Miniature biopsy forceps with single-strand drive cable and its molding method

Abstract

This invention relates to a miniature biopsy forceps with a single-strand drive cable and a method for forming the same. A laser is applied to the end of the cable, and the cable is fed at a speed between 3.6 mm and 4.4 mm per second to melt the end. The laser parameters are: operating current between 63 and 77 amps, pulse width between 2.9 and 3.5 milliseconds, pulse frequency between 18 and 22 Hz, and spot diameter between 0.18 and 0.22 mm. The laser application is stopped after the cable has been fed 0.45 to 1.7 mm, allowing the end of the cable to cool and harden under cohesive force, forming a sphere with a radius between 0.1957 and 0.3107 mm. The sphere is then flattened into the drive end. One end of each of the two drive linkages is pivotally connected to the drive end. Two clamp parts are each pivotally connected to the other end of one of the two drive linkages. The two clamps are driven by a single-strand drive cable. When the diameter of the two clamps is reduced to 0.8 mm when they are closed, they still have sufficient tensile strength to cut and grasp the tissue to be inspected.

Description

Technical Field

[0001] The invention relates to a miniature biopsy forceps with a single-strand drive cable, and more particularly to a miniature biopsy forceps with two clamps that can be driven by a single-strand drive cable, and a method for forming the single-strand drive cable, wherein when the diameter of the two clamps is reduced to 0.8 mm when closed, it still has sufficient tensile strength to cut and grasp the tissue to be examined. Background Technology

[0002] Endoscopy allows observation of whether internal organs are functioning normally. When it is necessary to obtain tissue samples for external physical examination, biopsy forceps are used to directly obtain the tissue to be examined.

[0003] With an endoscope working channel of approximately 2.8mm, the typical size of a biopsy forceps is approximately 2.2mm to 2.5mm in diameter when both forceps are closed, usually 2.4mm. Common biopsy forceps designs include those from US patents US6299630B1 / US20050054946A1, Japanese patents JP201119741A / JP2000296131A, and Chinese patent CN102217956A. These biopsy forceps typically consist of two steel cables connecting the two forceps to a single drive linkage. Medical personnel can then manipulate this linkage and use the two steel cables to drive the forceps, causing them to cut the tissue to be examined.

[0004] Ultrasound endoscopy uses added ultrasound waves to create clearer images, allowing for more precise detection of minute lesions. However, as in the first... Figure 13B As shown, when it is necessary to use the puncture aspiration needle 9 to pick up the tissue to be examined, the inner diameter of the puncture aspiration needle 9 is about 0.85mm to 0.9mm. The general biopsy forceps F with a diameter of 2.4mm is too large to pass through the puncture aspiration needle. If the traditional steel cable biopsy forceps are further miniaturized, there will be a problem that the diameter of the steel cable is too thin and the tensile strength is insufficient, which will prevent the tissue to be examined from being cut, and there is even a risk of instrument breakage and failure.

[0005] Miniature biopsy forceps (e.g., those that can be aspirated via puncture needles) have structures that utilize a drive rod made of double or multi-strand spiral wire, connected to two connecting rods. The drive rod pulls the two connecting rods to open or close the forceps. The double or multi-strand spiral wire connecting the two connecting rods maintains sufficient tensile strength, allowing the forceps to cut the tissue being tested with sufficient force. Chinese Patent No. CN113749696, "An Adjustable Forceps Head Assembly and Biopsy Forceps," uses a lateral adjustment mechanism to control the opening width of the forceps, and therefore clearly does not belong to the category of narrow-width miniature biopsy forceps. Figure 2 and Figure 3 An example is shown of a drive rod with a double or multi-strand spiral wire on a biopsy forceps. Summary of the Invention

[0006] Unlike the aforementioned cases, the purpose of this invention is to provide a miniature biopsy forceps with a single-strand drive cable and a method for forming the single-strand drive cable.

