CA1226906A - Method and apparatus for measuring cardiac output - Google Patents
Method and apparatus for measuring cardiac outputInfo
- Publication number
- CA1226906A CA1226906A CA000426283A CA426283A CA1226906A CA 1226906 A CA1226906 A CA 1226906A CA 000426283 A CA000426283 A CA 000426283A CA 426283 A CA426283 A CA 426283A CA 1226906 A CA1226906 A CA 1226906A
- Authority
- CA
- Canada
- Prior art keywords
- blood
- electrodes
- conductivity cell
- resistivity
- catheter
- 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
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14542—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring blood gases
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/026—Measuring blood flow
- A61B5/0275—Measuring blood flow using tracers, e.g. dye dilution
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1468—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means
- A61B5/1473—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means invasive, e.g. introduced into the body by a catheter
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
- A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
- A61B5/6852—Catheters
Abstract
Cardiac output is measured utilizing an indicator, such as saline, which alters blood resistivity, and an electrically calibrated conductivity cell positioned at the tip of a catheter.
The catheter with the tetrapolar conductivity cell at the top is inserted into a blood vessel for current injection to develop a potential which is proportional to blood resistivity for inscribing the dilution curve occurring due to injection of the indicator, which curve is utilized to determine blood flow or cardiac output.
The catheter with the tetrapolar conductivity cell at the top is inserted into a blood vessel for current injection to develop a potential which is proportional to blood resistivity for inscribing the dilution curve occurring due to injection of the indicator, which curve is utilized to determine blood flow or cardiac output.
Description
This invention relates to an apparatus for measuring blood flow and, more particularly, relates to measuring cardiac output utilizing an indicator, such as saline, and a conductivity cell positioned at the tip of a catheter.
It is often necessary, or at least desirable, that car-dice output be monitored or measured. While apparatus and methods have been heretofore suggested and/or utilized to accomplish this end, such apparatus and/or methods have not been completely satisfactory and have required, for example, mixing of calibrating solutions, withdrawal of blood and/or special preparation of the indicator (such as cooling), which has limited the usefulness of such methods and/or resulting apparatus.
In addition, while dilute saline has heretofore been utilized for the measurement of cardiac output (see, for example, Steward, G. N. "Researches on the Circulation and on the Influences Which Affect It" Mourn. Phsyiol. 22:159-183 (1897) and Stewart. "The Output of the Heart in Dots" Amer. Mourn.
Fishily. 57:27-50 (1921)), it is now seldom used even though use of such an indicator has attractive features including low cost, low toxicity and enables the use of a simple and inexpensive detector, namely a conductivity cell. This invention provides an improved apparatus and method for monitoring and/or measuring cardiac output. A saline indicator and a conductivity cell postponed at the tip of a catheter provides an economical yet efficient and dependable apparatus which enables measurement of blood resistivity without the necessity of blood withdrawal or the preparation of calibrating solutions; said blood resistivity measurement being then utilized for providing the means for calibrating and determining cardiac output.
I l2ll-73g It is therefore an object of -this invention -to pro-vise an improved apparatus for measurinc3 cardiac output.
It is another object of this invention to provide an improved apparatus for measurincJ cardiac output that does not require blood withdrawal or special preparation of calibrating or indicator solutions.
It is still another object of -this invention to provide an improved apparatus for measuring cardiac output utilizing an indicator, such as a saline indicator or a poorly conductive indicator such as a I dextrose in water Do and a conductivity cell.
It is yet another object of this invention to provide an improved apparatus for measuring cardiac output includinc3 a saline indicator and a conductivity cell positioned at the tip of a catheter.
It is still another object of this invention to provide an improved apparatus for measurinc3 blood resistivity.
With these and other objects in view which will become apparent to one skilled in -the art as the description proceeds, this invention resides in the novel construction, combination, arrangement of parts and method substantially as hereinafter described, and more particularly defined by the appended claims, it being understood that such chancres in the precise embodiment of the hereinclisclosed invention are meant to be included as come within the scope of the claims.
In accordance with a broad aspect of the invention there is provided an apparatus for enabling measurement of cardiac output by determination of blood resistivity, said apparatus comprising:
detector means for detecting resistivity;
I
positioning means for adapting said detector means to be positioned in the flow path of blood;
electrical means connected with said detector means for generating an output that is proportional to the resistivity owe the blood in said flow path, said electrical moans including means for generating an output indicative of baseline blood resistivity, and calibration means for electrically calibrating said apparatus, said calibration means including baseline calibration means for calibrating said output indicative of baseline blood resistivity.
In accordance with another broad aspect of the invention there is provided an apparatus for enabling measure-mint of cardiac output by determination of blood resistivity, said apparatus comprising:
a tetrapolar conductivity cell having four electrodes a catheter having said conductivity cell positioned on the tip thereof, said catheter briny adapted for insertion into a body so that said conductivity cell is in the flow path of blood in said body;
a constant-curren~ source connected with two of said electrodes of sand conductivity cell;
first amplifying means connected with the other two of said electrodes of said conductivity cell for amplifying a potential appearing on said electrodes;
indicating means connected with said first amplifying means for indicating resistivity;
isolation means connected with sail first amplifying means for providing signal isolation and -pa-second amplifying means connected with said isolation means and providing an isolated analog output of blood resistivity for enabling inscribing of the dilution curve of hood resistivi-ty, wherein said four electrodes are spaced with respect to one another in a line along the end of the -tip of said catheter, and wherein -the outer two of said electrodes are connected with said constant-current source and the inner two of said electrodes are connected with said first amplifying means.
The accompanying drawings illustrate a complete embodiment of the invention according -to -the best mode so far devised for the practical application of the principles thereof, and in which:
Figure 1 is a partial perspective view illustrating one typical positioning of a tetrapolar conductivity cell at the tip of a catheter;
-2b~
FIG. 2 is a front view illustrating the arrangement for the tip of the catheter shown in FIG. 1:
FIG. 3 is a front view illustrating an alternate arrangement of the electrodes at the tip of a catheter:
FIG. 4 is a block and electrical schematic diagram of circuitry used in conjunction with the conductivity cell shown in YIP&. 1 to measure blood resistivity continuously and enable recording of the dilution curve:
FIG. 5 is a graph illustrating the relationship between puke and p the receptivity of dog blood, and wherein puke is the quantity used to calibrate the dilution curve;
FIG. 6 is a typical dilution curve corrected for recirculation and a sample calculation of cardiac output using p and pi to calculate the conductivity cell having a constant k:
FIG. 7 is a graph illustrating cardiac output in the dog determined with the catheter tip transducer in the pulmonary artery and value, or comparison, obtained with the direct Flak method; and FIG. 8 is a partial cut-away perspective view illustrating positioning of the device of this invention in the pulmonary artery.
