Force-aware microinstrument

Abstract

The invention relates to the technical field of medical instruments, and provides a force sensing microscopic instrument, which comprises a shell and a medicine injection assembly, and is characterized in that the shell comprises a medicine injection needle tube, a first optical fiber and a second optical fiber; a bent needle head is arranged at the far end of the medicine injection needle tube; the first optical fiber and the second optical fiber are distributed on the periphery of the medicine injection needle tube in the length direction of the medicine injection needle tube and packaged in the shell. The first optical fiber and the second optical fiber are Bragg optical fibers and are both provided with grating areas, a plurality of grating areas are arranged on at least one of the first optical fiber and the second optical fiber at intervals, and the grating areas are used for sensing radial force borne by the medicine injection needle tube. According to the force sensing microscopic instrument, the puncture force of the medicine injection needle tube on the blood vessel can be detected only through the two Bragg optical fibers, the outer diameter of the force sensing microneedle is reduced, the force sensing microneedle can be matched with a trocar with a smaller size, and therefore damage to sclera in the retina intravenous injection operation is reduced, and the risks of bleeding, hyperplasia of tissue around an incision and retina traction are reduced.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and in particular to a force sensing microscopic device. Background Art

[0002] Retinal vein occlusion is the second most common retinal vascular disease. An effective treatment is to directly inject a sufficient dose of thrombolytic agent into the occluded retinal vein. The common clinical practice is to insert a trocar into the sclera to establish a channel for the instrument to enter the eye, illuminate the intraocular field through a fiber optic lamp, and insert the injection needle into the eye through the channel to puncture and inject drugs into the blood vessels at the fundus. Since the diameter of the retinal vein is only a few dozen microns, it is very easy to cause double puncture and damage the human eye. Therefore, accurate detection of the moment of retinal vein puncture is one of the necessary conditions to ensure the safety of the operation.

[0003] The methods used in the prior art to detect the moment of retinal vein puncture include OCT imaging-based detection methods and force-based detection methods. Among them, the force-based detection method is to arrange Bragg optical fibers on the retinal vein injection needle and detect the puncture force through the Bragg optical fibers. In the related art, three Bragg optical fibers are arranged around the circumference of the injection needle tube at an angle of 120° to each other to form a force-sensing microneedle, which can sense the two-dimensional force along the radial direction of the needle tube.

[0004] However, due to the need to ensure that the force-sensing microneedle has a certain degree of rigidity, the injection needle tube is generally made of stainless steel tube, and the current force fiber technology is limited, resulting in a large size of the force-sensing microneedle. Therefore, in clinical applications, only a trocar with a larger inner diameter can be used to establish a channel for the force-sensing microneedle to enter the sclera, or a direct incision is made on the sclera, but both will cause a large wound on the sclera, with the risk of bleeding, tissue hyperplasia around the incision, and traction of the retina. Summary of the invention

[0005] The present invention provides a force sensing microscopic instrument, which is used to solve the problem that the diameter of the force sensing microneedle used for retinal vein injection in the prior art is relatively large, resulting in a relatively large wound on the sclera in clinical practice.

[0006] The present invention provides a force sensing microscopic instrument, comprising: shell; The drug injection assembly includes a drug injection needle, a first optical fiber and a second optical fiber; a bent needle is provided at the distal end of the drug injection needle; the first optical fiber and the second optical fiber are distributed on the outer circumference of the drug injection needle along the length direction of the drug injection needle and are encapsulated in the outer shell; the first optical fiber and the second optical fiber are Bragg fibers, both of which are provided with grating areas, and at least one of the two is provided with multiple grating areas at intervals, and the grating areas are used to sense the radial force applied to the drug injection needle.

[0007] According to a force sensing microscopic instrument provided by the present invention, the first optical fiber and the second optical fiber are both provided with two grating regions spaced apart from each other, and the first optical fiber and the second optical fiber have the same structure.

[0008] According to a force-sensing microscopic instrument provided by the present invention, the injection component also includes: a potting part, the potting part is provided with a first potting channel, a second potting channel and a third potting channel, the first optical fiber is arranged in the first potting channel, the second optical fiber is arranged in the second potting channel, and the injection needle is arranged in the third potting channel.

