CN216061691U - Medical electrode lead assembly and cardiac pacing system - Google Patents

Abstract

The utility model provides a medical electrode lead assembly and a cardiac pacing system, wherein the medical electrode lead assembly comprises: a head electrode, a body and a buffer member; the head electrode is arranged at the far end of the body along the axial direction of the body and is used for penetrating into a preset part; when the buffer piece is at least in an expansion state, the buffer piece is arranged on the surface of the body in a protruding mode along the radial direction of the body and used for abutting against the preset part to limit the axial position of the body. So the configuration, after utilizing the head electrode to penetrate predetermined position, the bolster leans on with predetermined position and restricts the axial position of body, can prevent that the head electrode from leading to penetrating the left ventricle after acute phase or long-term pacing to the left ventricle removal, has reduced the perforation risk, has improved cardiac pacing system's reliability.

Description

Medical electrode lead assembly and cardiac pacing system

Technical Field

The utility model relates to the technical field of medical instruments, in particular to a medical electrode lead assembly and a cardiac pacing system.

Background

Artificial cardiac pacing has since been around for over half a century the way in which the heart is restored to beating simply by electrical stimulation, to now approach physiologic pacing, now the category of physiologic pacing is increasingly directed to self-conduction systems below the site of pacing block, to maximally maintain or correct the electrical and mechanical synchrony of the heart below the block site, thereby reducing or improving the incidence of heart failure. Bundle of his pacing was born in such pursuit and used clinically. Although bundle of his pacing is currently the most physiological pacing modality, its long-term safety concerns limit patients to bundle of his pacing for all pacing indications, particularly for diseases with partial block sites below or further from the bundle of his, such as atrioventricular block, left bundle branch block, etc. of the below bundle block, due to the generally high pacing threshold.

To cross the site of block and get a lower pacing threshold, the electrode can be passed deeper and farther and implanted into the ventricular septum to the left ventricular septum endomembrane for left bundle branch pacing where there is abundant left purkinje's fibrous reticulum, and the pacing morphology of RBBB (QRS complex time extension, complex morphology "M" type, ST lowering of lead V1, T inversion, ST elevation of V5, T uprightness), bundle branch potential and better pacing parameters than his bundle pacing can be obtained. However, no electrode specially designed for left bundle branch pacing exists in the market at present, so that when the left bundle branch pacing is performed by using an electrode lead, on one hand, the operation difficulty is high, and on the other hand, adverse events such as perforation and the like easily occur after the operation.

SUMMERY OF THE UTILITY MODEL

The utility model aims to provide a medical electrode lead assembly and a cardiac pacing system, and aims to solve the problem that the existing left bundle branch pacing operation is easy to punch.

In order to solve the above technical problems, the present invention provides a medical electrode lead assembly, which includes: a head electrode, a body and a buffer member;

the head electrode is arranged at the far end of the body along the axial direction of the body and is used for penetrating into a preset part;

when the buffer piece is at least in an expansion state, the buffer piece is arranged on the surface of the body in a protruding mode along the radial direction of the body and used for abutting against the preset part to limit the axial position of the body.

Optionally, the head electrode is smoothly transitionally connected with the body.

Optionally, the head electrode extends helically along the axial direction of the body.

Optionally, the head electrode is drill-bit shaped.

Optionally, the buffer member extends radially outward of the body and is inclined towards the distal end at least in the expanded state.

Optionally, the buffer member is continuously arranged around the circumference of the body to form a horn shape; or the buffer parts are arranged around the circumferential direction of the body at intervals to form at least two buffer blades.

Optionally, the buffer is switched from the expanded state to the retracted state when subjected to a restraining force.

Optionally, the body has a radially inward recessed region at a position corresponding to the distal end of the buffer; when the buffer piece is in the accommodating state, at least one part of the buffer piece is accommodated in the depressed area.

Optionally, the body includes an insulating layer and a first conductor radially from outside to inside, and the first conductor is connected to the head electrode.

Optionally, the insulating layer is tubular and has a hollow inner cavity; the first electric conductor is arranged in the inner cavity and extends spirally along the axial direction of the body.

Optionally, the medical electrode lead assembly further comprises: a ring electrode; the ring electrode is arranged on the periphery of the body around the circumferential direction of the body, is positioned on one side of the far end of the buffer piece along the axial direction of the body, and is used for contacting with the preset part; the body comprises an insulating layer and a second conductor from outside to inside along the radial direction, and the second conductor is connected with the ring electrode.

