Surgery – Diagnostic testing – Structure of body-contacting electrode or electrode inserted...
Reexamination Certificate
2000-02-22
2002-08-20
Cohen, Lee (Department: 3739)
Surgery
Diagnostic testing
Structure of body-contacting electrode or electrode inserted...
C607S124000
Reexamination Certificate
active
06438400
ABSTRACT:
TECHNICAL FIELD
The present invention relates, generally, to the evaluation of cardiac functions, and more particularly to the invasive determination of cardiac output and electrical activity via the use of electrodes placed within the esophagus region of a subject.
BACKGROUND OF THE INVENTION
Electrocardiography, or ECG, involving the collection and study of the electrical activity from the heart, has long been an effective method for the diagnosing of problems or irregularities related to the operation of the heart. Generally, ECG is used for two major purposes: (1) for diagnosing cardiac arrhythmia's, and (2) providing information on the status of the myocardium.
The early methods for obtaining an electrocardiogram or ECG included the placing of electrodes invasively through the skin or noninvasively attaching the electrodes to the surface of the patient's skin, such as the chest or limbs, by adhesion or clamping. However, certain anatomical disabilities of the human or animal physiology often obstruct the hearts electrical current from the measurement device and thus cause an inaccurate measurement. To avoid these problems, methods were developed for conducting invasive electrocardiograms via the esophagus.
Esophageal probes for monitoring a patient are, in general known. For example, U.S. Pat. No. RE 31,377, Mylrea et al., reissued Sep. 13, 1983, and U.S. Pat. Nos. 4,349,031 and 4,476,872, Perlin, issued Sep. 14, 1982 and Oct. 16, 1984, respectively, disclose catheters used for monitoring the patients electrocardiogram, heartbeat sounds and temperature. However, disadvantages exist with these probes due to the use of either pill or ring electrodes. Pill electrodes, as shown in
FIG. 1A
, which are electrodes capable of being swallowed by the patient in an attempt to position the electrodes in the esophagus at the level of the atria, have yielded results that were inconclusive because of variability in electrode placement. Ring electrodes, generally comprised of a conductive band wrapped around the circumference of the probes' flexible tubing, as shown in
FIGS. 1B and 1C
, can float within the esophagus, and thus, have also yielded inconclusive results for similar reasoning. In particular, when the electrode is not in contact with the tissue wall of the esophagus directly, a fluid or mucosal connection affects the impedance of the received signals, and thus, detrimentally impacts the diagnostic quality of the signals.
Another example, U.S. Pat. No. 3,951,136, Wall, issued Apr. 20, 1976, also discloses an esophageal probe used for monitoring a patient's cardiac electrical activity, heart sounds and temperature wherein the probe disclosed utilizes a pair of spaced electrodes with domed-shaped outer heads. Although these electrodes purport to provide improved contact surface over previously described electrodes, the disclosed electrodes limit and restrict the rotational position of the probe within the esophagus. Moreover, the electrodes configuration suffers from other inherent design inadequacies, such as, for example, a potentially weak soldered connection to the wiring system. Further, like the other prior art esophageal probes, the distal end of the probe comprises a thin membrane or diaphragm that seals the end of the probe. As one skilled in the art will appreciate, these thin-walled diaphragms, while effective in allowing for temperature and sound measurements to be obtained, are quite fragile and are often damaged during insertion and use within the patient's esophagus.
Other methods for evaluating cardiac functions are known in the prior art. One particular example, impedance cardiography, is increasingly an important mechanism for determining a patient's cardiac condition both during and following medical procedures.
Impedance cardiography falls within the more general category of impedance plethysmography, which refers to the measurement of volume changes (and thereby flow) in the body, as derived from observing changes in electrical impedance. Impedance cardiography, generally, is a noninvasive bioimpedance method for measuring cardiac output. Specifically, cardiac output measurements are based on the principal that blood is a conductor of electricity and that the electrical impedance of the thorax will change during a cardiac cycle. This change in impedance is caused by the thoracic aortic blood flow which is directly related to the amount of blood ejected from the heart.
U.S. Pat. No. 3,340,867, now Re. 30,101, reissued September 1979 to Kubicek, et al., discloses a method for determining cardiac output by measuring the patient's heart stroke volume. There, an impedance plethysmograph employs two sets of electrodes placed on the neck and chests of patients, to provide an impedance difference signal from the two center electrodes. A constant, low-amplitude, high-frequency alternating current is applied to the outermost pair of electrodes while the innermost pair of electrodes senses the voltage levels above and below the patient's heart. Kubicek et al.'s method entails first determining the heart stroke volume from these impedance signals, based on the observation that resistance to a current passed through the chest varies with thoracic aortic blood flow, and from this determination of stroke volume, then estimating the cardiac output.
U.S. Pat. No. 4,450,527, issued to Sramek on May 22, 1984, generally discloses a similar apparatus, model and equation for relating impedance and stroke volume to determine cardiac output. U.S. Pat. No. 5,309,917, issued May 10, 1994, U.S. Pat. No. 5,423,326 issued Jun. 13, 1995, and U.S. Pat. No. 5,443,073 issued Aug. 22, 1995, all of which were issued to Wang, et al., each generally disclose variations of the Kubicek and Sramek methods.
Yet another model and method of impedance cardiography regarding the placement and spacing of electrodes has been proposed by Bernstein. According to Bernstein, stroke volume (SV) is related to the change in impedance (Z) as shown in Equation 1:
SV
=
δ
×
(
0.17
H
)
3
×
T
LVE
×
(
ⅆ
Z
/
ⅆ
t
)
max
4.2
×
Z
0
SV
=
Stoke
Volume
δ
=
correction
factor
for
patient
weight
H
=
Patient
height
(
cm
)
T
LVE
=
left
ventricular
ejection
time
(
sec
)
(
ⅆ
Z
/
ⅆ
t
)
max
=
maximum
value
of
the
first
derivative
of
Z
,
where
Z
is
the
change
in
impedance
caused
by
thoracic
aortic
blood
flow
Z
0
=
mean
baseline
impedance
of
the
thorax
(
ohm
)
(
1
)
While each these methods can be helpful in determining cardiac output, the various types of non-invasive devices disclosed such as the outer skin electrodes of Kubicek and Sramek, often prove inefficient, for example when dealing with many surgical procedures or with skin abrasion patients. As one can imagine, these devices require a number of exposed connective wires and corresponding electrodes that may interfere with other surgical procedures. Furthermore, because the inner surface electrodes may receive impedance signals from various other regions within the patient due to the distance in placement of the electrodes from the thoracic aorta region, accuracy concerns have been raised. Additionally, incorrect electrode placement can result due to the changes in the patient's physiology of the thorax with respect to the placement of the electrodes on the sternum, as well as due to the size of the patient. Finally, as recognized in Equatio
Beard Lane
Howard James P.
Melnikoff Donald J.
Young Robert L.
Cohen Lee
Heska Corporation
Snell & Wilmer L.L.P.
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