[0009] A force sensing microscopic instrument according to the present invention further comprises: The sleeve comprises a tube seat and a straight tube, wherein the tube seat is connected to one end of the shell close to the bent needle, one end of the straight tube is penetrated through the tube seat, the potting part is penetrated through the straight tube, and the grating area is located outside the straight tube.

[0010] According to a force sensing microscopic instrument provided by the present invention, the injection needle tube comprises: a drug delivery tube and an injection needle; one end of the injection needle is inserted into the drug delivery tube and sealedly connected to the drug delivery tube, and the bent needle head is formed at one end of the injection needle away from the drug delivery tube.

[0011] According to a force sensing microscopic instrument provided by the present invention, the drug delivery tube is a nickel-titanium alloy tube.

[0012] A force sensing microscopic instrument according to the present invention further comprises: The drug delivery assembly includes a connector assembly, a first pressure extension tube and a transfer tube, wherein one end of the first pressure extension tube is connected to the connector assembly, and the other end is connected to the injection needle through the transfer tube, and the connector assembly is connected to one end of the shell away from the bent needle.

[0013] According to a force sensing microscopic instrument provided by the present invention, the drug delivery assembly further includes: a second pressure extension tube and a three-way valve, one end of the second pressure extension tube is connected to the three-way valve, and the other end is detachably connected to the connector assembly.

[0014] According to a force sensing microscopic instrument provided by the present invention, the adapter tube includes: a first tube body and a second tube body, the first pressure extension tube is sleeved on one end of the first tube body, the other end of the first tube body is sleeved on one end of the second tube body, and the end of the injection needle away from the bent needle is inserted into the other end of the second tube body.

[0015] According to a force sensing microscopic instrument provided by the present invention, the second tube body is provided with a first channel and a second channel connected to each other, the diameter of the second channel is larger than the diameter of the first channel, and the injection needle is inserted into the first channel.

[0016] The force sensing microscopic instrument provided by the present invention arranges the first optical fiber and the second optical fiber on the periphery of the injection needle tube, and both the first optical fiber and the second optical fiber are Bragg optical fibers, and at least one of the two optical fibers is provided with a plurality of grating regions at intervals, so that the first optical fiber and the second optical fiber have at least three grating regions in total. According to the mapping relationship between the radial force exerted on the at least three grating regions and the reflection wavelength change rate, the two-dimensional radial force exerted on the injection needle tube can be solved, so that the puncture force of the needle tip can be accurately obtained, and the precise detection of the moment of retinal vein puncture can be achieved. The force sensing microscopic instrument can detect the puncture force of the injection needle tube on the blood vessel through only two Bragg optical fibers, reduce the outer diameter of the force sensing microneedle, and adapt to a smaller size of the trocar, thereby reducing the damage to the sclera during the retinal vein injection operation, and reducing the risks of bleeding, tissue hyperplasia around the incision, and traction of the retina. BRIEF DESCRIPTION OF THE DRAWINGS

[0017] In order to more clearly illustrate the technical solutions in the present invention or the prior art, the following briefly introduces the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying creative work.

[0018] Figure 1 It is a schematic diagram of the overall structure of the force sensing microscopic instrument provided by the present invention.

[0019] Figure 2 It is a schematic diagram of the internal structure of the force sensing microscopic instrument provided by the present invention.

[0020] Figure 3 It is a partial structural schematic diagram of the drug injection component of the force sensing microscopic instrument provided by the present invention.

[0021] Figure 4 yes Figure 3 Schematic diagram of the cross section at AA.

[0022] Figure 5 It is a schematic diagram of the explosion structure of the force sensing microscopic instrument provided by the present invention.

[0023] Figure 6 It is a schematic diagram of the exploded structure of part of the force sensing microscopic instrument provided by the present invention.

[0024] Figure 7 yes Figure 6 A partial enlarged view of the part B circled in the middle.

[0025] Figure 8 yes Figure 6 A partial enlarged view of the C section circled in the middle.

