Triggered flow measurement

Abstract: The invention relates to a method of triggering a time measurement in a system for the measurement of a transit time of a finite amount of an indicator first liquid, injected in a flow of a second liquid in the course of a thermo-dilution measurement. The flow of liquid has a temperature that is different from the temperature of said indicator liquid. The system has a temperature sensitive part. It comprises recording a change in a system variable caused by exposure of said temperature sensitive part of said system to said indicator first liquid; and using the recorded change to determine a starting point for time measurement.

Description: The present invention relates to measurement of flow in blood vessel by thermo-dilution. In particular it relates to an improved apparatus for triggering such measurement in order to improve the measurements. Background of the Invention Devices and methods of flow measurements are disclosed in US serial No. 09/073,061, 09/117,416, all assigned to Radi Medical Systems AB, Sweden. In particular 09/073,061 relates to a method of flow measurements by thermo-dilution, wherein the time measurements are triggered by a pressure pulse detected as a result of the injection of a bolus dose of saline. The general theory described therein fully applies to the present invention. Nevertheless, the discussion therein is repeated below for ease of understanding. Application of the thermodilution principle in the coronary sinus was introduced by Ganz (Ganz et al, "Measurement of coronary sinus blood flow by continuous thermodilution in man, Circulation 44:181-195, 1971). A small catheter is introduced deeply into the coronary sinus and cold saline is delivered at its tip. Theoretically, flow can be calculated from the changes in blood temperature, registered by a thermistor close to the outlet of the coronary sinus. An advantage of this method is that only right heart catheterization is required. The principle of thermo-dilution involves injecting a known amount of cooled liquid, e.g. physiological saline in a blood vessel. After injection the temperature is continuously recorded with a temperature sensor attached to the tip of a guide wire that is inserted in the vessel. A temperature change due to the cold liquid passing the measurement site, i.e. the location of the sensor, will be a function of the flow. There are various methods of evaluating the temperature signal for diagnostic purposes. Either one may attempt to calculate the volume flow, or one may use a relative measure, where the flow in a "rest condition" is compared with a "work condition", induced by medicaments. The latter is the simpler way, and may be carried out by measuring the width at half height of the temperature change profile in the two situations indicated, and forming a ratio between these quantities. Another way of obtaining a ratio would be to measure the transit time from injection and until the cold liquid passes the sensor, in rest condition and in work condition respectively. The former method, i.e. the utilization of the volume flow parameter as such, requires integration of the temperature profile over time in accordance with the equations given below wherein V is the volume of injected liquid T r,m is the measured temperature at rest condition T r,l is the temperature of injected liquid at rest condition T 0 is the temperature of the blood, i.e. 37°C T w,m is the measured temperature at work condition T w,l is the temperature of injected liquid at work condition Q is the volume flow These quantities may than be used directly for assessment of the condition of the coronary vessels and the myocardium of the patient, or they may be ratioed as previously to obtain a CFR, i.e. CFR = Q work /Q rest The latter method, i.e. determination of the transit time requires an accurate time measurement, in view of the relatively small distances in question, about 10 cm or less from injection to measurement site. E.g. in order to obtain a correct measurement, the time has to be measured with some accuracy. Using a simple stop watch, which is a common means of timing, is far too inaccurate for obtaining reliable transit times. The flow F may be obtained as follows, which is a derivation for a similar technique, namely the indicator dilution technique. This is based on a rapidly injected amount of some kind of indicator, the concentration of which is measured. Suppose that the flow through a branching vascular bed is constant and equals F, and that a certain well-known amount M of indicator is injected into this bed at site A (se Fig. 7). After some time, the first particles of indicator will arrive at the measuring site B. The concentration of indicator at B, called c(t), will increase for some time, reach a peak and decrease again. The graphic representation of indicator concentration as a fucntion of time is called the indicator dilution curve. Consider M as a large number of indicator particles (or molecules). The number of particles passing at B during the time interval Δt, teween t i and t i+1 , equals the number of particles per unit time multiplied by the length f the time interval, in other words: c(t i ) · F · Δt (Fig. 8). Because all particles pass at B between t = 0 and t = ∞, this means that: or and it is the last expression which is used in most methods to calculate systemic flow as outlined above. Essential features of this approach is that the amount M of injected indicator should be known whereas no knowledge about the volume of the vascular compartment is needed. The calculation of volume is more complex. For this purpose, the function h(t) is introduced which is the fraction of indicator, passing per unit of time at a measurement site at time t. In other words, h(t) is the distribution function of transit times of the indicator particles. If it is assumed that that flow of the indicator is representative for flow of the total fluid (complete mixing), h(t) is