CN209392587U - Electric lead and Implanted bioelectrode - Google Patents

Abstract

The utility model provides a kind of electric lead and Implanted bioelectrode, and Implanted bioelectrode can be made to have corresponding rigidity in different sections, improve the success rate of electronic stimulation and the reliability of circuit connection.The Implanted bioelectrode of the utility model includes electric lead, and the electric lead includes spiral conductive body, the conductive body at least has sequentially connected distal section, centre portion and proximal section, and the rigidity of the centre portion is less than the rigidity of the distal section and the proximal section.In actually preparation, can helical cut metal tubular at the conductive body, while simplifying preparation process, effectively control the rigidity of each section.

Description

Electric lead and Implanted bioelectrode

Technical field

The utility model relates to the field of medical instrument technology, in particular to a kind of electric lead and Implanted bioelectrode.

Background technique

With the development of modern medical science, more and more helpless diseases of traditional medicine can pass through electro photoluminescence skill Art is treated, such as electro photoluminescence cardiac muscle can treat heart rate exception, and electro photoluminescence subthalamic nuclei or interior globus pallidus can improve pa gold Gloomy symptom, electrical vagus nerve stimulation can auxiliary therapeutic agent intractable epilepsy and depression.Electrical stimulating therapy passes through to muscle or mind Through cell inject charge come improve symptom and treatment disease, used device generally comprise implantation human body impulse generator with Bioelectrode (hereinafter referred to as electrode), impulse generator generate electric signal, and electric signal reaches electricity after certain conducting path Electric signal is transferred to target spot by pole, electrode.Therefore, important component of the implanted electrode as electric stimulation, plays and people The effect of body tissue interaction, the validity and security sense weight of the design and fabrication of Electrode for entire electric stimulation Greatly.

The electric stimulation for being currently used in deep brain stimulation (DBS) is as shown in Figure 1a, including impulse generator (is commonly abbreviated as IPG) 1, electrode extended line 2 and electrode 3, impulse generator 1 are implanted in thoracic cavity, and impulse generator 1 is close with electrode extended line 2 End is connected, and it is subcutaneous that electrode extended line 2 is embedded in human body, reaches skull surface, distal end and the electrode 3 of electrode extended line 2 by neck Proximal end be connected, electrode 3 passes through skull and is inserted into intracerebral, and the distal end of electrode 3 is in contact with target spot, and electrode 3 passes through the fixation of skull cap 4 At fenestrated skull, the pulse signal that impulse generator 1 generates is sent to electrode 3 by electrode extended line 2, then passes to target Point.

Electrode currently used for DBS generallys use structure shown in Fig. 2 a.The main structure of electrode is an elongated height Molecule plastic tube, referred to as electrode catheter 33；Several beckets are separately installed in the end of electrode catheter 33；Distal end is known as piercing Swash electrode retaining collar 31, plays the role of injecting charge generation electro photoluminescence to biological tissue；Proximal end is known as connection electrode ring 32, plays The effect being connect with electrode extended line generation circuit；The inside of electrode catheter 33 is installed with electric lead 34, for connecting the thorn of end Swash electrode retaining collar 31 and connection electrode ring 32, forms conductive channel.The material of electrode catheter 33 is usually polyurethane or silicon rubber etc. The good polymer of bio-compatibility, hardness is lower, rubber like, and the material of stimulating electrode ring 31 and connection electrode ring 32 is usual For noble metal (such as platinumiridio) and nickel cobalt (alloy) (such as MP35N), there is good corrosion resistance and bio-compatibility.