Optionally, the medical electrode lead assembly further comprises: a ring electrode; the ring electrode is arranged at the far end of the buffer piece and is used for contacting the preset part; the body comprises an insulating layer and a second conductor from outside to inside along the radial direction, and the second conductor is connected with the ring electrode.

In order to solve the technical problem, the utility model further provides a cardiac pacing system, which comprises the medical electrode lead assembly.

In summary, in the medical electrode lead assembly and the cardiac pacing system provided by the present invention, the medical electrode lead assembly includes: a head electrode, a body and a buffer member; the head electrode is arranged at the far end of the body along the axial direction of the body and is used for penetrating into a preset part; when the buffer piece is at least in an expansion state, the buffer piece is arranged on the periphery of the body in a protruding mode along the radial direction of the body and used for abutting against the preset part to limit the axial position of the body. So the configuration, after utilizing the head electrode to penetrate predetermined position, the bolster leans on with predetermined position and restricts the axial position of body, can prevent that the head electrode from leading to penetrating the left ventricle after acute phase or long-term pacing to the left ventricle removal, has reduced the perforation risk, has improved cardiac pacing system's reliability.

Drawings

It will be appreciated by those skilled in the art that the drawings are provided for a better understanding of the utility model and do not constitute any limitation to the scope of the utility model. Wherein:

FIG. 1 is a schematic view of a conventional electrode lead;

FIG. 2 is a schematic view in axial cross-section of a medical electrode lead assembly according to an embodiment of the present invention;

FIG. 3 is a schematic view of a preferred example of a buffer of an embodiment of the present invention;

FIG. 4 is a schematic view of another preferred example of a buffer of an embodiment of the present invention;

FIG. 5 is a schematic illustration of an application scenario for a medical electrode lead assembly in accordance with an embodiment of the present invention;

FIG. 6 is a schematic view of another preferred example of a ring electrode of an embodiment of the present invention.

In the drawings:

01-electrode lead; 011-helical electrodes; 012-a tubular body; 10-a head electrode; 11-a blade face; 12-cutting a groove; 20-body; 21-a recessed region; 22-an insulating layer; 23-a first electrical conductor; 24-a second electrical conductor; 30-a buffer; a 40-ring electrode; 50-chamber interval; 51-left ventricle; 52-left chamber wall; 53-right ventricle; 54-right chamber wall.

Detailed Description

To further clarify the objects, advantages and features of the present invention, a more particular description of the utility model will be rendered by reference to specific embodiments thereof which are illustrated in the appended drawings. It is to be noted that the drawings are in greatly simplified form and are not to scale, but are merely intended to facilitate and clarify the explanation of the embodiments of the present invention. Further, the structures illustrated in the drawings are often part of actual structures. In particular, the drawings may have different emphasis points and may sometimes be scaled differently.

As used in this application, the singular forms "a", "an" and "the" include plural referents, the term "or" is generally employed in a sense including "and/or," the terms "a" and "an" are generally employed in a sense including "at least one," the terms "at least two" are generally employed in a sense including "two or more," and the terms "first", "second" and "third" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicit to the number of technical features indicated. Thus, features defined as "first", "second", "third" may explicitly or implicitly include one or at least two of such features, the term "proximal" generally being the end closer to the operator, the term "distal" generally being the end closer to the patient, i.e. closer to the lesion (i.e. the end further from the operator), the terms "end" and "other end" and "proximal" and "distal" generally referring to the corresponding two parts, which include not only the end points, the terms "mounted", "connected", and "connected" should be understood broadly, e.g. as being either fixedly connected, detachably connected, or integrated; can be mechanically or electrically connected; either directly or indirectly through intervening media, either internally or in any other relationship. Furthermore, as used in the present invention, the disposition of an element with another element generally only means that there is a connection, coupling, fit or driving relationship between the two elements, and the connection, coupling, fit or driving relationship between the two elements may be direct or indirect through intermediate elements, and cannot be understood as indicating or implying any spatial positional relationship between the two elements, i.e., an element may be in any orientation inside, outside, above, below or to one side of another element, unless the content clearly indicates otherwise. The specific meanings of the above terms in the present invention can be understood by those skilled in the art according to specific situations.

