Patent Description:
A stent is an endoprostheses device that is used to secure a circulatory passage of blood, body fluid, food, body waste, etc. by inserting it into a blocked area in a human body.

The stent is mainly made of a plastic material or a metal material. First, there is a problem in that the plastic material with a thin diameter can be easily inserted, while due to its material property and thin diameter, the self-expansion is collapsed and the stent treatment area is blocked again.

Therefore, in the medical field, the stent of a metal material is used in many cases. The metal material is expensive but basically has an inherent rigidity, such that even if intermittent muscle contraction or external shock applied in the body tissue of the stent treatment area, etc. occurs, it is temporarily contracted but is self-expanded again, thereby efficiently keeping the function thereof.

Recently, when problems such as occlusion and damage have occurred on the circulatory passage of the human body, such as blood vessel, ureter, and bile duct, a non-surgical method is preferred rather than a surgical method as before, and as a part of this trend, the stent treatment is being activated.

A stent delivery system such as a catheter is used to insert the stent into the body tissue area to be treated.

Herein, in simply explaining the stent delivery system, the stent delivery system is basically configured to include an electrocautery tip, an insertion tube, a stent, a handle, a current connector, etc..

The current connector is a part that is connected to an external current source such as an electric treatment instrument to receive a current for heating, and the electrocautery tip is a part that is connected to the current connector by a conductive line to form a hole by receiving a current to cauterize the body tissue.

Then, the insertion tube is generally made of an insulating material, and the stent is embedded inside the insertion tube, such that the practitioner inserts the insertion tube into the body tissue through a cauterization hole by the operation of the handle, and positions the stent at the area to be treated.

Thereafter, the stent is exposed from the insertion tube through the operation of the handle and the stent is self-expanded, thereby solving occlusion, damage, etc. of the treatment area.

However, in the conventional stent delivery system, since the insertion tube is made of an insulating material, when a practitioner, such as a doctor or a nurse, accidentally applies an impact by incorrect use, the phenomenon that is easily bent or deflected occurs easily. In extreme cases, a problem that is broken due to external damage also occurs.

If such problems occur during the actual treatment, it can result in a fatal medical accident for the person to be treated, such as a patient.

The insertion tube is inserted into the human body, such that some flexibility thereof should be ensured, and in addition, it is a part touching the human body, such that the insulation property should be electrically kept. Therefore, in the stent treatment technology field, there is a demand for a tube with the enhanced durability in order not to be easily damaged even by the carelessness of the practitioner, such as a doctor or a nurse, while keeping the basic characteristics of the above-mentioned insertion tube. Of course, the position of the conductive line connected to the electrocautery tip should be also considered adequately.

<CIT>, <CIT>, <CIT>, <CIT>, <CIT>, <CIT>, <CIT>, <CIT>, and <CIT> disclose stent delivery systems.

In addition, there is a problem in that most of stent delivery systems currently used have a fixed size of the electrocautery tip, such that the size of the cauterization hole cannot be adjusted according to the treatment environment in the body tissue of the person to be treated. This results in the limitation that cannot adequately cope with a change in the variable treatment environment.

Therefore, in order to provide more advanced treatment environment, there is a demand for a treatment device that can variably adjust the cauterization hole in the body tissue for delivering various types of stents required in the treatment area of the body tissue.

The present disclosure is intended to solve the above problems of the relate art, and an object of the present disclosure is to provide an improved apparatus as defined in independent claim <NUM>.

The present disclosure for achieving the object relates to a stent delivery system, and can be configured to include a connector portion connected to an external current source, an electrocautery tip connected to the connector portion by a conductive line, and a delivery portion having one side connected to the electrocautery tip, having the other side connected to the connector portion, and having the conductive line for connecting the electrocautery tip and the connector portion positioned therein, and a stent space portion in which a stent is positioned is formed adjacent to the electrocautery tip inside the delivery portion, and the delivery portion gradually moves and supplies the stent into the human body tissue. The electrocautery tip comprises: a tip electrode body being made of a conductive material and having a tip guide hole formed therein, the tip electrode body having an outer circumferential surface tapered to be narrower in a direction towards a distal end of the electrocautery tip and a proximal end connected to the conductive line; a tip insulator having its distal end coupled to the proximal end of the tip electrode body, an outer circumferential surface tapered to be narrower in a direction opposite to the direction of the tip electrode body towards a proximal end of the electrocautery tip and its proximal end connected to the delivery portion a coupling portion formed at a portion of the outer circumferential surface of the tip electrode body; and a variable-sized ring configured to be coupled to the coupling portion to vary a maximum diameter of the tip electrode body, wherein the coupling portion has a threaded outer surface, and the variable-sized ring has a threaded inner surface formed to correspond to the threaded outer surface of the coupling portion; wherein the outer circumferential surface of the variable ring is tapered; wherein one side of the outer circumferential surface of the variable ring is tapered in the same direction as the tip electrode body, and the other side of the outer circumferential surface of the variable ring is tapered in the same direction as the tip insulator.

In addition, in an embodiment of the present disclosure, the delivery portion can include a first internal tube having the conductive line connected to the electrocautery tip positioned therein, and having an inner hole formed at the internal central side thereof, a second internal tube positioned to surround a portion of the outer circumference of the first internal tube, and provided to be connected to the first internal tube to be integrally moved, and an external tube positioned to surround the second internal tube.

In addition, in an embodiment of the present disclosure, the first internal tube can be an insulating coating material, and the conductive line can be formed integrally with the first internal tube and positioned in a straight-line form along the longitudinal direction of the first internal tube.

In addition, in an embodiment of the present disclosure, the first internal tube can be an insulating coating material, and the conductive line can be formed integrally with the first internal tube and positioned to be wound in a spiral direction along the circumference of the first internal tube.