I A sensing unit ~tetrapolar conductivity cell) 9, a shown in FOGGIER 1 and 2, it contained in a catheter 11. As shown, cell 9 preferably includes a plurality of four electrodes I 15, 16 and 17, preferably having insulation 19 there around, positioned at the end, or tip, 21 of catheter 11. As shown, a pair ox lumen Z2 and 23 are alp provided, which lumens may be us Ed for measurement of blood prowar and injection of indicator as well a contrast imaging media, as well as for balloon inflation by means of a third lumen (not shown in FIGURES 1 and I FIGURE 3 illustrates a different and alternate afrangemen~ of electrode 14-17. electrodes 14-17 are useful for pacing and enabling pl~eement in a pulmonary .
artery by recording the COG (in addition to acting as a conductivity cell as described herein).
Each electrode (14-17~ can be of any convenient material, such as, for example, silver wire, with the end of catheter 11 being heat formed or cemented, so that the four wires (electrodes) are positioned side-by-side or spaced with respect to one another so that the electrodes measure blood resistivity in the axial direction (i.e., across the front of the catheter it Outer electrodes I and 17 are connected, as shown in FIGURE 4, to an isolated constant-current source 25 which provides the desired current (typically Lola, Luke) while the two inner electrodes 15 and 16 are connected to an isolated amplifier 29 for measurement of a potential which is linearly proportional to blood resistivity.
The output of amplifier 29 it connected through resistor 30 to amplifier 31, the output of which is coupled through diode 32 to a digital display (digital panel meter) 33 (and also fed back to the input wide of amplifier 31 through diode 34 and resistor 35 at one side of diode 32, and through resistor 36 at the other wide of diode I, 33 32). Display provides a direct reading of resistivity multiplied by the cell constant (K) of the catheter-tip conductivity cell 9.
The blood receptivity is obtained by dividing the conductivity cell constant (~) into this reading when the catheter it in place for recording the dilution curve.
The output of amplifier 29 it alto coupled through isolation circuit 41 and resistor 43 to amplifier 45, the output of which amplifier it coupled through diode 47 to amplifier 49 Rand is alto fed back to the input wide through resistor 51 and diode 53). In addition, the input of amplifier 95 is connected with ground through resistor So and parallel connected writer 57 and capacitor 59 The output from amplifier 49 ion lead SO) it an isolated analog q f-3~
output of blood receptivity the changes of which are the dilution curve.
Calibration of the apparatus is provided by resistors 61 and 62, which as indicated in YIGVRE 4, are connected into the circuit in lieu of the electrodes of the conductivity cell by changing the positioning of switch 63 from the OX position to the CAL position, and closing CAL witch 64.
It has been heretofore demonstrated (see Jades, I.. A., E.
Peony, and R. Steinberg, "Cardiac Output Using an Electrically Calibrated Flow-Through Conductivity Cell," Mourn. . Fishily.
37:97Z-977 (1974); Jades, LEA., C. P. deCosta, and L. E. Baker, "Electrical Calibration of the Saline Conductivity Method for Cardiac Output Preliminary Report," Cardiovasc. Rest Cur. Bull.
10:91-106 (1972), and Smith, M. X., L. I. Jades, and H. E. Roll, "Cardiac Output Determined by the Saline Conductivity method Using an Extra-Arterial Conductivity Call," Cardiovasc. Rest Cur. Bull.
5:123-13g (1967~) that cardiac output can be determined in an animal such a a dog by use ox an electrically calibrated flow-through conductivity cell placed in an arteriovenous shunt. The essential information required or electrical calibration was a knowledge of the packed-cell volume, the manner in which blood resistivity decreased with the addition of sodium chloride, and the constant of the conductivity cell used to detect the dilution curve.
It ha also been found that one of these requirements, namely the need to draw a blood sample to obtain it packed-cell volume can by eliminated because the resistivity of blood it dependent on its packed-cell volume (Lee Jades, L. A. and L. I. aquaria, Principles ox plied Biomedical Instrumentation (end eddy New York, Wiley In~ersciencQ 1975. foe pup Therefore the conductivity cell used to obtain the dilution curve can proYidQ Thea information, as well as serving to detect the dilution curve.
The use of electrical calibration is possible if the manner in which blood decreases its receptivity with added sodium chloride pi it known. This information has been heretofore reported for a variety of species (see Jades, L. A. and L. E. Baker, Principle of Applied Biomedical Linen Lowe (end Ed.) New York, Wiley Intrusions 1975. 616 pp.). Therefore, if the conductivity cell constant (K) is known, it is possible to insert a resistance change OR) into the resistivity- measuring circuit and equate the refastens change to a concentration change I a follows:
a I
K~p~aC) (1) where I is the concentration change equivalent to the resistance change OR: K it the conductivity cell constant and pi it the manner in which blood resistivity decreases with added sodium chloride.
puke is a fundamental property of blood and depends on packed-cell volume (Ho according to:
apace z where A and are constants and I is the packed-cell volume.
Values of A and a for a variety of animal species are shown. for example, yin, Jades, L . A. and I. E. Baker, lo of A
Biomedical Instrumentation (end eddy New York, Wiley Intrusions 1975. 616 pp.
However it is well known thaw the resisti~ity ox blood pi it a function of its packed-cell volume (H). Many die rent expressions hove been used, the simplest being:
p = eye I
:, where p is the resistivity of blood, H is the packed- cell volume and B and are constants, the values for which have been heretofore summarized (see Jades, LEA. and L. E. Baker, Principles of Applied Biomedical Incitory on anion (end Ed.) Jew York, Wiley Intrusions 1975. 616 pp.).
It is possible to eliminate HI from these two equations and obtain the following:
~/~
pi =
Therefore, by knowing the receptivity of the blood (p), a value for pi can be obtained. Note that a log-log plot of equation will be a straight line (see FIGURE 5).
Measured values for pi and p heretofore obtained (see Jades, L. A., E. Perry, and R. Steinberg, "Cardiac Output Using an Electrically Calibrated Flow-Through Conductivity Cell," Mourn.
Apply Filial 37:972-977 (1~74)) were plotted and a lo log least-squares representation was obtained (FIGURE 5) to provide the following fundamental electrical calibration relationship fur dog blood:
. hp~C = 1.86xlO (S) where pi is an ohm-cmJ~m per liter and p, the blood resistivity, it in ohm-cm. FIGURE 5 presents this relationship graphically for dog blood. A similar relationship exists for human blood.
The conductivity cell constant I is easily determined by measuring the receptivity so a known solution, e.g. I Maul. The resistivity of such a solution was measured with a platinum-black electrode connected Jo a conductivity bridge yellow Springs Instrument, Yellow Springs, OH.) Once the value for has been determined, it need not be remeasured. The value for K is therefore: K = R catheter/p pla~;num-black electrode, where R
catheter is the l OH resistance, and p is the resistivity of the known calibrate solution.