Referring to fig. 1, a conventional electrode lead 01 is shown, which includes a spiral electrode 011 at a distal end (left end in fig. 1) and a tubular body 012 connected to the spiral electrode 011, wherein the spiral electrode 011 is wound with a wire having a diameter of about 0.2mm to 0.3mm to form a spring-like spiral structure. If left bundle branch pacing is performed using such an electrode lead 01, that is, the electrode lead 01 is implanted in the ventricular septum, when the operator initially screws the electrode lead 01 to cause the helical electrode 011 to enter the myocardial tissue of the ventricular septum, the myocardial tissue can be penetrated relatively easily because the cross-sectional area of the helical electrode 011 is small. Further, a section of the distal end of the tubular body 012 will follow the spiral electrode 011 and enter the myocardial tissue, and the subsequent screwing operation is difficult due to the sharp change of the cross-sectional area at the boundary of the spiral electrode 011 and the tubular body 012. In addition, the human ventricular septum thickness is generally about 9mm, the left bundle of electrodes is close to the left ventricle, that is, the spiral electrode 011 is screwed into a very close position to the left ventricular wall, because the electrode lead 01 will beat with the heart continuously after being implanted, the far end of the tubular body 012 and the spiral electrode 011 will hit the myocardial tissue continuously during beating, and after a while, the far end of the spiral electrode 011 can easily perforate into the left ventricle to cause serious adverse events.

Based on the above analysis and study, referring to fig. 2 in combination with fig. 5, an embodiment of the present invention provides a medical electrode lead assembly, which includes: a head electrode 10, a body 20, and a buffer 30; the head electrode 10 is disposed at the distal end (left end in fig. 2) of the body 20 in the axial direction of the body 20, and is used for penetrating into a predetermined site (referred to as myocardial tissue, such as ventricular septum 50); the buffer 30 is at least in an expanded state, and is protruded along the radial direction of the body 20 and disposed on the surface of the body 20, so as to abut against the predetermined portion to limit the axial position of the body 20.

It should be noted that, in some embodiments, the buffer member 30 may be elastic, and has an expanded state and a stored state, and when a constraint force is applied, for example, under the restriction of the transportation device, the buffer member 30 may be in the stored state, and after being released from the transportation device, the buffer member 30 may be converted from the stored state to the expanded state. In this embodiment, the buffer member 30 is disposed on the surface of the body 20 in a protruding manner along the radial direction of the body 20 at least in the expanded state, and is not limited to the shape in the accommodated state. In other embodiments, the buffer 30 may only have an expanded state and no storage state, i.e. it may not have elasticity, and cannot be switched, and it is disposed on the surface of the body 20 in a protruding manner along the radial direction of the body 20 when being delivered or after being released. The present invention is not limited to the form of the cushion member 30.

Since the buffer member 30 is disposed on the surface of the body 20 in a protruding manner along the radial direction of the body 20 at least in the expanded state, after a section of the region at the distal end of the head electrode 10 and the body 20 penetrates into the interior of the myocardial tissue (e.g., the ventricular septum 50), the buffer member 30 abuts against the myocardial tissue (e.g., the right ventricular wall 54), and the head electrode 10 and the body 20 are prevented from moving to the distal end (e.g., the left ventricle 51), so that the head electrode 10 can be prevented from moving to the left ventricle 51 after acute or long-term pacing to penetrate into the left ventricle 51, thereby reducing the risk of perforation and improving the reliability of the pacemaker.

Preferably, the head electrode 10 is smoothly transitionally connected with the body 20. Here, the smooth transition connection means that the radially outer dimension of the head electrode 10 and the radially outer dimension of the body 20 do not change abruptly, but transition smoothly. The radial outer dimensions are explained here: the radially outer dimension of the head electrode 10 refers to the maximum outer envelope dimension of the head electrode 10 in the radial direction of the body 20. In an alternative embodiment, the cross-section of the tip electrode 10 is circular or elliptical, and the radially outer dimension of the tip electrode 10 is its outer or major diameter. In particular, if the tip electrode 10 is in the form of a spiral spring, it is understood that the cross-sectional shape is also circular or oval, and the radial outer dimension of the tip electrode 10 is understood to be the radial outer dimension of the spiral filament itself. In other embodiments, the cross-section of the tip electrode 10 is multi-lobed, gear-shaped or other irregular shape, and the radially outer dimension of the tip electrode 10 is the diameter of its circumscribed circle. The radially outer dimension of the body 20 refers to the maximum outer envelope dimension in the radial direction of the body. In an alternative embodiment, the cross-section of the body 20 is circular or elliptical, and the radially outer dimension of the body 20 is its outer or major diameter. In other embodiments, the cross-section of the body 20 is polygonal, gear-shaped, or other irregular shape, and the radially outer dimension of the body 20 is the diameter of its circumscribed circle. The radial outer dimensions of the other components described below may also be defined with reference to the radial outer dimensions of the tip electrode 10 and body 20 described above.