As shown in Figure 2 b, traditional electric lead 34 is helical form, is formed by more uniform seal wire 34-2 coilings.Seal wire The surface of 34-2 is equipped with the coating 34-1 for insulation, the radical of seal wire 34-2 and stimulating electrode ring 31 or connection electrode ring 32 Quantity is equal, to guarantee that each stimulating electrode ring 31 passes through an independent conductive channel and corresponding connection electrode ring 32 It is connected.The generally circular section of seal wire for making electric lead 34, coiling is spiral, seal wire be usually platinumiridio or MP35N, for every seal wire by coating mutually insulated, coating is usually PTFE, ETFE or PFA etc..Spiral helicine conducting wire can guarantee Electrode has good mechanical flexibility, because electrode needs to be subjected to during installation or use the power of various complexity.Such as figure Shown in 1b, according to the difference of electrode stress, electrode can be divided into four sections: first segment is intracranial segment 301, is inserted in brain tissue In；Second segment is to wear cranium section 302, is connected with skull cap, and here, electrode, which is bent, to be had a certain degree and consolidated by skull cap 4 It is scheduled on skull, to guarantee that the stimulating electrode ring of electrode distal end is not displaced, because the displacement of stimulating electrode ring 31 will likely Stimulation is caused to be failed；Third section is changeover portion 303, longer, and electrode disk is intradermal outside skull at being placed on after a circle or a few circles；The Four sections are linkage sections 304, are inserted in electrode extended line, play the role of connecting circuit.

But the electrode integral rigidity for being currently used for DBS is uniform, and smaller relative to actual loading demand rigidity, is easy Axial change is easy to produce when causing dislocation of electrode and lead to failure in treatment, nor be convenient for the plug of electrode proximal end, and plugging Shape, cause connection electrode interannular away from variation, be more likely to cause electrode connection short circuit, influence to treat.

Utility model content

The purpose of this utility model is to provide a kind of electric lead and Implanted bioelectrodes, to solve to be currently used for biology Integral rigidity existing for the electric lead of electrode is uniformly constant and relative to the rigid lesser problem of actual loading demand.

In order to solve the above technical problems, the utility model provides a kind of electric lead comprising spiral conductive body, institute Stating conductive body at least has sequentially connected distal section, centre portion and proximal section, wherein the centre portion it is rigid Degree is less than the rigidity of the distal section and the proximal section.

Preferably, the coil cross section width of the centre portion is less than the spiral shell of the distal section and the proximal section Cross-sectional width is revolved, and/or, the screw pitch of the centre portion is less than the screw pitch of the distal section and the proximal section.

Preferably, the conductive body is formed by metal tube helical cut.

Preferably, the centre portion includes sequentially connected multiple sub-segments, and one connect with the distal section The rigidity of a sub-segments is less than the rigidity of other sub-segments.

Preferably, the sub-segments are two.

Preferably, the rigidity of the proximal section is greater than the rigidity of the distal section.

Preferably, the outer surface of the conductive body is covered with insulating layer.

Preferably, the conductive body is a spiral round tube.

Preferably, the coil cross section of the conductive body is rectangle, parallelogram or trapezoidal.

In order to solve the above technical problems, the utility model also provides a kind of Implanted bioelectrode comprising the electricity Conducting wire.

Preferably, the Implanted bioelectrode further includes electrode catheter, and the electric lead is threaded through the electrode catheter In, and the both ends of the electric lead are electrically connected with the both ends of the electrode catheter respectively.

In electric lead provided by the utility model and Implanted bioelectrode, due to electric lead have it is different rigid Degree, the especially rigidity of centre portion are less than the rigidity of distal section and proximal section, so that using the implanted of the electric lead The electrodes such as bioelectrode such as DBS, spinal nerves stimulation, vagal stimulation, intermediate position is easy curved in actual use Folding and deformation, and distal site has biggish rigidity and is less likely to occur to shift, in addition proximal end position also has biggish rigid Property and be not easy to deform when with the hot-line insertion and extractions such as electrode extended line, in this way, making Implanted bioelectrode that can meet different sections Rigid demand, so that electrode be made to be less likely to occur to shift in vivo, and be also convenient for the plug of electrode, be unlikely to cause electrode The short circuit of connection.Therefore, the success rate of electronic stimulation can be improved in the electric lead of the utility model, it is ensured that circuit connection can By property.

