Guide wire conveying system

Abstract

The utility model relates to a guide wire conveying system which comprises a guide wire and an outer sheath tube, a guide wire channel, an inflation channel and a blood drawing channel are arranged in the outer sheath tube, an air bag is connected to the outer sheath tube, the inflation channel is communicated with the air bag, and the blood drawing channel is communicated with the air bag. The guide wire channel, the inflation channel and the blood drawing channel all extend in the extension direction of the outer sheath tube, the guide wire channel and the blood drawing channel penetrate through the two ends of the outer sheath tube, and the guide wire penetrates through the guide wire channel. When the guide wire penetrates through the vein valve, the vein valve can be controlled to be opened, so that the guide wire can pass through the vein valve in a lossless mode, it is guaranteed that the guide wire cannot damage the vein valve, and the effect of an interventional operation is improved.

Description

Technical Field

[0001] This utility model relates to the field of medical device technology, specifically to a guidewire delivery system. Background Technology

[0002] For some interventional procedures (such as venous thrombectomy), the guidewire passes through a vein. There are venous valves in the local vein. When the guidewire passes through the venous valve, it needs to pass through at the moment when the venous valve opens. However, the timing of the venous valve opening is currently difficult to determine. Therefore, in actual clinical practice, when the guidewire passes through the venous valve, it often relies on the experience of the operator. As a result, there is a situation where the guidewire punctures the venous valve. In severe cases, it can cause damage to the venous valve, which can lead to venous reflux in the vein. Utility Model Content

[0003] In view of this, the present invention provides a guidewire delivery system that facilitates the insertion of the guidewire into the vein. When the guidewire passes through the venous valve, the system can control the opening of the venous valve, thereby allowing the guidewire to pass through the venous valve without damage and ensuring that the guidewire does not damage the venous valve, thus improving the effectiveness of interventional surgery.

[0004] The technical solution adopted in this utility model is as follows:

[0005] A guidewire delivery system includes a guidewire and an outer sheath. The outer sheath has a guidewire channel, an inflation channel, and a blood sampling channel. An air bladder is connected to the outer sheath. The inflation channel communicates with the air bladder. The guidewire channel, the inflation channel, and the blood sampling channel all extend along the extension direction of the outer sheath. The guidewire channel and the blood sampling channel pass through both ends of the outer sheath. The guidewire passes through the guidewire channel.

[0006] Preferably, the outer sheath includes an inner tube and an outer tube, a main channel is formed inside the inner tube, the outer tube is sleeved on the outside of the inner tube, the outer tube and the inner tube form the inflation channel, the distal end of the inner tube is connected to the distal end of the outer tube to close the distal end of the inflation channel; the airbag is connected to the outer tube, and the main channel serves as both the guide wire channel and the inflation channel.

[0007] Preferably, the inner diameter of the main channel is larger than the outer diameter of the guidewire, the guidewire is inserted into the main channel, and the portion of the main channel outside the guidewire constitutes the blood drawing channel.

[0008] Preferably, it further includes a Y-type connector, which is connected to the proximal side of the outer sheath. The Y-type connector includes a first connector, a second connector, and a third connector that are connected to each other. The first connector is connected to the proximal end of the main channel, the second connector is used for the guidewire to pass through the main channel, and the third connector is used for connection to the blood pump.

[0009] Preferably, the outer tube includes a first segment and a second segment, the first segment and the second segment are spaced apart, the second segment is located on the distal side of the first segment, the airbag is sleeved on the outside of the inner tube, the proximal end of the airbag is connected to the distal end of the first segment, and the distal end of the airbag is connected to the proximal end of the second segment.

[0010] Preferably, the length of the second segment is 0-5 mm.

