CN211325911U - Delivery guide wire and treatment device - Google Patents

Abstract

The utility model relates to a carry seal wire and treatment device, treatment device is including carrying seal wire, medical implant and conveyer pipe, carry the seal wire include the dabber with set up in the epaxial drive member of dabber, be formed with the depressed part on the drive member, medical implant quilt the conveyer pipe compression sleeve is established carry on the seal wire, just medical implant at least part imbeds in the depressed part to increase medical implant and carry the area of contact between the seal wire, be favorable to medical implant reduces the transport degree of difficulty along with carrying seal wire synchronous motion.

Description

Delivery guide wire and treatment device

Technical Field

The utility model relates to the technical field of medical equipment, concretely relates to carry seal wire and treatment device.

Background

Intracranial aneurysms are usually abnormal bulges on the wall of an intracranial artery, and are the first causes of subarachnoid hemorrhage. In cerebrovascular diseases, the incidence of intracranial aneurysm is second to cerebral thrombosis and hypertensive cerebral hemorrhage, and the intracranial aneurysm has great harm.

In the prior art, there are three main methods for treating intracranial aneurysms: (1) the surgical clamping method adopts a metal clamp to clamp the neck of the aneurysm to block intracranial aneurysm and cerebral circulation blood flow, and prevents the rupture and bleeding of the aneurysm while recovering normal blood supply of the parent artery. (2) The intratumoral embolization method adopts embolization materials to fill the aneurysm, so that thrombus is formed in the body of the aneurysm, and the rupture hemorrhage caused by further expansion of the body of the aneurysm is avoided. (3) The intravascular stent method is to implant a stent into a blood vessel to interfere the blood flow entering an aneurysm from a parent artery, so that the blood in the aneurysm is blocked and deposited, thereby forming aneurysm thrombus and further promoting the closure of the aneurysm body to prevent the rupture of the aneurysm body. Since aneurysms are generally longer than the periphery of the cerebral arterial loop, there are many important blood vessels, nerves and brain tissue around the cerebral arterial loop. When the surgical clamping method is used for treating the aneurysm, the medical requirements of doctors are extremely high, and the death rate of patients who treat the aneurysm by the surgical clamping method is still as high as 50 percent. When the intratumoral embolization method is simply used for treating large or huge complicated aneurysms, the recurrence rate of patients is high. Currently, the most widely used treatment for intracranial aneurysms is endovascular stenting.

Fig. 1 shows a treatment device for intracranial aneurysm treatment by using an intravascular stent method in the prior art, the treatment device includes a delivery guide wire 10 and a delivery tube 20, the delivery tube 20 has an inner cavity that axially penetrates through, a stent 30 to be delivered is accommodated in the inner cavity and sleeved on the delivery guide wire 10, and the delivery guide wire 10, the stent 30 and the delivery tube 20 are in an interference state. In this way, when the operator pushes the delivery guide wire 10 to move in the delivery tube 30, a first friction force is generated between the delivery guide wire 10 and the stent 20, and under the action of the first friction force, the stent 30 can move synchronously with the delivery guide wire 10 and finally reach the preset position. During which a second friction force, opposite to the first friction force, is generated between the stent 30 and the inner wall of the delivery tube 20 to resist movement of the stent 30 with the delivery guidewire 10. When the intracranial aneurysm is treated by adopting the intravascular stent method, the stent plays a role in guiding blood flow, so the stent has higher metal coverage rate, and the intracranial blood vessel is thin and roundabout, and needs to be conveyed by a small and flexible conveying device. This means that the fit between the stent and the delivery device is tighter than with a larger delivery device, resulting in a second friction force generated during delivery that is too high to make stent pushing difficult.

