A cardiac pacemaker lead

Abstract

The utility model discloses a kind of cardiac pacemaker lead wires, comprising: conductive transmission module, it includes conductor, the outer surface of the conductor is covered with insulating layer, two ends of the conductor are respectively fixed with two electrode heads, one of the electrode heads is used to contact with cardiac tissue, realize the perception and stimulation of electrical signal, limiting fixed module, it includes the corrugated sleeve and sleeve assembly of sliding sleeve in the conductor exterior, the sleeve assembly is fixedly connected with multiple evenly distributed oblique barbs.This utility model can hook pericardium of surrounding tissue by oblique barb, thereby preventing conductor from displacement, when pulling out conductor, only need to rotate conductor to make oblique barb not hook pericardium, can be smoothly extracted, by corrugated sleeve, sleeve assembly can be allowed to move moderately, make electrode head always keep good contact with cardiac tissue, and reduce the damage caused by oblique barb to endocardium in pulling process.

Description

Technical Field

[0001] This utility model relates to the field of medical technology, and in particular to a cardiac pacemaker lead. Background Technology

[0002] Cardiac pacing electrode leads are devices used temporarily in emergency situations or surgery to provide additional electrical stimulation to the heart to restore a normal heart rhythm. In some cases, the heart may lose its normal rhythm and contraction for various reasons. In such cases, cardiac pacing electrode leads can be used to send electrical stimulation signals to the heart so that it can resume normal contraction and rhythm.

[0003] The tip of a cardiac pacemaker lead is typically fixed to the endocardial surface of the right atrium (atrial pacing) or right ventricle (ventricular pacing). Existing pacemaker leads have relatively smooth insulation surfaces, resulting in less friction between the smooth surface and surrounding tissues. After implantation, the electrode lead may be more prone to displacement, especially during patient activity or heartbeat. Slight movement of the lead may affect its accurate fixation in the intended cardiac position, potentially leading to poor pacing or the need for electrode repositioning. Therefore, a new cardiac pacemaker lead is proposed. Utility Model Content

[0004] The purpose of this section is to outline some aspects of embodiments of the present invention and to briefly describe some preferred embodiments. Simplifications or omissions may be made in this section, as well as in the abstract and title of this application, to avoid obscuring the purpose of these documents; however, such simplifications or omissions should not be construed as limiting the scope of the present invention.

[0005] In view of the problems existing in the current cardiac pacemaker lead, this utility model is proposed.

[0006] Therefore, the purpose of this utility model is to provide a cardiac pacemaker lead that addresses the problem that the surface of the pacemaker lead's insulation layer is relatively smooth, and the lead may move slightly during patient activity or heartbeat, affecting its accurate fixation in the predetermined heart position, which may lead to poor pacing effect or the need to readjust the electrode position.

[0007] To solve the above-mentioned technical problems, this utility model provides the following technical solution: a cardiac pacemaker lead, comprising:

[0008] A conductive transmission module includes a conductor, the outer surface of which is covered with an insulating layer, and two electrode heads are fixed at both ends of the conductor, one of which is used to contact heart tissue to realize the sensing and stimulation of electrical signals.

[0009] The limiting and fixing module includes a corrugated sleeve that is slidably sleeved on the outside of the conductor and a sleeve assembly. The sleeve assembly is fixedly connected with a plurality of evenly distributed oblique barbs, which are used to prevent the conductor from shifting after implantation into the surrounding tissue.

[0010] As a preferred embodiment of the cardiac pacemaker lead of this utility model, the cannula assembly consists of two straight tubes, two V-shaped telescopic sleeves, and a connecting tube. The two straight tubes are respectively fixed to the insulating layer and the electrode head. Multiple oblique barbs are respectively fixed to the tube walls of the two straight tubes. The two V-shaped telescopic sleeves are respectively fixed to both ends of the connecting tube, and the two straight tubes are respectively fixed to the other ends of the two V-shaped telescopic sleeves. The V-shaped telescopic sleeves are used for the oblique barbs to adapt to the stress generated by the heartbeat or human activity.