In addition, in an embodiment of the present disclosure, the first internal tube can be an insulating coating material, and the conductive line can be formed integrally with the first internal tube and positioned in a woven form along the circumference of the first internal tube.

In addition, in an embodiment of the present disclosure, the delivery portion can further include a first grip portion connected to the external tube and a second grip portion connected to the second internal tube by a movable bar, and the connector portion is positioned on the second grip portion, and the first internal tube is positioned by passing through the movable bar and the second grip portion.

In addition, in an embodiment of the present disclosure, the tip electrode body and the tip insulator can be provided in a triangular form that a side cross-sectional surface thereof is inclined in the same direction.

In addition, in an embodiment not covered by the present invention, a portion of the outside of the variable ring can be tapered at an angle smaller than the tip electrode body.

In addition, in an embodiment not covered by the present invention, the outer circumference of the variable ring can be round-processed.

In addition, in an embodiment not covered by the present invention, a portion of the variable ring can have a different thickness.

In addition, in an embodiment of the present disclosure, the electrocautery tip can further include an adhesion pad positioned on at least any one side of the coupling portion in order to prevent a gap between the inner circumference of the variable ring and the outer circumference of the tip electrode body.

In addition, in an embodiment not covered by the present invention, the electrocautery tip can further include a cauterization protrusion formed at the outer circumference of the tip electrode body.

In addition, in an embodiment not covered by the present invention, the cauterization protrusion can be positioned in plural with predetermined intervals interposed therebetween on the outer circumference of the tip electrode body.

In addition, in an embodiment not covered by the present invention, the cauterization protrusion can be a straight-line form.

In addition, in an embodiment not covered by the present invention, the cauterization protrusion can be a curved form.

In addition, in an embodiment not covered by the present invention, the plurality of cauterization protrusions can be insulation-coated therebetween in the tip electrode body.

In addition, in an embodiment of the present disclosure, the stent delivery system with the mono-polar electrocautery tip can further include a guide wire positioned in an inner hole of the first internal tube and a tip guide hole of the tip electrode body, and for guiding the moving direction of the electrocautery tip.

In addition, in an embodiment not covered by the present invention, the delivery portion can further include a moving adjustment unit for gradually adjusting the movement of the movable bar, and the moving adjustment unit can include an uneven portion formed along the longitudinal direction of the movable bar and a fixing portion positioned inside the first grip portion in order to be coupled to the uneven portion and gradually fix the movement of the movable bar.

In addition, in an embodiment not covered by the present invention, the fixing portion can include an elastic body positioned inside the first grip portion and a fixing block having one side closely contacting the elastic body, and having the other side protruded to a first inner hole.

In addition, in an embodiment not covered by the present invention, the fixing portion can further include a rolling wheel rotatably positioned on the fixing block.

In addition, in an embodiment not covered by the present invention, the tip guide hole can be eccentrically positioned inside the tip electrode body.

According to the present disclosure, it can be expected to enhance the rigidity of the tube by integrating the conductive wire and the tube positioned at the innermost portion thereof. At this time, the form that the conductive wire is positioned to be spirally wound in plural and the form that is positioned to be connected by the repetitive woven structure further enhance the rigidity as the entire tube.

In addition, it is possible to change the size, that is, the diameter of the electrocautery tip, thereby appropriately adjusting the size that forms the hole in the human body according to the size of the treatment area, the cross-sectional size of the tube, the degree of expansion and contraction of the stent, etc..

In addition, it can be additionally expected to minimize the incision area of the human body tissue through the structure, which provides the electrocautery protrusion pattern to the electrocautery tip, and applies the current only to the pattern area.

Hereinafter, preferred embodiments of a stent delivery system according to the present disclosure will be described in detail with reference to the accompanying drawings.

<FIG> is an external diagram of a stent delivery system of the present disclosure, <FIG> is a side cross-sectional diagram illustrating a connector portion and a second grip portion in the disclosure illustrated in <FIG>, <FIG> are side cross-sectional diagrams illustrating forms of a first grip portion and a conductive line in the disclosure illustrated in <FIG>, <FIG> is a side cross-sectional diagram illustrating the first grip portion and a moving adjustment unit in the disclosure illustrated in <FIG>, <FIG> is a side cross-sectional diagram illustrating an electrocautery tip and a stent space portion in the disclosure illustrated in <FIG>, <FIG> are side cross-sectional diagrams illustrating a first embodiment of the electrocautery tip of the present disclosure, <FIG> is a side cross-sectional diagram illustrating another form that connects the conductive line of the electrocautery tip of the present disclosure, <FIG> is a side cross-sectional diagram illustrating still another form that connects the conductive line of the electrocautery tip of the present disclosure, <FIG> is a side cross-sectional diagram illustrating a second embodiment of the electrocautery tip of the present disclosure, <FIG> is a side cross-sectional diagram illustrating a state where a variable ring has been mounted thereon in the disclosure illustrated in <FIG>, <FIG> is a side cross-sectional diagram illustrating one form of the variable ring in the disclosure illustrated in <FIG>, <FIG> is a side cross-sectional diagram illustrating another form of the variable ring in the disclosure illustrated in <FIG>, <FIG> are diagrams illustrating various forms of the electrocautery protrusions that are positioned at the tip electrode body and the variable rings of the present disclosure, <FIG> is a partial perspective diagram of the disclosure illustrated in <FIG>.

Referring to <FIG>, a stent delivery system <NUM> of the present disclosure can be configured to include a connector portion <NUM>, an electrocautery tip <NUM>, and a delivery portion <NUM>.

First, referring to <FIG>, the connector portion <NUM> can be a portion electrically connected to an external current source <NUM>. Herein, the external current source <NUM> can be a high frequency generator or a low frequency generator, but is not necessarily limited thereto.