[0011] Preferably, the airbag includes a first connecting part, a second connecting part, and a pressing part, wherein the first connecting part and the second connecting part are both annular sheets, the pressing part is annular, and the cross surface of the pressing part is C-shaped;

[0012] An annular air supply gap is formed between the first segment and the second segment. The far end of the air supply gap is an annular first connecting end, and the near end of the air supply gap is an annular second connecting end. The radially inner side of the first connecting part is connected to the first connecting end, and the radially inner side of the second connecting part is connected to the second connecting end. The two side edges of the crimping part are the first side edge and the second side edge, respectively. The radially outer side of the first connecting part is connected to the first side edge, and the radially outer side of the second connecting part is connected to the second side edge.

[0013] In the radial direction of the outer sheath, from the inside out, the first connecting portion and the second connecting portion gradually approach each other.

[0014] Preferably, when the airbag is filled with gas, the center of the pressing part forms an annular pressing surface for pressing against the inner wall of the vein.

[0015] Preferably, the cross-section of the crimping portion includes a first C-shaped segment, a straight segment, and a second C-shaped segment connected in sequence, the first C-shaped segment and the second C-shaped segment being arranged opposite to each other, the straight segment constituting the crimping surface, and the length of the straight segment being consistent with the axial length of the air supply gap.

[0016] The beneficial effects of this utility model are:

[0017] When the guidewire is inserted into the vein, the balloon is in a contracted state, and the entire guidewire delivery system delivers the wire along the vein. Just before the distal end of the guidewire delivery system passes the venous valve, the delivery is stopped, and the balloon is inflated through the inflation channel. This causes the balloon to expand, its outer periphery adhering to the inner wall of the vein, creating a closed chamber between the balloon and the venous valve. The blood aspiration channel connects to this closed chamber, and blood is drawn through it. This draws blood from the closed chamber, reducing the pressure and creating a pressure difference across the venous valve. Under this pressure difference, the venous valve opens, allowing the guidewire to pass distally through the opened valve without damage. After the guidewire passes through the valve, blood aspiration is stopped, and the air in the balloon is removed, returning the balloon to a contracted state. The outer sheath is then removed, leaving the guidewire. The guidewire can then guide the necessary structures for the interventional procedure, improving its effectiveness. Attached Figure Description

[0018] The above and other objects, features and advantages of the present invention will become clearer from the following description of embodiments of the present invention with reference to the accompanying drawings, in which:

[0019] Figure 1 This is a schematic diagram of the guide wire delivery system;

[0020] Figure 2 This is a schematic diagram of the guidewire delivery system being delivered distally to the venous valve.

[0021] Figure 3 This is a schematic diagram of an airbag inflating to form a closed chamber;

[0022] Figure 4 This is a diagram illustrating how blood draw causes the venous valves to open.

[0023] Figure 5 This is a schematic diagram of the guidewire passing through the venous valve;

[0024] Figure 6 This is a schematic diagram of the airbag returning to its contracted state.

[0025] In the diagram: 1. Outer sheath; 2. Guidewire; 3. Airbag;

[0026] 11. Inner tube; 12. Outer tube; 13. Inflation channel;

[0027] 31. First connecting part; 32. Second connecting part; 33. Crimping part;

[0028] 331. First C-shaped segment; 332. Second C-shaped segment; 333. Straight line segment. Detailed Implementation

[0029] The present invention will now be described based on embodiments, but the present invention is not limited to these embodiments. In the following detailed description of the present invention, some specific details are described in detail, but well-known methods, processes, procedures, and elements are not described in detail in order to avoid obscuring the essence of the present invention.

[0030] Furthermore, those skilled in the art should understand that the accompanying drawings provided herein are for illustrative purposes only and are not necessarily drawn to scale.

[0031] Unless the context explicitly requires it, the words "comprising," "including," and similar terms throughout the specification and claims should be interpreted as encompassing rather than being exclusive or exhaustive; that is, meaning "including but not limited to."

[0032] In the description of this utility model, it should be understood that the terms "first," "second," etc., are used for descriptive purposes only and should not be construed as indicating or implying relative importance. Furthermore, in the description of this utility model, unless otherwise stated, "a plurality of" means two or more.

[0033] In this invention, during surgery, the end furthest from the operator is called "far," and the side closest to the operator is called "near."