[0011] In a preferred embodiment of the cardiac pacemaker lead described in this utility model, a plurality of reverse barbs are fixedly connected to the wall of the connecting tube, and the reverse barbs are tilted in the opposite direction to the oblique barbs.

[0012] In a preferred embodiment of the cardiac pacemaker lead described in this utility model, both the oblique barb and the reverse barb are triangularly arranged, and the end of the oblique barb and the reverse barb away from the straight tube is a pointed tip, which is used to embed into the surrounding tissue.

[0013] In a preferred embodiment of the cardiac pacemaker lead described in this utility model, the oblique barbs and the reverse barbs are distributed in a spiral or ring array along the axial direction of the straight tube, and the oblique barbs and the reverse barbs are arranged in a relatively aligned manner.

[0014] As a preferred embodiment of the cardiac pacemaker lead described in this utility model, the V-shaped telescopic sleeve is made of elastic metal material or polymer elastomer, which can deform when subjected to external force.

[0015] In a preferred embodiment of the cardiac pacemaker lead described in this utility model, the corrugated structure of the corrugated sleeve is parallel to the axial direction of the conductor, and the surfaces of the oblique barbs and reverse barbs are all smoothed.

[0016] The beneficial effects of this invention are as follows: the oblique barbs can hook onto the pericardium of the surrounding tissue after the electrode head is inserted into the heart tissue, thereby effectively preventing conductor displacement. When the patient moves or the heart beats, the corrugated sleeve allows the cannula assembly to move moderately, ensuring that the electrode head always maintains good contact with the heart tissue and reducing damage to the pericardium caused by the oblique barbs during conductor pulling. When removing the conductor, simply rotate the conductor so that the oblique barbs do not hook onto the pericardium, and it can be easily pulled out. Attached Figure Description

[0017] To more clearly illustrate the technical solutions of the embodiments of this utility model, the drawings used in the description of the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this utility model. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort. Among them:

[0018] Figure 1 This is a partial structural diagram of the cardiac pacemaker lead proposed in this utility model;

[0019] Figure 2 This is a schematic diagram of the conductor and electrode head connection structure proposed in this utility model;

[0020] Figure 3 This is a schematic diagram of the disassembled structure of the sleeve assembly proposed in this utility model. Attached image description:

[0022] 100. Conductive transmission module; 101. Conductor; 102. Insulating layer; 103. Electrode head;

[0023] 200. Limiting and fixing module; 201. Corrugated sleeve; 202. Sleeve assembly; 202a. Straight pipe; 202b. V-shaped telescopic sleeve; 202c. Connecting pipe; 203. Angled barb; 204. Reverse barb. Detailed Implementation

[0024] To make the above-mentioned objectives, features and advantages of this utility model more apparent and understandable, the specific embodiments of this utility model will be described in detail below with reference to the accompanying drawings.

[0025] Many specific details are set forth in the following description in order to provide a full understanding of the present invention. However, the present invention may also be implemented in other ways different from those described herein. Those skilled in the art can make similar extensions without departing from the spirit of the present invention. Therefore, the present invention is not limited to the specific embodiments disclosed below.

[0026] Secondly, the term "an embodiment" or "embodiment" as used herein refers to a specific feature, structure, or characteristic that may be included in at least one implementation of the present invention. The phrase "in one embodiment" appearing in different places in this specification does not necessarily refer to the same embodiment, nor is it a single embodiment or an embodiment selectively excluded from other embodiments.

[0027] Secondly, this utility model is described in detail with reference to the schematic diagrams. When describing the embodiments of this utility model, for ease of explanation, the cross-sectional views illustrating the device structure may be partially enlarged, not adhering to the usual scale. Furthermore, the schematic diagrams are merely examples and should not limit the scope of protection of this utility model. In addition, actual manufacturing should include the three-dimensional spatial dimensions of length, width, and depth.