[0026] Fig. 9 yes Figure 6 A partial enlarged view of the D portion circled in the middle.

[0027] Fig.10 yes Figure 6 A partial enlarged view of the E part circled in the middle.

[0028] Fig.11 It is a cross-sectional view of the internal structure of the force sensing microscopic instrument provided by the present invention.

[0029] Fig.12 yes Fig.11 A partial enlarged view of the F part circled in the middle.

[0030] Fig.13 yes Fig.11 A partial enlarged view of the G section circled in the middle.

[0031] Fig.14 yes Fig.11 A partial enlarged view of the H section circled in the middle.

[0032] Fig.15 It is a schematic diagram of the explosion structure of the drug delivery component of the force-sensing microscopic instrument provided by the present invention.

[0033] Reference numerals: 1. Shell; 2. Drug injection assembly; 20. Grating area; 21. First optical fiber; 211. First grating area; 212. Second grating area; 22. Second optical fiber; 221. Third grating area; 222. Fourth grating area; 23. Drug injection needle; 231. Drug delivery tube; 232. Drug injection needle; 230. Bend needle; 24. Potting part; 241. First potting channel; 242. Second potting channel; 243. Third potting channel; 25. Potting body; 3. Drug delivery Assembly; 31. Connector assembly; 311. First Luer connector; 312. Blade ring; 313. Split connector; 32. First pressure extension tube; 33. Adapter tube; 331. First tube body; 332. Second tube body; 3321. First channel; 3322. Second channel; 34. Second pressure extension tube; 35. Three-way valve; 36. Second Luer connector; 37. Third Luer connector; 4. Sleeve; 41. Tube seat; 42. Straight tube; 5. Fiber optic connector. DETAILED DESCRIPTION

[0034] In order to make the purpose, technical solution and advantages of the present invention clearer, the technical solution of the present invention will be clearly and completely described below in conjunction with the drawings in the present invention. Obviously, the described embodiments are part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0035] In the description of the embodiments of the present invention, it should be noted that, unless otherwise expressly specified and limited, the terms "first"... "fourth" are for the purpose of clearly describing the numbering of product components and do not represent any substantial difference. The terms "installed", "connected" and "connected" should be understood in a broad sense. For example, it can be a fixed connection, a detachable connection, or an integral connection; it can be a direct connection, or an indirect connection through an intermediate medium, or it can be a connection between the two components. For those of ordinary skill in the art, the specific meanings of the above terms in the embodiments of the present invention can be understood according to the specific circumstances. In addition, the meaning of "multiple" is two or more.

[0036] Combine the following Figure 1-Figure 15 The force-sensing microscopic device of the present invention is described.

[0037] like Figure 1-Figure 4 As shown, the force sensing microscopic instrument provided by the embodiment of the present invention includes a housing 1 and an injection assembly 2. The injection assembly 2 includes an injection needle 23, a first optical fiber 21 and a second optical fiber 22. A bent needle 230 is provided at the distal end of the injection needle 23. The first optical fiber 21 and the second optical fiber 22 are distributed on the periphery of the injection needle 23 along the length direction of the injection needle 23, and are encapsulated in the housing 1. The first optical fiber 21 and the second optical fiber 22 are Bragg fibers, both of which are provided with a grating area 20, and at least one of the two is provided with a plurality of grating areas 20 at intervals, and the grating area 20 is used to sense the radial force exerted on the injection needle 23.

[0038] Specifically, see Figure 1 A portion of the injection component 2 is located inside the housing 1, and a portion of the injection component 2 near its distal end extends out of the housing 1, and a bent needle 230 is provided at the distal end. Figure 2 It is the core functional part exposed after removing the shell 1. The bent needle 230 can be a bent angle needle, such as Figure 3 Needle shown with 45° bend. Figure 3 and Figure 4 The first optical fiber 21 and the second optical fiber 22 are distributed on the outer circumference of the injection needle 23 along the length direction of the injection needle 23, and the bent needle 230 extends relative to the first optical fiber 21 and the second optical fiber 22. The injection assembly 2 formed in this way is a force-sensing microneedle, and its outer diameter is jointly determined by the first optical fiber 21, the second optical fiber 22 and the injection needle 23.

