Hemostatic instruments and laparoscopic surgical systems

Abstract

This invention provides a hemostatic instrument and a laparoscopic surgical system. The hemostatic instrument includes a skeleton assembly and a pressing base disposed on the skeleton assembly. The proximal end of the pressing base converges to its own axis, and the distal end of the pressing base changes between a contracted and an expanded state under the drive of the skeleton assembly. With this configuration, the pressing base enters the patient's body in a contracted state. After determining the location of the bleeding point, the distal end of the pressing base, driven by the skeleton assembly, expands to press against and apply pressure to the bleeding point, thereby rapidly and effectively suppressing bleeding. This invention has a simple structure; it only requires changing the shape of the pressing base under the drive of the skeleton assembly to enter the patient's body and perform hemostasis, improving the operability and effectiveness of hemostasis in surgical procedures.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and in particular to a hemostatic device and a laparoscopic surgical system. Background Technology

[0002] Bleeding is a common occurrence in surgical procedures (such as laparoscopic surgery), and significant amounts of blood can fill the entire surgical cavity. Failure to quickly locate and effectively stop the bleeding can endanger the patient's life. Most existing hemostasis methods are relatively simple in function, lacking the ability to draw blood, and their hemostatic effect is generally limited. Furthermore, current hemostasis methods require precise clamping of the bleeding point, demanding a high level of skill from the operator and involving a cumbersome process. Summary of the Invention

[0003] The purpose of this invention is to provide a hemostatic device and laparoscopic surgical system, which aims to effectively suppress bleeding in patients during surgical procedures.

[0004] To solve the above-mentioned technical problems, based on one aspect of the present invention, the present invention provides a hemostatic device, which includes a skeleton assembly and a pressing base disposed on the skeleton assembly; the proximal end of the pressing base converges to its own axis, and the distal end of the pressing base switches between a contracted state and an expanded state under the drive of the skeleton assembly.

[0005] Optionally, when the distal end of the pressing base transitions from the contracted state to the expanded state, the proximal end and the distal end of the pressing base move closer to each other axially; when the distal end of the pressing base transitions from the expanded state to the contracted state, the proximal end and the distal end of the pressing base move further apart axially.

[0006] Optionally, the pressing substrate is wrapped around the skeleton assembly.

[0007] Optionally, when the skeleton assembly expands outward in a trumpet shape along the radial direction of the pressing base, the distal end of the pressing base is in the expanded state; when the skeleton assembly contracts inward in a straight shape along the radial direction of the pressing base, the distal end of the pressing base is in the contracted state.

[0008] Optionally, the skeleton assembly includes at least three skeleton shafts circumferentially distributed around the axis of the pressing base, with the proximal ends of the skeleton shafts fixed in a radial position along the pressing base and the distal ends of the skeleton shafts arranged radially offset along the pressing base.

[0009] Optionally, the skeleton shaft is rotatable, and the axis of rotation of the skeleton shaft is a tangent at the proximal end of the skeleton shaft on the skeleton assembly; the hemostatic device includes a drive assembly connected to the skeleton assembly, the drive assembly being used to drive the skeleton shaft to rotate.

[0010] Optionally, the driving assembly includes a driving part and at least three connecting shafts corresponding one-to-one with the skeleton shaft; one end of the connecting shaft is rotatably connected to the driving part, and the other end of the connecting shaft is rotatably connected to the skeleton shaft; the driving part is movable along the axial direction of the pressing base.

[0011] Optionally, the skeleton shaft has a first conveying channel extending through its proximal and distal ends.

[0012] Optionally, the skeleton assembly is made of shape memory alloy, and the shape memory of the skeleton assembly is configured such that the distal end of the skeleton assembly flares outward along the radial direction of the pressing base.

[0013] Optionally, the pressing base has a second conveying channel extending along its own axial direction.

[0014] Based on another aspect of the present invention, the present invention also provides a laparoscopic surgical system comprising a hemostatic instrument as described above, wherein the distal end of the pressing base of the hemostatic instrument is used to abut against the lesion site of a predetermined object in an expanded form.

[0015] Optionally, the laparoscopic surgical system includes a detection and identification device for detecting and identifying the lesion site.