To test the device of this invention, ten dogs, ranging in weight from 13.5 to 32.5 kg were used. Pentobarbital sodium (30 mg/kg ivy.) way used and the trachea way incubated with a cuffed tube. Data were obtained with normal, elevated and reduced cardiac output. Cardiac output way raised with an ivy. drip of epinephrine and lowered by controlled hemorrhage.
Cardiac output was also measured by means of the known Flak method. For this method, the oxygen uptake was measured with an oxygen-filled Spiro meter containing a carbon-dioxide absorber. The pyrometry way connected to the tracheal tube by a one breathing valve. Oxygen uptake was msasllred for five minutes to obtain a stable value which was recorded on a strip chart recorder. Blood samples were taken from a femoral artery arterial ample and a catheter advanced to the apex of the right ventricle venous sample). The samples were analyzed for oxygen Canaan with the lox 02-Con (Lexington Instruments, Walt ham, My). Since this device provide data at SUP dry, the oxen uptake measured with the ~pirome~e~ way converted to SUP dry with the gay law. Cardiac output KIWI was calculated from the known equation:
CO oxygen uptake per min~A-V Oxygen difference (6 To inscribe the dilution curve, the tetrapolar cell 9 was advanced down the jugular vein into toe pulmonary artery. From the digital reading on the recording equi~m~nt, blood restive was calculated by dividing the cull constant into this reading. The a value of pi was then calculated utilizing the graph of FIGURE
5. The dilution curve was recorded by injecting a 2 ml of I saline into the right ventricle.
The dilution curve was calibrated in ohms by substituting a decade resistor for the tetrapolar conductivity cell, FIGURE 6 illustrates a typical dilution curve obtained by injecting 2 ml of 5% saline into the right atrium. The mean height (h) in ohms of the dilution curve is converted to mean concentration a follows:
lo C k(~pJ~C) (7) The dilution curves were digitized manually with a Gray Pen science Accessory Corps South port, ON) and entered into a PDP-ll/03 digital computer, programmed to perform a semi log extrapolation to correct the dilution curve for recirculation. The area, mean height and length of the dilution curve were read out and converted to mean concentration (by sealing a shown in FIGURE
6). Cardiac output way calculated from:
C0 = 60m~Ct I
where m is the number of grams of sodium chloride injected, C it the mean concentration and t it the duration of the corrected dilution curve in seconds. Although FIGURE 6 illustrate a dilution curve obtained by injecting saline Size., an indicator having a higher conductivity than blood), it it to be realized what other indicators can be utilized such a, for example, a I dextrose in water (DEW) (i.e., an indicator having a lower conductivity than blood.
FIGURE 7 prevents the r~lation6hip between cardiac output obtained with the electrically calibrated conductivity cell and the direct-Fi~k method. The dashed line reprint the equal-value line and the solid line it the linear regression line for all of the data point. It is clear that thy saline method provide slightly hiker I Jo values for cardiac output that are vary close to those obtained with the Flak method. For all paired data points, the average value of the saline method underestimated the cardiac output by one percent.
This invention can be utilized or hemodilutions by adding saline with a resistivity equal to that of plasma. Use of the apparatus shown in FIGURES 1, 2 and 4 for recording conductivity in the pulmonary artery is shown in FIGURE 8.
With respect to use as shown in FIGURE 8, only a single vessel term vein) 65 need be used to insert the apparatus Noah the pulmonary artery. Catheter 67 preferably includes a balloon 69 for flow guidance, a first lumen (generally indicated by the numeral 71) for balloon inflation, and a second lumen (generally indicated by the numeral 73) for injecting the indicator lay means of injecting fitting 75~ connected with an inlet port (not shown). In the preferred embodiment, a third lumen is also included for recording pressure; but such a pressure lumen is not necessary for catheter placement. The identification of the location of the catheter tip is made by remolding the electron cardiogram from the catheter electrode and an indifferent electrode placed at any convenient site on the subject. The electrode 14-17 positioned at the tip of toe catheter provide outputs (indicated by the numerals 14 17~ which are coupled to the circuitry as shown in FIGURE 2 for measuring the blood resisitivity and inscribing the dilution curve in the same manner all described hereinabove.
Prom the foregoing, it can be appreciatated thaw this invention provides an apparatus and method for use of an indicator such all saline and a detector such as a catheter conductivity cell that does not require withdrawal of blood to make calibration solution for the detector or to measure packed-cell volume to determine a value of pi the manner in which blood resistive decreases with the addition of the indicator, and does not require that the conductivity cell be kept warm since it is inside the body.
Multiple dilution curves can therefore be recorded every few minute if desired without blood loss and electrical calibration of the dilution curve can be achieved without the need for preparing calibrating samples.
It is often necessary, or at least desirable, that car-dice output be monitored or measured. While apparatus and methods have been heretofore suggested and/or utilized to accomplish this end, such apparatus and/or methods have not been completely satisfactory and have required, for example, mixing of calibrating solutions, withdrawal of blood and/or special preparation of the indicator (such as cooling), which has limited the usefulness of such methods and/or resulting apparatus.
In addition, while dilute saline has heretofore been utilized for the measurement of cardiac output (see, for example, Steward, G. N. "Researches on the Circulation and on the Influences Which Affect It" Mourn. Phsyiol. 22:159-183 (1897) and Stewart. "The Output of the Heart in Dots" Amer. Mourn.
Fishily. 57:27-50 (1921)), it is now seldom used even though use of such an indicator has attractive features including low cost, low toxicity and enables the use of a simple and inexpensive detector, namely a conductivity cell. This invention provides an improved apparatus and method for monitoring and/or measuring cardiac output. A saline indicator and a conductivity cell postponed at the tip of a catheter provides an economical yet efficient and dependable apparatus which enables measurement of blood resistivity without the necessity of blood withdrawal or the preparation of calibrating solutions; said blood resistivity measurement being then utilized for providing the means for calibrating and determining cardiac output.
I l2ll-73g It is therefore an object of -this invention -to pro-vise an improved apparatus for measurinc3 cardiac output.
It is another object of this invention to provide an improved apparatus for measurincJ cardiac output that does not require blood withdrawal or special preparation of calibrating or indicator solutions.
It is still another object of -this invention to provide an improved apparatus for measuring cardiac output utilizing an indicator, such as a saline indicator or a poorly conductive indicator such as a I dextrose in water Do and a conductivity cell.
It is yet another object of this invention to provide an improved apparatus for measuring cardiac output includinc3 a saline indicator and a conductivity cell positioned at the tip of a catheter.
It is still another object of this invention to provide an improved apparatus for measurinc3 blood resistivity.
With these and other objects in view which will become apparent to one skilled in -the art as the description proceeds, this invention resides in the novel construction, combination, arrangement of parts and method substantially as hereinafter described, and more particularly defined by the appended claims, it being understood that such chancres in the precise embodiment of the hereinclisclosed invention are meant to be included as come within the scope of the claims.