In order to smoothly push the delivery guide wire 10 in the delivery tube 30, the existing delivery guide wire 10 has a smooth outer surface, and in order to increase the first friction between the delivery guide wire 10 and the stent 30, a part of the delivery guide wire 10 is provided with a driving member having a relatively high friction coefficient. However, the arrangement of the entraining member causes the outer diameter of the stent loaded on the delivery guidewire 10 to increase, causing a second frictional force between the stent and the inner wall of the delivery tube 30 to increase, and at the same time, the outer diameter of the entire treatment device may also increase, making the treatment device difficult to use for the treatment of distal end vascular lesions. Also, if too many entraining members are provided or the length is too long, this may result in reduced compliance of the distal end of the delivery guidewire 10.

SUMMERY OF THE UTILITY MODEL

An object of the utility model is to provide a carry seal wire and treatment device can reduce the transport degree of difficulty of support.

In order to achieve the above object, the present invention provides a delivering guide wire for delivering medical implant, comprising a core shaft and a driving member disposed on the core shaft, wherein a recess is formed on the driving member.

Optionally, the carrying member includes a body and a groove formed on an outer surface of the body, and the groove forms the recess.

Optionally, the structure of the recess matches at least part of the structure of the medical implant in the compressed state.

Optionally, the recess is a mirror image of the inner surface of the medical implant in the compressed state.

Optionally, the groove has a width of 0.0008 inch to 0.004 inch.

Optionally, the groove has a depth of 0.0002 inch to 0.004 inch.

Optionally, the groove comprises one or more sub-grooves, and a plurality of the sub-grooves are arranged on the outer surface of the body in a staggered arrangement, a continuous arrangement or an interval arrangement.

Optionally, the groove is helically wound along the axis of the body to form one or more helical grooves in the outer surface of the body.

Optionally, the carrying member is spirally wound by a winding wire along the axis of the mandrel to form one or more spiral structures, and the winding wire of two adjacent circles are arranged at intervals to form the recess.

Optionally, the winding wire is a polymer wire or a metal wire coated with a polymer coating.

Optionally, the wire is developable.

Optionally, the metal wire is a platinum tungsten alloy wire or a platinum iridium alloy wire.

Optionally, the mandrel is provided with at least two driving members, and the at least two driving members are arranged along the axial direction of the mandrel at intervals.

Optionally, the distance between two adjacent driving members is 0.5mm-150 mm.

Optionally, the distance between two adjacent driving members is 0.5mm-5 mm.

Optionally, one or more driving members are arranged on the mandrel, the outer diameter of each driving member is 0.01-0.03 inch, and the length of each driving member is 0.5-8 mm.

Optionally, each of the entraining members has a length of 0.5mm to 4 mm.

Optionally, still include first development and second development, first development set up in the tip of the distal end of dabber, the second development set up in on the dabber, drive the component set up in first development with between the second development.

In order to achieve the above object, the present invention also provides a therapeutic device, comprising a delivery tube, a medical implant and the delivery guide wire; the delivery pipe is provided with an inner cavity which is axially communicated and is used for accommodating the medical implant, and the wall of the inner cavity extrudes the medical implant so as to enable the medical implant to be in a compressed state; the medical implant in a compressed state is sleeved on the driving component, and at least part of the medical implant is embedded into the concave part.

Optionally, the lumen has a radial dimension in a range of 0.017 inches to 0.029 inches.

Optionally, the medical implant is a self-expanding stent.

Compared with the prior art, the utility model discloses a carry seal wire and treatment device has following advantage:

the treatment device comprises a delivery guide wire, a medical implant and a delivery pipe, wherein the delivery guide wire comprises a mandrel and a driving component arranged on the mandrel, and a concave part is formed on the driving component. Utilize the conveying seal wire carries medical implant, medical implant is held in the conveyer pipe, just the pipe wall of conveyer pipe is used for the compression medical implant, the compression state medical implant cover is established drive on the component, just medical implant at least part embedding depressed part, thereby the increase the support with the area of contact who drives the component improves medical implant with carry frictional force between the seal wire, and can make medical implant with the part of conveyer pipe contact tends towards levelly and smoothly and reduces medical implant with conveyer pipe and frictional force between with, reduces medical implant's the transport degree of difficulty. Meanwhile, the outer diameter of the medical implant compressed in the delivery pipe is reduced, and the outer diameter of the delivery pipe can be correspondingly reduced, so that the treatment device can reach a more remote target treatment position, the treatment range is expanded, the overall flexibility of the treatment device can be improved, a tortuous blood vessel can be smoothly passed, and the success rate of the operation is improved.

