CA1173914A - Electrode assembly for temporary pacing and heart measurement - Google Patents
Electrode assembly for temporary pacing and heart measurementInfo
- Publication number
- CA1173914A CA1173914A CA000379231A CA379231A CA1173914A CA 1173914 A CA1173914 A CA 1173914A CA 000379231 A CA000379231 A CA 000379231A CA 379231 A CA379231 A CA 379231A CA 1173914 A CA1173914 A CA 1173914A
- Authority
- CA
- Canada
- Prior art keywords
- wires
- electrode assembly
- catheter
- wire
- portions
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
- A61N1/056—Transvascular endocardial electrode systems
Abstract
ELECTRODE ASSEMBLY FOR TEMPORARY PACING AND HEART MEASUREMENTS
ABSTRACT
An electrode assembly for use with a catheter, is made of a plurality of insulated wires. The wires are bound together in a bundle by, for example, fine insulated wire for almost their entire lengths. At one end of the bundle are free wire ends of different lengths on which are electrically conductive ferrules. The ferrules are spaced apart axially when aligned with the bundle inside the catheter. The wires are made of springy material so that the free wire ends separate widely outside the catheter. Other cylindrical ferrules are mounted in axially spaced position on bared portions of the other end of the bundle, and encircle all the wires, but each ferrule is in direct electrical contact with only one of the wires.
ABSTRACT
An electrode assembly for use with a catheter, is made of a plurality of insulated wires. The wires are bound together in a bundle by, for example, fine insulated wire for almost their entire lengths. At one end of the bundle are free wire ends of different lengths on which are electrically conductive ferrules. The ferrules are spaced apart axially when aligned with the bundle inside the catheter. The wires are made of springy material so that the free wire ends separate widely outside the catheter. Other cylindrical ferrules are mounted in axially spaced position on bared portions of the other end of the bundle, and encircle all the wires, but each ferrule is in direct electrical contact with only one of the wires.
Description
~.~ 739~
This invention concerns an electrode assembly adapted for temporary heart pacing and making measurements of blood vessels.
A generally known typical catheter type flow sensor adapted for temporary pacing applications is comprised of a bifilar probe terminating in a wire loop in a lenticular shape. The loop is collapsed when inside the catheter and when it leaves the catheter and enters into a chamber of the heart or in~o a blood vessel it takes a lenticular shape. When the loop is withdrawn into the catheter, there is always the hazard that a leaf of a heart valve or other protrusion will be caught in the loop.
The present invention is directed at overcoming the above and other difficulties and disadvantages of the prior loop type of catheter probes, and for providing an improved electrode assembly which can employ a catheter of smaller external diame~er than that required by loop types of probes.
According to the invention there is provided an electrode assembly which can function as a temporary heart pacer as well as an instrument for measuring the flow in blood vessels. The assembly may employ insulated bifilar, trifilar, quadrafilar or the like wire terminating in free ends of different lengths. On the end of each wire is a contact means - typically a ferrule.
The ferrules are staggered or spaced in position lengthwise of and inside a catheter during insertion through the catheter, which may be positioned into a heart chamber via a blood vessel. The internal diameter of the catheter required to accomodate the ferrules and adjacent wires of the bifilar, trifilar or quadrafilar wire is less than required to accomodate a wire loop of a corresponding loop type probe.
.~
I ~ ~7~9~ i . i It is therefore, a principal object of the present ~nvention to provide an electrode assembly for use in making ~eart measurem~3nts and or temporary pacing, wherein the wires ~erminate in free ends, rather than in the prior known closed lire loop.
Another object of the present invention ig to provide ~n electrode assembly of the type described wherein the free ~nds of the wires ha~-~ different lengths.
Ii A further object of the present invention is to provide 'an electrode assembly as described, wherein ferrules are secured ¦~o the free ends of the wires, and wherein further ferrules al-e ~ounted on the other ends of the wires.
These and other objects and many of the attendant ,'advantages of this invention will be readily appreciated as the l'same becomes better understood by reference to the follow.tng de-l~ailed descxiption when con~idered in conneCtion with the accompany _ ,ing drawin~s in which:
Fig. 1 is a side elevational view of an electrode ~assembly embodying the invention, parts heing shown in section ~nd other parts being broken away to show internal construction ,~ Fig. 2 is an enlarged longitudinal sectional view of an . ~
,end portion of the electrode assembly ~` Figs~ 3, 5, and 6 are plan views showiny the wires at sùccessive stages of assembl~, Fig~ 4 is an enlarged crosS seCtion taken along line l,1 4 of Fig. 3;
¦I FigO 7 is an enlarged axial qectional view of one end ~f the electrode a7777emb1y7 Il .
.p73g~ 1 Fig. 8 is an enlarged axial view of the other end of the electrode as~qembly taken along line 8-8 of Fig. 1.