In accordance with a broad aspect of the invention there is provided an apparatus for enabling measurement of cardiac output by determination of blood resistivity, said apparatus comprising:
detector means for detecting resistivity;
I
positioning means for adapting said detector means to be positioned in the flow path of blood;
electrical means connected with said detector means for generating an output that is proportional to the resistivity owe the blood in said flow path, said electrical moans including means for generating an output indicative of baseline blood resistivity, and calibration means for electrically calibrating said apparatus, said calibration means including baseline calibration means for calibrating said output indicative of baseline blood resistivity.
In accordance with another broad aspect of the invention there is provided an apparatus for enabling measure-mint of cardiac output by determination of blood resistivity, said apparatus comprising:
a tetrapolar conductivity cell having four electrodes a catheter having said conductivity cell positioned on the tip thereof, said catheter briny adapted for insertion into a body so that said conductivity cell is in the flow path of blood in said body;
a constant-curren~ source connected with two of said electrodes of sand conductivity cell;
first amplifying means connected with the other two of said electrodes of said conductivity cell for amplifying a potential appearing on said electrodes;
indicating means connected with said first amplifying means for indicating resistivity;
isolation means connected with sail first amplifying means for providing signal isolation and -pa-second amplifying means connected with said isolation means and providing an isolated analog output of blood resistivity for enabling inscribing of the dilution curve of hood resistivi-ty, wherein said four electrodes are spaced with respect to one another in a line along the end of the -tip of said catheter, and wherein -the outer two of said electrodes are connected with said constant-current source and the inner two of said electrodes are connected with said first amplifying means.
The accompanying drawings illustrate a complete embodiment of the invention according -to -the best mode so far devised for the practical application of the principles thereof, and in which:
Figure 1 is a partial perspective view illustrating one typical positioning of a tetrapolar conductivity cell at the tip of a catheter;
-2b~
FIG. 2 is a front view illustrating the arrangement for the tip of the catheter shown in FIG. 1:
FIG. 3 is a front view illustrating an alternate arrangement of the electrodes at the tip of a catheter:
FIG. 4 is a block and electrical schematic diagram of circuitry used in conjunction with the conductivity cell shown in YIP&. 1 to measure blood resistivity continuously and enable recording of the dilution curve:
FIG. 5 is a graph illustrating the relationship between puke and p the receptivity of dog blood, and wherein puke is the quantity used to calibrate the dilution curve;
FIG. 6 is a typical dilution curve corrected for recirculation and a sample calculation of cardiac output using p and pi to calculate the conductivity cell having a constant k:
FIG. 7 is a graph illustrating cardiac output in the dog determined with the catheter tip transducer in the pulmonary artery and value, or comparison, obtained with the direct Flak method; and FIG. 8 is a partial cut-away perspective view illustrating positioning of the device of this invention in the pulmonary artery.
I A sensing unit ~tetrapolar conductivity cell) 9, a shown in FOGGIER 1 and 2, it contained in a catheter 11. As shown, cell 9 preferably includes a plurality of four electrodes I 15, 16 and 17, preferably having insulation 19 there around, positioned at the end, or tip, 21 of catheter 11. As shown, a pair ox lumen Z2 and 23 are alp provided, which lumens may be us Ed for measurement of blood prowar and injection of indicator as well a contrast imaging media, as well as for balloon inflation by means of a third lumen (not shown in FIGURES 1 and I FIGURE 3 illustrates a different and alternate afrangemen~ of electrode 14-17. electrodes 14-17 are useful for pacing and enabling pl~eement in a pulmonary .
artery by recording the COG (in addition to acting as a conductivity cell as described herein).
Each electrode (14-17~ can be of any convenient material, such as, for example, silver wire, with the end of catheter 11 being heat formed or cemented, so that the four wires (electrodes) are positioned side-by-side or spaced with respect to one another so that the electrodes measure blood resistivity in the axial direction (i.e., across the front of the catheter it Outer electrodes I and 17 are connected, as shown in FIGURE 4, to an isolated constant-current source 25 which provides the desired current (typically Lola, Luke) while the two inner electrodes 15 and 16 are connected to an isolated amplifier 29 for measurement of a potential which is linearly proportional to blood resistivity.
The output of amplifier 29 it connected through resistor 30 to amplifier 31, the output of which is coupled through diode 32 to a digital display (digital panel meter) 33 (and also fed back to the input wide of amplifier 31 through diode 34 and resistor 35 at one side of diode 32, and through resistor 36 at the other wide of diode I, 33 32). Display provides a direct reading of resistivity multiplied by the cell constant (K) of the catheter-tip conductivity cell 9.
The blood receptivity is obtained by dividing the conductivity cell constant (~) into this reading when the catheter it in place for recording the dilution curve.
The output of amplifier 29 it alto coupled through isolation circuit 41 and resistor 43 to amplifier 45, the output of which amplifier it coupled through diode 47 to amplifier 49 Rand is alto fed back to the input wide through resistor 51 and diode 53). In addition, the input of amplifier 95 is connected with ground through resistor So and parallel connected writer 57 and capacitor 59 The output from amplifier 49 ion lead SO) it an isolated analog q f-3~
output of blood receptivity the changes of which are the dilution curve.
Calibration of the apparatus is provided by resistors 61 and 62, which as indicated in YIGVRE 4, are connected into the circuit in lieu of the electrodes of the conductivity cell by changing the positioning of switch 63 from the OX position to the CAL position, and closing CAL witch 64.
It has been heretofore demonstrated (see Jades, I.. A., E.
Peony, and R. Steinberg, "Cardiac Output Using an Electrically Calibrated Flow-Through Conductivity Cell," Mourn. . Fishily.
37:97Z-977 (1974); Jades, LEA., C. P. deCosta, and L. E. Baker, "Electrical Calibration of the Saline Conductivity Method for Cardiac Output Preliminary Report," Cardiovasc. Rest Cur. Bull.
10:91-106 (1972), and Smith, M. X., L. I. Jades, and H. E. Roll, "Cardiac Output Determined by the Saline Conductivity method Using an Extra-Arterial Conductivity Call," Cardiovasc. Rest Cur. Bull.
5:123-13g (1967~) that cardiac output can be determined in an animal such a a dog by use ox an electrically calibrated flow-through conductivity cell placed in an arteriovenous shunt. The essential information required or electrical calibration was a knowledge of the packed-cell volume, the manner in which blood resistivity decreased with the addition of sodium chloride, and the constant of the conductivity cell used to detect the dilution curve.
It ha also been found that one of these requirements, namely the need to draw a blood sample to obtain it packed-cell volume can by eliminated because the resistivity of blood it dependent on its packed-cell volume (Lee Jades, L. A. and L. I. aquaria, Principles ox plied Biomedical Instrumentation (end eddy New York, Wiley In~ersciencQ 1975. foe pup Therefore the conductivity cell used to obtain the dilution curve can proYidQ Thea information, as well as serving to detect the dilution curve.