Drawings

FIG. 1 is a schematic view of a prior art treatment apparatus;

FIG. 2 is a schematic view of a pushwire according to an embodiment of the present invention, with the depression not shown;

FIG. 3 is a schematic view of a pushwire according to an embodiment of the present invention showing a depression;

fig. 4 is a schematic structural view of a bracket according to an embodiment of the present invention;

FIG. 5 is a schematic view of a modified version of the delivery guidewire of FIG. 3;

FIG. 6 is a schematic view of another alternative configuration of the delivery guidewire of FIG. 3;

fig. 7 is a schematic structural view of a pushwire according to another embodiment of the present invention.

In the figure:

10, 100-delivery guide wire;

110-a mandrel;

120-driving component, 121-body, 122-groove, 123-gap;

130-a first development;

140-a second development;

20-a delivery pipe;

30, 300-scaffold;

310-weaving silk;

311-weaving points.

Detailed Description

To make the objects, advantages and features of the present invention clearer, the present invention will be described in further detail with reference to the accompanying drawings. It should be noted that the drawings are in simplified form and are not to precise scale, and are provided for convenience and clarity in order to facilitate the description of the embodiments of the present invention.

As used in this specification, the singular forms "a", "an" and "the" include plural referents, and the plural forms "a plurality" includes more than two referents unless the content clearly dictates otherwise. As used in this specification, the term "or" is generally employed in its sense including "and/or" unless the content clearly dictates otherwise, and the terms "mounted," "connected," and "connected" are to be construed broadly, e.g., as meaning either fixedly connected, detachably connected, or integrally connected. Either mechanically or electrically. Either directly or indirectly through intervening media, either internally or in any other relationship. The specific meaning of the above terms in the present invention can be understood according to specific situations by those skilled in the art. The same or similar reference numbers in the drawings identify the same or similar elements.

As used herein, the terms "proximal" and "distal" refer to the relative orientation, relative position, and orientation of elements or actions with respect to one another from the perspective of an operator using the medical device, although "proximal" and "distal" are not intended to be limiting, but generally refers to the end of the medical device that is closer to the operator during normal operation, and generally refers to the end that is first introduced into the patient.

The present embodiments provide a delivery guidewire for delivering a medical implant to a predetermined location within a patient. The medical implant is, for example, a self-expanding stent (i.e., a self-expanding stent), which may be, in particular, a braided stent or a cut stent. In other embodiments, the medical implant may also be a medical embolic coil, a vascular occlusion device, or the like, without limitation. Hereinafter, for the convenience of description, the medical implant is described as a self-expandable stent, and for the sake of simplicity, the self-expandable stent is uniformly referred to as a "stent".

Referring to fig. 2 and 3, the guide wire 100 includes a core shaft 110 and a driving member 120 disposed on the core shaft 110, wherein a recess is formed on the driving member 120.

When the stent is delivered, the stent is compressed in the lumen of a delivery tube (at this time, the stent is in a compressed state), and tightly sleeved on the driving member 120, so that the stent generates a radial pressure on the driving member 120, and at least a portion of the stent is embedded in the recess. Thus, the contact area between the bracket and the driving member 120 can be greatly increased. When the operator pushes the delivery guidewire 100 to move axially in the delivery tube, the first friction force generated between the stent and the driving member 120 can also be greatly increased, thereby facilitating the stent to move synchronously with the delivery guidewire 100. For the braided stent, the braided wires used for braiding the stent are different in thickness; similarly, for the cutting stent, the wave bars on the cutting stent have different thicknesses, and at this time, the thicker braided wire or wave bars can be embedded into the concave parts more under the pressure of the delivery pipe so that the surface of the stent, which is in contact with the delivery pipe (namely the outer surface of the stent), tends to be flat, thereby reducing the second friction force generated between the stent and the inner wall of the delivery pipe and reducing the pushing resistance of the stent during delivery.