In a preferred embodiment, the coil cross section width of the centre portion is less than the distal section and described The coil cross section width of proximal section, so that conducting wire can get biggish coil cross section product in proximal section and distal section, this In the case of, since the resistance of electric lead is inversely proportional to coil cross section product and directlys proportional to length, in the certain feelings of conductance line length Under condition, the total length of conductor is reduced, also effectively reduces the impedance of entire conducting wire, advantageously reduces the energy of electronic stimulation Consumption, improves the service life of electrode.

In a preferred embodiment, the conductive body is formed by metal tube helical cut, it is only necessary to be cut by control The parameter of seam can obtain the helical structure of varying pitch and/or variable cross-section, and not only preparation process is simple, but also it is each to be also easy to control The rigidity of section, while being also convenient for the rigidity of flexible configuration conducting wire.

Detailed description of the invention

Fig. 1 a is the schematic diagram that the existing electric stimulation for DBS is installed in vivo；

Fig. 1 b is the structural schematic diagram of the existing bioelectrode for DBS；

Fig. 2 a is the schematic diagram of the electric lead insertion electrode catheter of the existing bioelectrode for DBS；

Fig. 2 b is the schematic diagram of the electric lead of the existing bioelectrode for DBS；

Fig. 3 is the structural schematic diagram of the electric lead of the bioelectrode provided by the embodiment of the utility model for DBS；

Fig. 4 is the process schematic provided by the embodiment of the utility model for preparing electric lead.

In figure,

Impulse generator 1；Electrode extended line 2；Electrode 3；Intracranial segment 301；Wear cranium section 302；Changeover portion 303；Linkage section 304；Electrode catheter 33；Stimulating electrode ring 31；Connection electrode ring 32；Electric lead 34；Coating 34-1；Seal wire 34-2；Skull cap 4；

Electric lead 340；Encephalic section 341；Wear cranium section 342；Transition zone 343；Jointing 344；Insulating layer 3401； Coil cross section 3402,3402 '；Thin-wall tube 30.

Specific embodiment

To keep the purpose of this utility model, advantages and features clearer, below in conjunction with specific drawings and examples pair The utility model proposes medical tubing and preparation method thereof be described in further detail.It should be noted that attached drawing be all made of it is non- Often simplified form and use non-accurate ratio, only to it is convenient, lucidly aid in illustrating the utility model embodiment Purpose.

As used in the specification and the appended claims, term "or" is usually to include containing for "and/or" Justice and carry out using, in addition in addition non-content explicitly points out.In addition, in the following description, for ease of description, using " distal end " and " proximal end "；" proximal end " is close to the side of medical instrument operator；" distal end " is far from medical instrument operator One end.In addition, in the following description, giving a large amount of concrete details and more thoroughly being managed in order to provide to the utility model Solution.It is, however, obvious to a person skilled in the art that the utility model may not need it is one or more of these thin It saves and is carried out.In other examples, in order to avoid obscuring with the utility model, for more well known in the art Technical characteristic is not described.

Here, first to proposed in background technique the problem of and the core concept of the utility model do specific description. As described in the background art, inventors have found that the existing electrode for DBS that there are integral rigidities is uniform, and rigidity is lesser Problem.Inventor further study show that, the electric lead 34 of traditional electrode is formed by uniform seal wire coiling, the section of seal wire Product, the screw pitch d of cross sectional shape and winding are constant always, thus electric lead 34 along its length on mechanical characteristic be also constant , i.e., rigid uniform is constant, this is not obviously consistent with the actual loading demand of electrode.