Fig. 9 is another embodiment of the electrode assembly l 10' similar to Fig. 1, and Fig. 10 is a further embodi~ent of the electrode asqembl~
10"~ ~
Referring now to the drawings wherei~ ref~rence characters designate like or corre~ponding p~rt~,throughout, there is illu~trated in Fig. 13 an electrode a39~mbly, g~nerally desi~nated as reference numeral 10 which includes a pair of insulated wires 12a, 12b bound together in a bifilar array 12 by an insulated fine wire winding 14~ The wihding 14 terminates shor' of the free ends 16a, 16b of the bifilar array 12u The end 16a is longer than the end 16b. A ferrule 18 i9 mou~ted on each of the wire ends 16a, 16b. As best shown in Fig. 7, the ferrule 18 has a cylindrical metal body into which the end 16a `:
! or 16b of the respective wire 12a or 12b is inserted. A coat of insulation 20 on the wire 12 is scraped away at the wire end and ,a conductive cement 22 such as silver filled epoxy is applied to l¦the bare wire end on which is axially mounted cylindrical ferrule ~l1B. At botih ends of the ferrule 18 are applied a re~pective j!bead 23, 24 of an insulation material such as epoxyO
, At the other end of the bifilar array 12 are two further Ijcylindrical ferrules 24 and 26; see Fig~. 1 and 80 These ferrule~
l'may be connected to an external electrical circuit. Ferrule 24 is mounted on the other end of bifilar wires 12a, 12b. The linsulation 20 is scraped away from the end of the wire 12a, and ¦the bared wire is coated with a conductive cement 30 to secure the ferrule 24 on the wire end. The ferrule 24 encircles both wires 12a, 12b, but i~ insulated frQm the wire 12b. Bedds 32, 34 !
~1 !
i ^1t ~ C 11 11739'14 ~of a~ inR~1atlo~ ~Ient ~r~ plac~d at oppooite end~ of the ~erru1 124- Axially ~a~d ~nom th2 f~rrul~ 24 i8 th~ cyl~ndrical ferrul~
. 26. ~nsul~tiQ~ 20 ia ~crap~d away ~rRm a pvrtion o~ wir~ 12b and ~he ~rrule 26 is mount~d on the bifilar w~r2s 12a and 12b and .
1 secur~d in place on th~ ~arad por~ion of wire 12b by a oonductive cement 36. A respec~ive bead 38, 39 of in~ulation cement i9 appli~d to an oppo~i~e end of the ferrule ~6~ ~he binding wire 14l is also removed from the portions of th~ bifilar wires 12a and ,112b carrying the ferru1es 24 a~d 260 o ?~ ~ig~ 2 ~hows the f~rrule~ 18 di~po~ed in lon~itudinal `~paced po~ition inside a flexible cathcter 40. In operation, the ~
,flexible catheter 40 may be inserted through a vein 42 tFig. 1)¦
~`through the right atrium 41 ~o the tricuspid valve 454 The 'electrode assembly 10 will pas~ axially through the catheter 40 1S l! and out of it~ free end through the tricu~pid valve 45 into the , right ventricle 44. There the ~ree end of the bifilar wire probe ¦
will separate and the ferrules 18 wnll contact the oppo~ite spaced, walls 46 of the riqht ventricle 44. ~he catheter 40 m~y then.be xemoved from the heartO
` Figs. 3 and 4 show one step in the method of fabricating ~' the electrode aQsemblyO Fine ~3pringy wire 12 ' made of beryllium ,~
copper or b~ryllium nickel or othe r suitable alloy ranging from 0aO04~ to 0.125" i8 coated with an insulating layer 20 s-;ch as polyurethane varniahO The wire 12' i8 b~nt to form a loop 48.
I' Then the wire 8ection8 12a and 12b are placed side~ side a~ I
shown in ~ig. 5 and wound with the fine binding wire 14 ~uch a~ ¦
1 0~002" in~ulated ~opper wireO The bir~ling wir~ 14 may be bonded ,: to th~ wire 8action8 12a and 12b wlth ~ev~ral ~d ooat~ of an ¦insulated materi~l (not E~own), xuch a~ polyur~l~na~ Yarni~h whlch I wa8 u8~!td for the inau~ation 20. ~he loop 4~ the~ ~ut on line ... .
3L739~
~-A so that the wire end 16a will be longer than the wire end 16b ¦as shown in Fig~ 60 Then the insulation 20 is scraped from the wire ends 16a and 16b and the ferrules 18 are mounted on the wire ends 16a, 16b as shown in FigsO 1 and 7. The lengths of the wire 5 ends 16a and 16b are critical~ One wire end ~6a ~hould be longer han the other end 16b by at least the length of one ferrule 18, so that the ferxules occupy minimum space inai ~ the catheter 40.
rhe axial spacing of the contact ferrules 18 ~ t the ferrules 8 to pass through a smaller catheter 40 than ~ould be needed if i~Dth of the ferrules 18 were in a ~ide-by-side position against ach other when passing through the catheter 40.
The arrangement described provides better contact ¦ibetween the walls of the chamber 44 than prior loop type probes.
liThe free ends of the wires can open wider than maximum diameter Ipf a prior closed loop type of probe. The ferru;es 18 make a ll!better contact wlth tlle chamber walls than the narro~Y sides of a ,,closed wire loep because the ferrules have a larger surface area than the electrodes of the prior loop type catheter probe.
I,Furthermore, the free wire ends will not catch on protrusions in ~ithe chamber walls as presently possible with closed wire loopsO
¦IIn addition, the free wire ends bearing ferrules 18 will pass through a catheter of narrower diameter than one sized to accomo-date a probe with closed wire loop~ The use of a catheter of ~narrower diameter facilitates passage of the catheter through Ivessels of the body such as chambers of the heart 5 or to other ¦organs .
FigO 9 illustrates another embodiment of the electrode . assembly 10' wherein the binding wire 14 has been formed into a terminal 16cin order to have bipolar pacing. That i~ to say, when ~¦the electrode assembly 10 of Fig. 1 is pulsed by ;a ~.C. Volta~e ¦each of the terminals 16a and 16b have a different polarity. On ~73~
the other hand, in the electrode a~;3embly 10~ oî Fi~. 9, the ! terminal 16a and 16b may have~ on~ polarity and the terminal 16c I which i8 located in the bh~d v~a~sel ~u~t outaide vf the heart ¦ ha~ the other polarity or te~rminal 16a 3nd 16c may hsve the ~ame polarity and terminal 16b the othe~r Eolarity c~r t4~rminal 16b and 16c may have ~he aa~ polarity and t~rmi~al 16a.1;~ other polarity O
It ~aould be not~d that for bipolar p~cing, ~nal 16c ~t be located outside of the heart.