[0028] Example 1

[0029] Reference Figures 1-3 The first embodiment of this utility model provides a cardiac pacemaker lead that can increase the friction of the lead surface and make its electrode hook onto the surrounding tissue to prevent the lead from shifting. It includes: a conductive transmission module 100 and a limiting and fixing module 200.

[0030] The conductive transmission module 100 includes a conductor 101, the outer surface of which is covered with an insulating layer 102. Two electrode heads 103 are fixed at both ends of the conductor 101, one of which is used to contact the heart tissue to realize the sensing and stimulation of electrical signals.

[0031] The limiting and fixing module 200 includes a corrugated sleeve 201 that is slidably sleeved on the outside of the conductor 101 and a sleeve assembly 202. Multiple evenly distributed oblique barbs 203 are fixedly connected to the sleeve assembly 202. The oblique barbs 203 are used to prevent the conductor 101 from shifting after implantation into the surrounding tissue.

[0032] The electrode heads 103 at both ends of the conductor 101 are used to embed into the endocardium and connect to the pacemaker, respectively. The insulating layer 102 wraps around the outside of the conductor to provide insulation and prevent electrical signal leakage. The conductor 101 is responsible for transmitting electrical signals and conducting the electrical pulses generated by the pacemaker to the heart. The corrugated sleeve 201 is a retractable tube sleeve, and space is left on the conductor 101 for the corrugated sleeve to move in and out. In use, the end of the heart is usually punctured or cut through a vein, and the electrode head 103 and the conductor 101 are carefully guided along the blood vessel path to a specific part of the heart. Then, the electrode head 103 located at the position of the limiting and fixing module 200 is inserted into the surrounding tissue, so that the oblique barb 203 passes through the endocardium. By rotating the oblique barb 203 to make it offset from the incision, it can hook the pericardium of the surrounding tissue, thereby preventing the electrode head 103 and the conductor 101 from sliding around the tissue.

[0033] Furthermore, during patient activity or heartbeat, the conductor 101 may be forced to stretch. The corrugated sleeve 201 allows the cannula assembly 202 to move moderately, enabling the oblique barb 203 to move slightly with the cannula assembly 202. This ensures that the electrode head 103 always maintains good contact with the heart tissue and reduces damage to the endocardium caused by the oblique barb 203 during the stretching of the conductor 101. When adjusting the position of the conductor 101 or pulling it out, the cannula assembly 202 can be rotated to align the oblique barb 203 with the incision of the oblique barb 203, thereby smoothly pulling out the oblique barb 203 along the incision to reduce damage to surrounding tissues.

[0034] Example 2

[0035] Reference Figure 1 and Figure 3 This is the second embodiment of the present invention. Unlike the previous embodiment, the sleeve assembly 202 consists of two straight tubes 202a, two V-shaped telescopic sleeves 202b, and a connecting tube 202c. The two straight tubes 202a are fixed to the insulating layer 102 and the electrode head 103, respectively. Multiple oblique barbs 203 are fixed to the tube walls of the two straight tubes 202a, and the two V-shaped telescopic sleeves 202b are fixed to both ends of the connecting tube 202c. The two straight tubes 202a are fixed to the other ends of the two V-shaped telescopic sleeves 202b. The V-shaped telescopic sleeves 202b are used to adapt the oblique barbs 203 to the stress generated by heartbeat or human activity.

[0036] The two V-shaped telescopic sleeves 202b are elastic and can extend and retract within a small range on the conductor 101. The oblique barbs 203 on the two straight tubes 202a are inserted into the endocardium. When the heart beats or the body moves and causes deformation of the surrounding tissue, the oblique barbs 203 on the two straight tubes 202a can pull the straight tubes 202a to slide on the conductor 101 with the deformation of the surrounding tissue. This allows the distance between the two straight tubes 202 to be adjusted adaptively with a small range, so that the oblique barbs 203 at different positions can make good contact with the endocardium where they are located, and further reduce the damage of the oblique barbs 203 to the surrounding tissue.