Similar to conventional delivery guidewires, the delivery guidewire 100 of the present embodiment further includes a first visualization member 130 and a second visualization member 140. The core shaft 110 has a first distal end and a first proximal end opposite to each other, the first developing member 130 may be a developing spring and disposed at an end of the first distal end, the second developing member 140 is disposed on the core shaft 110, and the driving member 120 is disposed between the first developing member 130 and the second developing member 140, so that the bracket is disposed between the first developing member 130 and the second developing member 140.

In some embodiments, the driving member 120 may be made of a polymer material such as silicone, thermoplastic polyurethane elastomer rubber (TPU), polyimide, thermoplastic elastomer (Pebax), Polytetrafluoroethylene (PTFE), or the like. In other embodiments, the driving member 120 may be made of a metal material such as stainless steel, nitinol, platinum-tungsten alloy, etc.

The mandrel 110 is provided with a plurality of driving members 120, such as one, two, three, four, five, six, etc., and the specific number of the driving members 120 is determined according to the length of the stent to be delivered (i.e., the size of the stent in the axial direction). Generally, if the length of each of the driving members 120 is fixed, the greater the length of the stent, the greater the pushing resistance generated during the delivery, and more driving members 120 are needed to increase the first friction between the delivery guidewire 100 and the stent, so as to ensure that the stent moves synchronously with the delivery guidewire 100. In this embodiment, the outer diameter of each of the driving members 120 may be between 0.01 inch and 0.03 inch, the length of each of the driving members 120 is between 0.5mm and 8mm, and preferably, the length of each of the driving members 120 is between 0.5mm and 4 mm. When the mandrel 110 is provided with more than two driving members 120, the more than two driving members 120 are arranged at intervals along the axial direction of the mandrel 110. Optionally, the distance between two adjacent driving members 120 is between 0.5mm and 150mm, and preferably the distance is between 0.5mm and 5 mm.

On the one hand, compared with the method of increasing the first friction force by simply increasing the friction coefficient of the driving members 120, the larger first friction force can be obtained more easily by designing the number of the driving members 120 arranged on the mandrel 110 and the size of each driving member 120. On the other hand, compared to a continuous longer driving member disposed on the mandrel 110, the at least two spaced and shorter driving members 120 disposed on the mandrel 110 can reduce the total length of the driving members 120 and increase the recoverable rate of the stent (i.e., the smaller the total length of the driving members 120, the higher the recoverable rate of the stent). On the other hand, the plurality of short driving members 120 at intervals are arranged, so that the flexibility of the conveying guide wire 100 can be improved, the conveying guide wire 100 can conveniently pass through tortuous blood vessels, and meanwhile, the plurality of short driving members 120 are adopted, so that the driving members 120 can be made of materials with relatively high hardness (relatively low friction coefficient), the tolerance is convenient to control, and the manufacturing difficulty is reduced. It will be appreciated that the recoverability of the scaffolds described herein is well known in the art and will be apparent to those skilled in the art: the recovery rate of the stent is (total length of the stent-the distance from the proximal end of the stent to the distal end of the driver member)/total length of the stent is 100%.

Next, the structure of the entraining member 120 will be described with reference to the accompanying drawings. It should be understood that the specific structure of the driving member 120 described in the following embodiments is only an optional implementation manner of the present invention, and it should not limit the present invention.

Referring to fig. 2-5, in an embodiment, the driving member 120 includes a body 121, the body 121 is a hollow tubular body, the body 121 is sleeved on the core shaft 110, a groove 122 is formed on an outer surface of the body 121, and the groove 122 forms the recess. It is understood that the "groove" of the present embodiment includes an elongated concave structure, and also includes a circular, square or irregular concave structure (i.e. a pit), and the groove 122 has different forms according to actual needs.

