although the present invention is applicable to many different types of cardiac devices , including monopolar and quatropolar devices , it is especially suitable for use in conjunction with a bipolar temporary cardiac pacing wire . accordingly , the present invention will be described below in connection with such a pacing wire . as used herein , the term “ distal ” shall mean that portion of the pacing wire or element thereof which is remote from a source of electric signals located external to the patient &# 39 ; s body . conversely , the term “ proximal ” shall mean that portion of the pacing wire or element thereof which is in close proximity to the external source of electrical signals . referring initially to fig1 a bipolar temporary cardiac pacing wire 10 includes a keith - type breakaway needle 12 arranged at a proximal end of the pacing wire 10 . the keith - type needle 12 , such as the one disclosed in u . s . pat . no . 4 , 010 , 756 issued on mar . 8 , 1977 to dumont et al ., has a distal section 12 a and a proximal section 12 b , which is pointed for piercing the thoracic wall to lead the proximal end of the pacing wire 10 outside the chest cavity of a patient in accordance with a medical procedure well known in this field . at the distal end of the pacing wire 10 there are first and second electrodes 22 , 24 . the electrodes are affixed to a patch 11 , which will be described in more detail below . a pair of insulated , electrical conductive electrode wires 18 , 20 extends between the distal and proximal ends of the pacing wire 10 . the electrode wires 18 , 20 are of the “ lamp cord ” type ( i . e ., they are arranged in a side - by - side fashion as shown in fig1 ) where each wire has a braided , multi - stand core of stainless steel and a surrounding layer of insulation made from polyethylene . the core of each wire could have a twisted construction with a surrounding layer of insulation made from polyethylene or any other suitable electrical non - conducting material , such as silicon , polytetrafluoroethtylene , or nylon . the electrode 22 is electrically connected to the electrode wire 18 , and the electrode 24 is electrically connected to the electrode wire 20 . the electrodes 22 , 24 have a conventional construction and are adapted to transmit electrical signals from one to the other for the purpose of stimulating , pacing , sensing , monitoring , or defibrillating the heart . alternatively , the electrodes 22 , 24 can be composed of a “ smart ” metal , or a shape memory alloy , preferably nitinol alloy . at the proximal end of the pacing wire 10 there are two connectors 26 , 28 . the connector 26 is mechanically and electrically connected to the electrode wire 20 , but only mechanically connected to the electrode wire 18 . electrode wire 18 passes through the elongated , sleeve - like connector 26 and is mechanically and electrically connected to the keith - type needle 12 in a conventional manner . the other elongated , sleeve - like connector 28 is positioned on the electrode wire 18 intermediate to the connector 26 and the keith - type needle 12 . unlike the connector 26 , which is electrically connected to the electrode wire 20 , the connector 28 does not have to be electrically connected to either of the electrode wires 18 , 20 . however , the connector 28 may be electrically connected to the electrode wire 20 , which could also be electrically connected to both of the connectors 26 , 28 . each of the connectors 26 , 28 extends circumferentially about the electrode wire 18 and is made from suitable electrically conductive material , such as stainless steel . while the connectors 26 , 28 have a generally circular cross - sectional shape , they could have other cross - sectional shapes , such as oval , square , rectangular , etc . the patch 11 is preferably a flat , polymeric film . it can be bioabsorbable or non - bioabsorbable . the patch desirably exhibits elasticity and flexibility to readily conform to a beating heart surface . in addition , the patch may have perforations to aid in conformity and adherence to the heart surface . the patch may be of a knitted construction , or a woven or non - woven construction , or any other textile fabric construction . alternatively , it can be a sponge , or a composite of several bioabsorbable or non - bioabsorbable materials . the patch is preferably a polymeric film which is gas and moisture permeable . preferably , the patch is a polymeric film composed of poly ( p - dioxanone ). referring to fig4 the patch has an external surface 13 and a tissue - contacting surface 14 . the tissue - contacting surface is coated with an adhesive film 15 . suitable adhesive compositions include , but are not limited to , bovine albumin and glutaraldhyde , polyethylene glycol , collagen pellets , thrombin , protein polymers , tacky gelatin adhesive , hydrocolloidal butyl base adhesive , and silicone adhesive . the adhesive may also be be composed of a moisture activated polymeric film such as , for example , a polyvinyl alcohol film . the preferred adhesive film is a pressure sensitive medical grade adhesive . the most preferred adhesive is a medical grade silicone adhesive , particularly rtv silicone adhesive . referring again to fig1 in combination with fig2 - 4 , the first and second electrodes 22 , 24 are l - shaped electrodes which are fixed to the tissue - contacting surface 14 of the patch 11 . affixing of the electrode to the patch is