[0037] Example 3

[0038] Reference Figure 1 and Figure 3 This is the third embodiment of the present invention. Unlike the previous embodiment, multiple reverse barbs 204 are fixedly connected to the wall of the connecting pipe 202c, and the inclination direction of the reverse barbs 204 is opposite to that of the oblique barbs 203.

[0039] When the size of the reverse barb 204 is smaller than that of the oblique barb 203, the reverse barb 204 can pass through the notch pierced by the oblique barb 203 and reduce damage to the tissue. After the oblique barb 203 passes through the endocardium, the reverse barb 204 can be slightly rotated to offset it from the notch created by the oblique barb 203. The reverse barb 204 is also used to hook the endocardium. The reverse barb 204 is used to improve the gripping force of the cannula assembly 202 on the tissue, so that the electrode head 103 will not penetrate into the interior of the tissue surrounding the heart, thereby further ensuring that the position of the electrode head 103 can be fixed and will not be displaced.

[0040] Specifically, both the oblique barb 203 and the reverse barb 204 are triangular in shape, and the ends of the oblique barb 203 and the reverse barb 204 that are away from the straight tube 202a are pointed and used to embed into the surrounding tissue.

[0041] The angled barb 203, with its triangular arrangement, increases the connection area between the angled barb 203 and the straight tube 202a, thus ensuring the stability of the angled barb 203. The reverse barb 204 works similarly to the angled barb 203. The tips of the angled barb 203 and the reverse barb 204 are designed to easily penetrate into the surrounding tissue, thereby hooking onto the surrounding components.

[0042] Example 4

[0043] Reference Figure 1 and Figure 3 This is the fourth embodiment of the present invention. Unlike the previous embodiment, the oblique barbs 203 and the reverse barbs 204 are both distributed in a spiral or ring array along the axial direction of the straight tube 202a, and the distribution positions of the oblique barbs 203 and the reverse barbs 204 are relatively aligned.

[0044] The oblique barbs 203 and the reverse barbs 204 are evenly distributed on the straight tube 202a and the connecting tube 202c, respectively, so that the oblique barbs 203 and the reverse barbs 204 can withstand stress from different directions during heart contraction or patient activity, so as to ensure the stable position of the electrode head 103.

[0045] Specifically, the V-shaped telescopic sleeve 202b is made of elastic metal material or polymer elastomer, which can deform when subjected to external force.

[0046] The material of the V-shaped telescopic sleeve 202b can automatically adapt to the physiological activities of the heart and the displacement and stress changes brought about by body movement, and reduce the risk of fatigue and breakage of the oblique barbs 203 and reverse barbs 204 due to long-term stress.

[0047] It should be noted that the corrugated structure of the corrugated sleeve 201 is parallel to the axial direction of the conductor 101, and the surfaces of the oblique barbs 203 and the reverse barbs 204 are both smoothed.

[0048] The parallel corrugated structure does not generate additional torsional or bending stress on the conductor 101 and ensures that the sleeve assembly 202 can adapt to expansion and contraction. The smooth surface reduces friction with surrounding tissues during the insertion of the oblique barbs 203 and the reverse barbs 204 into the heart tissue, so as to facilitate the puncture of surrounding tissues.

[0049] During use, the electrode head 103 and conductor 101 are carefully guided along the blood vessel path to a specific part of the heart. Then, the electrode head 103, located at the position of the limiting and fixing module 200, is inserted into the surrounding tissue, allowing the oblique barb 203 and the reverse barb 204 to pass through the endocardium. The reverse barb 204 is then slightly rotated to offset the notch created by the oblique barb 203, thereby hooking the endocardium of the surrounding tissue through the oblique barb 203 and the reverse barb 204, thus preventing the electrode head 103 and conductor 101 from sliding around the tissue. This ensures that the position of the electrode head 103 can be fixed and will not shift. When the patient moves or the heart beats, the conductor 101 may be forced to pull. The corrugated sleeve 201 allows the cannula assembly 202 to move moderately, allowing the oblique barb 203 to move slightly with the cannula assembly 202, thereby ensuring that the electrode head 103 always maintains good contact with the heart tissue.