[0007] This invention provides a method for forming a single-strand drive cable for a miniature biopsy forceps, comprising the following steps:

[0008] A medical-grade metal is formed into a cable with a cross-sectional width between 0.2 mm and 0.4 mm. A laser is applied to the end of the cable, and the cable is fed at a speed between 3.6 mm and 4.4 mm per second, melting the end of the cable. The laser parameters are: operating current between 63 amps and 77 amps, pulse width between 2.9 ms and 3.5 ms, pulse frequency between 18 Hz and 22 Hz, and spot diameter between 0.18 mm and 0.22 mm. After the cable has been fed for 0.45 mm to 1.7 mm, the laser application is stopped, allowing the end of the cable to cool and harden under cohesive force to form a sphere with a radius between 0.1957 mm and 0.3107 mm. The sphere is flattened to a width between 0.4 mm and 0.8 mm and a thickness between 0.175 mm and 0.325 mm to form a drive end, thereby forming the cable into a single-strand drive cable.

[0009] Furthermore, the medical-grade metal is made of one of the following materials: 304 stainless steel, 316 stainless steel, SUS420J2 stainless steel, SUS630 stainless steel, or nickel-titanium alloy.

[0010] Furthermore, the cable is formed into a round rod shape, and the width of the cross-section is the diameter. Preferably, the diameter is 0.3 mm.

[0011] Furthermore, the laser parameters are: operating current of 70 amperes, pulse width of 3.2 milliseconds, pulse frequency of 20 Hz, and spot diameter of 0.2 cm.

[0012] Furthermore, the sphere is flattened to a width between 0.5 mm and 0.63 mm and a thickness of 0.25 mm to form the drive end. Further, the drive end is disc-shaped, and the flat width is its diameter.

[0013] Furthermore, the end of the cable is supported by a carrier, so that the sphere is shaped at the center of the cable's axis.

[0014] Furthermore, the tensile strength (TS) of this single-strand drive cable is between 1550 MPa and 2500 MPa.

[0015] Furthermore, a first pivot hole is formed at the drive end by precision drilling or stamping, the diameter of which is between 0.2 mm and 0.3 mm. Preferably, a stamping member can be extended from a stamping plate, and the sphere is flattened by the stamping plate and the stamping member to integrally form the drive end and the first pivot hole.

[0016] This invention further proposes a miniature biopsy forceps with a single-strand drive cable component. The single-strand drive cable component, manufactured using the aforementioned method for forming the single-strand drive cable component of the miniature biopsy forceps, comprises:

[0017] The single-strand drive cable includes two drive links, one end of which is pivotally connected to the drive end; and two clamps, each pivotally connected to the other end of one of the two drive links, so that the two clamps can pivotally open or close relative to each other.

[0018] Furthermore, the drive end has a first pivot hole with a diameter between 0.2 mm and 0.3 mm, and one end of each of the two drive links has a second pivot hole with a diameter between 0.2 mm and 0.3 mm. A first pin passes through the first pivot hole and the second pivot hole to pivotally connect the two drive links together to the drive end.

[0019] Furthermore, the other end of the two drive links has a third pivot hole with a diameter between 0.2 mm and 0.3 mm. Each of the two clamps has a fourth pivot hole with a diameter between 0.2 mm and 0.3 mm. A second pin passes through the third pivot hole and the fourth pivot hole to pivotally connect the two clamps partially to the other end of one of the two drive links.

[0020] Furthermore, a clamp head frame is disposed at the drive end. The drive end of the single-strand drive cable extends from the clamp head frame and has an exposed section, the slenderness ratio of which does not exceed 50.

[0021] Furthermore, a flexible sleeve is fitted onto the single-strand drive cable. This flexible sleeve is, for example, a spring tube.

[0022] Furthermore, there is a gap between the integrally molded drive cable and the flexible sleeve, which is between 0.04 mm and 0.06 mm, preferably 0.05 mm.