Specifically, for the intracranial segment 301 of electrode, needing to remain at stimulating electrode ring 31 referring to Fig. 1 b and Fig. 2 a It in optimal stimulated zone, and is not displaced during the motion, therefore this section needs electrode to have biggish rigidity, keeps away Electrode is deformed by external force and is shifted after exempting from implantation.And cranium section 302 is worn for electrode, it needs to bend electrode into biggish angle Degree, such as 90 degree, and need to avoid the distal end stress of electrode to be provoked when bending, so as to cause dislocation of electrode, therefore This section needs electrode to have the smallest rigidity.In addition, the changeover portion 303 of electrode is the length of electrode redundancy, is needed It is coiled in skull outer surface, this section there should be relatively small rigidity, convenient for coiling, while also be capable of the proximal end of buffer electrode Biggish stress is generated after being pullled, which is applied to the fracture that may result in electrode on electrode.Finally, for electrode Linkage section 304 needs to insert electrodes into electrode extended line, it is therefore desirable to biggish rigidity, to resist contact engaging and separating force.Therefore, DBS, which is applied, has different requirements to each section of electrode of rigidity, and the electrode cable reported at present is not segmented, in other words Each section of rigidity is consistent.

In addition, inventor is also the study found that the rigidity of traditional electrode is usually smaller, this is because traditional electrode entirety is rigid Caused by degree is uniform, such as in DBS electrode, the electrode due to wearing cranium section 302 needs to carry out the bending of wide-angle, in order to protect Be not displaced after the distal end stress of electrode when card bending, rigid design need to be obtained it is very small, and due to rigidity be it is uniform, because This causes the rigidity of electrode entirety lower.

Therefore, the rigidity of traditional electrode entirety is not only single constant, but also smaller relative to actual loading demand rigidity, such as This one, be easy to happen following problem:

The first, since the rigidity of intracranial segment 301 is smaller, the electrode of intracranial segment 301 is caused to be easy to be influenced and deformed by external force, So as to cause dislocation of electrode, the problem of failure in treatment occurs；

The second, it since electrode integral rigidity is smaller, therefore needs to be inserted into one in the inside of electrode in the operation of electrode implantation The rigid biggish strengthening core of root, to improve the rigidity of electrode entirety, the axial force being subject to for resisting electrode when being inserted into intracerebral, Nonetheless, since the axial rigidity of electrode itself is smaller, certain overstrain can be also generated in implantation process, withdraws from reinforcement Electrode can still generate certain displacement after core；

Third, due to linkage section 304 rigidity it is smaller, the proximal end of electrode be typically only capable to bear be less than 1N contact engaging and separating force, this Sample is not easy to the plug of electrode proximal end, and electrode is easy to produce axial deformation when plug, so as to cause connection electrode interannular away from change Change, it is more serious, also result in electrode connection open circuit.

And then it is based on the studies above, the utility model proposes a kind of electric leads, are suitable for DBS electrode but not limited to this, The electric lead includes spiral conductive body, and the conductive body at least has sequentially connected distal section, centre portion And proximal section, wherein the rigidity of the centre portion is less than the rigidity of the distal section and the proximal section.It is preferred that , the rigidity of the distal section is less than the rigidity of the proximal section.Therefore, the rigidity of the electric lead of the utility model is whole Unevenly, and there is minimum rigidity and maximum rigidity, is easy to use the Implanted bioelectrode of the electric lead to meet it and is using The mechanics demand of different sections in the process, to prevent electrode from the problems such as displacement, short circuit occur, it is ensured that electrode normal use.

Next by taking the electric lead of DBS electrode as an example, as shown in figure 3, a kind of electric lead 340, including one spiral helicine is led Electric ontology, the conductive body include that four sections are sequentially connected encephalic section 341 respectively, wear cranium section from the distant to the near 342, transition zone 343 and jointing 344.Herein, it should be understood that the centre portion of the utility model includes two sub-districts Section, is to wear cranium section 342 and transition zone 343, and encephalic section 341 then constitutes the distal section of the utility model respectively, even Connect the proximal section that section 344 constitutes the utility model.Therefore, thorn of the encephalic section 341 to connect DBS electrode catheter distal end Swash electrode retaining collar, then to connect the connection electrode ring of DBS electrode catheter proximal end, connection type is not limited to weld jointing 344 Or bonding.