In some in~tances, it may ~ de~lrabl~ to have a oequ~-tial atrial and ~rentricular pacing. Por thi~ rpo~e, an alectrode .~ as~e~ly lOn as illustrated in Fig. 10 ~ay be utilized. l'he 1 electrode a~sembly lG" may be made from quadra~ r wire3 and i8 !` comprised of terminals 16a, 16b, 16d, and 16eO The terminals 16 I! and 16e are identical to the terminals 16a and 16b respectively.
I'The other end of the electrode a~sembly lOY ha~ four fexrule3 each . ~ubstantially the same as th~ ferrules 24 or 26. In operation fo i! sequential atrial and ventricular pacing, the catheter 40 is inserted through the ri~ht atrium to the tricuspid valve a~ beforel.
'The electrode a~sembly 10U i~ pass2d th~ough the eatheter 40 ~o ¦that the electrode 16a and 16b extend into and ~ont~ct the walls of th~ right ventricl~. The catheter 40 i~ t~en r~ov~d and a~
¦~it l~aves the r~ht atrium, th~ terminalA 16~ and 16e wh~c~
~entioned b~or~ are identlcal r~spect~v~ly to the ten~inal~ 16 and 16b~ ~xp~nd and o~nta~t th~ atrium wallo. ~h~ pul~ed D~Co voltaqe may ~e applied to the ~errul~ at ~h~ end o~ th~ electrod~
a~s~nbly 10" to pul~e t~ie rig~t atrium ter~nal~ 16d and 16e and then the ris~ht ventri~:ular t~rminals 16a and 16b in ~equence to i~itate the normal heart function.
¦ Although not illustrat~d, the .electro~ ;~a~ ly may be u8ed to determine the contractility o~ th~ l~ft ventricle after a ¢ 1~73914 I¦ myocardial in~arction, by an ele~trod~ a~s~ly (using 0004"
Il diameter wQre~) place~ in a cathoter which ha~ b~en introduced t~r _ lough a ~itral valve in th~ l~ft ventricl~O A radio-opaque dye ¦~ay th~n be pu~ped thro~gh th~ catheter ~nto th~ left ventricl~
and the el~ctrode a~e~bly may be pul~d whan the heart i~
depolariz~d so that the contraction i5 great0r t~an that which ~1 e.Yi~tR during a normal heart cycleO The contrac~i~n of the ¦, heart may be filmed and will display a measure of the damage !l of the heart by the i~fraction. It may al~o be under~tood that ¦jthe aforementioned electrode a~sembly may be u~ed a~ an EXG
!I Monitor in the v~ntricle and can thQn be 8W~ ~ched when fibrilla-,~tion OCCUX8 as a defribrillator~
In view of th~ foregoing, it i8 clear that by having 1~ wires of different len~ths, a trifilar, quadkafilar or any bundle 1¦ of wires will pass through a ~ubstantially ~maller diameter , catheter then that required ~or the prior ~st loop type catheter probe. It would also be noted, that the el~ctrode a~embly here~
' inbefore de~cribed, may be u~¢d ~or ~it~ure~nt of blood flow ln , a ve~sel in ~hich the a~s~ly i8 placed~ in much the same 1! manner as that of a loop typ~ catheter prob~.
It should be understood that the foregoing relate~ to only a preferred embodi~en~ of the inventisn~ a~d that it i~3 , intended to cover all chançles and modi~ication~ of the example ii of the invention herein cho3en for the purpo e~ of th~ di~closure~
i which do not constitute~ departures îrom the spirit and scope s:~f ~ the 1nvent1on.
i ` ~ ' , ~, ~` -8-`~ ~
.```" '51t
This invention concerns an electrode assembly adapted for temporary heart pacing and making measurements of blood vessels.
A generally known typical catheter type flow sensor adapted for temporary pacing applications is comprised of a bifilar probe terminating in a wire loop in a lenticular shape. The loop is collapsed when inside the catheter and when it leaves the catheter and enters into a chamber of the heart or in~o a blood vessel it takes a lenticular shape. When the loop is withdrawn into the catheter, there is always the hazard that a leaf of a heart valve or other protrusion will be caught in the loop.
The present invention is directed at overcoming the above and other difficulties and disadvantages of the prior loop type of catheter probes, and for providing an improved electrode assembly which can employ a catheter of smaller external diame~er than that required by loop types of probes.
According to the invention there is provided an electrode assembly which can function as a temporary heart pacer as well as an instrument for measuring the flow in blood vessels. The assembly may employ insulated bifilar, trifilar, quadrafilar or the like wire terminating in free ends of different lengths. On the end of each wire is a contact means - typically a ferrule.
The ferrules are staggered or spaced in position lengthwise of and inside a catheter during insertion through the catheter, which may be positioned into a heart chamber via a blood vessel. The internal diameter of the catheter required to accomodate the ferrules and adjacent wires of the bifilar, trifilar or quadrafilar wire is less than required to accomodate a wire loop of a corresponding loop type probe.
.~
I ~ ~7~9~ i . i It is therefore, a principal object of the present ~nvention to provide an electrode assembly for use in making ~eart measurem~3nts and or temporary pacing, wherein the wires ~erminate in free ends, rather than in the prior known closed lire loop.