[0023] The following effects can be achieved based on the above technical features:

[0024] 1. This invention uses laser processing control parameters to allow the ends of molten cable to polymerize and harden into spheres due to cohesive forces. A support component ensures that the spheres are centered on the cable's axis, and further processing forms a single-strand driven cable. The micro biopsy forceps, through the aforementioned single-strand driven cable structure and size configuration, maintains sufficient tensile strength even when the diameter of the two closed forceps is reduced to 0.8 mm. Therefore, it can be used for thrombus removal in narrow blood vessels, or as a puncture and aspiration needle inserted into endoscopic ultrasound aspiration to grasp the tissue to be examined.

[0025] 2. Compared to existing miniature biopsy forceps that use double or multi-strand spiral wires to maintain sufficient tensile strength, this invention only needs to use a single-strand drive cable to have sufficient tensile strength to be pulled and cut off the tissue to be examined in the endoscope.

[0026] 3. The clamp head holder can support the clamp and is used to install the drive linkage; the flexible sleeve provides the movement space of the single-strand drive cable and prevents bending, and the flexible sleeve provides excellent turning performance, which can move smoothly with the endoscope working channel.

[0027] 4. Maintaining a distance of approximately 0.05 mm between the single-strand drive cable and the flexible sleeve does not increase the width of the two clamps of the miniature biopsy forceps when closed. Combined with the single-strand drive cable having a tensile strength (TS) between 1550 MPa and 2500 MPa (semi-hard wire to fully hard wire) and an exposed section with a length-to-slenderness ratio not exceeding 50, this prevents the single-strand drive cable from bending and deforming under thrust when inserted into the endoscope, thus avoiding the problem of the single-strand drive cable failing to advance continuously within the endoscope and preventing the clamps from reaching the designated target position. Attached Figure Description

[0028] Figure 1 This is a schematic diagram of the laser melting of the end of the single-strand drive cable in the forming method of the present invention.

[0029] Figure 2 This is a schematic diagram of the single-strand drive cable forming method of the present invention, in which the laser application is stopped and the end of the cable is formed into a sphere due to cohesive force.

[0030] Figure 3 This is a schematic diagram of the forming method of the single-strand drive cable of the present invention, in which a stamping plate is used to flatten the sphere.

[0031] Figure 4 This is a schematic diagram of the molding method of the single-strand drive cable of the present invention, in which a sphere is flattened to form a drive end, thereby forming the cable into a single-strand drive cable.

[0032] Figure 5AThis is a schematic diagram of the method for forming a single-strand drive cable according to the present invention, in which a stamping part is used to stamp the drive end of the single-strand drive cable.

[0033] Figure 5B This is a schematic diagram of drilling a hole at the drive end of the single-strand drive cable using a precision drill bit in the forming method of the single-strand drive cable of the present invention.

[0034] Figure 6 This is a schematic diagram of the method for forming a single-strand drive cable according to the present invention, in which the drive end is drilled or stamped to form a first pivot hole.

[0035] Figure 7 This is a schematic diagram showing that, in the forming method of the single-strand drive cable of the present invention, when the sphere is flattened into a drive end by a stamping plate, a first pivot hole is simultaneously formed on the drive end by a stamping part.

[0036] Figure 8 This is an exploded perspective view of the miniature biopsy forceps according to an embodiment of the present invention.

[0037] Figure 9A This is a three-dimensional view of the miniature biopsy forceps without the flexible sleeve, according to one of the embodiments of the present invention.

[0038] Figure 9B This is a three-dimensional view of the miniature biopsy forceps without the flexible sleeve, according to another embodiment of the present invention.

[0039] Figure 9C This is a schematic diagram of the exposed section of a single-strand drive cable extending outside the forceps head frame in a miniature biopsy forceps according to an embodiment of the present invention.

[0040] Figure 10A This is a three-dimensional diagram of a combination of a miniature biopsy forceps and a flexible sleeve according to an embodiment of the present invention.

[0041] Figure 10B for Figure 10A A sectional view.

[0042] Figure 10C This is a schematic diagram of the connection between the rear end of the single-strand drive cable of the miniature biopsy forceps and the operating handle according to an embodiment of the present invention.

[0043] Figure 11 This is a schematic diagram illustrating the use of a miniature biopsy forceps in the removal of thrombi from narrow blood vessels, according to an embodiment of the present invention.

