiber Bragg grating demodulator or a spectrometer.

[0103] Based on Figure 7 , the embodiment of the present application further provides a structure of a laser ablation device including a circulator. For details, see Figure 8 . Figure 8 shows the first optical detector 50 and the second optical detector 60. In addition, in Figure 8 In another structure of the laser ablation device shown, it further includes: a first circulator 70 and a second circulator 80. From Figure 8 the optical paths of the three channels respectively docked by the first circulator 70 and the second circulator 80, it can be seen that the first circulator 70 and the second circulator 80 each have three ports, which are called the first port, the second port, and the third port for convenience of description. The first port is docked to the optical coupler 40, the second port is docked to the probe (ablation probe or lesion temperature sensing probe), and the third port is docked to the optical detector.

[0104] As shown in Figure 8 , the first port and the second port of the first circulator 70 are provided on the first fiber optic section 111 for conduction, and the third port of the first circulator 70 is connected to the input end of the first optical detector 50; the first port and the second port of the second circulator 80 are provided on the second fiber optic section 111' for conduction, and the third port of the second circulator 80 is connected to the input end of the second optical detector 60.

[0105] Since the characteristic of the circulator is that the light wave incident from a certain port can only be transmitted to the next port in a determined direction sequence, the optical path can be effectively isolated. Specifically, in the embodiment of the present application, the next port of the first port of the same circulator is the second port, and the next port of the second port is the third port. In this way, the light wave entering from the first port of the first circulator 70 exits from the second port, and the light wave incident from the second port exits from the third port and finally enters the first optical detector 50. The light wave entering from the first port of the second circulator 80 exits from the second port, and the light wave incident from the second port exits from the third port and finally enters the second optical detector 60. The use of the circulator enables bidirectional multiplexing of some sections of the first optical fiber and the third optical fiber.

[0106] In the above Embodiment 4, Figure 7 and Figure 8All show a single laser light source. Combining the introduction in Embodiment 2, in the laser ablation device, a light switch can also be configured to achieve switching selection of multiple laser light sources. The following will be introduced in combination with Embodiment 5.

[0107] Example 5:

[0108] In the embodiment of the present application, the laser ablation device not only has Figure 7 or Figure 8 the shown structural composition, but also further includes an N×1 structure optical switch and a switch control element. For the introduction of the optical switch and the switch control element, please refer to the corresponding content in Embodiment 2, which will not be elaborated here. Taking N = 2 as an example, in combination with Figure 9 the display, another example structure of the laser ablation device will be described.

[0109] As Figure 9 shown, on the basis of the structure shown in Figure 8 , the laser ablation device further includes a 2×1 structure optical switch 14 and a switch control element 13. The two first ends of the optical switch 14 are respectively connected to the output ends of the continuous laser 20a and the pulsed laser 20b through two second optical fibers 30a and 30b, and the second end of the optical switch is connected to the input end of the optical coupler 40. The switch control element 13 is used to control the second end of the optical switch 14 to establish an optical path with one of the first ends of the optical switch 14 according to the size of the remaining ablation area of the lesion tissue. For the selection and establishment of the optical path, reference can be made to Figure 4 and Figure 5 the shown light energy flow direction, which will not be elaborated here.

[0110] In the embodiment of the present application, the laser ablation device not only has the ability to sense the temperature of the lesion and the ability to sense the temperature change of the ablation probe, but also has the ability to switch and select the laser light source. Therefore, the laser ablation device has a wide application prospect in the medical scenario, can well be applicable to the ablation target of various types and sizes of lesion tissues, and avoids damaging healthy tissues. In addition, through crystalline silicon, heat can be conducted to the deep lesion tissue, and the deep lesion can be eliminated more thoroughly, reducing the hidden danger of incomplete lesion elimination and subsequent spread and growth.

[0111] In a possible implementation manner, if it is detected by the first photodetector 50 that the temperature of the ablation probe fails to reach the expectation and the temperature deviation from the expected temperature is large, under the condition that the used laser light source is the pulsed laser 20b, the parameters of the pulsed laser 20b can be controlled to adjust the light wave emitted by the pulsed laser 20b. Thus, the temperature of the ablation probe approaches the expected temperature.