[0039] In some embodiments of the present invention, Figure 7 and Fig.14 As shown, the injection needle tube 23 includes a drug delivery tube 231 and an injection needle 232. One end of the injection needle 232 is inserted into the drug delivery tube 231 and is sealed with the drug delivery tube 231, and the bent needle head 230 is formed at one end of the injection needle 232 away from the drug delivery tube 231. Specifically, the first optical fiber 21 and the second optical fiber 22 are distributed on the periphery of the drug delivery tube 231 along the length direction of the drug delivery tube 231. The injection needle 232 and the drug delivery tube 231 are bonded, fixed and sealed by biocompatible glue.

[0040] It should be noted that the injection needle 23 can also be an integrated needle, such as a stainless steel needle, which has a straight tube portion and a bent portion, one end of the bent portion forming a bent needle head 230. The first optical fiber 21 and the second optical fiber 22 are distributed on the outer periphery of the straight tube portion along the length direction of the straight tube portion.

[0041] In actual application, the first optical fiber 21 and the second optical fiber 22 are respectively connected to the demodulator through the optical fiber connector 5. The demodulator inputs a broadband light source to the first optical fiber 21 and the second optical fiber 22. When the light passes through the grating area 20, part of the light passes through the grating, and the other part of the light is reflected back under the action of the grating. The wavelength of the reflected light is captured and demodulated by the demodulator. The demodulator can be a component of the force sensing microscopic instrument of the embodiment of the present invention.

[0042] In the clinical application of retinal vein injection, a sheath needle with an inner diameter larger than the injection component 2 is first inserted into the sclera to establish a channel, and then the injection component 2 of the force-sensing microscopic instrument is placed into the eye through the channel, and the blood vessels in the fundus are punctured and injected by bending the needle 230. When the needle punctures the vein, the force will suddenly change at the moment of puncture, and the radial force on the position of the injection needle tube 23 corresponding to the grating area 20 will also suddenly change accordingly, so that the wavelength of the reflected light will suddenly change. The demodulator can obtain the puncture force of the needle on the blood vessel based on the mapping relationship between the puncture force and the wavelength change rate. According to the puncture force, it can be determined whether the needle has punctured the vein to prevent secondary puncture. It should be noted that the force-sensing microscopic instrument provided in the embodiment of the present invention can be used not only for retinal vein puncture, but also for vein puncture of other tissues of the human body.

[0043] At least one of the first optical fiber 21 and the second optical fiber 22 is provided with a plurality of grating regions 20 at intervals, that is, the number of the grating regions 20 on the first optical fiber 21 and the number of the grating regions 20 on the second optical fiber 22 is at least three in total. For example, one grating region 20 is provided on the first optical fiber 21, and two grating regions 20 are provided on the second optical fiber 22. Alternatively, two grating regions 20 are provided on the first optical fiber 21, and one grating region 20 is provided on the second optical fiber 22.

[0044] Optionally, the length of the grating region 20 is 0.9-1.1 mm, such as 1 mm. The interval between the two grating regions 20 is 0.9-1.1 mm, such as 1 mm. In this way, it can be ensured that when retinal vein puncture is performed, the two grating regions 20 on the same optical fiber can enter the eye to ensure that each grating region 20 can accurately sense the force, and sufficient intervals can ensure that the demodulator can accurately demodulate the reflection wavelengths of the two grating regions 20.

[0045] In a specific embodiment of the present invention, the first optical fiber 21 and the second optical fiber 22 are both provided with two mutually spaced grating regions 20. In this way, the first optical fiber 21 and the second optical fiber 22 with the same structure can be provided, that is, the same two optical fibers can be used, which is convenient for production and manufacturing. Fig. 9 As shown, a first grating region 211 and a second grating region 212 are provided on the first optical fiber 21 , and a third grating region 221 and a fourth grating region 222 are provided on the second optical fiber 22 .