[0016] In summary, the hemostatic instrument and laparoscopic surgical system provided by this invention includes a skeleton assembly and a pressing base disposed on the skeleton assembly. The proximal end of the pressing base converges to its own axis, and the distal end of the pressing base switches between a contracted and an expanded state under the drive of the skeleton assembly. With this configuration, the pressing base enters the patient's body in a contracted state. After determining the location of the bleeding point, the distal end of the pressing base, driven by the skeleton assembly, expands to press against and apply pressure to the bleeding point, thereby rapidly and effectively suppressing the patient's bleeding. This invention has a simple structure; it only requires changing the shape of the pressing base under the drive of the skeleton assembly to enter the patient's body and perform hemostasis, improving the operability and effectiveness of hemostasis in surgical procedures. Attached Figure Description

[0017] Those skilled in the art will understand that the accompanying drawings are provided to better understand the invention and do not constitute any limitation on the scope of the invention. Wherein:

[0018] Figure 1This is a schematic diagram of the hemostatic device in Embodiment 1 of the present invention when the pressing base is in an expanded state;

[0019] Figure 2 This is a schematic diagram of the hemostatic device in Embodiment 1 of the present invention when the pressing base is in its maximum expansion state;

[0020] Figure 3 This is a schematic diagram of the pressing base in the contracted state according to Embodiment 1 of the present invention;

[0021] Figure 4 This is a schematic diagram of the pressing base in the expanded state according to Embodiment 1 of the present invention;

[0022] Figure 5 This is a schematic diagram of the skeleton component radially narrowed according to Embodiment 1 of the present invention;

[0023] Figure 6 This is a schematic diagram of the skeleton component radially flared according to Embodiment 1 of the present invention;

[0024] Figure 7 This is a schematic diagram of the skeleton assembly with maximum radial flare in Embodiment 1 of the present invention;

[0025] Figure 8 This is an axial cross-sectional view of the skeleton shaft in Embodiment 1 of the present invention;

[0026] Figure 9 This is a schematic diagram of the fit between the skeleton shaft and the base when the skeleton assembly is radially narrowed according to Embodiment 1 of the present invention.

[0027] Figure 10 This is a schematic diagram of the fit between the skeleton shaft and the base when the skeleton assembly is radially flared according to Embodiment 1 of the present invention.

[0028] Figure 11 This is a schematic diagram of the base according to Embodiment 1 of the present invention;

[0029] Figure 12 This is a schematic diagram of the lateral guide shaft according to Embodiment 1 of the present invention;

[0030] Figure 13 yes Figure 10 Axial top view;

[0031] Figure 14 This is a schematic diagram of the fit between the side guide shaft and the base in Embodiment 1 of the present invention;

[0032] Figure 15 This is a schematic diagram of the connection between the connecting shaft and the skeleton shaft in Embodiment 1 of the present invention;

[0033] Figure 16 This is a schematic diagram of the connecting shaft and the driving part according to Embodiment 1 of the present invention;

[0034] Figure 17 This is a schematic diagram of Embodiment 2 of the present invention, in which the pressing base is in a contracted state and most of the hemostatic device is located in the delivery tube;

[0035] Figure 18 This is a schematic diagram of Embodiment 2 of the present invention, showing the pressing base in a contracted state and the hemostatic device mostly located outside the delivery device;

[0036] Figure 19 This is a schematic diagram of the pressing base in the expanded state according to Embodiment 2 of the present invention;

[0037] Figure 20 This is a schematic diagram of the laparoscopic surgical system according to Embodiment 3 of the present invention.

[0038] In the attached image:

[0039] 10-Skeleton assembly; 11-Skeleton shaft; 110-First conveying channel;

[0040] 20 - Pressing base; 200 - Second conveying channel;

[0041] 30 - Drive assembly; 31 - Drive unit; 32 - Connecting shaft;

[0042] 40 - Base; 41 - First mounting slot; 410 - Drain hole; 42 - Second mounting slot;

[0043] 50-Side guide shaft;

[0044] 60-pin;

[0045] 70 - Outer delivery pipe;

[0046] 81-Display screen; 82-Angiography machine; 83-Blood drawing channel; 84-Blood drawing mechanism. Detailed Implementation

[0047] To make the objectives, advantages, and features of this invention clearer, the invention will be further described in detail below with reference to the accompanying drawings and specific embodiments. It should be noted that the drawings are all in a very simplified form and are not drawn to scale, and are only used to facilitate and clarify the explanation of the embodiments of this invention. Furthermore, the structures shown in the drawings are often part of the actual structures. In particular, different figures may emphasize different aspects and may sometimes use different scales.

[0048] As used in this invention, the singular forms “a,” “an,” and “the” include plural objects; the term “or” is generally used to mean “and / or”; the term “a number” is generally used to mean “at least one”; and the term “at least two” is generally used to mean “two or more”. Furthermore, the terms “first,” “second,” and “third” are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of indicated technical features. Thus, a feature defined as “first,” “second,” or “third” may explicitly or implicitly include one or at least two of that feature. “One end” and “the other end,” as well as “proximal end” and “distal end,” generally refer to two corresponding parts, including not only endpoints. The terms “installed,” “connected,” and “joined” should be interpreted broadly, for example, as a fixed connection, a detachable connection, or an integral part; a mechanical connection or an electrical connection; a direct connection or an indirect connection through an intermediate medium; or a connection within two elements or an interaction between two elements. Furthermore, as used in this invention, the phrase "one element is disposed on another element" generally only indicates that there is a connection, coupling, cooperation, or transmission relationship between the two elements, and the connection, coupling, cooperation, or transmission between the two elements can be direct or indirect through an intermediate element. It should not be construed as indicating or implying a spatial positional relationship between the two elements, i.e., one element can be located arbitrarily inside, outside, above, below, or to one side of the other element, unless otherwise explicitly stated. Those skilled in the art can understand the specific meaning of the above terms in this invention according to the specific circumstances.