In some embodiments, the conductive body rigidity of the electric lead 340 is configured as: wearing the 342 < transition of cranium section 343 < encephalic section of section, 341 < jointing 344, therefore, the rigidity for wearing cranium section 342 are minimum, and jointing 344 Rigidity is maximum.But in further embodiments, the utility model is opposite with the rigidity of jointing 344 to encephalic section 341 Size is not construed as limiting, and the rigidity of the two both can be the same or different, when rigidity is not identical, the rigidity of encephalic section 341 Less than the rigidity that the rigidity of jointing 344 or the rigidity of encephalic section 341 are also greater than jointing 344；Also, this For utility model to cranium section 342 is worn and the rigidity relative size of transition zone 343 is also not especially limited, the rigidity of the two is practical Can also be identical, it is configured with specific reference to the stress needs of electrode.Therefore, the utility model only needs to guarantee to wear cranium section 342 Encephalic section 341 and jointing 344 are respectively less than with the rigidity of transition zone 343.

Thus according to the difference of the stress condition of DBS electrode, the rigidity of each section of the electric lead 340 is configured as not Identical, can ensure that DBS electrode so in use can preferably cope with the stress of each section, prevent electrode from moving Position avoids electrode proximal end short-circuit, can also facilitate the plug of electrode proximal end.

More specifically, in DBS electrode, 341 system of encephalic section corresponds to the intracranial segment 301 of electrode, the partial electrode It needs to be inserted in brain tissue, it is ensured that stimulating electrode ring is in optimal stimulated zone always, and when electrode is being implanted into When afterwards by external force, stimulating electrode ring is less likely to occur to shift under the larger rigid support of encephalic section 341, so as to compared with Good resistance external force.Cranium section 302 is worn corresponding to electrode in addition, wearing cranium section 342, which has lesser rigidity, can The pattern after electrode is finally implanted into is adapted to largely to be bent, and not easily leads to the remote of electrode when bending electrode It moves at end.In addition, transition zone 343 corresponds to the changeover portion 303 of electrode, there is preferable flexibility, can be held in electrode When by external force, intracranial electrode is pullled to reduce by the deformation of itself, so that circuit caused by avoiding thus disconnects The problems such as.And jointing 344 corresponds to the linkage section 304 of electrode, has biggish rigidity, is inserted by the proximal end of electrode When in electrode extended line, contact engaging and separating force can be preferably resisted, is unlikely to electrode when plug and generates axial deformation, so as to avoid Cause connection electrode interannular away from variation, prevent electrode connection short circuit.Therefore, the electric lead 340 of the utility model embodiment Rigidity can meet these force requests of electrode, it is ensured that its reliability and validity for using.

Further, the conductive body of the electric lead 340 is preferably formed by a thin-wall metal pipe helical cut, the metal Thin-wall tube is preferably a round tube, and outer diameter is chosen as 0.8mm, and internal diameter can be 0.5mm.It here, can on same root thin-wall metal pipe It is easy to make to be cut into more independent spiral electric leads.In practice, the quantity of electric lead and stimulating electrode ring or company The quantity of receiving electrode ring is consistent, and mutually insulated between each electric lead.

Further, the coil cross section of the conductive body is rectangle, parallelogram or trapezoidal, certain in sectional area In the case of, fatigue strength is higher than the seal wire of existing circular cross-section.Here, coil cross section refers to through helical cut metal tube It is formed by the axial cross section of helical structure.

Further, the material of thin-wall metal pipe is selected from the material of bio-compatible, and material can be platinumiridio, stainless steel And one of materials such as MP35N or multiple combinations.In addition, being formed with insulating layer 3401 on the outer surface of conductive body, absolutely The material of edge layer 3401 is selected from one of materials such as PTFE, ETFE and PFA or multiple combinations, and the thickness of insulating layer 3401 can For 0.025mm.Electrical isolation is realized by insulating layer 3401 between each electric lead.