Another object of the present invention ig to provide ~n electrode assembly of the type described wherein the free ~nds of the wires ha~-~ different lengths.
Ii A further object of the present invention is to provide 'an electrode assembly as described, wherein ferrules are secured ¦~o the free ends of the wires, and wherein further ferrules al-e ~ounted on the other ends of the wires.
These and other objects and many of the attendant ,'advantages of this invention will be readily appreciated as the l'same becomes better understood by reference to the follow.tng de-l~ailed descxiption when con~idered in conneCtion with the accompany _ ,ing drawin~s in which:
Fig. 1 is a side elevational view of an electrode ~assembly embodying the invention, parts heing shown in section ~nd other parts being broken away to show internal construction ,~ Fig. 2 is an enlarged longitudinal sectional view of an . ~
,end portion of the electrode assembly ~` Figs~ 3, 5, and 6 are plan views showiny the wires at sùccessive stages of assembl~, Fig~ 4 is an enlarged crosS seCtion taken along line l,1 4 of Fig. 3;
¦I FigO 7 is an enlarged axial qectional view of one end ~f the electrode a7777emb1y7 Il .
.p73g~ 1 Fig. 8 is an enlarged axial view of the other end of the electrode as~qembly taken along line 8-8 of Fig. 1.
Fig. 9 is another embodiment of the electrode assembly l 10' similar to Fig. 1, and Fig. 10 is a further embodi~ent of the electrode asqembl~
10"~ ~
Referring now to the drawings wherei~ ref~rence characters designate like or corre~ponding p~rt~,throughout, there is illu~trated in Fig. 13 an electrode a39~mbly, g~nerally desi~nated as reference numeral 10 which includes a pair of insulated wires 12a, 12b bound together in a bifilar array 12 by an insulated fine wire winding 14~ The wihding 14 terminates shor' of the free ends 16a, 16b of the bifilar array 12u The end 16a is longer than the end 16b. A ferrule 18 i9 mou~ted on each of the wire ends 16a, 16b. As best shown in Fig. 7, the ferrule 18 has a cylindrical metal body into which the end 16a `:
! or 16b of the respective wire 12a or 12b is inserted. A coat of insulation 20 on the wire 12 is scraped away at the wire end and ,a conductive cement 22 such as silver filled epoxy is applied to l¦the bare wire end on which is axially mounted cylindrical ferrule ~l1B. At botih ends of the ferrule 18 are applied a re~pective j!bead 23, 24 of an insulation material such as epoxyO
, At the other end of the bifilar array 12 are two further Ijcylindrical ferrules 24 and 26; see Fig~. 1 and 80 These ferrule~
l'may be connected to an external electrical circuit. Ferrule 24 is mounted on the other end of bifilar wires 12a, 12b. The linsulation 20 is scraped away from the end of the wire 12a, and ¦the bared wire is coated with a conductive cement 30 to secure the ferrule 24 on the wire end. The ferrule 24 encircles both wires 12a, 12b, but i~ insulated frQm the wire 12b. Bedds 32, 34 !
~1 !
i ^1t ~ C 11 11739'14 ~of a~ inR~1atlo~ ~Ient ~r~ plac~d at oppooite end~ of the ~erru1 124- Axially ~a~d ~nom th2 f~rrul~ 24 i8 th~ cyl~ndrical ferrul~
. 26. ~nsul~tiQ~ 20 ia ~crap~d away ~rRm a pvrtion o~ wir~ 12b and ~he ~rrule 26 is mount~d on the bifilar w~r2s 12a and 12b and .
1 secur~d in place on th~ ~arad por~ion of wire 12b by a oonductive cement 36. A respec~ive bead 38, 39 of in~ulation cement i9 appli~d to an oppo~i~e end of the ferrule ~6~ ~he binding wire 14l is also removed from the portions of th~ bifilar wires 12a and ,112b carrying the ferru1es 24 a~d 260 o ?~ ~ig~ 2 ~hows the f~rrule~ 18 di~po~ed in lon~itudinal `~paced po~ition inside a flexible cathcter 40. In operation, the ~
,flexible catheter 40 may be inserted through a vein 42 tFig. 1)¦
~`through the right atrium 41 ~o the tricuspid valve 454 The 'electrode assembly 10 will pas~ axially through the catheter 40 1S l! and out of it~ free end through the tricu~pid valve 45 into the , right ventricle 44. There the ~ree end of the bifilar wire probe ¦
will separate and the ferrules 18 wnll contact the oppo~ite spaced, walls 46 of the riqht ventricle 44. ~he catheter 40 m~y then.be xemoved from the heartO
` Figs. 3 and 4 show one step in the method of fabricating ~' the electrode aQsemblyO Fine ~3pringy wire 12 ' made of beryllium ,~
copper or b~ryllium nickel or othe r suitable alloy ranging from 0aO04~ to 0.125" i8 coated with an insulating layer 20 s-;ch as polyurethane varniahO The wire 12' i8 b~nt to form a loop 48.
I' Then the wire 8ection8 12a and 12b are placed side~ side a~ I
shown in ~ig. 5 and wound with the fine binding wire 14 ~uch a~ ¦
1 0~002" in~ulated ~opper wireO The bir~ling wir~ 14 may be bonded ,: to th~ wire 8action8 12a and 12b wlth ~ev~ral ~d ooat~ of an ¦insulated materi~l (not E~own), xuch a~ polyur~l~na~ Yarni~h whlch I wa8 u8~!td for the inau~ation 20. ~he loop 4~ the~ ~ut on line ... .