For example, with continued reference to FIG. 3, the grooves 122 are configured to match at least a portion of the configuration of the stent in a compressed state. Specifically, the shape and position of the groove 122 are matched with those of the stent, and the size of the groove 122 is also matched with that of the wave bar or the weaving wire of the stent, for example, the width of the groove 122 is greater than, equal to or slightly smaller than that of the weaving wire or the wave bar, the depth of the groove 122 (the distance between the bottom of the groove 122 and the outer surface of the body 121 at the top of the groove 122) is greater than, equal to or smaller than the radial size of the weaving wire or the wave bar, and the like. Depending on the size of the stent, the width of the grooves 122 is between 0.0008 inches and 0.004 inches, and the depth of the grooves 122 is between 0.0002 inches and 0.004 inches. It will be understood that the width of the grooves 122 corresponds to the width of the braided wires or struts of the stent, for example, when the braided wires of the stent extend in the circumferential direction of the stent, the width of the braided wires refers to the dimension of the braided wires in the axial direction of the stent, and the width of the grooves 122 refers to the dimension of the grooves 122 in the axial direction of the stent.

The groove 122 may be a continuous structure formed on the outer surface of the body 121, and may also include a plurality of sub-grooves, which may be staggered, arranged continuously or arranged at intervals on the outer surface of the body 121.

Taking the stent 300 shown in fig. 4 as an example, the stent 300 is woven by a plurality of weaving wires 310. Corresponding to the stent 300, the grooves 122 may include a plurality of sub-grooves, and the sub-grooves are staggered such that the grooves 122 and the inner surface of the stent in a compressed state are mirror images of each other (as shown in fig. 3), i.e., the size and arrangement of the grooves 122 are matched with the size and arrangement of the braided wires 310 of the stent in a compressed state. Each of the braided wires 310 may be at least partially embedded in the recess when the stent 300 is fitted over the delivery guidewire 100.

The recess 122 may be shaped in a variety of ways in this embodiment. The body 121 is made of a polymer material, and when the body 121 is formed but not cured, a wire is wound on the body 121 along an axis of the body 121 in a spiral or staggered manner, and the wire is in close contact with a surface of the body 121 to apply a radial acting force to the body 121. Under the extrusion of the wire, the contact part of the outer surface of the body 121 and the wire is deformed in a concave manner toward the axis of the body 121 to form the groove 122, and then the wire is removed. The silk threads can be metal threads, polymer threads or silk threads made of other materials. In this embodiment, the diameter of the filament is the same as the diameter of the woven filament of the stent 300 that needs to be sleeved on the delivery guidewire 100, and in other embodiments, the diameter of the filament may be slightly larger or smaller than the diameter of the woven filament of the stent 300. The groove 122 may also be formed after the body 121 has been cured, for example, by first heating the body 121 to soften the body 121, and then forming the groove 122 with a wire; alternatively, after the body 121 is cured, the groove 122 is carved on the outer surface of the body 121 by using a carving process.

When the material of the body 121 is metal, the groove 122 may also be formed on the outer surface of the body 121 by an engraving process (e.g., laser engraving).

For the stent formed by the cutting process, a groove 122 matched with the stent may be formed on the surface of the body 121 by an engraving process.

For another example, referring to fig. 5, the groove 122 may be a continuous groove formed on the body 121, and the continuous groove spirally surrounds along the axis of the body 121 to form a spiral groove on the outer surface of the body 121. In this embodiment, the grooves 122 are preferably formed by using a wire to form the grooves 122.

For another example, referring to fig. 6, the groove 122 may include at least two sub-grooves spaced apart from each other on the body 121. The sub-grooves may be in various shapes such as a circle, a square, a prism, etc. (i.e., the sub-grooves are recesses), and when the number of the sub-grooves is more than two, a plurality of sub-grooves are distributed on the outer surface of the body 121 as required. The groove 122 may be formed by engraving or the like in this embodiment.