The use of electrical calibration is possible if the manner in which blood decreases its receptivity with added sodium chloride pi it known. This information has been heretofore reported for a variety of species (see Jades, L. A. and L. E. Baker, Principle of Applied Biomedical Linen Lowe (end Ed.) New York, Wiley Intrusions 1975. 616 pp.). Therefore, if the conductivity cell constant (K) is known, it is possible to insert a resistance change OR) into the resistivity- measuring circuit and equate the refastens change to a concentration change I a follows:
a I
K~p~aC) (1) where I is the concentration change equivalent to the resistance change OR: K it the conductivity cell constant and pi it the manner in which blood resistivity decreases with added sodium chloride.
puke is a fundamental property of blood and depends on packed-cell volume (Ho according to:
apace z where A and are constants and I is the packed-cell volume.
Values of A and a for a variety of animal species are shown. for example, yin, Jades, L . A. and I. E. Baker, lo of A
Biomedical Instrumentation (end eddy New York, Wiley Intrusions 1975. 616 pp.
However it is well known thaw the resisti~ity ox blood pi it a function of its packed-cell volume (H). Many die rent expressions hove been used, the simplest being:
p = eye I
:, where p is the resistivity of blood, H is the packed- cell volume and B and are constants, the values for which have been heretofore summarized (see Jades, LEA. and L. E. Baker, Principles of Applied Biomedical Incitory on anion (end Ed.) Jew York, Wiley Intrusions 1975. 616 pp.).
It is possible to eliminate HI from these two equations and obtain the following:
~/~
pi =
Therefore, by knowing the receptivity of the blood (p), a value for pi can be obtained. Note that a log-log plot of equation will be a straight line (see FIGURE 5).
Measured values for pi and p heretofore obtained (see Jades, L. A., E. Perry, and R. Steinberg, "Cardiac Output Using an Electrically Calibrated Flow-Through Conductivity Cell," Mourn.
Apply Filial 37:972-977 (1~74)) were plotted and a lo log least-squares representation was obtained (FIGURE 5) to provide the following fundamental electrical calibration relationship fur dog blood:
. hp~C = 1.86xlO (S) where pi is an ohm-cmJ~m per liter and p, the blood resistivity, it in ohm-cm. FIGURE 5 presents this relationship graphically for dog blood. A similar relationship exists for human blood.
The conductivity cell constant I is easily determined by measuring the receptivity so a known solution, e.g. I Maul. The resistivity of such a solution was measured with a platinum-black electrode connected Jo a conductivity bridge yellow Springs Instrument, Yellow Springs, OH.) Once the value for has been determined, it need not be remeasured. The value for K is therefore: K = R catheter/p pla~;num-black electrode, where R
catheter is the l OH resistance, and p is the resistivity of the known calibrate solution.
To test the device of this invention, ten dogs, ranging in weight from 13.5 to 32.5 kg were used. Pentobarbital sodium (30 mg/kg ivy.) way used and the trachea way incubated with a cuffed tube. Data were obtained with normal, elevated and reduced cardiac output. Cardiac output way raised with an ivy. drip of epinephrine and lowered by controlled hemorrhage.
Cardiac output was also measured by means of the known Flak method. For this method, the oxygen uptake was measured with an oxygen-filled Spiro meter containing a carbon-dioxide absorber. The pyrometry way connected to the tracheal tube by a one breathing valve. Oxygen uptake was msasllred for five minutes to obtain a stable value which was recorded on a strip chart recorder. Blood samples were taken from a femoral artery arterial ample and a catheter advanced to the apex of the right ventricle venous sample). The samples were analyzed for oxygen Canaan with the lox 02-Con (Lexington Instruments, Walt ham, My). Since this device provide data at SUP dry, the oxen uptake measured with the ~pirome~e~ way converted to SUP dry with the gay law. Cardiac output KIWI was calculated from the known equation:
CO oxygen uptake per min~A-V Oxygen difference (6 To inscribe the dilution curve, the tetrapolar cell 9 was advanced down the jugular vein into toe pulmonary artery. From the digital reading on the recording equi~m~nt, blood restive was calculated by dividing the cull constant into this reading. The a value of pi was then calculated utilizing the graph of FIGURE
5. The dilution curve was recorded by injecting a 2 ml of I saline into the right ventricle.
The dilution curve was calibrated in ohms by substituting a decade resistor for the tetrapolar conductivity cell, FIGURE 6 illustrates a typical dilution curve obtained by injecting 2 ml of 5% saline into the right atrium. The mean height (h) in ohms of the dilution curve is converted to mean concentration a follows:
lo C k(~pJ~C) (7) The dilution curves were digitized manually with a Gray Pen science Accessory Corps South port, ON) and entered into a PDP-ll/03 digital computer, programmed to perform a semi log extrapolation to correct the dilution curve for recirculation. The area, mean height and length of the dilution curve were read out and converted to mean concentration (by sealing a shown in FIGURE
6). Cardiac output way calculated from:
C0 = 60m~Ct I
where m is the number of grams of sodium chloride injected, C it the mean concentration and t it the duration of the corrected dilution curve in seconds. Although FIGURE 6 illustrate a dilution curve obtained by injecting saline Size., an indicator having a higher conductivity than blood), it it to be realized what other indicators can be utilized such a, for example, a I dextrose in water (DEW) (i.e., an indicator having a lower conductivity than blood.
FIGURE 7 prevents the r~lation6hip between cardiac output obtained with the electrically calibrated conductivity cell and the direct-Fi~k method. The dashed line reprint the equal-value line and the solid line it the linear regression line for all of the data point. It is clear that thy saline method provide slightly hiker I Jo values for cardiac output that are vary close to those obtained with the Flak method. For all paired data points, the average value of the saline method underestimated the cardiac output by one percent.
This invention can be utilized or hemodilutions by adding saline with a resistivity equal to that of plasma. Use of the apparatus shown in FIGURES 1, 2 and 4 for recording conductivity in the pulmonary artery is shown in FIGURE 8.
With respect to use as shown in FIGURE 8, only a single vessel term vein) 65 need be used to insert the apparatus Noah the pulmonary artery. Catheter 67 preferably includes a balloon 69 for flow guidance, a first lumen (generally indicated by the numeral 71) for balloon inflation, and a second lumen (generally indicated by the numeral 73) for injecting the indicator lay means of injecting fitting 75~ connected with an inlet port (not shown). In the preferred embodiment, a third lumen is also included for recording pressure; but such a pressure lumen is not necessary for catheter placement. The identification of the location of the catheter tip is made by remolding the electron cardiogram from the catheter electrode and an indifferent electrode placed at any convenient site on the subject. The electrode 14-17 positioned at the tip of toe catheter provide outputs (indicated by the numerals 14 17~ which are coupled to the circuitry as shown in FIGURE 2 for measuring the blood resisitivity and inscribing the dilution curve in the same manner all described hereinabove.