[0049] It should be noted that the terms "proximal" and "distal" in this article are defined as follows: "proximal" usually refers to the end of the medical device that is closer to the operator during normal operation, while "distal" usually refers to the end of the medical device that first enters the patient's body during normal operation.

[0050] The core idea of ​​this invention is to provide a hemostatic device and a laparoscopic surgical system, wherein the hemostatic device includes a skeleton assembly and a pressing base disposed on the skeleton assembly; the proximal end of the pressing base converges and retracts to its own axis (which can be understood as the proximal end of the pressing base converging radially inward to a point), and the distal end of the pressing base switches between a contracted state and an expanded state under the drive of the skeleton assembly. Understandably, when the distal end of the pressure base is in a contracted state, it contracts radially inward and closes (i.e., contracts along its own axis). Furthermore, when the distal end of the pressure base is in a contracted state, it is roughly linear along its own axis. When the distal end of the pressure base is in an expanded state, it expands radially outward (i.e., expands away from its own axis). Furthermore, when the distal end of the pressure base is in an expanded state, it roughly takes the form of a cone (e.g., a cone) or a frustum (e.g., a frustum of a cone or a truncated pyramid), where the distal end of the pressure base is the base of the cone or frustum, and the proximal end is the top. With this configuration, both the proximal and distal ends of the pressure base can enter the patient's body in a contracted state. After determining the location of the bleeding point, the distal end of the pressure base, driven by the skeletal components, expands to press against and apply pressure to the bleeding point, thereby quickly and effectively suppressing the bleeding. The present invention has a simple structure. It can enter the patient’s body and perform hemostasis by changing the shape of the pressing base under the drive of the skeleton component, which improves the operability and effectiveness of hemostasis in surgery.

[0051] The hemostatic device and laparoscopic surgical system of the present invention will be described in detail below with reference to the accompanying drawings.

[0052] Example 1

[0053] Please refer to this embodiment. Figures 1 to 16 .

[0054] Figure 1 This is a schematic diagram of the hemostatic device according to Embodiment 1 of the present invention when the pressing base is in the expanded state. Figure 3 This is a schematic diagram of the pressing base in a contracted state according to Embodiment 1 of the present invention. Figure 4 This is a schematic diagram of the pressing base in the expanded state according to Embodiment 1 of the present invention. (See attached diagram.) Figure 1 , Figure 3 and Figure 4 The present invention provides a hemostatic device, which includes a skeleton assembly 10 and a pressing base 20 disposed on the skeleton assembly 10; the proximal end of the pressing base 20 converges to its own axis (in this embodiment, the axis of the pressing base 20 can be denoted as H), and the distal end of the pressing base 20 switches between a contracted state and an expanded state under the drive of the skeleton assembly 10.

[0055] Further reading Figure 3 and Figure 4 The pressing base 20 has a second conveying channel 200 extending along its own axial direction. Based on this, when the distal end of the pressing base 20 is in a contracted state, the pressing base 20 is generally tubular along its own axial direction, and correspondingly, the second conveying channel 200 is also tubular; when the distal end of the pressing base 20 is in an expanded state, the pressing base 20 is generally trumpet-shaped, and correspondingly, the second conveying channel 200 is also trumpet-shaped. The skeleton assembly 10 is enclosed within the tubular or trumpet-shaped interior, or the skeleton assembly 10 is enclosed on the outer periphery of the tubular or trumpet-shaped exterior, thereby allowing the shape of the pressing base 20 to change through the characteristics of the skeleton assembly 10 itself. In one embodiment, the pressing base 20 is configured to be formed by winding a thin film. Specifically, after the film is wound once, a hollow hole is formed, which is the second delivery channel 200, and the axis of the hollow hole is the axis H. When the pressing base 20 is connected to the skeleton assembly 10, the hollow hole and the skeleton assembly 10 are substantially coaxial. Typically, the proximal end of the pressing base 20 is connected to the inner tube inserted in the outer tube 70, so that the second delivery channel 200 communicates with the inner tube. When the skeleton assembly 10 drives the distal end of the pressing base 20 to abut against the bleeding point in an expanded form, a large amount of blood can be quickly aspirated through the second delivery channel 200, the inner tube, and the external suction device.