[0034] See Figures 1-6 This utility model provides a guidewire delivery system for delivering a guidewire 2 within a vein, ensuring that the guidewire 2 does not puncture the venous valves during delivery. The guidewire delivery system includes a guidewire 2 and an outer sheath 1. The outer sheath 1 has a guidewire 2 channel, an inflation channel 13, and a blood draw channel. An air bag 3 is connected to the outer sheath 1. The inflation channel 13 communicates with the air bag 3. The guidewire 2 channel, the inflation channel 13, and the blood draw channel all extend along the extension direction of the outer sheath 1. The guidewire 2 channel and the blood draw channel pass through both ends of the outer sheath 1. The guidewire 2 passes through the guidewire 2 channel.

[0035] Guidewire 2 is inserted into the guidewire 2 channel of the outer sheath 1. When guidewire 2 is delivered in the vein, the entire guidewire delivery system is delivered along the vein. For the guidewire delivery system, at this time, the distal ends of the outer sheath 1 and guidewire 2 are basically flush. In the vein, the delivery direction of the guidewire delivery system is against the direction of blood flow, that is, from downstream to upstream. When the distal end of the guidewire delivery system reaches the venous valve ( Figure 2 (As shown), the guidewire delivery system is stopped, and air is inflated into the balloon 3 through the inflation channel 13, causing the balloon 3 to expand and the outer periphery of the balloon 3 to adhere to the inner wall of the vein. Figure 3(As shown), this creates a closed chamber between the balloon 3 and the venous valve. The distal end of the blood-drawing channel connects to this closed chamber. Blood is drawn through the blood-drawing channel, removing blood from the closed chamber and reducing the pressure within it. This creates a pressure difference across the venous valve (the blood pressure upstream of the venous valve is greater than the blood pressure downstream). Under this pressure difference, the venous valve opens (the two valves in the venous valve separate). Figure 4 As shown), guidewire 2 is advanced distally (outer sheath 1 remains stationary), allowing guidewire 2 to pass through the opened venous valve. Figure 5 (As shown), thus enabling the guidewire 2 to pass through the venous valve without damage; after the guidewire 2 passes through the venous valve, blood aspiration is stopped, and the gas in the balloon 3 is removed, causing the balloon 3 to return to its contracted state. Figure 6 (As shown), at this time the closed chamber is connected to the downstream, and the venous valves are freely opened or closed under the control of blood flow.

[0036] In this invention, the guidewire 2 extends along the extension direction of the outer sheath 1 and passes through both ends of the outer sheath 1, allowing the guidewire 2 to be pulled relative to the outer sheath 1. After the balloon 3 is inflated, the outer sheath 1 is anchored relative to the vein, and the blood pump can be operated on the proximal side to draw blood through the blood draw channel. Since the guidewire 2 can be pulled relative to the outer sheath 1, the guidewire 2 can be delivered distally, allowing the distal end of the guidewire 2 to move toward the venous valve and pass through the gap between the two valves.

[0037] The inflation channel 13 is connected to the airbag 3, so air can be inflated or deflated through the proximal end of the inflation channel 13, thereby controlling the expansion and contraction of the airbag 3.

[0038] The proximal end of the blood collection channel is connected to the proximal end of the outer sheath 1, so the proximal end of the blood collection channel can be connected to the blood collection pump. Through the operation of the blood collection pump, blood can be drawn to reduce the pressure in the closed chamber.

[0039] During the procedure, the distal end of the guidewire delivery system is approximately close to the venous valve (for example, the distance between the distal end of the delivery system and the venous valve is within 6 mm). Therefore, the distance between the balloon 3 and the distal end of the sheath is positively correlated with the size of the closed chamber. The distance between the balloon 3 and the distal end of the outer sheath 1 is controlled within 6 mm, resulting in a smaller volume of the closed chamber. Thus, during blood draw, the pressure within the closed chamber can be reduced instantly, ensuring that the venous valve can be fully opened, that the guidewire 2 can pass smoothly through the venous valve, and that the guidewire 2 will not puncture the venous valve during delivery, thereby improving the safety of the procedure.