The connector portion <NUM> can be made of a conductive material such as a metal material. Then, the connector portion <NUM> can have a connection protrusion <NUM> functioning as a terminal for connecting a connector body <NUM> and the external current source <NUM> formed at one side portion of the connector body <NUM>, and have a screw pin <NUM> positioned at the other side portion thereof in order to be screw-fastened and coupled to a connection beam <NUM>. Then, the connection beam <NUM> can be formed with a through-hole <NUM> to which a movable bar <NUM>, which will be described below, is connected.

Herein, an end block <NUM> is processed at the end portion of the movable bar <NUM>, and the end block <NUM> can be formed to have the diameter greater than a stepped portion <NUM> of the movable bar <NUM>.

At this time, the through-hole <NUM> is processed to have the diameter through which the end block <NUM> can pass, and when the connector body <NUM> is further rotated after the end block <NUM> is fitted and passed through, the screw pin <NUM> is rotated down to the stepped portion <NUM>.

Through such a structure, the movable bar <NUM> is not detached from a second grip portion <NUM> even when it is pulled excessively. This is because the end block <NUM> is blocked and not pulled out by the lower end of the screw pin <NUM> inside the through-hole <NUM>.

The connector portion <NUM> can be provided to be fixed to a second grip body <NUM> of the second grip portion <NUM>, which will be described below. A wire outlet <NUM> can be positioned at the end portion of the second grip body <NUM>.

Next, the delivery portion <NUM> can be a portion that has one side connected to the electrocautery tip <NUM>, and has the other side connected to the connector portion <NUM>. The delivery portion <NUM> can be configured to include a first internal tube <NUM>, a second internal tube <NUM>, an external tube <NUM>, a first grip portion <NUM>, the second grip portion <NUM>, and the movable bar <NUM>.

Hereinafter, the insulating material used in the present disclosure can be urethane, polyester, polyimide, other plastic materials, ceramic, silicone, fluorine resin, teflon, etc., but is not necessarily limited thereto. Such an insulating material can be selectively applied to various tubes, insulating coating materials, tip insulators, etc., which will be described below.

Referring to <FIG>, the first internal tube <NUM> is a portion that is positioned at the innermost portion in the delivery portion <NUM>, and a conductive line <NUM> connected to the electrocautery tip <NUM> can be positioned therein.

The first internal tube <NUM> can be divided into three forms according to the positional form of the conductive line <NUM>.

First, referring to <FIG>, one form of the first internal tube <NUM> is disclosed. In this form, the first internal tube <NUM> is provided with an insulating coating material, and a conductive line 120a is formed integrally with the first internal tube <NUM> and positioned in a straight-line form along the internal longitudinal direction of the first internal tube <NUM>.

Specifically, the conductive line 120a is positioned in parallel along the external longitudinal direction of the first internal tube <NUM> that is an insulating coating material, and can be a structure that insulation-coats the first internal tube <NUM> and the conductive line 120a together once again at the external portion thereof.

For another example, the first internal tube <NUM> has an inner hole <NUM> formed at the internal central side thereof, and for this purpose, should have a constant thickness, and the conductive line 120a can be a structure that is positioned at the thickness portion to be insulation-processed together.

Of course, it is not necessarily limited to the above structure, and other structures capable of keeping the insulating property are also possible.

Then, a portion, which contacts the movable bar <NUM>, of the end portion of the conductive line 120a can be welded-coupled <NUM> and fused by resistance welding, laser welding, or non-soldering, and electrically connected thereto. Of course, it is not necessarily limited thereto, and it is also possible to connect in the method of knotting one end portion of the conductive line 120a after processing the through-hole in the movable bar <NUM>, or other connection methods other than the above are also possible.

A portion, which contacts the electrocautery tip <NUM>, of the end portion of the conductive line 120a can also be welded-coupled <NUM> and fused and electrically connected to a tip electrode body <NUM> as in <FIG>, and of course, is not limited to the connection method.

At this time, the movable bar <NUM> can be made of a conductive material such as a metal material, and can be formed with a stepped portion whose diameter is slightly reduced along the outer circumference of a portion, which is exposed between the first grip portion <NUM> and the second grip portion <NUM>, of a portion of the movable bar <NUM> and an insulating material that is a bar insulator <NUM> can be applied to the stepped portion in order to prevent the electric shock of a practitioner.

The bar insulator <NUM> can be a polytetrafluoroethylene (PTFE) coating material. This is excellent in chemical resistance, heat resistance, etc., and can be suitable as an insulating material for the medical instruments using electricity.

Next, referring to <FIG>, another form of the first internal tube <NUM> is disclosed. In this form, the first internal tube <NUM> is provided with an insulating coating material, and a conductive line 120b is formed integrally with the first internal tube <NUM> and positioned in a form wound in a spiral direction along the circumference of the first internal tube <NUM>.

At this time, the conductive line 120b can be made of a metal material, and the conductive line 120b is positioned at the first internal tube <NUM> while being wound in plural times, thereby improving the rigidity of the first internal tube <NUM>.

Accurately, the inner hole <NUM> is formed at the internal central side of the first internal tube <NUM>, and for this purpose, the first internal tube <NUM> has a constant thickness. The conductive line 120b is positioned at the thickness portion, and therefore, the conductive line 120b is entirely surrounded by an insulating coating material and positioned while being wound in plural times in a spiral direction along the circumference of the first internal tube <NUM>.