While the smooth transition is divided into two cases: the radially outer dimension of the head electrode 10 is the same as the radially outer dimension of the body 20; alternatively, the radially outer dimension of the tip electrode 10 is different from the radially outer dimension of the body 20 (e.g., the radially outer dimension of the tip electrode 10 is smaller than the radially outer dimension of the body 20), and the two are connected by a ramp transition. The slope surface can be an inclined surface or a curved surface. It will be appreciated that the ramp should be at a small angle (e.g., less than 45) to the axial direction of the body 20 to avoid creating a large resistance when the distal portion of the body 20 penetrates into myocardial tissue.

Alternatively, the tip electrode 10 extends spirally along the axial direction of the body 20. So configured, the head electrode 10 can be firmly combined with the myocardial tissue without slipping after penetrating the myocardial tissue. In an alternative embodiment, the tip electrode 10 is in the form of a drill, as shown in figure 2. The drill bit may be shaped like a twist drill, and the distal end of the drill bit has a blade surface 11, and the blade surface 11 is connected with a helical cutting groove 12, so that the head electrode 10 can conveniently enter the interior of myocardial tissue when rotating. The drill bit-shaped structure can be understood and configured by those skilled in the art according to the prior art, and the present invention will not be described in detail. Alternatively, the body 20 may have a circular cross-section, and the drill-shaped tip electrode 10 may have a radially outer dimension that is the diameter of the circumscribed circle of the tip electrode 10, which is preferably the same as the outer diameter of the body 20. So configured, the distal end portion of the body 20 can easily penetrate myocardial tissue with less resistance following the head electrode 10.

In another alternative embodiment, the tip electrode 10 may also be in the form of a helical spring, such as may be similar to the helical electrode 011 shown in FIG. 1. To solve the abrupt change in the sectional area of the spring-shaped tip electrode 10 and the body 20, a transition connection with the body 20 may be formed by gradually enlarging the radial outer dimension of the proximal section of the spring-shaped tip electrode 10. Or an additional transition section may be used to connect the spring-like tip electrode 10 to the distal end of the body 20, which may form a smooth transition connection between the tip electrode 10 and the body 20.

With continued reference to fig. 2, preferably, the buffer 30 extends radially outward of the body 20 and is inclined toward the distal end at least in the expanded state. The buffer member 30 extends outwards along the radial direction of the body 20 and inclines towards the far end, so that the stress condition when the buffer member 30 abuts against myocardial tissue (such as the right chamber wall 54) can be improved, and the buffer member 30 is prevented from being fatigued and broken in long-term use. In general, to reduce the delivery size (primarily the radial dimension) of the medical electrode lead assembly and pacemaker, the buffer member 30 is preferably configured as a sheet member having a reduced thickness in the radial direction. More preferably, the buffer 30 is switched from the expanded state to the storage state when receiving a restraining force; the maximum radial outer dimension of the buffer 30 in the stowed condition is less than the maximum radial outer dimension in the expanded condition. The buffer 30 extends outward in the radial direction of the body 20 when in the expanded state, and may be close to or attached to the body 20 toward the outer circumference of the body 20 when in the stored state, thereby reducing its transport size. However, the joint between the sheet-shaped cushion 30 and the body 20 is weak, and if not handled, it is likely to be broken by fatigue in long-term use. Based on this, the buffer member 30 extends outward in the radial direction of the body 20 and inclines toward the distal end, so that the resisting moment of the buffer member 30 in the axial direction of the body 20 can be increased, and the service life of the buffer member 30 can be prolonged. Preferably, the buffer member 30 is made of a polymer material containing a developing material or a metal material having elastic deformability.