[0056] Furthermore, when the distal end of the pressing base 20 transitions between the contracted and expanded states, the proximal and distal ends of the pressing base 20 move closer to or further away from each other axially. That is, when the distal end of the pressing base 20 transitions from the contracted to the expanded state, the proximal and distal ends of the pressing base 20 move closer to each other axially; when the distal end of the pressing base 20 transitions from the expanded to the contracted state, the proximal and distal ends of the pressing base 20 move further away from each other axially. Specifically, during the process of the skeleton component 10 driving the distal end of the pressing base 20 to change from a contracted state to an expanded state, the proximal and distal ends of the pressing base 20 move closer to each other, the axial length of the pressing base 20 gradually decreases, and the pressing base 20 as a whole tends to unfold in a planar shape, with the distal end of the pressing base 20 gradually surrounding the proximal end; during the process of the skeleton component 10 driving the distal end of the pressing base 20 to change from an expanded state to a contracted state, the proximal and distal ends of the pressing base 20 move further apart, the axial length of the pressing base 20 gradually increases, and the pressing base 20 as a whole tends to contract in a linear shape. Figure 2 This is a schematic diagram of the hemostatic device in Embodiment 1 of the present invention when the pressing base is in its maximum expansion state. Further, please refer to... Figure 2The distal end of the pressing base 20 can be expanded to the maximum expansion state. When it is in the maximum expansion state, the proximal and distal ends of the pressing base 20 are roughly on the same plane, so that the area of ​​the distal end of the pressing base 20 reaches the maximum and the contact area with the bleeding site is increased.

[0057] Regarding the specific way in which the skeleton component 10 drives the shape change of the pressing base 20, for example, the skeleton component 10 may be surrounded on the tubular or trumpet-shaped inner periphery of the pressing base 20 (i.e., on the inner wall of the second conveying channel 200), or the skeleton component 10 may be surrounded on the tubular or trumpet-shaped outer periphery of the pressing base 20, thereby driving the shape change of the pressing base 20 through the structural characteristics of the skeleton component 10 itself. When the skeleton component 10 and the pressing base 20 are arranged in the above manner, the two are basically coaxial. For example, the structural characteristics of the skeleton component 10 include: the proximal ends of the skeleton component 10 converge at a single point; the distal end of the skeleton component 10 is used to expand outward along the radial direction of the pressing base 20 (i.e., expand towards the axis H away from the pressing base 20), analogous to the blooming process of multiple petals of a flower; and the distal end of the skeleton component 10 is used to contract inward along the radial direction of the pressing base 20 (i.e., contract towards the axis H closer to the pressing base 20), analogous to the closing process of multiple petals of a flower. Thus, when the skeleton component 10 expands outward along the radial direction of the pressing base 20 in a trumpet shape, the distal end of the pressing base 20 is in the expanded state; and when the skeleton component 10 contracts inward along the radial direction of the pressing base 20 in a straight line, the distal end of the pressing base 20 is in the contracted state. That is, the pressing base 20 disposed on the skeleton assembly 10 can change its distal end from a contracted state to an expanded state as the skeleton assembly 10 widens, and can change its distal end from an expanded state to a contracted state as the skeleton assembly 10 narrows. It should be noted that the convergence of the proximal ends of the skeleton assembly 10 at a single point can be understood as the proximal ends of the skeleton assembly 10 converging near the axis H of the pressing base 20, or the proximal ends of the skeleton assembly 10 converging on the axis H of the pressing base 20. In one embodiment, the pressing base 20 is disposed on the skeleton assembly 10 in a specific manner, such as by covering the skeleton assembly 10, either inside or around it, changing its shape as the skeleton assembly 10 narrows or widens. The pressing base 20 is made of an elastic material, such as silicone or a thin film.

[0058] Figure 5 This is a schematic diagram of the skeleton component radially narrowed according to Embodiment 1 of the present invention. Figure 6 This is a schematic diagram of the radially flared skeleton assembly according to Embodiment 1 of the present invention. Further, see... Figure 5 and Figure 6The skeleton assembly 10 includes at least three skeleton shafts 11 circumferentially distributed around the axis H of the pressing base 20 (preferably, the at least three skeleton shafts 11 are circumferentially equidistant). The proximal ends of the skeleton shafts 11 are fixed in a radial position along the pressing base 20, that is, the proximal ends of the skeleton shafts 11 are fixed in a direction perpendicular to the axis H. The distal ends of the skeleton shafts 11 are arranged radially offset along the pressing base 20, that is, the distal ends of the skeleton shafts 11 are movable radially along the pressing base 20. Preferably, the skeleton shafts 11 are substantially coplanar with the axis H during offset. In this way, the distal end of the skeleton assembly 10 can be narrowed / expanded by offsetting the distal ends of the skeleton shafts 11 radially inward / outward along the pressing base 20, thereby driving the distal end of the pressing base 20 into a contracted or expanded state. Understandably, when the distal end of the skeleton assembly 10 is radially constricted inward along the pressing base 20 to make the skeleton assembly 10 straight, the axial direction of the skeleton shaft 11 is approximately parallel to the axis H of the pressing base 20. When the distal end of the skeleton assembly 10 is radially flared outward along the pressing base 20 to form a trumpet shape, the axial direction of the skeleton shaft 11 is arranged at an angle to the axis H (the angle being, for example, 45°, 60°, or 75°). Furthermore, please refer to... Figure 7 , Figure 7 This is a schematic diagram of the skeleton assembly at its maximum radial flare in Embodiment 1 of the present invention. When the distal end of the skeleton assembly 10 reaches its maximum radial flare to allow the pressing base 20 to reach its maximum expansion state, the axial direction of the skeleton shaft 11 can be considered to be substantially perpendicular to the axis H of the pressing base 20. It should be noted that the skeleton shaft 11 in this embodiment should not be narrowly interpreted as a straight shaft, but should be broadly understood as an shaft that extends approximately in a certain direction, such as the skeleton shaft 11 extending in a wavy shape.