[0112] Specifically, the laser ablation device further includes: a controller, the output end of the controller is connected to the control end of the pulsed laser 20b, and the input end of the controller is connected to the output end of the first photodetector 50. The controller is configured to adjust the current optical pulse parameters of the pulsed laser 20b based on the correspondence between the optical pulse parameters and the heat when an optical path is established between the second end of the optical switch 14 and the first end of the pulsed laser 20b docked by the optical switch 14, and the deviation between the temperature detected by the first photodetector 50 and the target control temperature (i.e., the expected temperature) exceeds the preset deviation range, so as to reduce the deviation. For example, if the temperature detected by the first photodetector 50 is higher than the target control temperature and the deviation exceeds the preset deviation range, the optical pulse width is shortened or the optical power is reduced; if the temperature detected by the first photodetector 50 is lower than the target control temperature and the deviation exceeds the preset deviation range, the optical pulse width is increased or the optical power is increased.

[0113] By connecting the photodetector and the laser light source, the controller can, on the one hand, sense the temperature of the ablation probe, and on the other hand, effectively control the laser light source. Since the heat converted by the ablation probe comes from the laser light source, the laser ablation device provided by the embodiments of the present application realizes the closed-loop control of the laser light source based on the principles of photothermal conversion, heat conduction, and temperature sensing, improves the precise control effect of the temperature of the ablation probe, and thus can be effectively applied in medical scenarios to eliminate human diseased tissue.

[0114] The controller can be a combination of some devices, such as a combination of an operational amplifier, a microcontroller, a programmable logic device, and a data acquisition and control system.

[0115] As an optional implementation manner of the above embodiments of the present application, the laser ablation device includes a plurality of spare crystalline silicon with different cross-sectional sizes. The crystalline silicon that is docked with the second end of the first optical fiber to form the ablation probe is selected from the plurality of spare crystalline silicon based on the size of the remaining ablation area of the diseased tissue. For example, if the size of the remaining ablation area of the diseased tissue is relatively large, the medical worker can select a crystalline silicon with a relatively large cross-sectional size from the plurality of spare crystalline silicon and combine it with the first optical fiber. Correspondingly, if the size of the remaining ablation area of the diseased tissue is relatively small, the medical worker can select a crystalline silicon with a relatively small cross-sectional size from the plurality of spare crystalline silicon and combine it with the first optical fiber.

[0116] It should be noted that if the cross-sectional size of the selected crystalline silicon exceeds the first preset size, the first optical fiber is a plastic optical fiber. Compared with ordinary optical fibers, plastic optical fibers have a larger cross-sectional size, and thus are also convenient for docking with crystalline silicon with a cross-sectional size exceeding the first preset size to form an ablation probe.

[0117] In the embodiments of the present application, the working wavelength band of the ablation probe is 980 nm or below 980 nm. Crystalline silicon has a strong absorption effect on light with a wavelength not exceeding 980 nm. Under the influence of the photothermal effect, crystalline silicon will absorb light energy and convert it into heat energy, so as to achieve the purpose of thermal ablation of tumor tissues.

[0118] In an alternative implementation, the crystalline silicon is columnar crystalline silicon, which is convenient for fusing with an optical fiber to form an ablation probe. The formation process of the ablation probe is introduced below:

[0119] First, one end of the polished and cut columnar crystalline silicon is bonded to an optical fiber (referred to as the fourth optical fiber for convenience) with hot melt adhesive;

[0120] Then, the fourth optical fiber attached with the columnar crystalline silicon and the first optical fiber are placed into a fusion splicer together. When the fusion splicer discharges, due to the action of arc heating, the hot melt adhesive will be melted, and the columnar crystalline silicon will fall off from the originally bonded fourth optical fiber. At the same time, the columnar crystalline silicon and the first optical fiber are fused together under the action of arc discharge heating to form an ablation probe.

[0121] If an ablation probe is made by using polydimethylsiloxane (PDMS) and an optical fiber, the manufacturing process is generally too complex, and it often takes several days to make one. The long manufacturing cycle and complex manufacturing process make it difficult to industrially prepare and popularize this type of ablation probe. In addition, the thermal decomposition temperature of PDMS is three hundred degrees Celsius, and long-term use at high temperatures will cause it to decompose. Therefore, its poor heat resistance and poor stability characteristics also affect its application in ablating diseased tissues. In addition, the rigidity of PDMS is much smaller than that of crystalline silicon, and it is very easy to deform or damage during operation.

[0122] The ablation probe made of diamond has the following defects: Due to its natural scarcity (or the complexity of artificial synthesis) and extremely high hardness, diamond requires special tools (such as laser or high-pressure high-temperature methods) for processing, which greatly increases the manufacturing difficulty and cost. The thermal expansion coefficient of diamond (~1.0 × 10⁻ 6 / K) varies greatly, which may cause mechanical structure stress problems. The wide bandgap of diamond results in low absorption in most wavelength ranges, so stronger optical power is required to achieve a similar thermal effect.