Then, a portion, which contacts the movable bar <NUM>, of the end portion of the conductive line 120b protruded from the end portion of the first internal tube <NUM> can be welded-coupled <NUM> and electrically connected thereto. Of course, it is not necessarily limited thereto, and it is also possible to connect in the method of knotting by protruding a portion of the conductive line 120b from the end portion of the first internal tube <NUM> after processing the through-hole in the movable bar <NUM>, and other connection methods other than the above are also possible.

In addition, a portion, which contacts the electrocautery tip <NUM>, of the end portion of the conductive line 120b can also be welded-coupled <NUM> and electrically connected to the tip electrode body <NUM> as in <FIG>, but is not necessarily limited to the connection method.

Next, referring to <FIG>, still another form of the first internal tube <NUM> is disclosed. In this form, the first internal tube <NUM> is provided with an insulating coating material, and a conductive line 120c is formed integrally with the first internal tube <NUM> and positioned in a woven form along the circumference of the first internal tube <NUM>.

At this time, the conductive line 120c can be made of a metal material, and the conductive line 120c is repeatedly positioned at the first internal tube <NUM> in a woven form, thereby improving the rigidity of the first internal tube <NUM>.

Accurately, the inner hole <NUM> is formed at the internal central side of the first internal tube <NUM>, and for this purpose, the first internal tube <NUM> has a constant thickness. The conductive line 120c is positioned at the thickness portion, and therefore, the conductive line 120c is entirely surrounded by an insulating coating material and positioned in a repetitive woven form along the circumference of the first internal tube <NUM>.

Then, a portion, which contacts the movable bar <NUM>, of the end portion of the conductive line 120c protruded from the end portion of the first internal tube <NUM> can be welded-coupled <NUM> and electrically connected thereto. Of course, it is not necessarily limited thereto, and it is also possible to connect in the method of knotting by protruding a portion of the conductive line 120c from the end portion of the first internal tube <NUM> after processing the through-hole in the movable bar <NUM>, and other connection methods other than the above are also possible.

In addition, a portion, which contacts the electrocautery tip <NUM>, of the end portion of the conductive line 120c can also be welded-coupled <NUM> and electrically connected to the tip electrode body <NUM> as in <FIG>, but is not necessarily limited to the connection method.

Next, referring to <FIG>, <FIG>, and <FIG>, the second internal tube <NUM> can be positioned to surround a portion of the outer circumference of the first internal tube <NUM>, and provided to be connected to the first internal tube <NUM> to move integrally. The second internal tube <NUM> can be made of an insulating material.

First, referring to <FIG>, it can be confirmed that the second internal tube <NUM> is positioned to surround a portion of the outer circumference of the first internal tube <NUM>, and at this time, a sign block <NUM> pushing the stent <NUM> is positioned at the end portion of the second internal tube <NUM>.

Referring to <FIG>, it can be confirmed that the second internal tube <NUM> is positioned inside the external tube <NUM>, and fitted into and connected to the outer circumference of a tube connection portion <NUM> of the movable bar <NUM>, and the first internal tube <NUM> positioned therein is fitted into and connected to the through-hole of the tube connection portion <NUM> of the movable bar <NUM>.

Therefore, when the practitioner moves the movable bar <NUM>, the first internal tube <NUM> connected to the movable bar <NUM> and the second internal tube <NUM> integrally move together in the moving direction of the movable bar <NUM>.

Next, referring to <FIG>, <FIG>, and <FIG>, the external tube <NUM> can be a portion that is positioned to surround the second internal tube <NUM> and connected and fixed to the end portion of the first grip portion <NUM>. That is, since the external tube <NUM> is fixed to the first grip portion <NUM>, it does not move according to the movement of the movable bar <NUM>, but guides and supports the movement of the first internal tube <NUM> and the second internal tube <NUM>. The external tube <NUM> can be made of an insulating material.

Referring to <FIG>, it can be seen that the stent <NUM> can be positioned in a non-expansion state in a stent space portion <NUM> formed by the first internal tube <NUM> and the external tube <NUM>. That is, the stent <NUM> is positioned along the circumference of a portion, which is surrounded and not supported by the second internal tube <NUM>, of the first internal tube <NUM>, and the stent <NUM> keeps the non-expansion state while contacting the inner circumferential surface of the external tube <NUM>.

At this time, a stent support block <NUM> can be positioned at the outer circumferential surface of the first internal tube <NUM>.

Next, referring to <FIG>, the first grip portion <NUM> is a portion that is connected to the end portion of the external tube <NUM>, and can be a portion for the practitioner to grip in order to move the movable bar <NUM>.

A fixing handle <NUM> can be positioned at one side portion of the first grip portion <NUM>. When the practitioner wishes to restrict the movement of the movable bar <NUM> after moving the movable bar <NUM>, the practitioner can rotate the fixing handle <NUM> in one direction. Although not illustrated in the drawing, when the fixing handle <NUM> is rotated in one direction, the movable bar <NUM> is pressed to restrict the movement of the movable bar <NUM>. Conversely, when the practitioner wishes to move the movable bar <NUM> again, the practitioner can rotate the fixing handle <NUM> in the opposite direction to loosen the pressure on the movable bar <NUM>.

The fixing handle <NUM> is provided to allow the stent <NUM> to be positioned at the accurate body tissue area when the stent <NUM> has been adjacent to the body tissue area to be expanded. This is because if the movable bar <NUM> moves during the treatment, the position of the stent <NUM> can be incorrectly positioned.

Meanwhile, in the present disclosure, another form for fixing the movable bar <NUM> is disclosed. Referring to <FIG>, the delivery portion <NUM> can be configured to further include a moving adjustment portion <NUM> for gradually adjusting the movement of a first grip body <NUM> that moves along the movable bar <NUM>. Conversely, this can gradually adjust the movement of the movable bar <NUM> through the relationship with the first grip body <NUM>.