As shown in fig. 3, in a preferred example, the buffer 30 is continuously disposed around the circumference of the body 20, forming a flare shape. The horn-shaped buffer member 30 is stable in structure, not easy to deform, and beneficial to prolonging the service life. As shown in fig. 4, in another preferred example, the buffering members 30 are arranged around the circumference of the body 20 at intervals, forming at least two buffering leaves, such as 4 buffering leaves. The buffer members 30 in the form of a plurality of pieces are easily gripped to a storage state, and are easily loaded into a conveying device for conveying.

Optionally, the body 20 has a recessed area 21 radially inward at a position corresponding to the distal end of the buffer 30; when the buffer member 30 is in the storage state, at least a portion of the buffer member is accommodated in the recessed area 21. Preferably, the depth of the recessed area 21 along the radial direction of the body 20 is matched with the radial thickness of the buffer member 30, and the length of the recessed area 21 along the axial direction of the body 20 is matched with the axial length of the buffer member 30, so that the buffer member 30 can be completely accommodated in the recessed area 21 in the accommodating state. Alternatively, the recessed region 21 is disposed around the circumference of the body 20, preferably continuously around the circumference of the body 20.

With continued reference to fig. 2, the body 20 further includes an insulating layer 22 and a first conductive body 23 from outside to inside in the radial direction, and the first conductive body 23 is connected to the head electrode 10. It should be understood that the connection of the first conductor 23 to the head electrode 10 may be an electrical connection or a mechanical connection (which forms an electrical connection). The first conductor 23 is used to connect the electrode 10 with the electrical components of the pacemaker, and also serves as a mechanical stress component of the body 20 to bear a part of the bending moment and the torque.

Preferably, the insulating layer 22 is tubular and has a hollow inner cavity; the first electric conductor 23 is disposed in the inner cavity, and the first electric conductor 23 spirally extends along the axial direction of the body 20. In an alternative example, the first electrical conductor 23 is formed by winding one or more wires with an insulating coating on the surface to form a helical coil of the same diameter, which is mechanically connected to the head electrode 10 and at the same time electrically connected thereto. The first conductor 23 extending in a spiral shape is advantageous for improving the torsion resistance of the medical electrode lead assembly, since in use, the head electrode 10 is screwed into the myocardial tissue by rotating the medical electrode lead assembly, so that the body 20 receives torsion in practice, and the first conductor 23 extending in a spiral shape can be used as a bending-resistant and torsion-resistant member of the body 20 besides conducting electricity.

Further, the medical electrode lead assembly further comprises: a ring electrode 40; the ring electrode 40 is disposed on the outer circumference of the body 20 around the circumferential direction of the body 20, and the ring electrode 40 is located on one side of the distal end of the buffer 30 (the left side of the buffer 30 in fig. 2) along the axial direction of the body 20, that is, the ring electrode 40 is located at a position where the body 20 extends distally beyond the buffer 30, and the ring electrode 40 is used for contacting the predetermined portion, such as inserting myocardial tissue and forming an electrical connection with the myocardial tissue; the body 20 further includes a second electrical conductor 24 disposed radially within the insulating layer 22, the second electrical conductor 24 being connected to the ring electrode 40. Alternatively, the first conductor 23 and the second conductor 24 may be co-wound to form a set of helical coils with equal diameters, such as two-wire wound or multi-wire wound. The second conductor 24 may be electrically connected to the ring electrode 40 or mechanically connected (simultaneously electrically connected). The structure and arrangement principle of the second conductor 24 can be referred to the first conductor 23.

In another embodiment, referring to fig. 6, the ring electrode 40 may also be disposed at the distal end of the buffer 30 instead of the outer periphery of the body 20, and the ring electrode 40 is used for contacting the predetermined portion; similarly, the ring electrode 40 may be connected to the second conductor 24, for example, a lead wire may be embedded in the buffer 30, and the ring electrode 40 may be electrically connected to the second conductor 24 through the lead wire. With such a configuration, the ring electrode 40 may not be disposed on the main body 20, and the process of the main body 20 is simplified, thereby facilitating the production and assembly.

Based on the medical electrode lead assembly, the embodiment further provides a cardiac pacing system, which includes the medical electrode lead assembly as described above. Other components of the cardiac pacing system may be configured according to the prior art by those skilled in the art and will not be described in detail herein.