[0059] Figure 8 This is an axial cross-sectional view of the skeleton shaft according to Embodiment 1 of the present invention. Preferably, see... Figure 8 The skeleton shaft 11 has a first delivery channel 110 that extends from its proximal end to its distal end. For example, the first delivery channel 110 can extend along the axial direction of the skeleton shaft 11. In a specific application scenario, after the pressing base 20 expands radially with the skeleton assembly 10 to adhere to the lesion site of the predetermined object (such as a bleeding site in a patient's cavity), a large amount of blood that has filled the cavity can be drawn out of the cavity through the first delivery channel 110. Then, hemostatic drugs can be sprayed onto the bleeding site through the first delivery channel 110, thereby further improving the hemostatic effect after the pressing base 20 is pressed against the bleeding site. Preferably, the distal end of the skeleton shaft 11 is configured to bend towards the axis H. This can also be understood as at least a portion of the distal end of the skeleton shaft 11 being configured to extend radially inward along the pressing base 20, so that the opening of the distal end of the first delivery channel 110 faces the axis H. This helps to improve the accuracy of spraying hemostatic drugs onto the bleeding site and enhance the hemostatic effect.

[0060] In this embodiment, the radial offset of the skeleton shaft 11 can be achieved through the characteristics of the mechanical structure. Specifically, the skeleton shaft 11 is rotatably arranged, and the axis of rotation of the skeleton shaft 11 is the tangent line on the skeleton assembly 10 at the proximal end of the skeleton shaft 11, and the skeleton shaft 11 is perpendicular to this tangent line. It is understood that at least three skeleton shafts 11 are arranged circumferentially (i.e., in the circumferential direction) around the axis H to form the skeleton assembly 10, with the proximal end of the skeleton shaft 11 being the tangent point on this circumference, and the axis of rotation of the skeleton shaft 11 being the tangent line at that tangent point. Thus, the radial offset of the skeleton shaft 11 along the pressing base 20 can be achieved through the rotatable mechanical characteristic of the skeleton shaft 11.

[0061] Figure 9 This is a schematic diagram of the fit between the skeleton shaft and the base when the skeleton assembly is radially narrowed according to Embodiment 1 of the present invention. Figure 10 This is a schematic diagram illustrating the fit between the skeleton shaft and the base when the skeleton assembly is radially flared according to Embodiment 1 of the present invention. In one embodiment, see [reference needed]. Figure 9 and Figure 10 The hemostatic device includes a base 40, a skeleton assembly 10 disposed on the base 40, and a skeleton shaft 11 rotatably mounted on the base 40 via a shaft-hole fitting. The base 40 can be positioned at the distal end of the delivery tube 70 of the laparoscopic surgical system. For details, see [link to relevant documentation]. Figure 11 , Figure 11 This is a schematic diagram of the base according to Embodiment 1 of the present invention. The base 40 has at least three first mounting grooves 41 and at least three second mounting grooves 42 circumferentially distributed around axis H. The number of first mounting grooves 41 and the number of second mounting grooves 42 are equal to the number of skeleton shafts 11, and the first mounting grooves 41 correspond one-to-one with the skeleton shafts 11. Furthermore, one second mounting groove 42 is arranged in every two adjacent first mounting grooves 41, and one first mounting groove 41 is arranged in every two adjacent second mounting grooves 42. Further, see... Figure 12 , Figure 13 and Figure 14 , Figure 12 This is a schematic diagram of the side guide shaft according to Embodiment 1 of the present invention. Figure 13 yes Figure 10 Axial top view, Figure 14This is a schematic diagram of the cooperation between the lateral guide shaft and the base in Embodiment 1 of the present invention. The first mounting groove 41 accommodates the proximal end of its corresponding skeleton shaft 11. A lateral guide shaft 50 is installed on each side of the second mounting groove 42, and the lateral guide shaft 50 extends through a hole into the adjacent first mounting groove 41. The extended portion of the lateral guide shaft 50 is parallel to the tangent of the skeleton component 10 corresponding to the proximal end of the skeleton shaft 11, so that the proximal end of the skeleton shaft 11 is connected to the lateral guide shaft 50 through a shaft hole, thereby realizing the rotatability of the skeleton shaft 11. In addition, the lateral guide shaft 50 can be fixed to the base 40 by a pin 60. Furthermore, the first mounting groove 41 is provided with a drainage hole 410 that penetrates the base 40. A large amount of blood in the patient's cavity can be sucked out sequentially through the first delivery channel 110 of the skeleton shaft 11, the drainage hole 410 of the base 40, and the drainage channel in the delivery outer tube 70. It should be noted that if the rotation shaft at the proximal end of the skeleton shaft 11 is placed in the first mounting groove 41, this rotation shaft will inevitably cover part of the drainage hole 410, affecting the drainage function of the hemostatic device. In this embodiment, lateral guide shafts 50 that can extend to the adjacent first mounting are respectively provided on both sides of the second mounting groove 42, and the extended part is outside the range of the drainage hole 410. This can be further understood as dividing the rotation shaft corresponding to the proximal end of the skeleton shaft 11 into two sections and installing them on both sides of the first mounting groove 41 respectively, thereby avoiding the drainage hole 410 being partially covered.