The moving adjustment unit <NUM> can be configured to include an uneven portion <NUM> and a fixing portion <NUM>. First, the uneven portion <NUM> can be formed in plural with a bent shape along the longitudinal direction of the movable bar <NUM>. Then, the fixing portion <NUM> can be positioned inside the first grip portion <NUM> in order to gradually fix the movement of the first grip body <NUM> that moves along the movable bar <NUM> while being coupled to the uneven portion <NUM>.

Specifically, the fixing portion <NUM> can be configured to include an elastic body <NUM> and a fixing block <NUM>. The elastic body <NUM> can be positioned in an internal space 471a formed inside the first grip portion <NUM>. The elastic body <NUM> can be the form such as a coil spring or a plate spring, but when an elastic force can be provided, it is not necessarily limited thereto.

Then, the fixing block <NUM> can be implemented as a form that has one side closely contacting the elastic body <NUM> and has the other side protruded to a first inner hole <NUM>. At this time, when the practitioner pulls or pushes the movable bar <NUM>, a rolling wheel 479a can be positioned at the fixing block <NUM> in order to go beyond the bent shape of the uneven portion <NUM> relatively and easily.

The gradual movement of the movable bar <NUM> through the above structure enables the stable gradual self-expansion of the stent in the treatment area of the body tissue when the practitioner actually performs the stent treatment.

The completeness of the stent treatment can be changed according to the treatment environment, the skill of the practitioner, etc. If the practitioner is immature, he/she forcibly pulls the movable bar <NUM> or the movable bar <NUM> shakes during the pulling, such that the vibration can be delivered to the stent, thereby not smoothly performing the self-expansion of the stent.

At this time, if the movable bar <NUM> can be gradually moved and fixed, the movement of the external tube <NUM> can also be adjusted clearly and gradually as the movable bar <NUM> is pulled, such that the stent is also exposed slowly and gradually. This induces the accurate self-expansion of the stent, and also enhances the treatment effect. It is also possible to slightly mitigate and prevent the carelessness of the practitioner.

Next, referring to <FIG>, a first embodiment of the electrocautery tip <NUM> can be configured to include the tip electrode body <NUM> and a tip insulator <NUM>.

The tip electrode body <NUM> can be configured to have a tip guide hole <NUM>, in which a guide wire <NUM> is inserted and positioned, formed at the central side thereof, have one side portion of the outer circumferential surface tapered in one direction, and have the other side portion of the outer circumferential surface welded-coupled <NUM> and connected to the conductive line <NUM>. Of course, it is not necessarily limited thereto, and although not illustrated in the drawing, for example, a structure of forming the through-hole and tying and connecting the conductive line <NUM> in a knotting method is also possible.

The tip electrode body <NUM> can entirely have a circular cross-sectional shape, and the tip electrode body <NUM> can be a conductive material such as a metal material as a portion that forms a hole by receiving a current to apply heat to the body tissue. For example, it can be a metal material such as stainless or Ni+Ti alloy.

Next, it can be configured so that one side of the tip insulator <NUM> is connected to the other side portion of the tip electrode body <NUM>, and the other side thereof is connected to the end portion of the first internal tube <NUM> of the delivery portion <NUM>. The tip insulator <NUM> can be an insulating material so that a current does not flow.

Then, the tip insulator <NUM> can be coated on the tip electrode body <NUM> in a molding method. In an embodiment of the present disclosure, as illustrated in <FIG>, the tip insulator <NUM> and the tip electrode body <NUM> can be implemented in a form having the side cross-sectional diagram of triangle. Of course, the tip insulator <NUM> and the tip electrode body <NUM> can be a shape that is tapered in the same direction when viewed from the front thereof.

In this case, the first internal tube <NUM> can be formed as a structure that is directly adhered to the tip electrode body rather than the tip insulator, and the electrocautery tip <NUM> can be easily inserted into the body tissue with the above form.

Alternatively, as illustrated in <FIG>, <FIG>, and <FIG>, which are another embodiment of the present disclosure, it can also be implemented in a form that has one portion tapered in the same direction as the tip electrode body <NUM>, and has the other portion tapered in the direction opposite to the tip electrode body <NUM>.

In the case that the tip insulator <NUM> has a tapered form, when the electrocautery tip <NUM> is pulled out again after delivering the stent <NUM> in the body tissue, this operation can be performed relatively and easily.

The body tissue is mainly made of protein, such that even if a cauterization hole is formed by the electrocautery tip <NUM>, the cauterization hole becomes narrow due to the flexibility of the body tissue.

At this time, if the tip insulator <NUM> has been tapered in the direction opposite to the tip electrode body <NUM>, the cauterization hole widens while spreading along the tapered shape when the practitioner pulls out the electrocautery tip <NUM> through the cauterization hole, such that the electrocautery tip <NUM> is easily pulled out.

In this case, the first internal tube <NUM> is inserted into the tip insulator <NUM> and adhered to the tip electrode body <NUM>.

Of course, the tip insulator <NUM> is not necessarily limited to the above forms.

Herein, as another form of a structure of the conductive line <NUM> connected to the tip electrode body <NUM>, as illustrated in <FIG>, the conductive line <NUM> positioned in a spiral form along the circumference of the first internal tube <NUM> can be used. In this case, the first internal tube <NUM> itself is made of a flexible insulating material, but the conductive line <NUM> of a conductive metal material is wound along the circumference thereof, thereby improving the rigidity of the first internal tube <NUM>.

In addition, as still another form of a structure of the conductive line <NUM> connected to the tip electrode body <NUM>, as illustrated in <FIG>, the conductive line <NUM> positioned in a woven form along the circumference of the first internal tube <NUM> can be used. In this case, the first internal tube <NUM> made of an insulating material can be prevented from being broken or stretched during use due to its flexibility. That is, this is because the conductive line <NUM> made of a conductive metal material is positioned in a woven form along the circumference of the first internal tube <NUM>, thereby improving the rigidity of the first internal tube <NUM>.