Referring to fig. 5, an implantation method of the medical electrode lead assembly and the cardiac pacing system according to the present embodiment is exemplarily described:

the operator first uses the conventional method of implanting a cardiac pacing electrode, such as by delivering the distal end of a medical electrode lead assembly through a sheath into the right ventricle 53 and placing the tip electrode 10 against the right ventricular wall 54, and then rotates the body 20 such that torque is transmitted through the body 20 to the tip electrode 10, causing the tip electrode 10 to penetrate the interior of the ventricular septum 50 until the bumper 30 reaches the right ventricular wall 54 and then stops rotating.

The electrical parameter is measured and if the parameter is not satisfactory, the body 20 can be rotated until the electrical parameter is satisfactory. At this time, the buffer member 30 is left in the right ventricle 53, which can prevent the head electrode 10 from moving towards the left ventricle 51 to penetrate into the left ventricle 51 after acute or long-term pacing, thereby reducing the risk of perforation and improving the reliability of the pacemaker.

In summary, in the medical electrode lead assembly and the cardiac pacing system provided by the present invention, the medical electrode lead assembly includes: a head electrode, a body and a buffer member; the head electrode is arranged at the far end of the body along the axial direction of the body and is used for penetrating into a preset part; when the buffer piece is at least in an expansion state, the buffer piece is arranged on the surface of the body in a protruding mode along the radial direction of the body and used for abutting against the preset part to limit the axial position of the body. So the configuration, after utilizing the head electrode to penetrate predetermined position, the bolster leans on with predetermined position and restricts the axial position of body, can prevent that the head electrode from leading to penetrating the left ventricle after acute phase or long-term pacing to the left ventricle removal, has reduced the perforation risk, has improved cardiac pacing system's reliability.

It should be noted that, several of the above embodiments may be combined with each other. The above description is only for the purpose of describing the preferred embodiments of the present invention, and is not intended to limit the scope of the present invention, and any variations and modifications made by those skilled in the art based on the above disclosure are within the scope of the appended claims.

Claims (13)

1. A medical electrode lead assembly, comprising: a head electrode, a body and a buffer member;

the head electrode is arranged at the far end of the body along the axial direction of the body and is used for penetrating into a preset part;

when the buffer piece is at least in an expansion state, the buffer piece is arranged on the surface of the body in a protruding mode along the radial direction of the body and used for abutting against the preset part to limit the axial position of the body.

2. The medical electrode lead assembly of claim 1, wherein the tip electrode is smoothly transitioned with the body.

3. The medical electrode lead assembly of claim 2, wherein the tip electrode extends helically along an axial direction of the body.

4. The medical electrode lead assembly of claim 3, wherein the tip electrode is drill-shaped.

5. The medical electrode lead assembly of claim 1, wherein the buffer member extends radially outward of the body while being angled distally at least in the expanded state.

6. The medical electrode lead assembly of claim 5, wherein the buffer member is continuously disposed around a circumference of the body, forming a flare; or the buffer parts are arranged around the circumferential direction of the body at intervals to form at least two buffer blades.

7. The medical electrode lead assembly of claim 1, wherein the buffer is transitioned from the expanded state to the stowed state when subjected to a restraining force.

8. The medical electrode lead assembly of claim 7, wherein the body has a radially inward recessed region at a location corresponding to the distal end of the buffer; when the buffer piece is in the accommodating state, at least one part of the buffer piece is accommodated in the depressed area.

9. The medical electrode lead assembly of claim 1, wherein the body comprises an insulating layer and a first electrical conductor radially outward and inward, the first electrical conductor being connected to the tip electrode.

10. The medical electrode lead assembly of claim 9, wherein the insulating layer is tubular having a hollow lumen; the first electric conductor is arranged in the inner cavity and extends spirally along the axial direction of the body.

11. The medical electrode lead assembly of claim 1, further comprising: a ring electrode; the ring electrode is arranged on the periphery of the body around the circumferential direction of the body, is positioned on one side of the far end of the buffer piece along the axial direction of the body, and is used for contacting with the preset part; the body comprises an insulating layer and a second conductor from outside to inside along the radial direction, and the second conductor is connected with the ring electrode.

12. The medical electrode lead assembly of claim 1, further comprising: a ring electrode; the ring electrode is arranged at the far end of the buffer piece and is used for contacting the preset part; the body comprises an insulating layer and a second conductor from outside to inside along the radial direction, and the second conductor is connected with the ring electrode.

13. A cardiac pacing system comprising a medical electrode lead assembly according to any one of claims 1 to 12.

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