Prom the foregoing, it can be appreciatated thaw this invention provides an apparatus and method for use of an indicator such all saline and a detector such as a catheter conductivity cell that does not require withdrawal of blood to make calibration solution for the detector or to measure packed-cell volume to determine a value of pi the manner in which blood resistive decreases with the addition of the indicator, and does not require that the conductivity cell be kept warm since it is inside the body.
Multiple dilution curves can therefore be recorded every few minute if desired without blood loss and electrical calibration of the dilution curve can be achieved without the need for preparing calibrating samples.
Claims (10)
PROPERTY OR PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:
1. An apparatus for enabling measurement of cardiac output by determination of blood resistivity, said apparatus comprising:
detector means for detecting resistivity;
positioning means for adapting said detector means to be positioned in the flow path of blood;
electrical means connected with said detector means for generating an output that is proportional to the resistivity of the blood in said flow path, said electrical means including means for generating an output indicative of baseline blood resistivity, and calibration means for electrically calibrating said apparatus, said calibration means including baseline calibration means for calibrating said output indicative of baseline blood resistivity.
detector means for detecting resistivity;
positioning means for adapting said detector means to be positioned in the flow path of blood;
electrical means connected with said detector means for generating an output that is proportional to the resistivity of the blood in said flow path, said electrical means including means for generating an output indicative of baseline blood resistivity, and calibration means for electrically calibrating said apparatus, said calibration means including baseline calibration means for calibrating said output indicative of baseline blood resistivity.
2. The apparatus of Claim 1 wherein said apparatus includes indicating means for receiving said output from said electrical means and indicating said blood resistivity.
3. The apparatus of Claim 2 wherein said indicating means includes a digital readout device.
4. The apparatus of Claim 2 wherein said indicating means includes means for enabling inscribing of a dilution curve.
5. The apparatus of Claim 1 wherein said detector means is a conductivity cell having a plurality of electrodes, and wherein said positioning means includes a catheter having said conductivity cell positioned at the tip thereof and means for preventing said electrodes from contacting a wall defining the flow path of blood.
6. The apparatus of Claim 5 wherein said conductivity cell is a tetrapolar conductivity cell.
7. The apparatus of Claim 6 wherein said tetrapolar conductivity cell includes a pair of exciting electrodes an a pair of output electrodes, and wherein said electrical means includes a constant-current source connected with said exciting electrodes.
8. The apparatus of Claim 5 wherein said conductivity cell has four electrodes arranged along said tip of said catheter in a plane perpendicular to the longitudinal axis of said catheter.
9. The apparatus of Claim 5 wherein said catheter is adapted for insertion in a blood vessel, has an inflatable balloon therein, and at least a first lumen for inflation of said balloon and a second lumen for injecting indicator.
10. An apparatus for enabling measurement of cardiac output by determination of blood resistivity, said apparatus comprising:
a tetrapolar conductivity cell having four electrodes;
a catheter having said conductivity cell positioned on the tip thereof, said catheter being adapted for insertion into a body so that said conductivity cell is in the flow path of blood in said body;
a constant-current source connected with two of said electrodes of said conductivity cell;
first amplifying means connected with the other two of said electrodes of said conductivity cell for amplifying a potential appearing on said electrodes;
indicating means connected with said first amplifying means for indicating resistivity;
isolation means connected with said first amplifying means for providing signal isolation; and second amplifying means connected with said isolation means and providing an isolated analog output of blood resistivity for enabling inscribing of the dilution curve of blood resistivity, wherein said four electrodes are spaced with respect to one another in a line along the end of the tip of said catheter, and wherein the outer two of said electrodes are connected with said constant-current source and the inner two of said electrodes ore connected with said first amplifying means.
a tetrapolar conductivity cell having four electrodes;
a catheter having said conductivity cell positioned on the tip thereof, said catheter being adapted for insertion into a body so that said conductivity cell is in the flow path of blood in said body;
a constant-current source connected with two of said electrodes of said conductivity cell;
first amplifying means connected with the other two of said electrodes of said conductivity cell for amplifying a potential appearing on said electrodes;
indicating means connected with said first amplifying means for indicating resistivity;
isolation means connected with said first amplifying means for providing signal isolation; and second amplifying means connected with said isolation means and providing an isolated analog output of blood resistivity for enabling inscribing of the dilution curve of blood resistivity, wherein said four electrodes are spaced with respect to one another in a line along the end of the tip of said catheter, and wherein the outer two of said electrodes are connected with said constant-current source and the inner two of said electrodes ore connected with said first amplifying means.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US370,568 | 1982-04-21 | ||
| US06/370,568 US4572206A (en) | 1982-04-21 | 1982-04-21 | Method and apparatus for measuring cardiac output |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1226906A true CA1226906A (en) | 1987-09-15 |
Family
ID=23460230
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000426283A Expired CA1226906A (en) | 1982-04-21 | 1983-04-20 | Method and apparatus for measuring cardiac output |
Country Status (5)
| Country | Link |
|---|---|
| US (1) | US4572206A (en) |
| EP (1) | EP0092438A3 (en) |
| JP (1) | JPS5944A (en) |
| AU (1) | AU549880B2 (en) |
| CA (1) | CA1226906A (en) |
Families Citing this family (65)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4485200A (en) * | 1982-02-03 | 1984-11-27 | National Starch And Chemical Corporation | Neoprene latex contact adhesives |