[0046] The following describes the principle of detecting the needle puncture force through the first optical fiber 21 and the second optical fiber 22 by taking the first optical fiber 21 and the second optical fiber 22 both having two grating regions 20 as an example: See also Figure 3 and Figure 4 The puncture force of the needle tip of the bent needle 230 is F, which can be decomposed into the axial force and radial force along the drug delivery tube 231 of the injection needle tube 23 (or the straight tube part of the integrated injection needle tube 23) and radial force Take section AA, radial force Can be decomposed into mutually perpendicular radial forces along the X direction and Y direction respectively and radial force , the first optical fiber 21 and The angle is , the second optical fiber 22 and The angle is The distances from the needle tip to the centers of the four grating regions 20 are recorded as , , , .

[0047] According to the cantilever beam theory, the strain magnitude of each grating region 20 on the first optical fiber 21 and the second optical fiber 22 is: (1) in, is the strain of each grating region 20, r is the distance between the central axis of the optical fiber and the central axis of the injection needle 23, E is the elastic modulus of the optical fiber, is the cross-sectional moment of inertia of the optical fiber in the X direction, is the cross-sectional moment of inertia of the optical fiber in the Y direction, is the distance between the center of each grating region 20 and the tip of the bending needle 230. i ={1,2}, j ={1,2}.

[0048] According to the formula of the reflection wavelength change rate of the fiber Bragg grating, the wavelength change rate of each grating region 20 can be obtained as follows: (2) in, is the wavelength change, is the wavelength, is the temperature constant, is the change in ambient temperature; is the strain constant.

[0049] Eliminate the influence of temperature coefficient by differential mode, that is, define the measured wavelength change rate for: (3) According to the above equations (1), (2) and (3), the radial force can be obtained and Mapping relationship with wavelength change rate:

[0050] in, .

[0051] By calibrating the constant matrix, the mapping relationship between the wavelength change rate and the two-dimensional radial force can be established. and It is obtained by decomposing the puncture force F. According to the parallelogram theorem of force decomposition, the mapping relationship between the fiber grating wavelength change rate and the puncture force F can be obtained. According to the wavelength change rate and the mapping relationship, the puncture force of the needle on the blood vessel can be obtained.

[0052] The force sensing microscopic instrument provided by the embodiment of the present invention arranges the first optical fiber 21 and the second optical fiber 22 on the periphery of the injection needle tube 23, and both the first optical fiber 21 and the second optical fiber 22 are Bragg fibers, and at least one of the two is provided with a plurality of grating regions 20 at intervals, so that the first optical fiber 21 and the second optical fiber 22 have at least three grating regions 20 in total. According to the mapping relationship between the radial force exerted on the at least three grating regions 20 and the reflection wavelength change rate, the two-dimensional radial force exerted on the injection needle tube 23 can be solved, so that the puncture force of the needle tip can be accurately obtained, and the precise detection of the moment of retinal vein puncture can be achieved. The force sensing microscopic instrument can detect the puncture force of the injection needle tube 23 on the blood vessel through only two Bragg fibers, reduces the outer diameter of the force sensing microneedle, and can be adapted to a smaller size of trocar, thereby reducing the damage to the sclera during the retinal vein injection operation, and reducing the risks of bleeding, tissue hyperplasia around the incision, and traction of the retina.

[0053] like Figure 6 and Figure 8 As shown, the injection assembly 2 also includes a potting portion 24, which is provided with a first potting channel 241, a second potting channel 242, and a third potting channel 243. The first optical fiber 21 is inserted into the first potting channel 241, the second optical fiber 22 is inserted into the second potting channel 242, and the injection needle 23 is inserted into the third potting channel 243. The outer diameter of the potting portion 24 is the outer diameter of the force sensing microneedle.

[0054] Specifically, the straight tube portion of the injection needle 23 or the drug delivery tube 231 is combined with the first optical fiber 21 and the second optical fiber 22 by a potting process to form a potting body 25, see Fig.13 The potting material portion is the potting portion 24, which forms a first potting channel 241, a second potting channel 242 and a third potting channel 243 after potting. In this embodiment, the injection needle 23, the first optical fiber 21 and the second optical fiber 22 are potted into one body, which can improve the relative positions of the three and the stability of the structure of the injection assembly 2.