Still taking the stent 300 shown in fig. 4 as an example, the knitting points 311 where the knitting filaments 310 intersect have a larger radial thickness than other portions of the stent 300, and the knitting points 311 may be partially embedded in the sub-grooves when the stent 300 is mounted on the pushwire 100. Alternatively, in other stents, a site of greater radial dimension may be present at a location on the stent, and the site of greater radial dimension may be partially or fully embedded in the sub-groove when the stent is placed over the delivery guidewire. Thus, when the stent 300 is sleeved on the delivery guidewire 100 and inserted into the lumen of the delivery tube, the contact area between the braided wire or wave rod of the stent 300 and the body 121 is increased, so that the first friction between the stent 300 and the driving member 120 is increased; meanwhile, the outer diameter of the stent 300 tends to be uniform as a whole, and the surface of the stent 300 in contact with the delivery pipe (i.e., the outer surface of the stent 300) is smoother, so that the second friction between the stent and the inner wall of the delivery pipe is reduced, and the pushing resistance of the stent during delivery is reduced.

In another embodiment of the present invention, as shown in fig. 7, the driving member 120 is formed by a winding wire wound around the mandrel 110. The winding wire is spirally wound around the axis of the mandrel 110 for a plurality of turns to form a spiral structure, and a gap 123 exists between two adjacent turns of the winding wire, wherein the gap 123 constitutes the recess.

In this embodiment, the number of turns and the pitch of the winding wire can be adjusted as required. For example, when the stent to which the delivery guidewire 100 is mated has a relatively large PPI (PPI refers to the number of braid points contained within a unit length of the braided stent, where the length is the axial dimension of the stent), the number of windings of the wire on the mandrel 110 may be increased and the pitch may be decreased to provide a greater contact area between the stent and the driver member 120.

Alternatively, the winding filament may be a polymer filament, which preferably has a large surface friction coefficient, and may be selected according to the requirement.

Optionally, the winding wire is composed of a metal wire and a polymer coating layer coated on the outer surface of the metal wire. Preferably, the metal wire is a metal wire having developability, such as a platinum-tungsten alloy wire or a platinum-iridium alloy wire, so that the carrying member 120 has developability. Since the driving member 120 has developability, when the stent is delivered, an operator can conveniently judge the specific position of the stent in the body, and can further judge whether the partially released stent can be recovered into the delivery tube. Specifically, the conveying pipe for conveying through the stent has a second distal end and a second proximal end which are opposite to each other, and the second distal end is provided with the third developing member, and when the operator observes through the developing device that the driving member 120 starts to coincide with the third developing member while conveying the stent, the operator can judge that the stent cannot be recovered any more.

Further, the present embodiments also provide a treatment apparatus comprising a delivery tube, a medical implant, and a delivery guidewire as described above. The delivery tube has an axially through lumen for receiving the medical implant, and the wall of the lumen compresses the medical implant so that it is compressed. The compressed medical implant is tightly sleeved on the driving member 120, a first friction force is generated between the compressed medical implant and the driving member 120, and at least part of the medical implant is embedded in the recess to increase the first friction force. The medical implant described herein is, for example, a self-expanding stent, and may be, in particular, a woven stent or a cut stent.

It should be noted that, in order to improve the matching degree between the driving member 120 and the medical implant and simplify the assembling process of the therapeutic device, the delivery guidewire 100 according to this embodiment is preferably manufactured according to a specific medical implant. That is, in the process of producing the delivery guidewire 100, the medical implant to be delivered is first provided, then the form of the entrainment member 120 and the recess portion is determined according to the structure of the medical implant, and finally the production of the delivery guidewire 100 is performed.