also the distribution function of transit times of all fluid particles. Suppose the total volume of fluid is made up of a very large number of volume elements dV i which are defined in such a way that dV i contains all fluid particles present in the system at t=0, with transit times between t i and t i+1 . The fraction of fluid particles requiring times between t i and t i+1 to pass the measurement site, is h(t i ) Δt by definition, and because the rate at which the fluid particles pass at the measurement site, equals F, the rate at which the particles making up dV i pass at the measurement site is F · h(t i ) · Δt. The total volume of dV i equals the time t i , required for all particles segments in dV i to pass at the measurement site multiplied by the rate at which they leave. In other words: dV i = t i · F · h(t i ) · Δt and by integration: The integral in the equation above represents the mean transit time T mn , which is the average time, needed by one particle to travel from an injection site to a measurement site. Therefore: V = F · T mn or: F = V/T mn ; T mn = V/F which states the fundamental fact that flow equals volume divided by mean transit time. The mean transit time (T mn ) can now be calculated easily from the indicator or thermo dilution curve in the following way. When looking at the hatched rectangle in Fig. 8, it can be seen that the number of indicator particles passing between t i and t i+1 , equals the number of particles c(t i ) · F passing per unit of time, multiplied by the length of the time interval, Δt, in other words: c(t i ) · F Δt. Therefore, the total (summed) transit time of all these indicator particles together equals t i · c(t i ) · F · Δt. The total transit time of all indicator particles together, by integration, is and the mean transit time of the indicator particles can be obtained by dividing equation 3.8 by the total number of particles M, resulting in: or By substitution of equation 3.3 in 3.10, T mn is obtained: Equation 3.11 describes how mean transit time T mn can be calculated from the indicator dilution curve c(t). Because in the assessment of myocardial perfusion, using contrast agent as the indicator, the amount of injected contrast agent is unknown and changing because of the necessary leakage of the contrast agent into the aorta and the unknown and changing distribution of contrast agent over the different branches of the coronary arterial tree, use of T mn is advantageous because no knowledge about the amount of injected indicator is necessary. Although the above derivation was made for the mentioned indicator dilution technique, the result is the same for thermo-dilution since the same distribution function may be employed, and the skilled man will easily adjust the equations accordingly. The prior art pressure pulse triggering of the time measurements, although improving the method considerably, has some drawbacks. I.a. the sensitivity in the pressure measurement may not be adequate, the magnitude of the pulse being quite low, and therefore the accuracy may be negatively influenced. A catheter as claimed is known from WO 01/52728 which is prior art under Art. 54(3) EPC. Summary of the Invention Thus, there is a need for an improved triggering of the measurement. The inventors have realized that a previous problem acknowledged in connection with thermo-dilution can be used to an advantage for triggering purposes. Namely, when a bolus does of cold saline is injected into a catheter where a wire carrying the sensor unit and electrical leads for signal transmission is located, the lead resistance will be instantly affected by the cold saline by a change in the resistivity. This is a problem in that the change must be compensated for in order to arrive at a correct output signal. However, this compensation can be done, and is one of the issues discussed in our pending Swedish application 9901962-2, corresponding to US provisional 60/136,401. Thus, in accordance with the present invention, the resistivity change is recorded as a resistance variation curve, and various parts of the recorded curve, or the entire curve, can be mathematically processed to give as a result a starting point for the determination for a transit time of the injected liquid. In this way the accuracy in the time measurement is significantly improved. The method of flow determination is advantageous in that it is independent of the injected amount of bolus liquid of temperature of the injected liquid, so long as detectable signals are obtained Brief Description of Drawings Fig. 1 is an overview that shows a system wherein the novel method is performed; Figs. 2a-c are graphs illustrating the resistivity profiles of the electrical leads during measurement; Fig. 3 is a graph showing measurements on a patient during hyperemia; Fig. 4 is a graph showing measurements on a patient during a resting period; Fig. 5 is a graph showing the correlation between measurement data on patients according to the invention and a reference method; Fig. 6 is a graph showing the correlation between another set of patient data according to the invention and a reference method; Fig. 7 illustrates an indicator dilution curve obtained in a vascular network; Fig. 8 illustrates calculation of flow in indicator dilution; and Fig. 9 illustrates the derivation of center of mass. Detailed Description of the Invention In fig. 1 there is disclosed a system suitable for implementation of the present invention. The system comprises a hollow guide catheter insertable into the body of a patient, the distal end of which functions as an outlet for liquid to be passed therethrough. The catheter is located at a point in region in the artery system where it is desired to know the flow. Inside the catheter a wire is inserted, the distal end of which carries a sensor unit having a temperature sensor and optionally a pressure sensor. Other additional sensors are also conceivable, e.g. pH sensors, ion selective sensors