3L739~
~-A so that the wire end 16a will be longer than the wire end 16b ¦as shown in Fig~ 60 Then the insulation 20 is scraped from the wire ends 16a and 16b and the ferrules 18 are mounted on the wire ends 16a, 16b as shown in FigsO 1 and 7. The lengths of the wire 5 ends 16a and 16b are critical~ One wire end ~6a ~hould be longer han the other end 16b by at least the length of one ferrule 18, so that the ferxules occupy minimum space inai ~ the catheter 40.
rhe axial spacing of the contact ferrules 18 ~ t the ferrules 8 to pass through a smaller catheter 40 than ~ould be needed if i~Dth of the ferrules 18 were in a ~ide-by-side position against ach other when passing through the catheter 40.
The arrangement described provides better contact ¦ibetween the walls of the chamber 44 than prior loop type probes.
liThe free ends of the wires can open wider than maximum diameter Ipf a prior closed loop type of probe. The ferru;es 18 make a ll!better contact wlth tlle chamber walls than the narro~Y sides of a ,,closed wire loep because the ferrules have a larger surface area than the electrodes of the prior loop type catheter probe.
I,Furthermore, the free wire ends will not catch on protrusions in ~ithe chamber walls as presently possible with closed wire loopsO
¦IIn addition, the free wire ends bearing ferrules 18 will pass through a catheter of narrower diameter than one sized to accomo-date a probe with closed wire loop~ The use of a catheter of ~narrower diameter facilitates passage of the catheter through Ivessels of the body such as chambers of the heart 5 or to other ¦organs .
FigO 9 illustrates another embodiment of the electrode . assembly 10' wherein the binding wire 14 has been formed into a terminal 16cin order to have bipolar pacing. That i~ to say, when ~¦the electrode assembly 10 of Fig. 1 is pulsed by ;a ~.C. Volta~e ¦each of the terminals 16a and 16b have a different polarity. On ~73~
the other hand, in the electrode a~;3embly 10~ oî Fi~. 9, the ! terminal 16a and 16b may have~ on~ polarity and the terminal 16c I which i8 located in the bh~d v~a~sel ~u~t outaide vf the heart ¦ ha~ the other polarity or te~rminal 16a 3nd 16c may hsve the ~ame polarity and terminal 16b the othe~r Eolarity c~r t4~rminal 16b and 16c may have ~he aa~ polarity and t~rmi~al 16a.1;~ other polarity O
It ~aould be not~d that for bipolar p~cing, ~nal 16c ~t be located outside of the heart.
In some in~tances, it may ~ de~lrabl~ to have a oequ~-tial atrial and ~rentricular pacing. Por thi~ rpo~e, an alectrode .~ as~e~ly lOn as illustrated in Fig. 10 ~ay be utilized. l'he 1 electrode a~sembly lG" may be made from quadra~ r wire3 and i8 !` comprised of terminals 16a, 16b, 16d, and 16eO The terminals 16 I! and 16e are identical to the terminals 16a and 16b respectively.
I'The other end of the electrode a~sembly lOY ha~ four fexrule3 each . ~ubstantially the same as th~ ferrules 24 or 26. In operation fo i! sequential atrial and ventricular pacing, the catheter 40 is inserted through the ri~ht atrium to the tricuspid valve a~ beforel.
'The electrode a~sembly 10U i~ pass2d th~ough the eatheter 40 ~o ¦that the electrode 16a and 16b extend into and ~ont~ct the walls of th~ right ventricl~. The catheter 40 i~ t~en r~ov~d and a~
¦~it l~aves the r~ht atrium, th~ terminalA 16~ and 16e wh~c~
~entioned b~or~ are identlcal r~spect~v~ly to the ten~inal~ 16 and 16b~ ~xp~nd and o~nta~t th~ atrium wallo. ~h~ pul~ed D~Co voltaqe may ~e applied to the ~errul~ at ~h~ end o~ th~ electrod~
a~s~nbly 10" to pul~e t~ie rig~t atrium ter~nal~ 16d and 16e and then the ris~ht ventri~:ular t~rminals 16a and 16b in ~equence to i~itate the normal heart function.
¦ Although not illustrat~d, the .electro~ ;~a~ ly may be u8ed to determine the contractility o~ th~ l~ft ventricle after a ¢ 1~73914 I¦ myocardial in~arction, by an ele~trod~ a~s~ly (using 0004"
Il diameter wQre~) place~ in a cathoter which ha~ b~en introduced t~r _ lough a ~itral valve in th~ l~ft ventricl~O A radio-opaque dye ¦~ay th~n be pu~ped thro~gh th~ catheter ~nto th~ left ventricl~
and the el~ctrode a~e~bly may be pul~d whan the heart i~
depolariz~d so that the contraction i5 great0r t~an that which ~1 e.Yi~tR during a normal heart cycleO The contrac~i~n of the ¦, heart may be filmed and will display a measure of the damage !l of the heart by the i~fraction. It may al~o be under~tood that ¦jthe aforementioned electrode a~sembly may be u~ed a~ an EXG
!I Monitor in the v~ntricle and can thQn be 8W~ ~ched when fibrilla-,~tion OCCUX8 as a defribrillator~
In view of th~ foregoing, it i8 clear that by having 1~ wires of different len~ths, a trifilar, quadkafilar or any bundle 1¦ of wires will pass through a ~ubstantially ~maller diameter , catheter then that required ~or the prior ~st loop type catheter probe. It would also be noted, that the el~ctrode a~embly here~
' inbefore de~cribed, may be u~¢d ~or ~it~ure~nt of blood flow ln , a ve~sel in ~hich the a~s~ly i8 placed~ in much the same 1! manner as that of a loop typ~ catheter prob~.