[0050] Furthermore, the oblique barbs 203 on the two straight tubes 202a can pull the straight tubes 202a to slide on the conductor 101 as the surrounding tissue deforms, so that the distance between the two straight tubes 202 can be adaptively adjusted in a small range. This makes it easier for the oblique barbs 203 at different positions to make good contact with their respective endocardium, and reduces the damage to the endocardium caused by the oblique barbs 203 during the pulling process of the conductor 101. When adjusting the position of the conductor 101 or pulling it out, the cannula assembly 202 can be rotated to align the oblique barbs 203 with the incision of the oblique barbs 203, so that the oblique barbs 203 can be pulled out smoothly along the incision.

[0051] It should be noted that the above embodiments are only used to illustrate the technical solution of this utility model and are not intended to limit it. Although this utility model has been described in detail with reference to preferred embodiments, those skilled in the art should understand that modifications or equivalent substitutions can be made to the technical solution of this utility model without departing from the spirit and scope of the technical solution of this utility model, and all such modifications or substitutions should be covered within the scope of the claims of this utility model.

Claims

1. A cardiac pacemaker lead, characterized in that, include: A conductive transmission module (100) includes a conductor (101) with an insulating layer (102) covering the outer surface of the conductor (101). Two electrode heads (103) are fixed at both ends of the conductor (101), one of which is used to contact the heart tissue to realize the sensing and stimulation of electrical signals. The limiting and fixing module (200) includes a corrugated sleeve (201) that is slidably sleeved on the outside of the conductor (101) and a sleeve assembly (202). The sleeve assembly (202) is fixedly connected with a plurality of evenly distributed oblique barbs (203), which are used to prevent the conductor (101) from shifting after implantation into the surrounding tissue.

2. The pacemaker lead according to claim 1, characterized in that: The sleeve assembly (202) consists of two straight tubes (202a), two V-shaped telescopic sleeves (202b), and a connecting tube (202c). The two straight tubes (202a) are fixed to the insulating layer (102) and the electrode head (103), respectively. Multiple oblique barbs (203) are fixed to the tube walls of the two straight tubes (202a). The two V-shaped telescopic sleeves (202b) are fixed to both ends of the connecting tube (202c), and the two straight tubes (202a) are fixed to the other ends of the two V-shaped telescopic sleeves (202b). The V-shaped telescopic sleeves (202b) are used to adapt the oblique barbs (203) to the stress generated by heartbeat or human activity.

3. The pacemaker lead according to claim 2, characterized in that: The connecting tube (202c) has multiple reverse barbs (204) fixedly connected to its wall, and the reverse barbs (204) are inclined in the opposite direction to the oblique barbs (203).

4. The cardiac pacemaker lead according to claim 3, characterized in that: Both the oblique barb (203) and the reverse barb (204) are arranged in a triangular shape, and the end of the oblique barb (203) and the reverse barb (204) away from the straight tube (202a) is a pointed tip, which is used to embed into the surrounding tissue.

5. The pacemaker lead according to claim 4, characterized in that: The oblique barbs (203) and the reverse barbs (204) are both distributed in a spiral or ring array along the axial direction of the straight tube (202a), and the oblique barbs (203) and the reverse barbs (204) are arranged in a relatively aligned position.

6. The pacemaker lead according to claim 2, characterized in that: The V-shaped telescopic sleeve (202b) is made of elastic metal material or polymer elastomer, and can deform when subjected to external force.

7. The cardiac pacemaker lead according to claim 5, characterized in that: The corrugated structure of the corrugated sleeve (201) is parallel to the axial direction of the conductor (101), and the surfaces of the oblique barbs (203) and the reverse barbs (204) are both smoothed.

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