Further, it in helical cut thin-wall metal pipe, is cut with specified path, so that each section is rigid Degree is not identical, and specified path includes that the coil cross section width of each section is not identical, alternatively, the screw pitch of each section is not identical, again Alternatively, the coil cross section width and screw pitch of each section are all different.It is preferred that being cut by laser to obtain helical structure, not only Machining accuracy is high, and compared with the mode of simple spiral winding, and cutting can preferably control the rigidity of each section.It is specific next It says, obtains helical structure by the way of helical cut thin-wall metal pipe, convenient for passing through the section of helical structure in pilot Size and screw pitch carry out the mechanics rigidity of pilot, such as using big sectional area and big screw pitch to obtain biggish mechanics rigid Property, it is not only convenient for the continuous production of tubing, the rigidity for being also convenient for tubing can obtain good control, and can get and appoint The conducting wire for the parameter and performance of anticipating, convenient for the rigidity of flexible configuration conducting wire.Also, due to the sectional area of the resistance of conducting wire and conductor at Inverse ratio and directly proportional to length, it is therefore, long in the section when the helical structure of partial sector has biggish coil cross section product The total length (i.e. conductor be stretched to linear state length) of conductor (i.e. helical structure) can be reduced in the case that degree is certain, in this way The impedance that can effectively reduce entire conducting wire is beneficial to reduce the energy consumption of electronic stimulation.Here, coil cross section width refers to The sectional dimension of helical structure in metal tube axial direction.

And then Fig. 3 discloses one preferred embodiment of the utility model, wherein upper left corner partial enlargement is encephalic section 341 Locate four continuous coil cross sections 3402, the width of each coil cross section 3402 is w, and screw pitch is d, at the same time Fig. 3 upper right Angle partial enlargement is that four continuous coil cross sections 3402 ', the width of each coil cross section 3402 ' are at transition zone 343 W, screw pitch d.

As shown in figure 3, in a preferred embodiment, wearing the coil cross section width w < transition zone 343 of cranium section 342 The coil cross section width w of the coil cross section width w < jointing 344 of coil cross section width w < encephalic section 341, it is same with this When, wear the screw pitch d < jointing 344 of the screw pitch d < encephalic section 341 of the screw pitch d < transition zone 343 of cranium section 342 Screw pitch d.But not limited to this, in other embodiments of the utility model, it can also only wear the coil cross section width of cranium section 342 The spiral of the coil cross section width w < jointing 344 of the coil cross section width w < encephalic section 341 of w < transition zone 343 Cross-sectional width w, and the screw pitch d of these sections is identical.Alternatively, can also only wear cranium in other embodiments of the utility model The screw pitch d of the screw pitch d < jointing 344 of the screw pitch d < encephalic section 341 of the screw pitch d < transition zone 343 of section 342, and The coil cross section width w of these sections is identical.It should be understood that the rigidity of section is positively correlated with coil cross section width w and screw pitch d, Coil cross section width w and screw pitch d are bigger, and the rigidity of section is also bigger, therefore biggish coil cross section width and screw pitch can get Biggish mechanics rigidity.

Further, in an optional scheme, coil cross section width and the screw pitch setting of each section are as follows:

Encephalic section 341: coil cross section width and screw pitch are larger, and the range of coil cross section width w is 0.5~1.0mm, and The range of screw pitch d is 0.51~1.01mm；

Wear cranium section 342: coil cross section width and screw pitch are smaller, and the range of coil cross section width w is 0.15~0.19mm, The range of screw pitch d is 0.16~0.2mm；

Transition zone 343: coil cross section width and the setting of screw pitch median size, the range of coil cross section width w is 0.2~ The range of 0.3mm, screw pitch d are 0.21~0.31mm；

Jointing 344: coil cross section width and screw pitch are larger, and the range of coil cross section width w is 0.6~1.5mm, spiral shell Range away from d is 0.61~1.51mm, can get the mechanics rigidity of relative maximum.