Meanwhile, referring to <FIG>, a second embodiment of the electrocautery tip <NUM> can be configured to include the tip electrode body <NUM>, the tip insulator <NUM>, the coupling portion <NUM>, and a variable ring <NUM>.

The tip electrode body <NUM> can be configured to have the tip guide hole <NUM>, in which the guide wire <NUM> is inserted and positioned, formed at the central side thereof, have one side portion of the outer circumferential surface tapered in one direction, and have the other side portion of the outer circumferential surface welded-coupled <NUM> and connected to the conductive line <NUM>. Of course, it is not necessarily limited thereto, and although not illustrated in the drawing, for example, a structure of forming the through-hole and tying and connecting the conductive line <NUM> in a knotting method is also possible.

The tip electrode body <NUM> can entirely have a circular cross-sectional shape, and the tip electrode body <NUM> can be a conductive material such as a metal material as a portion that forms a hole by receiving a current to apply heat to the body tissue.

Then, the coupling portion <NUM> can be positioned at a portion of the outer circumferential surface of the tip electrode body <NUM>. In an embodiment of the present disclosure, the coupling portion <NUM> can be provided in a thread form, but since it is a portion that contacts the body tissue, the protruded portion of the thread can be provided to be smoothly round-processed in order to prevent fine damage of the body tissue.

The variable ring <NUM> can be a portion connected to the coupling portion <NUM> in order to vary the diameter of the tip electrode body <NUM>. The variable ring <NUM> can be in a circular ring form, and a thread corresponding to the thread of the coupling portion <NUM> can be processed at the inner circumferential surface thereof, and provided to be smoothly round-processed as well. The variable ring <NUM> can be made of the same material as the tip electrode body <NUM>, and that is, can be a conductive metal material. The variable ring <NUM> also forms a hole in the body tissue.

As an example of the variable ring <NUM>, as illustrated in <FIG>, it can be a form that the outer circumferential surface of the variable ring <NUM> has been rounded. In this case, when heat is applied to the body tissue to form a hole and the tip electrode body <NUM> enters into the body tissue or exits therefrom after the treatment of the stent <NUM>, the tip electrode body <NUM> can enter into or exit from the body tissue more smoothly without damage on the body tissue due to the round-processed outer circumferential surface. Of course, since the variable ring <NUM> closely contacts and is electrically connected to the tip electrode body <NUM>, it is also possible to adjust a range of the diameter that forms a hole in the body tissue.

For example, when the practitioner wishes to reduce the size of a hole in the body tissue, the tip electrode body <NUM> can be used in a state where the variable ring <NUM> has been separated, and conversely, when the practitioner wishes to form a slightly larger hole at the area of the body tissue to which the stent <NUM> is to be delivered, the tip electrode body <NUM> can be used with the variable ring <NUM> fitted therein.

In an embodiment of the present disclosure, although only one round-processed variable ring <NUM> has been disclosed, the round-processed shape of the variable ring <NUM> can be more various, and other shapes can also be included naturally as long as it is within a range that can be inferred from the present disclosure.

In addition, as another example of the variable ring <NUM>, as illustrated in <FIG>, it can be implemented as a form that the outer circumferential surface of the variable ring <NUM> has been tapered. At this time, one side of the outer circumferential surface of the variable ring <NUM> can be processed in a shape tapered in the same direction as the tip electrode body <NUM>, and the other side of the outer circumferential surface of the variable ring <NUM> can be processed in a shape tapered in the same direction as the tip insulator <NUM>.

In this case, when entering into the body tissue or exiting from it after the treatment of the stent <NUM>, the variable ring <NUM> has been tapered in the same direction as the tip electrode body <NUM> or the tip insulator <NUM>, thereby preventing the problem of being caught by the hole formed in the body tissue and causing damage.

Of course, the variable ring <NUM> closely contacts and is electrically connected to the tip electrode body <NUM>, thereby also adjusting a range of the diameter that forms a hole in the body tissue. A detailed description thereof is as described above.

Although only one taper-processed variable ring <NUM> has been disclosed in an embodiment of the present disclosure, the taper-processed shape of the variable ring <NUM> can be more various, and other forms can also be included naturally as long as it is within a range that can be inferred from the present disclosure.

In addition, in an embodiment of the present disclosure, one side of the outer circumferential surface of the variable ring <NUM> can be processed to be tapered at an angle smaller than that of the tip electrode body <NUM>, and the other side of the outer circumferential surface of the variable ring <NUM> can be processed to be tapered at an angle smaller than that of the tip insulator <NUM>.

Even if the variable ring <NUM> is mounted at the tip electrode body <NUM> through the above processing, the size of the cauterization hole in the body tissue due to the heat caused by the conducted current can be further reduced. Of course, it is possible to reduce not only the size of the cauterization hole simply but also to expand it conversely. The practitioner can have the variable rings <NUM> having a taper angle in plural, and the variable ring <NUM> can be used by changing and coupling therewith according to the size of the hole of the body tissue to be cauterized.

Meanwhile, referring to <FIG> and <FIG>, an adhesion pad <NUM> can be positioned at least any one side of the coupling portion <NUM> in order to prevent a gap between the inner circumference of the variable ring <NUM> and the outer circumference of the tip electrode body <NUM>.

In an embodiment of the present disclosure, the adhesion pad <NUM> is positioned at both sides of the coupling portion <NUM>. The adhesion pad <NUM> can be entirely a ring shape, and positioned by being forcibly fitted along the outer circumferential surface of the tip electrode body <NUM>. The adhesion pad <NUM> can be a flexible insulating material slightly protruded outwardly from the coupling portion <NUM>.