It should be understood that the foregoing relate~ to only a preferred embodi~en~ of the inventisn~ a~d that it i~3 , intended to cover all chançles and modi~ication~ of the example ii of the invention herein cho3en for the purpo e~ of th~ di~closure~
i which do not constitute~ departures îrom the spirit and scope s:~f ~ the 1nvent1on.
i ` ~ ' , ~, ~` -8-`~ ~
.```" '51t
Claims (14)
PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:
1. An electrode assembly for insertion into a catheter and establishing an electrical connection to an electronic circuit, said assembly comprising:
a plurality of wires, each of said wires insulated from each other and each of said wires being electrically conductive and extending together side-by-side and having different lengths at one end thereof;
means binding said plurality of wires together for substantially their entire length except for a free end at said one end of each of said wires;
an end portion of each of said free ends being bared of insulation;
an electrically conductive contact means positioned on each of said bared portions on each of said free ends of said wires, said contact means being spaced apart axially of each other when axially aligned with said free ends of said wires inside said catheter; and a conductive means for connecting the other ends of each of said wires to said electronic circuit.
a plurality of wires, each of said wires insulated from each other and each of said wires being electrically conductive and extending together side-by-side and having different lengths at one end thereof;
means binding said plurality of wires together for substantially their entire length except for a free end at said one end of each of said wires;
an end portion of each of said free ends being bared of insulation;
an electrically conductive contact means positioned on each of said bared portions on each of said free ends of said wires, said contact means being spaced apart axially of each other when axially aligned with said free ends of said wires inside said catheter; and a conductive means for connecting the other ends of each of said wires to said electronic circuit.
2. An electrode assembly as defined in claim 1, wherein each said contact means comprises a ferrule.
3. An electrode assembly as defined in claim 2, wherein said wires are made of springy material so that said free ends separate widely outside of said catheter.
4. An electrode assembly as defined in claim 2, further comprising insulation material forming insulative beads at opposite ends of each cylindrical ferrule.
5. An electrode assembly as defined in claim 4, wherein said conductive means comprises electrically conductive other elements positioned on bared portions of other ends of each of said wires.
6. An electrode assembly as defined in claim 5, wherein said other conductive elements are spaced apart axially of each other on each of said wires.
7. An electrode assembly as defined in claim 6, wherein each of said other conductive elements is another cylindrical ferrule each enclosing each of said wires but electrically contacting only one of said wires.
8. An electrode assembly as defined in claim 7, wherein each of said other ferrules is held in place by conductive material on said wires.
9. An electrode assembly as defined in claim 2 wherein said plurality of wires is bifilar.
10. An electrode assembly as defined in claim 1 wherein said means binding said plurality of wires together is an insulated other wire.
11. An electrode assembly as defined in claim 10, wherein said other wire is formed as another contact element and is axially spaced between said ferrules and other ends of said wires.
12. An electrode assembly as defined in claim 2, wherein said plurality of said wires is quadrafilar.
13. In an electrode assembly for insertion into the heart of a person via a catheter or the like for establishing an electrical connection between heart tissue and an electronic circuit, said assembly comprising at least two wire leads insulated from each other and carrying relatively large contact portions on their ends, said wire leads being slidable relative to said catheter, the improvement wherein said wire leads are bound together in a manner providing discrete free distal end portions of fixed relative length, said free end portions of said wire leads comprising oppositely bent springs that carry said relatively large contact portions, when residing within said cannular passage, said wire portions being temporarily straightened in a manner known per se by the confining walls of said cannular passage, and lying alongside one another, the fixed lengths of the free end portions of said wires being of preselected, only slightly different length in a manner to stagger within the cannular passage the positions of the relatively large contact portions, thereby to enable said cannular passage to be of minimum diameter, whereby said assembly can enter via a single cannular passage to position multiple wire leads within one cavity of the heart, and said free end portions of said wires can spring apart to their original bent shape within said one heart chamber upon relative withdrawal of said cannular passage, thereby to enable stable contact of said contact portions at multiple positions within a relatively small region of the heart.