[0055] like Figure 5 , Fig.11 and Fig.13 As shown, some embodiments of the present invention provide a force sensing microscopic instrument further comprising a sleeve 4. The sleeve 4 comprises a tube seat 41 and a straight tube 42. The tube seat 41 is connected to one end of the housing 1 close to the bent needle 230, and one end of the straight tube 42 is passed through the tube seat 41. The potting portion 24 is passed through the straight tube 42, and the grating region 20 is located outside the straight tube 42.

[0056] Specifically, the straight tube 42 is inserted into the tube seat 41 and fixed by glue. The straight tube 42 is sleeved on the outside of the potting body 25 formed by potting the injection needle 23, the first optical fiber 21 and the second optical fiber 22. Fig.14Moreover, the straight tube 42 does not cover the grating region 20 on the optical fiber. The injection assembly 2 is sequentially arranged in the housing 1, the tube seat 41 and the straight tube 42. The straight tube 42 can provide structural support for the injection assembly 2 so that it meets sufficient rigidity.

[0057] It is understandable that, when the injection needle tube 23 is a stainless steel needle tube or the drug delivery tube 231 has sufficient rigidity, the straight tube 42 may not be provided. In this case, the injection assembly 2 is sequentially provided in the housing 1 and the tube seat 41, and the tube seat 41 may be a part of the housing 1, or the tube seat 41 and the housing 1 may be integrally formed.

[0058] In some embodiments of the present invention, the drug delivery tube 231 is a nickel-titanium alloy tube. The nickel-titanium alloy material can make a thinner drug delivery tube 231. When the drug delivery tube 231 is thin enough, in order to compensate for the problem of insufficient rigidity of the drug delivery tube 231, the straight tube 42 in the above embodiment can be provided to provide structural support for the drug injection needle tube 23, the first optical fiber 21 and the second optical fiber 22.

[0059] In a specific example of using a nickel-titanium alloy dosing tube 231, the diameter of the injection assembly 2 formed after potting can be 0.4 mm, which is suitable for the trocar of 23G specification (inner diameter is about 0.6 mm) commonly used on the market. In the prior art, three Bragg optical fibers are distributed at an angle of 120° to each other on the outer periphery of a stainless steel needle tube, and the minimum diameter of a commonly used stainless steel needle tube is 0.64 mm, and the diameter of the Bragg optical fiber is about 0.11~0.165 mm. In this embodiment, by setting the dosing tube 231 as a nickel-titanium alloy tube, the diameter of the injection assembly 2 can be significantly reduced.

[0060] Based on the above embodiments, the force sensing microscopic device provided by the present invention further includes a drug delivery component 3. Figure 1 and Figure 5 As shown, the drug delivery assembly 3 includes a connector assembly 31, a first pressure extension tube 32 and a transfer tube 33. One end of the first pressure extension tube 32 is connected to the connector assembly 31, and the other end is connected to the injection needle 23 through the transfer tube 33. The connector assembly 31 is connected to one end of the housing 1 away from the bent needle 230.

[0061] The connector assembly 31, the first pressure extension tube 32, the transfer tube 33 and the injection needle tube 23 are connected in sequence to form a drug delivery channel. The connector assembly 31 is used to connect special equipment to inject drugs and provide injection pressure. The drug solution flows through the first pressure extension tube 32 and the transfer tube 33 in sequence and then enters the injection needle tube 23.

[0062] Specifically, Fig.15As shown, the connector assembly 31 includes a first Luer connector 311, a blade ring 312 and a split connector 313, wherein the blade ring 312 is disposed in the first Luer connector 311. One end of the split connector 313 is connected to the first pressure extension tube 32, and the other end is connected and fixed to the first Luer connector 311 through the blade ring 312. Optionally, the first Luer connector 311 is a female Luer connector.

[0063] In the embodiment of the present invention, both ends of the housing 1 are connected to the connector assembly 31 and the tube holder 41 respectively, so that the portion between the connector assembly 31 and the tube holder 41 is encapsulated in the housing 1 for easy handheld operation.