The position of the adhesion pad <NUM> allows the practitioner to closely contact them such an extent that there is no gap therebetween after rotating and fitting the variable ring <NUM> into the coupling portion <NUM>. This is because when the tip electrode body <NUM> enters into or exits from the body tissue, it is possible to block the phenomenon that blood, tissue, etc. are flowed and fitted into the spaced interval between the variable ring <NUM> and the tip electrode body <NUM>.

That is, since the variable ring <NUM> and the tip electrode body <NUM> are both made of a metallic material, it is difficult to fit therein perfectly and mechanically, and a minute gap is generated. The gap is blocked by the adhesion pad <NUM>, thereby helping the precision of the human body medical instrument.

Meanwhile, referring to <FIG> and <FIG>, in an embodiment of the present disclosure, the variable ring <NUM> can be provided to have different thicknesses from each other. For example, first, referring to <FIG>, when the cauterization hole formed in the body tissue is required to have an elliptical shape, the variable ring <NUM>, which has been formed so that the thickness D1 of one portion thereof is thicker than the thickness D2 of another portion thereof, is mounted thereon and used.

If the hole to be cauterized requires having any one portion protruded, as illustrated in <FIG>, the variable ring <NUM>, which has been formed so that the thickness D3 of any one portion of the variable ring <NUM> is thicker than the thickness D4 of another portion thereof, is mounted thereon and used.

Although only two shapes of the variable rings <NUM> has been illustrated in <FIG> and <FIG>, it will be apparent that the variable ring <NUM>, which has been formed to have various thicknesses that can be inferred within a range having the same object, can be included therein.

<FIG> illustrates a shape of the tip electrode body <NUM> according to the present disclosure when viewed from the front thereof.

Then, <FIG> illustrates another shape of the tip electrode body <NUM>, which is a structure in which the tip guide hole <NUM> is eccentrically positioned.

The tip electrode body <NUM> having the eccentric tip electrode body <NUM> processed is not generally used, but can be used according to the treatment environment. For example, if the stent delivery system <NUM> of the present disclosure has been inserted into the branch point where the blood vessel in the vascular system is divided in plural, when it is desired to move the tip electrode body <NUM> to the blood vessel in a desired direction, the guide wire <NUM> can be moved into the blood vessel more easily when it is positioned to face by rotating the eccentric tip guide hole <NUM> in the direction of the blood vessel.

In addition, in the present disclosure, as illustrated in <FIG>, the electrocautery tip <NUM> can be configured to further include a cauterization protrusion <NUM> formed at the outer circumferential surface of the tip electrode body <NUM>. The cauterization protrusion <NUM> can be positioned in plural with predetermined intervals interposed therebetween at the outer circumferential surface of the tip electrode body <NUM>.

It can be confirmed that <FIG> illustrates two cauterization protrusions <NUM> positioned at intervals of <NUM> degrees, <FIG> illustrates three cauterization protrusions <NUM> positioned at intervals of <NUM> degrees, and <FIG> illustrates four cauterization protrusions <NUM> positioned at intervals of <NUM> degrees, respectively, and this can guide the cauterization incision direction in advance when cauterizing the body tissue, such that the effect of minimizing the body tissue damage can also be expected. As in <FIG>, the cauterization protrusion <NUM> can also be positioned in a spiral form rather than a straight-line form.

<FIG> is a partial perspective diagram illustrating the shape of the cauterization protrusion <NUM> illustrated in <FIG>.

Of course, it is not limited to the disclosed form. The cauterization protrusion <NUM> can also be positioned at respective different intervals rather than the predetermined intervals, and other forms that can be inferred from the present disclosure can also be included in an embodiment of the present disclosure.

Meanwhile, although not illustrated in the drawing, as another example of the present disclosure, an interval between the plurality of cauterization protrusions <NUM> can be insulation-coated. In this case, since the tip electrode body <NUM> is insulation-coated, the cauterization of the body tissue is performed only for the cauterization protrusion <NUM>, thereby reducing the cauterization range of the body tissue. Of course, although not illustrated in the drawing, it can be considered that the variable ring <NUM> is also insulation-coated according to the treatment environment.

The description of the structure and various embodiments of the present disclosure are as described above, and hereinafter, a stent delivery procedure according to the present disclosure will be described.

<FIG> and <FIG> are diagrams illustrating a state where the stent is delivered in the present disclosure, and <FIG> are diagrams illustrating the operation states of the present disclosure inside the human body tissue. Reference numerals necessary for describing the operation states will be described with reference to <FIG>, <FIG>, and <FIG>.

First, referring to <FIG>, the practitioner first inserts the guide wire <NUM> in order to accurately specify the in-body position to be treated by the stent <NUM> and to guide the insertion path of the stent <NUM>. That is, in <FIG>, the guide wire <NUM> is inserted into the body tissue areas T1, T2 to be treated by the stent <NUM>.

Next, when the guide wire <NUM> is positioned at the body tissue areas T1, T2 and the delivery direction of the stent <NUM> is set, the practitioner operates so that the end portion of the guide wire <NUM> is fitted into the tip guide hole <NUM> of the tip electrode body <NUM>, and therefore, the guide wire <NUM> enters into the tip guide hole <NUM>, and positioned by passing through the inner hole <NUM> of the first internal tube <NUM>, a bar inner hole <NUM> of the movable bar <NUM>, and a second inner hole <NUM> formed at the second grip body <NUM>.

Thereafter, as in FIG. 15B, the practitioner grips the entire stent delivery system <NUM> and pushes it toward the guide wire <NUM>. Therefore, the external tube <NUM> and the electrocautery tip <NUM> enter into the body tissue areas T1, T2.