[0044] Figure 12 This is a schematic diagram illustrating the use of miniature biopsy forceps in ultrasonic endoscopic puncture and aspiration of tissue according to an embodiment of the present invention.

[0045] Figure 13AThis is a schematic diagram comparing the miniature biopsy forceps of this invention with the puncture and aspiration needle of an ultrasonic endoscope, showing that the biopsy forceps of this invention can be inserted into the puncture and aspiration needle.

[0046] Figure 13B This is a schematic diagram comparing the miniature biopsy forceps of this invention with the puncture and aspiration needle of an ultrasonic endoscope, showing that the size of the conventional biopsy forceps is too small to fit through the puncture and aspiration needle.

[0047] Explanation of reference numerals in the attached drawings: 100-cable; 200-sphere; 300-bearing component; 400-stamping plate; 500-stamping component; 600-precision drill bit; 10-miniature biopsy forceps; 20-operating handle; 1-single-strand drive cable; 11-drive end; 12-first pivot hole; 13-exposed section; 2-drive linkage; 21-second pivot hole; 22-third pivot hole; 3-forceps; 31-fourth pivot hole; 4-forceps head frame; 5-flexible sleeve; 6-first pin; 7-second pin; 8-third pin; 9-puncture and aspiration needle; d-spacing; e-effective length; A-narrower blood vessel; B-endoscope; C-thrombus; D-ultrasound endoscope; E-pancreatic tumor; F-general biopsy forceps; L-laser. Detailed Implementation

[0048] Based on the above technical features, the main advantages of the micro biopsy forceps with a single-strand drive cable and the method for forming the single-strand drive cable of the present invention will be clearly demonstrated in the following embodiments.

[0049] The forming method of the single-strand drive cable includes:

[0050] See Figure 1 and Figure 2As shown, a medical-grade metal is formed into a cable 100 with a cross-sectional width between 0.2 mm and 0.4 mm. The medical-grade metal can be 304 stainless steel, 316 stainless steel, SUS420J2 stainless steel, SUS630 stainless steel, or nickel-titanium alloy, etc. In this embodiment, the cable 100 is formed into a round rod shape, so the cross-sectional width is the diameter, and the diameter in this embodiment is 0.3 mm. A laser L is applied to the end of the cable 100, and the end of the cable 100 is supported by a carrier 300. The cable 100 is fed at a speed between 3.6 mm and 4.4 mm per second to melt the end of the cable 100. The parameters of the laser L are: operating current between 63 amps and 77 amps, pulse width between 2.9 ms and 3.5 ms, pulse frequency between 18 Hz and 22 Hz, and spot diameter between 0.18 mm and 0.22 mm. Specifically, the laser L used in this embodiment has the following parameters: operating current 70 amps, pulse width of 3.2 ms, pulse frequency of 20 Hz, and spot diameter of 0.2 cm. When the cable is fed to a length of 0.45 mm to 1.7 mm, the laser L is stopped, allowing the end of the cable 100 to cool down and harden under cohesive force to form a sphere 200 with a radius between 0.1957 mm and 0.3107 mm.

[0051] See Figure 3 and Figure 4 As shown, a stamping plate 400 flattens the sphere 200 into a flat shape with a width between 0.4 mm and 0.8 mm and a thickness between 0.175 mm and 0.325 mm to form a drive end 11, thus forming the cable 100 into a single-strand drive cable 1. In this embodiment, the flat width is between 0.5 mm and 0.63 mm, and the thickness is 0.25 mm. In this embodiment, the drive end 11 is disc-shaped, and the flat width is the diameter. The support member 300 ensures that the drive end 11 is centered on the axis of the single-strand drive cable 1. Specifically, according to the required flat width of the drive end 11, the above-mentioned dimensional configuration satisfies 0.152πL = 4 / 3πr. 3 =0.25R 2 π, where L is the wire length, r is the radius of the sphere, and R is the radius of the flat drive end.