etc. The wire is extended past the distal end of the catheter such that the sensor unit is located at a relatively small distance, e.g. 10 cm, from the catheter outlet. Alternatively, the wire can be inserted as above and positioned in an appropriate position, and then a second catheter is passed over the wire, inside the guide catheter and the distal end of this second catheter is positioned in the artery system where it is desired to know the flow. The first catheter will thereby only be used for guiding. This alternative approach can be used if the vessel tree is fairly complex with many narrow blood vessels, such that it can be difficult to position a catheter without the help of the wire. The guide catheter (or the second catheter in the alternative) is provided at the proximal end with an inlet for saline. Suitably a Luer® lock is provided in order that a syringe easily be connected. The sensor unit is coupled to a control unit for the processing of the signals from the sensor unit, said signals being transferred via electrical leads running along the wire. The method will now be described in some detail with reference to the figures. When the above-mentioned catheter has been positioned appropriately, it will become filled with blood because of the prevailing pressure difference between the interior of the body and the ambient atmosphere. I.e. the pressure inside the vessel is slightly higher than the atmospheric pressure externally of the body, P body -P outside > 0. When the wire carrying the sensor has been inserted and the sensor appropriately located at the point of measurement, the operator fills a syringe with a suitable amount of cold saline, say 20°C. The volume to be expelled by the syringe is preferably equal to the volume inside the catheter from the inlet point up to the outlet plus the bolus-dose to be expelled into the flowing blood. The volume of a catheter is commonly about 3 ml, and a suitable bolus-dose could be e.g. 1-3 ml, although the exact volumes will of course differ from case to case. The sensor is connected via the electrical leads to a detection unit which has the capability of switching between measurement of cable resistance and detecting the signal from the sensor. The operator connects the syringe to the inlet port and begins injecting the cold saline at a relatively low rate, such that the time to fill the guide catheter all the way up to the outlet will typically take 1-15, preferably 10-15 seconds, although this can vary substantially from case to case outside this interval. The volume of the catheter is known and thus when the operator has expelled a volume corresponding to the catheter volume during the mentioned time period, he will more rapidly expel the last dose, say during 0,5 seconds, although this time is not strictly critical. The detection unit operates according to the method disclosed in the previously mentioned U.S. provisional 60/136,401. The compensation disclosed therein is based on a switching between measurements of the sensor signal and of the resistance of the leads so as to enable compensation of changes in lead resistance. Thus, when the operator begins injecting the cold saline of course the resistivity of the electrical leads will instantly be changed but this will be compensated for such that the detection unit will always deliver a readout of a constant temperature inside the blood vessel at the point of location of the sensor. For the purpose of the invention the change in resistance of the leads will not be recorded during the initial phase of filling the catheter with saline, but immediately prior to or at the same time as the operator injects the last bolus-dose into the catheter, the recording of lead signal will be initiated and monitored and also the sensor signal will be recorded and monitored simultaneously. Because of the rapid injection of the last volume segment of cold saline (at point t start in Fig. 2a; the bolus ends at t stop ), the cable resistivity will abruptly change since it will experience more cold liquid during a shorter period of time and this will be reflected in a drop in the readout signal as shown in figure 2a. The sensor being located at a relatively short distance from the catheter outlet, say approximately 10 cm, although this distance is not strictly critical, will be subjected to the cooler bolus-dose of saline a short period of time after it has been expelled from the outlet of the catheter, of the order of a fraction of a second up to a few seconds. A sensor signal is schematically shown in Fig. 2b, and this signal is recorded and used as the basis for determining the starting point of time measurement. If it can be assumed that the actual injection of the bolus-dose into the blood-flow will not affect the measurement of the flow at the measurement point, then a calculation as recited under the background of the invention can be performed on the basis of the sensor signal, i.e. by numeric integration, or by fitting the entire signal from the sensor element to a mathematical function, e.g. Log Normal, Gamma, and then use this function to calculate the point c in Fig. 2d, wherein c is the center of mass of the curve defined by the sensor signal. Also a combination of numeric integration and curve fitting can be used. In the latter case the curve fitting is performed at the portion of the curve approaching the base line, after the cut off point D (see Fig. 2c). However, of course also the starting point for the integration must be determined, e.g. t=0. This point in time can be determined in different ways, using the recorded resistance variation curve. One way is to register the onset of resistivity reduction. Here the derivative of the curve may be calculated, and if the derivative exceeds a preset value, time measurment is triggered. Another way is to use the peak value as a starting point for time measurement. Again the derivative, or preferably the second derivative, is calculated and the