[0040] The outer sheath 1 includes an inner tube 11 and an outer tube 12. A main channel is formed inside the inner tube 11. The outer tube 12 is sleeved on the outside of the inner tube 11. The outer tube 12 and the inner tube 11 form the inflation channel 13. The distal end of the inner tube 11 is connected to the distal end of the outer tube 12 to close the distal end of the inflation channel 13. The airbag 3 is connected to the outer tube 12. The main channel serves as both the guide wire 2 channel and the inflation channel 13.

[0041] The inner diameter of the inner tube 11 is larger than the outer diameter of the guide wire 2, and the outer diameter of the inner tube 11 is smaller than the inner diameter of the outer tube 12, so that an annular cavity (inflation channel 13) is formed between the inner tube 11 and the outer tube 12. The distal end of the inner tube 11 is connected to the distal end of the outer tube 12, so that the inner tube 11 and the outer tube 12 form a whole and seal the distal end of the inflation channel 13. An airbag 3 is connected to the outer tube 12, so the airbag 3 can be inflated and deflated through the inflation channel 13.

[0042] The inner diameter of the main channel is larger than the outer diameter of the guidewire 2. The guidewire 2 is inserted into the main channel, and the part of the main channel outside the guidewire 2 constitutes the blood drawing channel.

[0043] In this invention, the inner diameter of the main channel is relatively large, which allows the main channel to serve as both a guidewire channel 2 and a blood collection channel, thus enabling the main channel to achieve functional reuse.

[0044] It also includes a Y-type connector, which is connected to the proximal side of the outer sheath 1. The Y-type connector includes a first connector, a second connector, and a third connector that are connected to each other. The first connector is connected to the proximal end of the main channel, the second connector is used for the guidewire 2 to pass through the main channel, and the third connector is used for connection to the blood pump.

[0045] The outer tube 12 includes a first section and a second section, which are spaced apart. The second section is located at the distal end of the first section. The airbag 3 is sleeved on the outside of the inner tube 11. The proximal end of the airbag 3 is connected to the distal end of the first section, and the distal end of the airbag 3 is connected to the proximal end of the second section. This ensures a seamless connection between the airbag 3 and the outer tube 12, guaranteeing that the inflation channel 13 can efficiently inflate and deflate the airbag 3.

[0046] The second segment has a length of 0-5 mm. This allows the airbag 3 to be closer to the distal end of the outer sheath 1, reducing the volume of the sealed chamber.

[0047] The airbag 3 includes a first connecting part 31, a second connecting part 32 and a pressing part 33. The first connecting part 31 and the second connecting part 32 are both annular sheets. The pressing part 33 is annular and its cross surface is C-shaped.

[0048] An annular air supply gap is formed between the first segment and the second segment. The far end of the air supply gap is an annular first connecting end, and the near end of the air supply gap is an annular second connecting end. The radially inner side of the first connecting part 31 is connected to the first connecting end, and the radially inner side of the second connecting part 32 is connected to the second connecting end. The two side edges of the crimping part 33 are the first side edge and the second side edge, respectively. The radially outer side of the first connecting part 31 is connected to the first side edge, and the radially outer side of the second connecting part 32 is connected to the second side edge.

[0049] In the radial direction of the outer sheath 1, from the inside out, the first connecting part 31 and the second connecting part 32 gradually approach each other.

[0050] The first connecting part 31 and the second connecting part 32 lift the crimping part 33. The connection between the first connecting part 31 and the crimping part 33 is easy to bend, and the connection between the second connecting part 32 and the crimping part 33 is easy to bend. Therefore, when the airbag 3 contracts, the crimping part 33 can bend along these two connections, thereby allowing the airbag 3 to contract better.

[0051] When the airbag 3 is inflated, the center of the pressing part 33 forms an annular pressing surface for pressing against the inner wall of the vein. This allows the airbag 3 to better conform to the inner wall of the vein, thereby blocking the vein.