[0052] See Figure 5A , Figure 5B and Figure 6 As shown, a first pivot hole 12 is formed on the drive end 11 by a stamping part 500 or a precision drill bit 600 by drilling or stamping, respectively. The diameter of the first pivot hole 12 is between 0.2 mm and 0.3 mm.

[0053] See Figure 7 As shown, the stamping part 500 can protrude from the stamping plate 400, and the ball 200 is flattened by the stamping plate 400 and the stamping part 500 to integrally form the driving end 11 and the first pivot hole 12.

[0054] See Figures 8 to 10A As shown, the miniature biopsy forceps 10 of this embodiment includes: the single-strand drive cable 1, two drive linkages 2, two forceps 3, a forceps head frame 4, and a flexible sleeve 5. The miniature biopsy forceps 10 is attached to an operating handle 20.

[0055] The two drive links 2 are pivotally connected at one end to the drive end 11. Specifically, one end of each drive link 2 has a second pivot hole 21 with a diameter between 0.2 mm and 0.3 mm. A first pin 6 passes through the first pivot hole 12 and the second pivot hole 21 to pivotally connect the two drive links 2 to the drive end 11. The other end of each drive link 2 has a third pivot hole 22 with a diameter between 0.2 mm and 0.3 mm.

[0056] The two clamps 3 are respectively pivotally connected to the other end of one of the two drive links 2, so that the two clamps 3 can be pivotally opened or closed by the operation of the drive links 2. Specifically, each of the two clamps 3 has a fourth pivot hole 31, the diameter of which is between 0.2 mm and 0.3 mm. A second pin 7 passes through the third pivot hole 22 and the fourth pivot hole 31 to pivotally connect the two clamps 3 to the other end of one of the two drive links 2. Thus, the two clamps 3 open or close relative to the axis of the single-strand drive cable 1.

[0057] The aforementioned clamp head frame 4 is fitted onto the drive end 11 and connected to the clamp portion 3 by a third pin 8, allowing the clamp head frame 4 to support the clamp portion 3 and to mount the aforementioned drive linkage 2. During assembly, the drive end 11 of the single-strand drive cable 1 extends from the clamp head frame 4, with an exposed section 13. The slenderness ratio of this exposed section 13 does not exceed 50, for example, it is between 40 and 50. The slenderness ratio is the ratio of the effective length e of the exposed section 13 to its cross-sectional area. The aforementioned flexible sleeve 5 is fitted onto the single-strand drive cable 1 and smoothly abuts the clamp head frame 4. Thus, by having the clamp head frame 4 and the flexible sleeve 5 completely fitted over the single-strand drive cable 1, damage from impact and bending deformation can be avoided. (See also...) Figure 10B A gap d is maintained between the single-strand drive cable 1 and the flexible sleeve 5. The gap d is between 0.04 mm and 0.06 mm. In this embodiment, the gap is 0.05 mm.

[0058] After assembly, the miniature biopsy forceps 10 of this embodiment has a diameter of 0.8 mm when the two forceps 3 are closed, and the width of the forceps head frame 4 and the flexible sleeve 5 is no greater than 0.8 mm. The tensile strength of the single-strand drive cable 1 of this embodiment is between 1550 MPa and 2500 MPa (from semi-hard wire to fully hard wire), which is sufficient to open / close the two forceps 3 and cut off the tissue to be examined in the body.