change in sign is detected. A further usable point is to take the average of the two values, e.g. (t start - stop )/2. In an alternative embodiment the same "triggering" of the time measurement can be used (by "triggering" we mean for the purposes of this invention, the determination of a starting point for the time measurement, or put in other words the determination of t=0 for the purpose of integration). In this alternative embodiment only the increasing part of the sensor signal (indicated with B' will be used). For this purpose the mentioned part B' of the sensor signal curve will entirely or partly be fitted to a mathematical function, e.g. e -t/τ , which is an exponential function. The simplest way of doing this is to take the logarithm of the measurement data at this part and to plot this against time. From the slope of the linear portion of that plot the time constant, τ of the exponential function can be determined. The point on said curve portion B' of Fig. 2b, corresponding to the point on the time axis at t min, sensor + τ will be center of mass of the exponential curve, which is the point up to which T mn will be calculated from t=0. Strictly mathematically, 0,7τ should be used for the identification of the center of mass, but for the purpose of this application the approximation to τ is adequate. τ can be calculated by fitting the sensor element signal from the point P s in Fig. 2c up to a point D, where D is the cut-off point, e.g. 10% of the peak value (at P s ). If we assume that t=0 is set to be equal to the point between t start and t stop , e.g. (t stop -t start )/2, then the total mean transit time T mn will be sum T mn = (t stop -t start )/2 + t min, sensor - t stop + τ The terms of this sum are illustrated in Fig. 2c as t 1 , t 2 and t 3 respectively, and thus T mn = t 1 + t 2 + t 3 wherein τ or 0.7τ can be used for t 3 , as indicated above. Of the above possible approaches to the determination of T mn , the method discussed in conection with Fi.g 2d is the most "correct" in a mathematical sense. However, the initial flank will very easily be affected by the injection, and the curve fitting may therefore be incorrect. The other method (Fig. 2c), where only the portion after the peak is fitted to a curve is more independent of the injection, because the injection stopped before any calculations are performed on the curve. In Fig. 3 and 4 respectively measurement data on a patient are shown for a hyperemic condition and a resting condition respectively. As can be clearly seen in these figures there is a difference in the time between the minimum of the cable signal and the minimum of the temperature sensor response signal for the two cases, where in the hyperemic state the distance is shorter i.e. the flow is higher, than in the resting condition. It is also clearly visible that the time constant for the increasing portion is slower for the resting condition than under hypermia. The CFR is calculated as CFR = T mn, rest /T mn, hyper Finally in figures 5 and 6 respectively the method according to the invention has been qualitativly evaluated against a reference method which is a determination of CFR by a doppler-technique. In this case however, it should be born in mind that also the doppler-technique has its limitations and is not entirely accurate. As disclosed previously in this application, CFR can be obtained by measuring the mean transit time, T mn for a bolus dose of cold liquid by employing the response curve from the lead resistance measurements and a temperature sensor respectively. For the calculation of T mn , the time constant τ of an exponential function e -t/τ is calculated. It is also discovered by the inventors that τ itself is correlated to the flow in a coronary vessel, and therefore τ itself can be used to determine a value of CFR, namely as CFR = τ rest / τ hyper where τ rest is the time constant of the temperature sensor response in a resting condiciton, and τ hyper is the time constant of the temperature sensor response in a hypereminc condition. Calculation of Center of Mass for a mono exponential curve. (See Fig. 9) In this case the center of mass is located at position x. The center of mass is found where area of A 1 = area of A 2 . and and A 1 = A 2 ⇒ -τ e -x/τ + τ = τ e -x/τ ⇒ 2 τ e -x/τ = τ ⇒ 2 e -x/τ = 1 ⇒ e -x/τ = 1/2 ⇒ -x/τ = ln(1/2) ⇒ x = -τ ln(1/2) ≅ 0.7τ

Claims: An apparatus for performing thermo-dilution measurements in blood vessels, comprising a hollow catheter insertable into the body of a patient, the distal end of which functions as an outlet for a liquid to be passed therethrough, at a point in a region in the artery system where it is desired to know the flow; a wire insertable into said catheter; a sensor unit having a temperature sensor and optionally a pressure sensor arranged at the distal end of said wire so as to be positionable beyond the distal catheter end, the sensor unit being couplable to a control unit by electrical leads running along said wire; said control unit being i) adapted for the processing of signals from the sensor unit, said control unit further having the capability of switching between measurement of cable resistance and detecting the signal from the sensor, and ii) being adapted for recording a resistance variation curve for said cable resistance, caused by exposure of said cable to said liquid, wherein said resistance variation curve is usable for calculating a starting point for time measurement. The apparatus as claimed in claim I, wherein said wire extends past the distal end of the catheter such that the sensor unit is located at a relatively small distance, e.g. 10 cm, from the catheter outlet; The apparatus as claimed in claim I, comprising further additional sensors, e.g. pH sensors, ion selective sensors.

Inventors: SMITH LEIF, TULKKI SAULI, SMITH, LEIF, TULKKI, SAULI
Applicants: RADI MEDICAL SYSTEMS, RADI MEDICAL SYSTEMS AB
Application year: 2001
Main classification: A61B5
IPC codes: A61B5, G01F1