[0123] In contrast, crystalline silicon is the basic material of the semiconductor industry, with mature processes and abundant raw materials, and high-quality crystals can be manufactured at low cost. Furthermore, the cost is low, and it is easier to process into a laser ablation device. In addition, crystalline silicon is easy to cut, etch, polish, and micro-machine, and can achieve precise design. The thermal expansion coefficient of silicon (2.6 × 10⁻6 ( / K) is close to common optical fiber cladding materials, reducing the stress problem caused by thermal expansion mismatch of the thermal ablation head at high temperatures. The optical band gap and optical properties of crystalline silicon are in the infrared range, so it is more suitable for thermal conversion.

[0124] The above compares and analyzes crystalline silicon and diamond materials from multiple aspects, including material cost and processing difficulty, absorption efficiency for specific wavelengths, compatibility of thermal expansion coefficients, and complexity and compatibility of machining. It is found that using crystalline silicon as the ablation probe proposed in the technical solution of this application has outstanding advantages. In addition, from the perspectives of high temperature resistance and stability, crystalline silicon also has a better application prospect compared with PDMS, with lower implementation difficulty and easier processing.

[0125] The above is only a specific implementation manner of this application, but the protection scope of this application is not limited thereto. Any changes or substitutions that can be easily thought of by those skilled in the art within the technical scope disclosed in this application should be covered by the protection scope of this application. Therefore, the protection scope of this application should be subject to the protection scope of the claims.

Claims

1. A laser ablation device, characterized in that, Comprising: A first optical fiber and crystalline silicon; wherein, the first end of the first optical fiber is used to dock with the output end of a laser light source, and the second end of the first optical fiber is used to dock with the crystalline silicon to form an ablation probe; When the ablation probe enters the lesion area, the crystalline silicon is used to convert the light transmitted by the second end of the first optical fiber into heat energy, and conduct the heat energy to the lesion tissue to perform laser ablation on the lesion tissue; The crystalline silicon is columnar crystalline silicon, and the first end of the columnar crystalline silicon and the second end of the first optical fiber are fused together under the action of arc discharge heating of a fusion splicer to form the ablation probe.

2. The device according to claim 1, wherein The device further comprises: a switch control element and an N×1 optical switch, where N is an integer greater than 1, the optical switch includes N first ends and one second end, wherein, the N first ends are respectively used to dock with the output ends of N different types of laser light sources, and the second end of the optical switch is used to dock with the first end of the first optical fiber; The switch control element is used to control a light path to be formed between the second end of the optical switch and one of the first ends of the optical switch.

3. The device according to claim 2, wherein The optical switch is a 2×1 structure, and the two first ends of the optical switch are respectively docked with the output ends of a continuous laser and a pulsed laser through two second optical fibers; The switch control element is used to control a light path to be established between the second end of the optical switch and one of the first ends of the optical switch according to the size of the remaining ablation area of the lesion tissue, and / or, the distance between the remaining ablation area and adjacent healthy tissue.

4. The device according to claim 3, characterized in that, If the size of the remaining ablation area is greater than a preset size threshold, the switch control element is used to control the second end of the optical switch to be connected to the first end of the optical switch that docks with the continuous laser; if the size of the remaining ablation area is less than or equal to the preset size threshold, the switch control element is used to control the second end of the optical switch to be connected to the first end of the optical switch that docks with the pulsed laser.

5. The device according to claim 3, characterized in that, If the distance between the remaining ablation area and adjacent healthy tissue is less than a preset distance, the switch control element is used to control the second end of the optical switch to be connected to the first end of the optical switch that docks with the continuous laser; if the distance between the remaining ablation area and adjacent healthy tissue is greater than or equal to the preset distance, the switch control element is specifically used to control a light path to be established between the second end of the optical switch and one of the first ends of the optical switch according to the size of the remaining ablation area of the lesion tissue.

6. The device according to claim 5, characterized in that If the distance between the remaining ablation area and adjacent healthy tissue is greater than or equal to the preset distance, and the size of the remaining ablation area is greater than a preset size threshold, the switch control element is specifically used to control the second end of the optical switch to be connected to the first end of the optical switch that docks with the continuous laser; if the distance between the remaining ablation area and adjacent healthy tissue is greater than or equal to the preset distance, and the size of the remaining ablation area is less than or equal to the preset size threshold, the switch control element is used to control the second end of the optical switch to be connected to the first end of the optical switch that docks with the pulsed laser.