[0059] See Figure 10B , Figure 10C and Figure 11 As shown, during thrombectomy in a narrower blood vessel A, when an endoscope B is inserted into the narrower blood vessel A to observe the location of a thrombus C, the miniature biopsy forceps 10 of this embodiment can be inserted into the endoscope B, and the forceps 3 can extend from the end of the endoscope B into the narrower blood vessel A. The medical personnel can control the single-strand drive cable 1 by operating the operating handle 20, which can drive the two drive linkages 2 to drive the two forceps 3, so that the two forceps 3 can grasp and remove the thrombus C. The single-strand drive cable 1 and the flexible sleeve 5 maintain a distance d of approximately 0.05 mm. The tensile strength (TS) of the single-strand drive cable 1 is between 1550 MPa and 2500 MPa, and the length-to-slenderness ratio of the exposed section 13 does not exceed 50. When the operating handle 20 controls the feeding of the single-strand drive cable 1, it can prevent the single-strand drive cable 1 from bending and deforming due to the thrust when it is inserted into the endoscope B, thus preventing it from collapsing. The flexible sleeve 5 can also drive the integrally molded drive cable 1 to feed along the curvature of the endoscope B, allowing the integrally molded drive cable 1 to continuously advance in the endoscope B, enabling the clamp 3 to reach the designated target position or to withdraw from the endoscope B after the work is completed. This embodiment further tested three different sizes of single-strand drive cables made of 304 stainless steel. The first type had a diameter of 0.3 mm and a TS value of approximately 1550 MPa to 1750 MPa; the second type had a diameter of 0.3 mm and a TS value of approximately 1750 MPa to 1950 MPa; and the third type had a diameter of 0.25 mm and a TS value of approximately 2300 MPa to 25000 MPa. The experiment found that the steering performance of the third type of single-strand drive cable was better than that of the first type, and the first type of single-strand drive cable was better than that of the second type. However, the steering performance of all three types of single-strand drive cables could meet the requirements for the use of miniature live-picking pliers.

[0060] See Figure 10B , Figure 10C and Figure 12As shown, in the case of endoscopic ultrasound aspiration for pancreatic tumors, for example, when an endoscopic ultrasound device D travels along the gastrointestinal tract to a location near the pancreatic tumor E (or a suspected lesion) and is about to grasp a tissue to be examined, a puncture and aspiration needle 9 is inserted into the pancreatic tumor E (or the suspected lesion). Since the inner diameter of the puncture and aspiration needle 9 is approximately 0.85 mm to 0.9 mm, a miniature biopsy forceps 10 of this embodiment is then inserted into the endoscopic ultrasound device D and extends out from the puncture and aspiration needle 9. The medical personnel then control the single-strand drive cable 1 by operating the operating handle 20, which drives the two drive linkages 2 to drive the two forceps 3, so that the two forceps 3 grasp the tissue to be examined. Similarly, the flexible sleeve 5 allows the single-strand drive cable 1 to be smoothly fed to the target position or withdrawn from the endoscopic ultrasound device D.

[0061] See Figure 12 , No. Figure 13A and Figure 13B In procedures such as endoscopic ultrasound biopsy, a standard biopsy forceps F, approximately 2.4 mm wide, cannot pass through a biopsy needle 9 with an inner diameter of approximately 0.85 mm to 0.9 mm. The miniature biopsy forceps 10 of this embodiment, approximately 0.8 mm in size, can therefore pass through the biopsy needle 9.

[0062] Based on the above description of the embodiments, one can fully understand the operation, use, and effects of the present invention. The above embodiments are only preferred embodiments of the present invention and should not be construed as limiting the scope of the present invention. Simple equivalent changes and modifications made in accordance with the claims and description of the present invention are all within the scope of the present invention.

Claims

1. A method for forming a single-strand drive cable for a miniature biopsy forceps, characterized in that, Includes the following steps: A medical-grade metal is formed into a cable with a cross-sectional width between 0.2 mm and 0.4 mm; A laser is applied to the end of the cable, and the cable is fed at a speed between 3.6 mm and 4.4 mm per second to melt the end of the cable. The laser parameters are: operating current between 63 amperes and 77 amperes, pulse width between 2.9 ms and 3.5 ms, pulse frequency between 18 Hz and 22 Hz, and spot diameter between 0.18 mm and 0.22 mm. After the cable has been fed to a length of 0.45 mm to 1.7 mm, the laser is stopped, allowing the end of the cable to cool down and harden under cohesive force to form a sphere with a radius between 0.1957 mm and 0.3107 mm. The sphere is flattened to a width between 0.4 mm and 0.8 mm and a thickness between 0.175 mm and 0.325 mm, and a drive end is formed, so that the cable is formed into a single-strand drive cable. The drive end is disc-shaped, and the flat width is the diameter.