[0052] The cross-section of the crimping portion 33 includes a first C-shaped segment 331, a straight segment 333, and a second C-shaped segment 332 connected in sequence. The first C-shaped segment 331 and the second C-shaped segment 332 are arranged opposite to each other. The straight segment 333 forms the crimping surface. The length of the straight segment 333 is consistent with the axial length of the air supply gap.

[0053] It should be understood that the above-described embodiments are merely exemplary and not restrictive. Without departing from the basic principles of this utility model, any obvious or equivalent modifications or substitutions made by those skilled in the art regarding the above details will be included within the scope of the claims of this utility model.

Claims

1. A wire feeding system, characterized in that, The device includes a guidewire and an outer sheath. The outer sheath contains a guidewire channel, an inflation channel, and a blood sampling channel. An air bladder is connected to the outer sheath. The inflation channel communicates with the air bladder. The guidewire channel, the inflation channel, and the blood sampling channel all extend along the extension direction of the outer sheath. The guidewire channel and the blood sampling channel pass through both ends of the outer sheath. The guidewire passes through the guidewire channel.

2. The guide wire feeding system according to claim 1, characterized in that, The outer sheath includes an inner tube and an outer tube. A main channel is formed inside the inner tube. The outer tube is sleeved on the outside of the inner tube. The outer tube and the inner tube form the inflation channel. The distal end of the inner tube is connected to the distal end of the outer tube to seal the distal end of the inflation channel. The airbag is connected to the outer tube. The main channel serves as both the guide wire channel and the inflation channel.

3. The guide wire feeding system according to claim 2, characterized in that, The inner diameter of the main channel is larger than the outer diameter of the guidewire. The guidewire passes through the main channel, and the portion of the main channel outside the guidewire constitutes the blood drawing channel.

4. The guide wire feeding system according to claim 3, characterized in that, It also includes a Y-type connector, which is connected to the proximal side of the outer sheath. The Y-type connector includes a first connector, a second connector, and a third connector that are connected to each other. The first connector is connected to the proximal end of the main channel, the second connector is used for the guidewire to pass through the main channel, and the third connector is used for connection to the blood pump.

5. The guide wire feeding system according to claim 4, characterized in that, The outer tube includes a first section and a second section, which are spaced apart. The second section is located on the distal side of the first section. The airbag is sleeved on the outside of the inner tube. The proximal end of the airbag is connected to the distal end of the first section, and the distal end of the airbag is connected to the proximal end of the second section.

6. The guide wire feeding system according to claim 5, characterized in that, The length of the second segment is 0-5mm.

7. The guide wire feeding system according to claim 5, characterized in that, The airbag includes a first connecting part, a second connecting part, and a pressing part. The first connecting part and the second connecting part are both annular sheets. The pressing part is annular, and the cross surface of the pressing part is C-shaped. An annular air supply gap is formed between the first segment and the second segment. The far end of the air supply gap is an annular first connecting end, and the near end of the air supply gap is an annular second connecting end. The radially inner side of the first connecting part is connected to the first connecting end, and the radially inner side of the second connecting part is connected to the second connecting end. The two side edges of the crimping part are the first side edge and the second side edge, respectively. The radially outer side of the first connecting part is connected to the first side edge, and the radially outer side of the second connecting part is connected to the second side edge. In the radial direction of the outer sheath, from the inside out, the first connecting portion and the second connecting portion gradually approach each other.

8. The guide wire feeding system according to claim 7, characterized in that, When the airbag is filled with gas, an annular pressing surface is formed in the middle of the pressing part for pressing against the inner wall of the vein.

9. The wire feeding system according to claim 8, characterized in that, The cross-section of the crimping portion includes a first C-shaped segment, a straight segment, and a second C-shaped segment connected in sequence. The first C-shaped segment and the second C-shaped segment are arranged opposite to each other. The straight segment constitutes the crimping surface, and the length of the straight segment is consistent with the axial length of the air supply gap.

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