[0062] Further, see Figure 6 The hemostatic device further includes a drive assembly 30 connected to the skeleton assembly 10, the drive assembly 30 being used to drive the skeleton shaft 11 to rotate. Regarding the specific manner in which the drive assembly 30 drives the skeleton shaft 11 to rotate, for example, the drive assembly 30 includes a drive unit 31 and at least three connecting shafts 32 corresponding one-to-one with the skeleton shaft 11. (See also...) Figure 15 and Figure 16 , Figure 15 This is a schematic diagram of the connection between the connecting shaft and the skeleton shaft in Embodiment 1 of the present invention. Figure 16This is a schematic diagram of the connecting shaft and the driving part according to Embodiment 1 of the present invention. One end of the connecting shaft 32 is rotatably connected to the driving part 31, and the other end of the connecting shaft 32 is rotatably connected to the skeleton shaft 11. The driving part 31 is movable along the axial direction of the pressing base 20. The rotatable connection between the connecting shaft 32 and the skeleton shaft 11 or the driving part 31 can be, for example, a hinge or a shaft-hole fit connection, and the present invention is not limited to this. In this way, the skeleton shaft 11 can be driven to offset radially along the pressing base 20 by the cooperation of the driving part 31, the connecting shaft 32 and the skeleton shaft 11. Specifically, when the drive unit 31 moves in the direction from the proximal end to the distal end, it drives at least three skeleton shafts 11 to be radially outward along the pressing base 20 via the connecting shaft 32, causing the distal end of the skeleton assembly 10 to widen; when the drive unit 31 moves in the direction from the distal end to the proximal end, it drives at least three skeleton shafts 11 to be radially inward along the pressing base 20 via the connecting shaft 32, causing the distal end of the skeleton assembly 10 to narrow. In one embodiment, the drive unit 31 extends along the axis H as a drive shaft, which axially movably passes through the base 40 and is inserted into the delivery outer tube 70.

[0063]

Example 2

[0064] Please refer to this embodiment. Figures 17 to 19 This embodiment only describes the differences from Embodiment 1; for the similarities, please refer to the description in Embodiment 1.

[0065] Unlike the first embodiment which uses mechanical structural features to achieve the radial offset function of the skeleton shaft 11, this embodiment uses the physical properties of the skeleton shaft 11 itself to make it offset radially along the pressing base 20.

[0066] Figure 17 This is a schematic diagram of Embodiment 2 of the present invention, showing the pressing base in a contracted state and most of the hemostatic device located in the delivery tube. Figure 18 This is a schematic diagram of Embodiment 2 of the present invention, showing the pressing base in a contracted state and most of the hemostatic device located outside the delivery device. Figure 19 This is a schematic diagram of the pressing base in the expanded state according to Embodiment 2 of the present invention. Specifically, see [link to related documentation]. Figure 17 , Figure 18 and 19 and in conjunction with reference Figure 3 and Figure 4The skeleton assembly 10 is made of shape memory alloy (such as nickel-titanium alloy), and the shape memory of the skeleton assembly 10 is configured such that the distal end of the skeleton assembly 10 flares outward along the radial direction of the pressing base 20. The skeleton assembly 10 is confined inside the delivery outer tube 70 in a radially inward constricted manner, thereby causing the pressing base 20 to be in a contracted state and accommodated within the delivery outer tube 70; when the skeleton assembly 10 is completely detached from the delivery outer tube 70, the skeleton assembly 10 will return to its original shape memory configuration, thereby causing the pressing base 20 to be in an expanded state.