14. The electrode assembly of claim 13 wherein at the other end of the assembly a number of axially spaced apart contact portions encircle all the wire ends, each of said contact portions being in direct electrical contact with only one of said wire leads.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US157,504 | 1980-06-09 | ||
| US06/157,504 US4289138A (en) | 1980-06-09 | 1980-06-09 | Electrode assembly for temporary pacing and heart measurements |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1173914A true CA1173914A (en) | 1984-09-04 |
Family
ID=22564020
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000379231A Expired CA1173914A (en) | 1980-06-09 | 1981-06-08 | Electrode assembly for temporary pacing and heart measurement |
Country Status (9)
| Country | Link |
|---|---|
| US (1) | US4289138A (en) |
| JP (1) | JPS5819301B2 (en) |
| CA (1) | CA1173914A (en) |
| DE (1) | DE3122812C2 (en) |
| FR (1) | FR2483786B1 (en) |
| GB (1) | GB2077596B (en) |
| IT (1) | IT1143402B (en) |
| NL (1) | NL8102756A (en) |
| SE (1) | SE450683B (en) |
Families Citing this family (33)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4630611A (en) * | 1981-02-02 | 1986-12-23 | Medtronic, Inc. | Orthogonally-sensing lead |
| US4750494A (en) * | 1981-05-12 | 1988-06-14 | Medtronic, Inc. | Automatic implantable fibrillation preventer |
| CA1231392A (en) * | 1982-10-14 | 1988-01-12 | Edward E. Elson | Flexible tip cardiac pacing catheter |
| US4602645A (en) * | 1982-12-16 | 1986-07-29 | C. R. Bard, Inc. | Atrio-ventricular pacing catheter |
| US4497849A (en) * | 1983-09-26 | 1985-02-05 | Hughes Howard C | Process for polymer coating electrical conductors |
| US4522212A (en) * | 1983-11-14 | 1985-06-11 | Mansfield Scientific, Inc. | Endocardial electrode |
| DE3412950A1 (en) * | 1984-04-06 | 1985-10-17 | Peter Dr.-Ing. 7889 Grenzach-Wyhlen Osypka | SURGICAL ELECTRODE |
| US4530368A (en) * | 1984-05-24 | 1985-07-23 | Cordis Corporation | Temporary bipolar pacing lead |
| US4641656A (en) * | 1985-06-20 | 1987-02-10 | Medtronic, Inc. | Cardioversion and defibrillation lead method |
| US4699147A (en) * | 1985-09-25 | 1987-10-13 | Cordis Corporation | Intraventricular multielectrode cardial mapping probe and method for using same |
| JPS6442005U (en) * | 1987-09-07 | 1989-03-14 | ||
| DE3735190C1 (en) * | 1987-10-17 | 1989-05-24 | Labionics Ag | Device for measuring haemodynamic parameters of blood circulation, especially of the cardiac output |
| SE8800019D0 (en) * | 1988-01-07 | 1988-01-07 | Knut Olof Edhag | FOR CARDIALLY DEFIBLATION USED INTRAVASCULES ELECTRO CABLE |
| US5052407A (en) * | 1988-04-14 | 1991-10-01 | Mieczyslaw Mirowski | Cardiac defibrillation/cardioversion spiral patch electrode |
| US4896671A (en) * | 1988-08-01 | 1990-01-30 | C. R. Bard, Inc. | Catheter with contoured ablation electrode |
| US5056517A (en) * | 1989-07-24 | 1991-10-15 | Consiglio Nazionale Delle Ricerche | Biomagnetically localizable multipurpose catheter and method for magnetocardiographic guided intracardiac mapping, biopsy and ablation of cardiac arrhythmias |
| US5050601A (en) * | 1990-05-29 | 1991-09-24 | Joel Kupersmith | Cardiac defibrillator electrode arrangement |
| DE4025369A1 (en) * | 1990-08-10 | 1991-02-07 | J Prof Dr Nitsch | Mapping electrode catheter for exact localisation of tachycardia - has five electrodes at distal end in form of spiral spring to register intracardiac potentials |
| US5282845A (en) * | 1990-10-01 | 1994-02-01 | Ventritex, Inc. | Multiple electrode deployable lead |
| US5144960A (en) * | 1991-03-20 | 1992-09-08 | Medtronic, Inc. | Transvenous defibrillation lead and method of use |
| US5313953A (en) * | 1992-01-14 | 1994-05-24 | Incontrol, Inc. | Implantable cardiac patient monitor |
| WO1995005773A1 (en) * | 1992-02-11 | 1995-03-02 | Cardiac Pathways Corporation | Endocardial electrical mapping catheter |
| US6086581A (en) | 1992-09-29 | 2000-07-11 | Ep Technologies, Inc. | Large surface cardiac ablation catheter that assumes a low profile during introduction into the heart |
| US5471982A (en) * | 1992-09-29 | 1995-12-05 | Ep Technologies, Inc. | Cardiac mapping and ablation systems |
| US5526810A (en) * | 1993-10-07 | 1996-06-18 | Wang; Dai-Yuen | Intraventricular mapping catheter |
| SE9402775D0 (en) * | 1994-08-19 | 1994-08-19 | Siemens Elema Ab | Electrode device for intracardiac stimulation of the heart tissue and / or sensing of the heart signals of a patient |
| US6475213B1 (en) | 1996-01-19 | 2002-11-05 | Ep Technologies, Inc. | Method of ablating body tissue |
| US5851226A (en) * | 1996-10-22 | 1998-12-22 | Medtronic, Inc. | Temporary transvenous endocardial lead |
| IT1302900B1 (en) * | 1998-12-04 | 2000-10-10 | Riccardo Fenici | AMAGNETIC CATHETER FOR THE SINGLE-CATHETER REGISTRATION OF MULTIPLE SINGLE-PHASE ACTION POTENTIALS, LOCABLE THREE-DIMENSIONALLY AND |
| US10695126B2 (en) | 2008-10-06 | 2020-06-30 | Santa Anna Tech Llc | Catheter with a double balloon structure to generate and apply a heated ablative zone to tissue |
| US8929969B2 (en) * | 2009-04-14 | 2015-01-06 | Medtronic Ablation Frontiers Llc | Catheter assembly and associated method |
| AU2012246723C9 (en) | 2011-04-22 | 2014-08-28 | Topera, Inc. | Basket style cardiac mapping catheter having an atraumatic basket tip for detection of cardiac rhythm disorders |
| US11331140B2 (en) | 2016-05-19 | 2022-05-17 | Aqua Heart, Inc. | Heated vapor ablation systems and methods for treating cardiac conditions |