7. The device according to claim 1, characterized in that The device further includes: a first photodetector; The first optical fiber includes a first optical fiber section for conduction and a first optical fiber section for detection; the first end of the first optical fiber section for conduction is used to dock with the output end of the laser light source, the second end of the first optical fiber section for conduction is used to dock with the first end of the first optical fiber section for detection, and the second end of the first optical fiber section for detection is used to dock with the crystalline silicon to form an ablation probe with temperature detection ability; The first optical fiber section for detection is connected to the first photodetector; the first optical fiber section for detection is used to receive the laser from the second end of the first optical fiber section for conduction, transmit it to the crystalline silicon, and reflect the laser matching the central wavelength of the first optical fiber section for detection to the first photodetector; The first photodetector is used to detect the temperature of the ablation probe according to the change of the central wavelength of the laser reflected by the first optical fiber section for detection.

8. The device according to claim 7, characterized in that, The device further includes: a second photodetector, an optical coupler, and a third optical fiber; the optical coupler includes an input end, a first output end, and a second output end; the input end of the optical coupler is used to dock with the output end of the laser light source, and the first output end and the second output end are respectively used to dock with the first end of the first optical fiber section for conduction and the first end of the second optical fiber section for conduction in the third optical fiber; The second end of the second optical fiber section for conduction is used to dock with the first end of the second optical fiber section for detection in the third optical fiber, and the second end of the second optical fiber section for detection is used to contact the lesion tissue to form a lesion temperature sensing probe; The second optical fiber section for detection is connected to the second photodetector; the second optical fiber section for detection is used to receive the laser from the second end of the second optical fiber section for conduction, transmit it to the contacted lesion tissue, and reflect the laser matching the central wavelength of the second optical fiber section for detection to the second photodetector; The second photodetector is used to detect the temperature of the lesion tissue according to the change of the central wavelength of the laser reflected by the second optical fiber section for detection.

9. The device according to claim 8, characterized in that, The device further includes: a first circulator and a second circulator; the first circulator and the second circulator are each provided with a first port, a second port, and a third port; The first port and the second port of the first circulator are arranged on the first optical fiber section for conduction, and the third port of the first circulator is connected to the input end of the first photodetector; The first port and the second port of the second circulator are arranged on the second optical fiber section for conduction, and the third port of the second circulator is connected to the input end of the second photodetector.

10. The device according to claim 8, characterized in that, The device further includes: an optical switch with a 2×1 structure and a switch control element; The two first ends of the optical switch are respectively docked with the output ends of a continuous laser and a pulsed laser through two second optical fibers, and the second end of the optical switch is connected to the input end of the optical coupler; The switch control element is used to control the establishment of an optical path between the second end of the optical switch and one of the first ends of the optical switch according to the size of the remaining ablation area of the lesion tissue and / or the distance between the remaining ablation area and the adjacent healthy tissue.

11. The device according to claim 10, characterized in that, The device further includes: a controller, an output end of the controller is connected to a control end of the pulsed laser, and an input end of the controller is connected to an output end of the first photodetector; When an optical path is established between the second end of the optical switch and the first end of the pulsed laser docked by the optical switch, and the deviation between the temperature detected by the first photodetector and the target control temperature exceeds a preset deviation range, the controller is used to adjust the current optical pulse parameters of the pulsed laser based on the corresponding relationship between the optical pulse parameters and the heat to reduce the deviation.

12. The device according to any one of claims 8-11, characterized in that, Both the first detection optical fiber section and the second detection optical fiber section are fiber Bragg gratings; the first photodetector and the second photodetector are any one of the following: A fiber Bragg grating demodulator or a spectrometer.

13. The device according to claim 1, characterized in that, The device includes a plurality of spare crystalline silicons with different cross-sectional sizes; the crystalline silicon that docks with the second end of the first optical fiber to form an ablation probe is selected from the plurality of spare crystalline silicons based on the size of the remaining ablation area of the lesion tissue.

14. The device according to claim 13, wherein If the cross-sectional size of the selected crystalline silicon exceeds a first preset size, the first optical fiber is a plastic optical fiber.

15. The device according to claim 1, characterized in that, The working wavelength band of the ablation probe is 980 nm or below 980 nm.

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