[0067] Further reading Figure 19 The skeleton assembly 10 has at least three skeleton shafts 11 made of shape memory alloy. The skeleton shafts are coplanar with the axis H, and the shape memory of the skeleton shafts 11 is configured such that the skeleton shafts 11 and the axis H are arranged at an angle. It is understood that different angles between the shape memory of the skeleton shafts 11 and the axis H result in different flare sizes in the skeleton assembly 10, and consequently, different final expansion shapes at the distal end of the pressing base 20. Preferably, the angle between the skeleton shafts 11 and the axis H in the shape memory can be configured to be 90° or close to 90°, so that after the skeleton assembly 10 returns to its shape memory, the distal end of the pressing base 20 can achieve its maximum expansion shape, thereby expanding the contact area between the pressing base 20 and the lesion site and improving the hemostatic effect. Compared to Embodiment 1, this embodiment does not require an additional drive assembly 30, making the implementation simpler and saving materials.

[0068] Furthermore, the skeleton shaft 11 has a first delivery channel 110 (preferably axially continuous) penetrating its proximal and distal ends. The skeleton shaft 11 can be understood as a hollow tubular (metal tube), which serves as a blood suction channel or a drug delivery channel. Due to the physical properties of the skeleton shaft 11 itself, this embodiment does not require additional components such as the base 40, side guide shaft 50, and pin 60 compared to Embodiment 1. Therefore, it is not necessary to align and connect the first delivery channel 41 with the drainage hole 410 on the base 40, thus saving structural components. It should be noted that the cooperation between the drive component 30 and the mechanically structured skeleton component 10 in Embodiment 1 allows for arbitrary adjustment of the angle between the skeleton shaft 11 and the axis H during surgery, thereby arbitrarily adjusting the radial flare size of the skeleton component 11 and consequently arbitrarily adjusting the distal size of the pressing base 20 to change the pressing area on the bleeding site.

[0069] Furthermore, the compression base 20 has a second delivery channel 200 extending along its own axis, and the compression base 20 can be wrapped in a thin film around the outer periphery of the skeleton assembly 10. Typically, the proximal end of the compression base 20 is connected to the inner tube inserted in the delivery outer tube 70, so that the second delivery channel 200 communicates with the inner tube. When the skeleton assembly 10 is pushed out of the delivery outer tube 70 and returns to its memory shape, the skeleton assembly 10 drives the distal end of the compression base 20 to adhere to the bleeding point in an expanded shape. Subsequently, a large amount of blood can be rapidly aspirated through the second delivery channel 200, the inner tube, and the external suction device.

[0070]

Example 3

[0071] Please refer to this embodiment. Figure 20 .

[0072] This embodiment provides a laparoscopic surgical system, which includes the hemostatic instrument described above. The distal end of the pressing base 20 of the hemostatic instrument is expanded and abutted against the lesion site of the predetermined object under the drive of the skeleton assembly 10. Since the laparoscopic surgical system includes the hemostatic instrument described above, it also possesses the beneficial effects brought by the hemostatic instrument. Those skilled in the art can configure other components of the laparoscopic surgical system according to the prior art, which will not be described in detail in this invention.

[0073] For example, the laparoscopic surgical system also includes a detection and identification device for identifying the lesion site of a predetermined object. After the detection and identification device identifies the bleeding site of the patient, the distal end of the pressing base 20 of the hemostatic instrument is precisely placed against the bleeding site (such as the aorta) in an expanded form, and pressure is applied to stop the bleeding.

[0074] Figure 20 This is a schematic diagram of the laparoscopic surgical system according to Embodiment 3 of the present invention. In one embodiment, see [reference needed]. Figure 20 The detection and identification device includes several nanoscale robots, a display screen 81, an angiography machine 82, a blood collection channel, and a blood collection mechanism 84. First, after the angiography machine 82 identifies the blood vessels in the patient's body, several nanoscale robots are injected into the patient's body. The direction of blood flow is observed by the robots in conjunction with the angiography machine 82 and the display screen 81. Then, with the cooperation of the robots and the display screen 81, the location where blood accumulates in the patient's body, i.e., the bleeding site, is found. Next, the skeleton assembly 10 is driven to move so that the distal end of the pressing base is extended and placed against the bleeding site to stop the bleeding. Finally, the large amount of blood that has accumulated in the cavity is aspirated through the blood collection mechanism 84, the blood collection channel, the outer tube or the blood drainage channel within the outer tube, and the first delivery channel 110 of the skeleton shaft 11. The angiography machine 82 can be, for example, a digital subtraction angiography machine 82 (DSA), a CT angiography machine 82 (CTA), or a magnetic resonance angiography machine 82 (MRA).