| US4745928A (en) * | 1984-01-13 | 1988-05-24 | American Hospital Supply Corporation | Right heart ejection fraction and cardiac output catheter |
| US4513706A (en) * | 1984-07-26 | 1985-04-30 | Atzet Jon E | Anti-dieseling device for demand carburetors |
| US4739771A (en) * | 1986-02-20 | 1988-04-26 | Kim Manwaring | Thermal method and apparatus for measuring organ blood perfusion |
| US4721115A (en) * | 1986-02-27 | 1988-01-26 | Cardiac Pacemakers, Inc. | Diagnostic catheter for monitoring cardiac output |
| JPS62207435A (en) * | 1986-03-07 | 1987-09-11 | テルモ株式会社 | Catheter for measuring cardiac output |
| EP0374248B1 (en) * | 1987-03-05 | 1995-05-17 | Terumo Kabushiki Kaisha | Apparatus for measuring cardiac output |
| JPS6470024A (en) * | 1987-03-05 | 1989-03-15 | Terumo Corp | Cardiac output measuring apparatus equipped with automatic starting function of measurement |
| US5000190A (en) * | 1988-06-22 | 1991-03-19 | The Cleveland Clinic Foundation | Continuous cardiac output by impedance measurements in the heart |
| US4898176A (en) * | 1988-06-22 | 1990-02-06 | The Cleveland Clinic Foundation | Continuous cardiac output by impedance measurements in the heart |
| JPH02128753A (en) * | 1988-11-09 | 1990-05-17 | Terumo Corp | Apparatus for measuring cardiac output |
| JPH02185232A (en) * | 1989-01-13 | 1990-07-19 | Terumo Corp | Bio-information measuring device |
| US4899759A (en) * | 1989-01-17 | 1990-02-13 | Cardiac Pacemakers, Inc. | Flow-through resistivity cell |
| JP2866132B2 (en) * | 1990-01-29 | 1999-03-08 | テルモ株式会社 | Flow sensor probe |
| US5092339A (en) * | 1990-07-23 | 1992-03-03 | Geddes Leslie A | Method and apparatus for electrically compensated measurement of cardiac output |
| US5720293A (en) * | 1991-01-29 | 1998-02-24 | Baxter International Inc. | Diagnostic catheter with memory |
| US5553622A (en) * | 1991-01-29 | 1996-09-10 | Mckown; Russell C. | System and method for controlling the temperature of a catheter-mounted heater |
| US6387052B1 (en) | 1991-01-29 | 2002-05-14 | Edwards Lifesciences Corporation | Thermodilution catheter having a safe, flexible heating element |
| US5184621A (en) * | 1991-05-29 | 1993-02-09 | C. R. Bard, Inc. | Steerable guidewire having electrodes for measuring vessel cross-section and blood flow |
| US7189208B1 (en) * | 1992-09-23 | 2007-03-13 | Endocardial Solutions, Inc. | Method for measuring heart electrophysiology |
| US5553611A (en) * | 1994-01-06 | 1996-09-10 | Endocardial Solutions, Inc. | Endocardial measurement method |
| JP3581888B2 (en) * | 1992-09-23 | 2004-10-27 | エンドカーディアル・セラピューティクス・インコーポレーテッド | Endocardial mapping system |
| US7930012B2 (en) * | 1992-09-23 | 2011-04-19 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Chamber location method |
| USRE41334E1 (en) | 1992-09-23 | 2010-05-11 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Endocardial mapping system |
| US5390679A (en) * | 1993-06-03 | 1995-02-21 | Eli Lilly And Company | Continuous cardiac output derived from the arterial pressure waveform using pattern recognition |
| US5824029A (en) * | 1994-04-28 | 1998-10-20 | Medtronic, Inc. | Implantable medical system for performing transthoracic impedance measurements associated with cardiac function |
| US6149620A (en) | 1995-11-22 | 2000-11-21 | Arthrocare Corporation | System and methods for electrosurgical tissue treatment in the presence of electrically conductive fluid |
| US7572251B1 (en) | 1995-06-07 | 2009-08-11 | Arthrocare Corporation | Systems and methods for electrosurgical tissue treatment |
| US7186234B2 (en) * | 1995-11-22 | 2007-03-06 | Arthrocare Corporation | Electrosurgical apparatus and methods for treatment and removal of tissue |
| US5928155A (en) * | 1997-01-24 | 1999-07-27 | Cardiox Corporation | Cardiac output measurement with metabolizable analyte containing fluid |
| DE19728031A1 (en) * | 1997-07-01 | 1999-01-07 | Bernd Horst Dr Meier | Moving liquid flow and volume measuring method |
| EP1024769B1 (en) * | 1997-10-23 | 2009-02-25 | Arthrocare Corporation | Power supply for electrosurgery in conductive fluid |
| US6299583B1 (en) | 1998-03-17 | 2001-10-09 | Cardiox Corporation | Monitoring total circulating blood volume and cardiac output |
| US7263397B2 (en) | 1998-06-30 | 2007-08-28 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Method and apparatus for catheter navigation and location and mapping in the heart |
| US7670297B1 (en) | 1998-06-30 | 2010-03-02 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Chamber mapping system |
| US7806829B2 (en) * | 1998-06-30 | 2010-10-05 | St. Jude Medical, Atrial Fibrillation Division, Inc. | System and method for navigating an ultrasound catheter to image a beating heart |
| US6986744B1 (en) | 1999-02-02 | 2006-01-17 | Transonic Systems, Inc. | Method and apparatus for determining blood flow during a vascular corrective procedure |
| NL1016122C2 (en) * | 2000-09-07 | 2002-03-11 | Jozef Reinier Cornelis Jansen | Method and device for determining the segmental volume and the electrical parallel conduction of a heart chamber or blood vessel of a patient, as well as a catheter for use in this method or device. |
| ES2186566B1 (en) * | 2001-09-25 | 2004-03-01 | Univ Jaen | INTRAVENOUS BIOSENSOR FOR THE MEASUREMENT OF BLOOD CONDUCTIVITY |
| US7096059B2 (en) * | 2002-07-03 | 2006-08-22 | Bioanalytical Systems, Inc. | Device and method for electrocardiography on freely moving animals |
| US7297143B2 (en) * | 2003-02-05 | 2007-11-20 | Arthrocare Corporation | Temperature indicating electrosurgical apparatus and methods |
| EP1651127B1 (en) * | 2003-07-16 | 2012-10-31 | Arthrocare Corporation | Rotary electrosurgical apparatus |
| US7632267B2 (en) * | 2005-07-06 | 2009-12-15 | Arthrocare Corporation | Fuse-electrode electrosurgical apparatus |
| US20070106288A1 (en) * | 2005-11-09 | 2007-05-10 | Arthrocare Corporation | Electrosurgical apparatus with fluid flow regulator |
| US8876746B2 (en) * | 2006-01-06 | 2014-11-04 | Arthrocare Corporation | Electrosurgical system and method for treating chronic wound tissue |
| US7691101B2 (en) | 2006-01-06 | 2010-04-06 | Arthrocare Corporation | Electrosurgical method and system for treating foot ulcer |
| US20070161981A1 (en) * | 2006-01-06 | 2007-07-12 | Arthrocare Corporation | Electrosurgical method and systems for treating glaucoma |
| EP2020943B1 (en) | 2006-05-30 | 2015-07-08 | ArthroCare Corporation | Hard tissue ablation system |
| US8192424B2 (en) | 2007-01-05 | 2012-06-05 | Arthrocare Corporation | Electrosurgical system with suction control apparatus, system and method |
| US7862560B2 (en) * | 2007-03-23 | 2011-01-04 | Arthrocare Corporation | Ablation apparatus having reduced nerve stimulation and related methods |
| US9358063B2 (en) * | 2008-02-14 | 2016-06-07 | Arthrocare Corporation | Ablation performance indicator for electrosurgical devices |