Fig. 4 (a)-Fig. 4 (c) is subsequently combined, the preparation process of electric lead 340 is further described.Such as Fig. 4 (a)- (b) shown in, the preparation process of electric lead 340 is specifically included:

First as shown in Fig. 4 (a), a platinumiridio thin-wall tube 30 is provided；

It is secondly by specified path, platinumiridio light-wall conduit laser cutting is helically shaped as shown in Fig. 4 (b), Obtain a spiral helicine original conductive body；

Pickling, polishing and insulation processing are successively carried out to original conductive body later, finally obtain table shown in Fig. 4 (c) Face is provided with the conductive body of insulating layer.Wherein, the residue of laser melting formation can be removed by pickling；And it polishes and is preferably Electrochemical polish can remove the burr of metal surface, keep metal surface smooth, improve the fatigue life of conducting wire；After polishing Original conductive body carries out insulation processing, such as spraying or dip-coating insulation material, and to each electric lead that insulate, but insulation processing is not It is limited to spraying or dip-coating, can also be realized by original conductive body and the insulating materials coextrusion that will be polished, so that insulation material Material is covered on the surface of conductive body.

In turn it should be noted that the utility model preferred embodiment is as described above, but be not limited to the above embodiments disclosure , such as the section that electric lead is included is not limited to four, is also possible to three or four or more, mainly according to electric lead institute The stress condition of the electrode of application divides.

Finally, the utility model embodiment also provides a kind of Implanted bioelectrode, it is not limited to DBS electrode, is also possible to Other electrodes, such as spinal nerves stimulation, the electrode of vagal stimulation.The Implanted bioelectrode of the utility model includes Electric lead provided by the embodiment of the utility model.

Further, the Implanted bioelectrode of the utility model embodiment further includes electrode catheter, in the electrode catheter It is equipped with electric lead, the both ends of electric lead are electrically connected with the both ends of electrode catheter respectively, as the both ends of electrode catheter are respectively set There is electrode retaining collar, connect the both ends of electric lead with electrode retaining collar respectively.

Foregoing description is only the description to the utility model preferred embodiment, not to any limit of the scope of the utility model Fixed, any change, the modification that the those of ordinary skill in the utility model field does according to the disclosure above content belong to right and want Seek the protection scope of book.

Claims (11)

1. a kind of electric lead, including spiral conductive body, which is characterized in that the conductive body, which at least has, to be sequentially connected Distal section, centre portion and proximal section, wherein the rigidity of the centre portion is less than the distal section and described The rigidity of proximal section.

2. electric lead according to claim 1, which is characterized in that the coil cross section width of the centre portion is less than described The coil cross section width of distal section and the proximal section, and/or, the screw pitch of the centre portion is less than the distal area The screw pitch of section and the proximal section.

3. electric lead according to claim 1 or 2, which is characterized in that the conductive body by metal tube helical cut and At.

4. electric lead according to claim 1 or 2, which is characterized in that the centre portion includes sequentially connected multiple Sub-segments, and the rigidity for the sub-segments connecting with the distal section is less than the rigidity of other sub-segments.

5. electric lead according to claim 4, which is characterized in that the sub-segments are two.

6. electric lead according to claim 1 or 2, which is characterized in that the rigidity of the proximal section is greater than the distal end The rigidity of section.

7. electric lead according to claim 1 or 2, which is characterized in that the outer surface of the conductive body is covered with insulation Layer.

8. electric lead according to claim 1 or 2, which is characterized in that the conductive body is a spiral round tube.

9. electric lead according to claim 1 or 2, which is characterized in that the coil cross section of the conductive body is rectangle, puts down Row quadrangle is trapezoidal.

10. a kind of Implanted bioelectrode, which is characterized in that including conductance according to any one of claim 1 to 9 Line.

11. Implanted bioelectrode according to claim 10, which is characterized in that it further include electrode catheter, the conductance Line is threaded through in the electrode catheter, and the both ends of the electric lead are electrically connected with the both ends of the electrode catheter respectively.