At this time, the connector portion <NUM> receives a current from the external current source <NUM> and supplies the current to the tip electrode body <NUM> by the conductive line <NUM>, thereby forming the cauterization hole in the body tissue by the heating reaction of the tip electrode body <NUM>. Therefore, the external tube <NUM> can stably enter into the body tissue areas T1, T2.

Thereafter, the practitioner pulls out the guide wire <NUM> through the wire outlet <NUM> positioned at the rear end portion of the second inner hole <NUM> to remove the guide wire <NUM> from the body tissue areas T1, T2 and the inside of the stent delivery system <NUM>.

Now, when positioning the stent <NUM> relatively adjacent to the treatment area, the practitioner grips the first grip portion <NUM> and the second grip portion <NUM>, and pulls the first grip portion <NUM> in the direction of the second grip portion <NUM>. At this time, since the first grip portion <NUM> is connected to the external tube <NUM> and the second grip portion <NUM> is connected to the second internal tube <NUM> by the movable bar <NUM>, the external tube <NUM> is retracted while the first grip portion <NUM> moves along the movable bar <NUM>.

Herein, since the end portion of the second internal tube <NUM> and the end portion of the first internal tube <NUM> are connected to each other, the first internal tube <NUM>, which has been in place, is exposed to the outside of the external tube <NUM> as the external tube <NUM> is retracted.

Referring to <FIG>, <FIG>, and <FIG>, as the first internal tube <NUM> is exposed to the outside of the external tube <NUM>, the stent <NUM>, which has been positioned in the stent space portion <NUM>, is exposed to the body tissue areas T1, T2. The stent <NUM> is unfolded through self-expansion, and performs its function at the desired body tissue areas T1, T2.

Although <FIG> illustrate a state where the stent <NUM> has been unfolded for the purpose of connecting between two areas T1, T2 of the body tissue, the present disclosure can also be used for expanding the circulatory system tube such as blood vessel, urethra, or lung in the circulatory system, such as blood vessel, urethra, or lung, which has been contracted or blocked.

Referring back to <FIG>, as the external tube <NUM> retreats, the stent <NUM> is relatively pushed back by the sign block <NUM> positioned at the end portion of the second internal tube <NUM>. That is, one end portion of the stent <NUM> is blocked and fixed by the sign block <NUM>, and at this time, the external tube <NUM> moves backwardly, such that it is opened from the other end portion of the stent <NUM> to the outside of the external tube <NUM>. Then, the stent <NUM> is positioned inside the body tissue areas T1, T2 and is self-expanded slowly.

Herein, the practitioner can confirm the current position of the stent inside the body tissue through the position identification of the sign block <NUM>. For this purpose, the sign block <NUM> can be painted in a color that can be identified by the practitioner.

Thereafter, as in <FIG>, the practitioner accurately positions the stent <NUM> in the desired body tissue by slightly pulling the stent <NUM> that has been partially expanded, and then further retreats the first grip portion <NUM> along the movable bar <NUM> so that the entire stent <NUM> is completely self-expanded.

Then, as in <FIG>, the stent treatment is completed by slowly pulling out the entire stent delivery system <NUM> and removing it from the body tissue.

The above description is merely a specific embodiment of the stent delivery system.

Therefore, it can be easily understood by those skilled in the art that the substitution and modification of the present disclosure can be made in various forms without departing from the scope of the disclosure as defined in the following claims.

Claim 1:
A stent delivery system, comprising:
a connector portion (<NUM>) connected to an external current source (<NUM>);
an electrocautery tip (<NUM>) connected to the connector portion (<NUM>) by a conductive line; and
a delivery portion (<NUM>) having a first side connected to the electrocautery tip (<NUM>) and a second side connected to the connector portion (<NUM>), the conductive line being accommodated in the delivery portion (<NUM>) for connecting the electrocautery tip (<NUM>) and the connector portion (<NUM>) positioned therein,
wherein the delivery portion (<NUM>) includes a stent space portion (<NUM>) accommodating a stent (<NUM>) and formed adjacent to the electrocautery tip (<NUM>) inside the delivery portion (<NUM>), and the delivery portion (<NUM>) is configured to move to supply the stent (<NUM>) into a human body tissue,
wherein the electrocautery tip (<NUM>) comprises:
a tip electrode body (<NUM>) being made of a conductive material and having a tip guide hole (<NUM>) formed therein, the tip electrode body (<NUM>) having an outer circumferential surface tapered to be narrower in a direction towards a distal end of the electrocautery tip (<NUM>) and a proximal end connected to the conductive line; characterized in that
a tip insulator (<NUM>) having its distal end coupled to the proximal end of the tip electrode body (<NUM>), its outer circumferential surface tapered to be narrower in a direction opposite to the direction of the tip electrode body (<NUM>) towards a proximal end of the electrocautery tip (<NUM>) and its proximal end connected to the delivery portion (<NUM>);
a coupling portion (<NUM>) formed at the proximal end of the outer circumferential surface of the tip electrode body (<NUM>); and
a variable-sized ring (<NUM>) configured to be coupled to the coupling portion (<NUM>) to vary a maximum diameter of the tip electrode body (<NUM>),
wherein the coupling portion (<NUM>) has a threaded outer surface, and the variable-sized ring (<NUM>) has a threaded inner surface formed to correspond to the threaded outer surface of the coupling portion (<NUM>); wherein
the outer circumferential surface of the variable ring (<NUM>) is tapered; wherein one side of the outer circumferential surface of the variable ring (<NUM>) is tapered in the same direction as the tip electrode body (<NUM>), and the other side of the outer circumferential surface of the variable ring (<NUM>) is tapered in the same direction as the tip insulator (<NUM>).