| US20100152726A1 (en) * | 2008-12-16 | 2010-06-17 | Arthrocare Corporation | Electrosurgical system with selective control of active and return electrodes |
| US8574187B2 (en) | 2009-03-09 | 2013-11-05 | Arthrocare Corporation | System and method of an electrosurgical controller with output RF energy control |
| US8257350B2 (en) | 2009-06-17 | 2012-09-04 | Arthrocare Corporation | Method and system of an electrosurgical controller with wave-shaping |
| US8372067B2 (en) | 2009-12-09 | 2013-02-12 | Arthrocare Corporation | Electrosurgery irrigation primer systems and methods |
| US8747399B2 (en) | 2010-04-06 | 2014-06-10 | Arthrocare Corporation | Method and system of reduction of low frequency muscle stimulation during electrosurgical procedures |
| USD658760S1 (en) | 2010-10-15 | 2012-05-01 | Arthrocare Corporation | Wound care electrosurgical wand |
| US8685018B2 (en) | 2010-10-15 | 2014-04-01 | Arthrocare Corporation | Electrosurgical wand and related method and system |
| US8568405B2 (en) | 2010-10-15 | 2013-10-29 | Arthrocare Corporation | Electrosurgical wand and related method and system |
| US9131597B2 (en) | 2011-02-02 | 2015-09-08 | Arthrocare Corporation | Electrosurgical system and method for treating hard body tissue |
| US9713489B2 (en) | 2013-03-07 | 2017-07-25 | Arthrocare Corporation | Electrosurgical methods and systems |
| US9693818B2 (en) | 2013-03-07 | 2017-07-04 | Arthrocare Corporation | Methods and systems related to electrosurgical wands |
| US9801678B2 (en) | 2013-03-13 | 2017-10-31 | Arthrocare Corporation | Method and system of controlling conductive fluid flow during an electrosurgical procedure |
| CN109310338B (en) | 2016-06-29 | 2021-11-19 | 皮科洛医疗公司 | Device and method for vessel navigation, evaluation and/or diagnosis |
| WO2019046769A1 (en) * | 2017-08-31 | 2019-03-07 | Piccolo Medical, Inc. | Devices and methods for vascular navigation, assessment and/or diagnosis |
Family Cites Families (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3290589A (en) * | 1965-06-07 | 1966-12-06 | Lafayette R Hubbard | Device for measuring and indicating changes in resistance of a living body |
| US3689393A (en) * | 1969-10-20 | 1972-09-05 | Merlin Davis | Blood diagnostic instruments |
| DE2302156A1 (en) * | 1973-01-17 | 1974-07-18 | Guenter Dr Hennersdorf | CATHETER TO DETERMINE THE VOLUME OF THE HUMAN HEART |
| US3930493A (en) * | 1974-01-23 | 1976-01-06 | Cordis Corporation | Intravascular liquid velocity sensing method using a polarographic electrode |
| US4015593A (en) * | 1975-03-24 | 1977-04-05 | Elings Virgil B | Apparatus and method for measuring cardiac output |
| US3985123A (en) * | 1975-07-17 | 1976-10-12 | Avco Everett Research Laboratory, Inc. | Method and means for monitoring cardiac output |
| US4175566A (en) * | 1975-08-07 | 1979-11-27 | Millar Instruments, Inc. | Catheter fluid-velocity flow probe |
| DE2819128A1 (en) * | 1978-04-29 | 1979-11-08 | Raben Ralph Holger Dr | Blood flow determination process through vessels - adds fluid altering electrical conductivity and measures conductivity using HF |
| GB2041761B (en) * | 1978-09-06 | 1983-06-15 | American Hospital Supply Corp | Apparatus and method for measuring extravascular lung water |
| US4380237A (en) * | 1979-12-03 | 1983-04-19 | Massachusetts General Hospital | Apparatus for making cardiac output conductivity measurements |
| FR2485364A1 (en) * | 1980-06-25 | 1981-12-31 | Commissariat Energie Atomique | Skin conductivity measuring circuit - comprises wheatstone bridge with low voltage DC supply, digital meter and can be incorporated in bracelet |
| JPS5757495A (en) * | 1980-09-22 | 1982-04-06 | Matsushita Electric Ind Co Ltd | High frequency heater |
-
1982
- 1982-04-21 US US06/370,568 patent/US4572206A/en not_active Expired - Lifetime
-
1983
- 1983-04-08 AU AU13260/83A patent/AU549880B2/en not_active Ceased
- 1983-04-20 CA CA000426283A patent/CA1226906A/en not_active Expired
- 1983-04-20 JP JP58069858A patent/JPS5944A/en active Pending
- 1983-04-20 EP EP83302246A patent/EP0092438A3/en not_active Withdrawn
Also Published As
| Publication number | Publication date |
|---|---|
| US4572206A (en) | 1986-02-25 |
| JPS5944A (en) | 1984-01-05 |
| US4572206B1 (en) | 1991-01-01 |
| AU1326083A (en) | 1983-10-27 |
| EP0092438A2 (en) | 1983-10-26 |
| EP0092438A3 (en) | 1986-01-22 |
| AU549880B2 (en) | 1986-02-20 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA1226906A (en) | Method and apparatus for measuring cardiac output | |
| US5092339A (en) | Method and apparatus for electrically compensated measurement of cardiac output | |
| US20200245882A1 (en) | Probe data mapping using contact information | |
| US4380237A (en) | Apparatus for making cardiac output conductivity measurements | |
| US5425361A (en) | Apparatus for the determination of medical, electro-chemical measured values relevant to organic or metabolic functions | |
| US5022396A (en) | Catheter for simultaneously measuring monophasic action potential and endocardiac cavity pressure | |
| US9173586B2 (en) | System and method for assessing coupling between an electrode and tissue | |
| US4836214A (en) | Esophageal electrode array for electrical bioimpedance measurement | |
| EP0132344A2 (en) | Improved catheter based cardiac output sensor | |
| US9974608B2 (en) | Determining absence of contact for a catheter | |
| WO2002081022B1 (en) | System and method for detecting dislodgement of an implantable medical device | |
| GB2187100A (en) | Diagnostic catheter for monitoring cardiac output | |
| US5271398A (en) | Intra-vessel measurement of blood parameters | |
| Hyman et al. | Hydrogen-platinum electrode system in detection of intravascular shunts | |
| US4296754A (en) | Method for determining the value of cardiologic quantities and apparatus for performing said method | |
| Bond et al. | Evaluation of an electromagnetic catheter tip velocity-sensitive blood flow probe. | |
| GB2100864A (en) | Investigating substances in bloodstream and detecting blood flow | |
| Geddes et al. | Cardiac output using an electrically calibrated flow-through conductivity cell. | |
| US3773037A (en) | Simplified external field electromagnetic catheter flow meter | |
| Vliers et al. | Choice of detection site for the determination of cardiac output by thermal dilution: the injection-thermistor-catheter | |
| GB2123965A (en) | A cannular sensor and a method of measuring polarographic PO2 using the sensor | |
| Rothe et al. | Continuous measurement of conductivity of biological fluids. | |
| McNamee et al. | Peribronchial electrical admittance measures lung edema and congestion in the dog | |
| Grubbs et al. | A new technique for obtaining values of cardiac output in rapid succession | |
| JPH0432968B2 (en) |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| MKEX | Expiry |