Family Cites Families (14)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3347224A (en) * | 1964-05-26 | 1967-10-17 | Brandon L Adams | Apparatus and method for measuring cardiac output |
| US3348548A (en) * | 1965-04-26 | 1967-10-24 | William M Chardack | Implantable electrode with stiffening stylet |
| US3769984A (en) * | 1971-03-11 | 1973-11-06 | Sherwood Medical Ind Inc | Pacing catheter with frictional fit lead attachment |
| US3788329A (en) * | 1972-04-17 | 1974-01-29 | Medtronic Inc | Body implantable lead |
| US3866615A (en) * | 1973-01-15 | 1975-02-18 | Daigle Claude W | Portable electronic cardiac stimulator |
| DE2309749B2 (en) * | 1973-02-27 | 1978-05-24 | Siegfried Dr.Med. Dipl.-Ing. Dipl.-Wirtsch.-Ing. Lehr | Electrode for medical purposes |
| US3865118A (en) * | 1973-12-27 | 1975-02-11 | Univ California | Transvenous coaxial catheter |
| DE2605590A1 (en) * | 1976-02-12 | 1977-08-18 | Heinz Dr Med Praeuer | Pacemaker electrode with flexible electrode catheter - with flexible projecting base for abutment against wall of heart |
| US4135518A (en) * | 1976-05-21 | 1979-01-23 | Medtronic, Inc. | Body implantable lead and electrode |
| US4112952A (en) * | 1977-02-11 | 1978-09-12 | The United States Of America As Represented By The Secretary Of Health, Education And Welfare | Electrode for artificial pacemaker |
| US4154247A (en) * | 1977-04-01 | 1979-05-15 | Medtronic, Inc. | Formable cardiac pacer lead and method of assembly and attachment to a body organ |
| US4164939A (en) * | 1977-06-24 | 1979-08-21 | The Regents Of The University Of California | Orthogonal electromagnetic flow and diameter sensor system |
| FR2421626A1 (en) * | 1978-02-01 | 1979-11-02 | Anvar | Multiple contact heart stimulating electrode - has coiled wire inside sleeve interrupted for intermediate contacts, terminating in spherical final contact |
| JPS5554963A (en) * | 1978-10-18 | 1980-04-22 | Fujiwara Akimasa | Catheter that fix pacemaker electrode into atrium |
-
1980
- 1980-06-09 US US06/157,504 patent/US4289138A/en not_active Expired - Lifetime
-
1981
- 1981-06-03 GB GB8117070A patent/GB2077596B/en not_active Expired
- 1981-06-05 SE SE8103573A patent/SE450683B/en not_active IP Right Cessation
- 1981-06-08 CA CA000379231A patent/CA1173914A/en not_active Expired
- 1981-06-09 NL NL8102756A patent/NL8102756A/en not_active Application Discontinuation
- 1981-06-09 JP JP56088752A patent/JPS5819301B2/en not_active Expired
- 1981-06-09 FR FR8111300A patent/FR2483786B1/en not_active Expired
- 1981-06-09 IT IT48638/81A patent/IT1143402B/en active
- 1981-06-09 DE DE3122812A patent/DE3122812C2/en not_active Expired
Also Published As
| Publication number | Publication date |
|---|---|
| IT1143402B (en) | 1986-10-22 |
| IT8148638A0 (en) | 1981-06-09 |
| GB2077596A (en) | 1981-12-23 |
| FR2483786B1 (en) | 1985-10-25 |
| DE3122812C2 (en) | 1986-04-10 |
| DE3122812A1 (en) | 1982-03-25 |
| FR2483786A1 (en) | 1981-12-11 |
| JPS5722769A (en) | 1982-02-05 |
| US4289138A (en) | 1981-09-15 |
| SE450683B (en) | 1987-07-20 |
| NL8102756A (en) | 1982-01-04 |
| JPS5819301B2 (en) | 1983-04-18 |
| GB2077596B (en) | 1984-08-08 |
| SE8103573L (en) | 1981-12-10 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA1173914A (en) | Electrode assembly for temporary pacing and heart measurement | |
| USRE32204E (en) | Electrode assembly for temporary pacing and heart measurements | |
| US5483022A (en) | Implantable conductor coil formed from cabled composite wire | |
| CA1082317A (en) | Body implantable lead with stiffening stylet | |
| US5522872A (en) | Electrode-conductor sleeve joint for cardiac lead | |
| US5458629A (en) | Implantable lead ring electrode and method of making | |
| US5760341A (en) | Conductor cable for biomedical lead | |
| US5545201A (en) | Bipolar active fixation lead for sensing and pacing the heart | |
| US5342414A (en) | Transvenous defibrillation lead | |
| US5796044A (en) | Coiled wire conductor insulation for biomedical lead | |
| US6456888B1 (en) | Geometry for coupling and electrode to a conductor | |
| US7168165B2 (en) | Fabrication of electrical medical leads employing multi-filar wire conductors | |
| US5439485A (en) | Flexible defibrillation electrode of improved construction | |
| AU661623B2 (en) | Torque indicator for fixed screw leads | |
| US5330521A (en) | Low resistance implantable electrical leads | |
| US5897585A (en) | Stretchable pacing lead | |
| US6615483B2 (en) | Method for coating a tip region of a multipolar electrode lead | |
| EP2890446B1 (en) | Mri compatible lead coil | |
| US5569883A (en) | Joint for providing a secure connection between a wound element and a mating part in a body implantable lead assembly and method for making such joint | |
| US5014720A (en) | Lead to electrode joint assembly and method of manufacture thereof | |
| JP2006501029A (en) | Implantable medical device lead conductor and manufacturing method thereof | |
| US20040267328A1 (en) | Electrode selection system for medical electrical leads | |
| EP2207588B1 (en) | Stimulation and sensing lead wtih non-coiled wire construction | |
| US7921554B2 (en) | Method for manufacturing a medical electrical lead connector ring | |
| US20050060013A1 (en) | Cardiac lead with anodic electrode assembly having dual support hulls |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| MKEX | Expiry |