[0064] Furthermore, the drug delivery assembly 3 also includes a second pressure extension tube 34 and a three-way valve 35. One end of the second pressure extension tube 34 is connected to the three-way valve 35, and the other end is detachably connected to the connector assembly 31. The three-way valve 35, the second pressure extension tube 34, the connector assembly 31, the first pressure extension tube 32, the transfer tube 33 and the injection needle 23 are sequentially connected to form a drug delivery channel.

[0065] Specifically, see Fig.15 The drug delivery assembly 3 further includes a second Luer connector 36 and a third Luer connector 37. Both ends of the second pressure extension tube 34 are respectively connected to the second Luer connector 36 and the third Luer connector 37, and are connected to the first Luer connector 311 through the second Luer connector 36, and are connected to the three-way valve 35 through the third Luer connector 37. Optionally, the second Luer connector 36 is a male Luer connector, and the third Luer connector 37 is a female Luer connector.

[0066] When the drug needs to be injected manually through a syringe, the second Luer connector 36 is connected to the first Luer connector 311, and then the second pressure extension tube 34, the third Luer connector 37 and one interface of the three-way valve 35 are connected in sequence, and the syringe is connected to the other interface of the three-way valve 35. When the drug needs to be injected through a dedicated device, the second Luer connector 36 is removed from the first Luer connector 311, and the first Luer connector 311 is connected to the dedicated device.

[0067] The three-way valve 35 has a first interface, a second interface and a third interface. The first interface is connected to the second pressure extension tube 34 through a third Luer connector 37. The second interface is used to connect a thin syringe, and the third interface is used to connect a thick syringe.

[0068] Before performing puncture injection, connect the thin syringe to the first interface, and adjust the three-way valve 35 to connect the first interface with the second interface. Inject the medicine into the medicine delivery channel through the thin syringe, so that the medicine fills the medicine delivery channel to expel the air in the medicine delivery channel. In this process, when the medicine in the thin syringe is completely injected and needs to be replenished, adjust the three-way valve 35 to switch the second interface to connect with the third interface, and replenish the medicine into the thin syringe through the thick syringe. After the replenishment is completed, adjust the three-way valve again to switch the second interface to connect with the first interface, and continue to inject medicine into the medicine delivery channel. Repeat this cycle until the medicine delivery channel is filled with liquid medicine.

[0069] like Fig.10 , Fig.11 and Fig.12 As shown, the adapter tube 33 includes a first tube body 331 and a second tube body 332. The first pressure extension tube 32 is sleeved on one end of the first tube body 331, and the other end of the first tube body 331 is sleeved on one end of the second tube body 332. The end of the injection needle 23 away from the bent needle 230 is plugged into the other end of the second tube body 332.

[0070] Specifically, the drug delivery tube 231 of the injection needle tube 23 is plugged into the other end of the second tube body 332. After the second tube body 332 is inserted into the first tube body 331, a stepped channel is formed in the transfer tube 33, which can reduce the local pressure loss caused by the reduction of the tube diameter from the transfer tube 33 to the injection needle tube 23, thereby reducing energy loss and flow resistance, and the drug solution can smoothly flow into the injection needle tube 23 through the stepped channel. The insertion depth of the second tube body 332 into the first tube body 331 can be adjusted, so that the length of the drug delivery component 3 has a certain adjustment margin.

[0071] Alternatively, see Fig.12 One end of the first tube body 331 is provided with an inverted cone connection portion, so that the first tube body 331 is tightly connected to the first pressure extension tube 32 through the inverted cone connection portion.

[0072] Further, see Fig.12 , the second tube body 332 is provided with a first channel 3321 and a second channel 3322 connected to each other, the diameter of the second channel 3322 is larger than the diameter of the first channel 3321, and the injection needle 23 is inserted into the first channel 3321. In other words, a stepped channel is provided in the second tube body 332. The second tube body 332 is inserted into the middle area of ​​the first tube body 331, so that a stepped channel with two steps can be formed in the transfer tube 33, including three sections of channels with gradually decreasing diameters. In this way, the pressure loss caused by the reduction of the tube diameter when the liquid medicine flows from the transfer tube 33 to the injection needle 23 can be further reduced.