accomplished when the electrodes are adhered to the adhesive film 15 coated on the tissue - contacting surface of the patch . the electrode wires 18 , 20 of the bipolar pacing wire 10 are received through a hole 17 in the patch . the wires are bent or curved at the portion passing through hole 17 . this works to further secure the wires to the patch in combination with the adhesive film . in order to cover the tissue - contacting surface of the patch which contains the adhesive film , a release paper 16 is attached to the adhesive film for proper storage , handling and use . in the most preferred embodiment , each of the first and second l - shaped electrodes 22 , 24 has a spiral portion 30 , 31 to increase the surface area of the electrodes exposed to the heart tissue and enhance the bonding of the electrodes to the tissue as a result of the adhesive film . when the surgeon wishes to apply the preferred bipolar temporary pacing wire , he attaches the patch 11 carrying the exposed electrodes to the heart 32 of the surgical patient 33 ( see fig5 - 7 ). to do this , he removes the release paper 16 , thus exposing the adhesive film 15 on the tissue - contacting surface 14 of the patch . with the application of pressure , the patch can be adhered to the heart . as illustrated in fig3 - 5 , once pressure is applied , the exposed first and second l - shaped electrodes 22 , 24 are positioned into electrical contact with the heart surface 33 . the adhesive film on the tissue - contacting surface of the patch assures an adequate bond between the patch and the heart surface , thus insuring that the exposed electrodes attached to the heart surface will not be dislodged during use of the bipolar temporary pacing wire . also illustrated in fig4 there is shown the myocardium 34 and endocardium 35 of the heart . fig4 nicely shows the protrusion of the insulated electrode wires through the hole 17 of the patch . turning now to fig6 the keith - type needle is used to pierce the thoracic wall 38 of the patient . once the bipolar wire protrudes from the patient , the needle 12 is severed at distal section 12 a to expose the connector 28 . as illustrated in fig7 the connectors 26 , 28 are inserted into the sockets of a pacemaker 40 . for a more detailed explanation of the connection between the connectors and the pacemaker , the reader is referred to co - pending and commonly assigned u . s . application ser . no . 09 / 451 , 590 , filed nov . 30 , 1999 . once the temporary pacing is completed , the bipolar wire is removed from the patient . as illustrated in fig4 the insulated electrode wires and patch can simply be pulled in the direction of directional arrow “ a ” at a 0 ° angle with respect to the surface of the heart surface 33 . alternatively , if desired , the wires and patch can be pulled in the direction of directional arrow “ b ” at an angle of 180 ° to remove the wire . the direction of pulling will be pre - determined based on the orientation of the patch with respect to the path the electrodes take to exit the body cavity . this is determined during implantation . the following example illustrates the application of the preferred temporary pacing wire of this invention . this example is intended to be illustative only , and it is not intended to limit the scope or spirit of the invention , which is defined in the claims which appear below . numerous additional embodiments will become readily apparent to those skilled in this art . bipolar temporary pacing wires were constructed in accordance with the preferred embodiment of this invention and as illustrated in the figures . the wires were applied to wet pig hearts . the patches used for affixing the electrodes to the heart were composed of poly ( p - dioxanone ) polymer films coated with pressure sensitive medical grade rtv silicone adhesive . each patch was about two square inches in size . 7 mg / in . sq . of adhesive was applied from the adhesive tube directly onto the tissue - contacting surface of each film . the first and second electrodes of the pacing wire were then affixed to the tissue - contacting surface of the polymeric film . alternatively , any pressure sensitive adhesive could have been pre - applied to the film and subsequently covered by a release paper such as silicone paper . a chatillon tensile tester ( crosshead speed = 12 in / min with force gauge dfsi - 50 ) was clamped onto a free portion of the proximal end of the pacing wire . the pacing wire was then removed . results showed an average pullout force of 70 gm ., with a standard deviation of 10 gm . these values were comparable to those generated with commercially available pacing wire . measurements were then made to obtain the force required to remove the two square inch polymer film from the wet heart surface . these measurements resulted in a pullout force of 150 gm ., with a standard deviation of 20 gm ., demonstrating that the polymeric film could be removed from the heart without excessive trauma .
an electrical connector for a cardiac device is disclosed . the connector has a wire and an electrode at the distal end of the wire . the wire is attached to a patch , and the patch is coated with an adhesive film for adhering the patch to tissue . the preferred connector is a bipolar temporary cardiac pacing wire . the use of an adhesive film eliminates or reduces the need for suturing the patch to tissue , thus avoiding or significantly reducing tissue trauma associated with suturing .