2. The method for forming the single-strand drive cable of the miniature biopsy forceps as described in claim 1, characterized in that, The medical-grade metal is made of one of the following materials: 304 stainless steel, 316 stainless steel, SUS420J2 stainless steel, SUS630 stainless steel, or nickel-titanium alloy.

3. The method for forming the single-strand drive cable of the miniature biopsy forceps as described in claim 1, characterized in that, The cable is formed into a round rod shape, and the width of the cross section is the diameter.

4. The method for forming the single-strand drive cable of the miniature biopsy forceps as described in claim 3, characterized in that, The diameter is 0.3 mm.

5. The method for forming the single-strand drive cable of the miniature biopsy forceps as described in claim 1, characterized in that, The laser parameters are: operating current of 70 amps, pulse width of 3.2 milliseconds, pulse frequency of 20 Hz, and spot diameter of 0.2 millimeters.

6. The method for forming the single-strand drive cable of the miniature biopsy forceps as described in claim 1, characterized in that, The sphere is flattened to a width between 0.5 mm and 0.63 mm and a thickness of 0.25 mm to form the drive end.

7. The method for forming the single-strand drive cable of the miniature biopsy forceps as described in claim 1, characterized in that, The end of the cable is supported by a carrier, so that the sphere is shaped at the center of the cable's axis.

8. The method for forming the single-strand drive cable of the miniature biopsy forceps as described in claim 1, characterized in that, The tensile strength of this single-strand drive cable is between 1550 MPa and 2500 MPa.

9. The method for forming the single-strand drive cable of the miniature biopsy forceps as described in claim 1, characterized in that, A first pivot hole is formed at the drive end by drilling with a precision drill bit or by stamping, the diameter of the first pivot hole being between 0.2 mm and 0.3 mm.

10. The method for forming the single-strand drive cable of the miniature biopsy forceps as described in claim 9, characterized in that, A stamping part protrudes from a stamping plate, and the ball is flattened by the stamping plate and the stamping part to integrally form the drive end and the first pivot hole.

11. A miniature biopsy forceps with a single-strand drive cable, the single-strand drive cable being manufactured using the molding method for the single-strand drive cable of the miniature biopsy forceps according to any one of claims 1 to 10, characterized in that, Including: The single-strand drive cable; Two drive links are pivotally connected at one end to the drive end; Two clamps are pivotally connected to the other end of one of the two drive links, allowing the two clamps to pivot open or close relative to each other.

12. The miniature biopsy forceps with a single-strand drive cable as described in claim 11, characterized in that, The drive end has a first pivot hole with a diameter between 0.2 mm and 0.3 mm. One end of each of the two drive links has a second pivot hole with a diameter between 0.2 mm and 0.3 mm. A first pin passes through the first pivot hole and the second pivot hole to pivotally connect the two drive links together to the drive end.

13. The miniature biopsy forceps with a single-strand drive cable as described in claim 12, characterized in that, The other end of the two drive links has a third pivot hole with a diameter between 0.2 mm and 0.3 mm. Each of the two clamps has a fourth pivot hole with a diameter between 0.2 mm and 0.3 mm. A second pin passes through the third pivot hole and the fourth pivot hole to pivotally connect the two clamps to the other end of one of the two drive links.

14. The miniature biopsy forceps with a single-strand drive cable as described in claim 11, characterized in that, A clamp holder is installed at the drive end.

15. The miniature biopsy forceps with a single-strand drive cable as described in claim 14, characterized in that, The drive end of the single-strand drive cable extends from the clamp head frame and has an exposed section, the aspect ratio of which does not exceed 50.

16. The miniature biopsy forceps with a single-strand drive cable as described in claim 11, characterized in that, A flexible sleeve is fitted onto the single-strand drive cable.

17. The miniature biopsy forceps with a single-strand drive cable as described in claim 16, characterized in that, There is a gap between the single-strand drive cable and the flexible sleeve, which is between 0.04 mm and 0.06 mm.

18. The miniature biopsy forceps with a single-strand drive cable as described in claim 17, characterized in that, The spacing is 0.05 mm.

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