[0073] When assembling the adapter tube 33 and the injection needle 23, a cylindrical plug is inserted into the second channel 3322 of the second tube 332 in advance, and then the injection needle 23 is inserted into the first channel 3321. The injection needle 23 is positioned by the plug so that the end of the injection needle 23 is flush with the end of the first channel 3321. The injection needle 23 and the second tube 332 are bonded, fixed and sealed by biocompatible glue. Then the plug is removed and the end of the second tube 332 away from the injection needle 23 is inserted into the first tube 331, and the second tube 332 and the first tube 331 are bonded, fixed and sealed by biocompatible glue.

[0074] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit it. Although the present invention has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the aforementioned embodiments, or make equivalent replacements for some of the technical features therein. However, these modifications or replacements do not deviate the essence of the corresponding technical solutions from the spirit and scope of the technical solutions of the embodiments of the present invention.

Claims

1. A force sensing microscopic instrument, characterized in that: include: shell; The drug injection assembly includes a drug injection needle, a first optical fiber and a second optical fiber; a bent needle is provided at the distal end of the drug injection needle; the first optical fiber and the second optical fiber are distributed on the outer circumference of the drug injection needle along the length direction of the drug injection needle and are encapsulated in the outer shell; the first optical fiber and the second optical fiber are Bragg fibers, both of which are provided with grating areas, and at least one of the two is provided with multiple grating areas at intervals, and the grating areas are used to sense the radial force applied to the drug injection needle.

2. The force sensing microscopic device according to claim 1, characterized in that: The first optical fiber and the second optical fiber are both provided with two grating regions spaced apart from each other, and the first optical fiber and the second optical fiber have the same structure.

3. The force sensing microscopic device according to claim 1, characterized in that: The injection component also includes: a potting part, which is provided with a first potting channel, a second potting channel and a third potting channel, the first optical fiber is arranged in the first potting channel, the second optical fiber is arranged in the second potting channel, and the injection needle is arranged in the third potting channel.

4. The force sensing microscopic device according to claim 3, characterized in that: Also includes: The sleeve comprises a tube seat and a straight tube, wherein the tube seat is connected to one end of the shell close to the bent needle, one end of the straight tube is penetrated through the tube seat, the potting part is penetrated through the straight tube, and the grating area is located outside the straight tube.

5. The force sensing microscopic device according to any one of claims 1 to 4, characterized in that: The injection needle tube comprises: a drug administration tube and an injection needle; one end of the injection needle is inserted into the drug administration tube and sealedly connected to the drug administration tube, and the bent needle head is formed at one end of the injection needle away from the drug administration tube.

6. The force sensing microscopic device according to claim 5, characterized in that: The drug delivery tube is a nickel-titanium alloy tube.

7. The force sensing microscopic device according to any one of claims 1 to 4, characterized in that: Also includes: The drug delivery assembly includes a connector assembly, a first pressure extension tube and a transfer tube, wherein one end of the first pressure extension tube is connected to the connector assembly, and the other end is connected to the injection needle through the transfer tube, and the connector assembly is connected to one end of the shell away from the bent needle.

8. The force sensing microscopic device according to claim 7, characterized in that: The drug delivery assembly further includes: a second pressure extension tube and a three-way valve, one end of the second pressure extension tube is connected to the three-way valve, and the other end is detachably connected to the connector assembly.

9. The force sensing microscopic device according to claim 7, characterized in that: The adapter tube includes: a first tube body and a second tube body, the first pressure extension tube is sleeved on one end of the first tube body, the other end of the first tube body is sleeved on one end of the second tube body, and the end of the injection needle away from the bent needle is inserted into the other end of the second tube body.

10. The force sensing microscopic device according to claim 9, characterized in that: The second tube body is provided with a first channel and a second channel connected to each other, the diameter of the second channel is larger than the diameter of the first channel, and the injection needle is inserted into the first channel.

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