[0075] In another embodiment, the angiography machine 82 first identifies the location of blood vessels in the patient's body and then determines the direction of blood flow using a phase comparison method. Next, the location of blood accumulation in the patient's body, i.e., the bleeding site, is determined by blood pressure detection and blood flow direction. Then, the skeleton assembly 10 is driven to move so that the distal end of the pressing base is extended and placed against the bleeding site to stop the bleeding. Finally, the large amount of blood that has accumulated in the cavity is drawn out through the blood drawing mechanism 84, the blood drawing channel, the outer tube or the blood drainage channel in the outer tube, and the first delivery channel 110 of the skeleton shaft 11.

[0076] It should be noted that the various embodiments in this specification are described in a progressive manner, with each embodiment focusing on the differences from other embodiments. Similar or identical parts between embodiments can be referred to mutually. In addition, the different parts between embodiments can also be combined with each other, and this invention does not limit this.

[0077] In summary, the hemostatic instrument and laparoscopic surgical system provided by this invention includes a skeleton assembly and a pressing base disposed on the skeleton assembly. The proximal end of the pressing base converges to its own axis, and the distal end of the pressing base switches between a contracted and an expanded state under the drive of the skeleton assembly. With this configuration, the pressing base enters the patient's body in a contracted state. After determining the location of the bleeding point, the distal end of the pressing base, driven by the skeleton assembly, expands to press against and apply pressure to the bleeding point, thereby rapidly and effectively suppressing the patient's bleeding. This invention has a simple structure; it only requires changing the shape of the pressing base under the drive of the skeleton assembly to enter the patient's body and perform hemostasis, improving the operability and effectiveness of hemostasis in surgical procedures.

[0078] The above description is only a description of preferred embodiments of the present invention and is not intended to limit the scope of the present invention in any way. Any changes or modifications made by those skilled in the art based on the above disclosure shall fall within the protection scope of the present invention.

Claims

1. A hemostatic device, characterized in that, It includes a skeleton assembly and a pressing base disposed on the skeleton assembly; the proximal end of the pressing base converges and retracts to its own axis, and the distal end of the pressing base changes between a contracted state and an expanded state under the drive of the skeleton assembly. The skeleton assembly includes at least three skeleton shafts circumferentially distributed around the axis of the pressing base. The proximal end of each skeleton shaft is fixed in a radial position along the pressing base, and the distal end of each skeleton shaft is arranged offset in a radial position along the pressing base. Each skeleton shaft has a first delivery channel penetrating its proximal and distal ends, the first delivery channel serving as a blood-absorbing channel or a drug delivery channel.

2. The hemostatic device according to claim 1, characterized in that, When the distal end of the pressing base transitions from the contracted state to the expanded state, the proximal end and the distal end of the pressing base move closer to each other axially; when the distal end of the pressing base transitions from the expanded state to the contracted state, the proximal end and the distal end of the pressing base move further apart axially.

3. The hemostatic device according to claim 1, characterized in that, The pressing substrate covers the skeleton assembly.

4. The hemostatic device according to claim 1, characterized in that, When the skeleton assembly expands outward along the radial direction of the pressing base to form a trumpet shape, the distal end of the pressing base is in the expanded state; when the skeleton assembly contracts inward along the radial direction of the pressing base to form a straight line, the distal end of the pressing base is in the contracted state.

5. The hemostatic device according to claim 1, characterized in that, The skeleton shaft is rotatable, and the axis of rotation of the skeleton shaft is a tangent to the skeleton assembly at the proximal end of the skeleton shaft; the hemostatic device includes a drive assembly connected to the skeleton assembly, the drive assembly being used to drive the skeleton shaft to rotate.

6. The hemostatic device according to claim 5, characterized in that, The drive assembly includes a drive unit and at least three connecting shafts corresponding one-to-one with the skeleton shaft; one end of each connecting shaft is rotatably connected to the drive unit, and the other end of each connecting shaft is rotatably connected to the skeleton shaft; the drive unit is movable along the axial direction of the pressing base.

7. The hemostatic device according to claim 1, characterized in that, The skeleton component is made of shape memory alloy, and the shape memory of the skeleton component is configured such that the distal end of the skeleton component flares outward along the radial direction of the pressing base.

8. The hemostatic device according to claim 1, characterized in that, The pressing base has a second conveying channel that runs through its own axial direction.

9. A laparoscopic surgical system, characterized in that, The hemostatic device includes any one of claims 1 to 8, wherein the distal end of the pressing base of the hemostatic device is used to abut against the lesion site of a predetermined object in an expanded form.

10. The laparoscopic surgical system according to claim 9, characterized in that, The laparoscopic surgical system includes a detection and identification device for detecting and identifying the lesion site.

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