In addition, the inner cavity of the delivery pipe has different radial sizes according to actual requirements, and preferably, the radial size of the inner cavity ranges from 0.017 inches to 0.029 inches. More preferably, the radial dimension of the lumen is less than or equal to 0.027 inches, or the radial dimension of the lumen is less than or equal to 0.021 inches. Because the transport seal wire has adopted the drive component that has the depressed part, can reduce the external diameter of medical implant under compression state, therefore the utility model discloses a less conveyer pipe of radial dimension of inner chamber can be adopted to the treatment device, and this treatment device can reduce the external diameter of conveyer pipe correspondingly, and thinner conveyer pipe can reach the blood vessel of more distal end or more tiny pathological change position, enlarges the treatment range, has also improved the holistic compliance of treatment device simultaneously, more is favorable to reaching pathological change position smoothly through comparatively tortuous blood vessel, improves the operation success rate.

Although the present invention is disclosed above, it is not limited thereto. Various modifications and alterations of this invention may be made by those skilled in the art without departing from the spirit and scope of this invention. Thus, if such modifications and variations of the present invention fall within the scope of the claims and their equivalents, the present invention is also intended to include such modifications and variations.

Claims (21)

1. A delivery guide wire is used for delivering a medical implant and is characterized by comprising a mandrel and a driving component arranged on the mandrel, wherein a concave part is formed on the driving component.

2. The pushwire of claim 1, wherein said entraining member comprises a body and a groove formed in an outer surface of said body, said groove defining said recess.

3. The pushwire of claim 2, wherein said groove is configured to match at least a portion of the configuration of said medical implant in a compressed state.

4. The pushwire of claim 3, wherein said groove mirrors an inner surface of said medical implant in a compressed state.

5. The pushwire of claim 3 wherein said groove has a width of 0.0008 to 0.004 inches.

6. The pushwire of claim 3 wherein said groove has a depth of 0.0002 to 0.004 inches.

7. The pushwire of claim 2, wherein said groove comprises one or more sub-grooves, a plurality of said sub-grooves being staggered, consecutive, or spaced on an outer surface of said body.

8. The pushwire of claim 2, wherein said groove spirals along the axis of said body to form one or more helical grooves in the outer surface of said body.

9. The pushwire of claim 1 wherein said entraining member is helically wrapped around the axis of said mandrel by a wrap wire to form one or more helical structures, and wherein adjacent turns of said wrap wire are spaced to form said depression.

10. The pushwire of claim 9, wherein said winding wire is a polymer wire or a metal wire coated with a polymer coating.

11. The pushwire of claim 10, wherein said wire is visualization.

12. The pushwire of claim 11, wherein said wire is a platinum-tungsten alloy wire or a platinum-iridium alloy wire.

13. The pushwire of any of claims 1-12, wherein said mandrel has at least two of said plurality of.

14. The pushwire of claim 13, wherein the distance between adjacent pairs of said entraining members is in the range of 0.5mm to 150 mm.

15. The pushwire of claim 12, wherein the distance between two adjacent entraining members is 0.5mm-5 mm.

16. The pushwire of any of claims 1-12, wherein said mandrel has one or more of said plurality of driver members, said driver members having an outer diameter of 0.01 inch to 0.03 inch, and each of said driver members having a length of 0.5mm to 8 mm.

17. The pushwire of claim 16, wherein each said entraining member has a length of 0.5mm to 4 mm.

18. The pushwire of any of claims 1-12, further comprising a first visualization member disposed at a distal end of said mandrel and a second visualization member disposed on said mandrel, said entraining member being disposed between said first visualization member and said second visualization member.

19. A treatment device comprising a delivery tube, a medical implant, and a delivery guidewire according to any one of claims 1-18; the delivery pipe is provided with an inner cavity which is axially communicated and is used for accommodating the medical implant, and the wall of the inner cavity extrudes the medical implant so as to enable the medical implant to be in a compressed state; the medical implant in a compressed state is sleeved on the driving component, and at least part of the medical implant is embedded into the concave part.

20. The treatment device of claim 19, wherein the lumen has a radial dimension in a range of 0.017 inches to 0.029 inches.

21. The treatment device of claim 19, wherein the medical implant is a self-expanding stent.

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